US20070218097A1 - Subcutaneous Glucose Electrode - Google Patents

Subcutaneous Glucose Electrode Download PDF

Info

Publication number
US20070218097A1
US20070218097A1 US11/695,611 US69561107A US2007218097A1 US 20070218097 A1 US20070218097 A1 US 20070218097A1 US 69561107 A US69561107 A US 69561107A US 2007218097 A1 US2007218097 A1 US 2007218097A1
Authority
US
United States
Prior art keywords
electrode
glucose
layer
sensor
electrodes
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US11/695,611
Inventor
Adam Heller
Michael Pishklo
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Abbott Diabetes Care Inc
Original Assignee
Abbott Diabetes Care Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=23155192&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=US20070218097(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Priority claimed from US08/161,682 external-priority patent/US5356786A/en
Application filed by Abbott Diabetes Care Inc filed Critical Abbott Diabetes Care Inc
Priority to US11/695,611 priority Critical patent/US20070218097A1/en
Publication of US20070218097A1 publication Critical patent/US20070218097A1/en
Abandoned legal-status Critical Current

Links

Images

Classifications

    • CCHEMISTRY; METALLURGY
    • C12BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12QMEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
    • C12Q1/00Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/54Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions involving glucose or galactose
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/145Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/145Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1486Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/145Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1495Calibrating or testing of in-vivo probes
    • CCHEMISTRY; METALLURGY
    • C12BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12QMEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
    • C12Q1/00Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/001Enzyme electrodes
    • C12Q1/005Enzyme electrodes involving specific analytes or enzymes
    • C12Q1/006Enzyme electrodes involving specific analytes or enzymes for glucose
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S435/00Chemistry: molecular biology and microbiology
    • Y10S435/817Enzyme or microbe electrode
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S435/00Chemistry: molecular biology and microbiology
    • Y10S435/8215Microorganisms
    • Y10S435/911Microorganisms using fungi
    • Y10S435/913Aspergillus
    • Y10S435/917Aspergillus niger
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S435/00Chemistry: molecular biology and microbiology
    • Y10S435/962Prevention or removal of interfering materials or reactants or other treatment to enhance results, e.g. determining or preventing nonspecific binding

Definitions

  • the present invention relates to in vivo enzyme biosensors and more specifically to miniature glucose sensors for subcutaneous measurement of glucose with one-point calibration.
  • in vivo glucose electrodes In response to the need for frequent or continuous in vivo monitoring of glucose in diabetics, particularly in brittle diabetes, a range of possible in vivo glucose electrodes have been studied.
  • the desired characteristics of these electrodes include safety, clinical accuracy and reliability, feasibility of in vivo recalibration, stability for at least one hospital shift of eight hours, small size, ease of insertion and removal, and a sufficiently fast response to allow timely intervention.
  • the in vivo recalibration should be based upon withdrawal of a single sample of body fluid, e.g., blood, and measuring its glucose concentration. This is termed “one point calibration”.
  • the sensitivity must be sufficiently stable for the frequency of required in vivo recalibration to not be excessive.
  • the sensor must be small enough to be introduced and removed with minimal discomfort to the patient and for minimal tissue damage. It is preferred that the sensor be subcutaneous and that it be inserted and removed by the patient or by staff in a physician's office. Finally, its response time must be fast enough so that corrective measures, when needed, can be timely.
  • two-electrode differential measurements were used, one electrode being sensitive to glucose and electrooxidizable interferants and the other only to interferants.
  • One strategy for overcoming the problem of interferants, applicable also to the present invention involves their preoxidation.
  • Another strategy involves shifting, through chemical changes, the redox potential of the polymer in the sensing layer to more reducing potentials.
  • the rate of electrooxidation of interferants such as ascorbate, urate, and acetaminophen is very slow relative to that of glucose through its physiological concentration range.
  • the currents from electrooxidation of interferants are small relative to those of glucose.
  • hydrophilic polyurethanes poly(vinyl alcohol) and polyHEMA membranes have been used.
  • Diffusional mediators through which the O 2 partial pressure dependence of the signals is reduced, are leached from sensors. Such leaching introduces an unwanted chemical into the body, and also leads to loss in sensitivity, particularly in small sensors. In microsensors, in which outward diffusion of the mediator is radial, the decline in sensitivity is rapid.
  • This problem has been overcome in “wired” enzyme electrodes, i.e., electrodes made by connecting enzymes to electrodes through crosslinked electron-conducting redox hydrogels (“wires”).
  • Glucose oxidase has been “wired” with polyelectrolytes having electron relaying [Os(bpy) 2 Cl] +/2+ redox centers in their backbones.
  • Hydrogels were formed upon crosslinking the enzyme and its wire on electrodes. These electrodes had high current densities and operated at a potential of 0.3V vs. SCE.
  • the electrooxidizable interferants are eliminated through peroxidase-catalyzed preoxidation in a second, nonwired, hydrogen peroxide generating layer on the “wired” enzyme electrode.
  • the electrode was constructed by depositing active polymer layers into a recess formed by etching away gold from an insulated gold wire.
  • the active polymer layers including a sensing layer, a glucose flux-limiting layer, a biocompatable layer, and optionally a peroxidase-based interferant eliminating layer, were protected within the recess against mechanical damage.
  • the peroxidase-based interferant eliminating layer is not required when a lower redox potential polymer is used, as described above.
  • the recess and its polymer layers also reduced the transport of glucose to the wire electrode contacting sensing layer.
  • the inventive biosensors are able to accurately measure, for example, approximately 2-30 m ⁇ glucose and approximately 0.5-10 m ⁇ lactate, in vivo.
  • the sensor has no leachable components, and its four crosslinked polymer layers contain only about 5 ⁇ g of immobilized material, and only a few nanograms of polymer-bound osmium. Preoxidation of the interferants in one of the four layers makes possible one-point in vivo calibration of the sensor.
  • FIG. 1 is a schematic drawing of an electrode of the present invention.
  • FIG. 2 is a graphical representation of data generated comparing current density of glucose electrooxidation on electrodes made with PVI 5 -Os (open triangles) with those made with PVI 3 -Os (filled triangles).
  • FIG. 3 is a graphical representation of data generated comparing dependency of current generated on the depth of the recess.
  • FIG. 4 is a graphical representation of data generated comparing dependency of the ratio of the current generated and the charge required to electoreduce or oxidize the polymer redox centers in the sensing layer on the thickness of the sensing layer.
  • FIG. 5 is a graphical representation of data generated comparing variation of current generated by electrodes having sensing layers of differing thickness and diffusion limiting layers of different compositions and thickness.
  • Solid circles 7.5 ⁇ m thick sensing layer of PVI 5 -Os (52%), rGOX (35%), PEGDGE (13%), coated with 4 ⁇ m PAL/PAZ (1:1 ratio).
  • Solid triangles 12.5 ⁇ m sensing layer and 7 ⁇ m PAL/PAZ (1:2 ratio).
  • FIG. 6 is a graphical representation of data generated comparing dependency of current generated on the presence of ascorbate, in the absence and presence of lactate and glucose.
  • concentrations of ascorbate (A), lactate (L) and glucose (G) are shown.
  • Ascorbate is an electrooxidzable interferant. Upon addition of lactate its electrooxidation current is suppressed while that of glucose is not suppressed.
  • FIG. 7 is a graphical representation of data showing current density and corresponding subcutaneous glucose concentration measured with the subcutaneously implanted electrodes of the present invention in a rat animal model. Large solid circles show blood glucose concentrations measured on withdrawn blood samples using a YSI analyzer.
  • FIG. 8 is a Clarke-type clinical grid analyzing the clinical relevance of the blood glucose measurements of FIG. 7 .
  • FIG. 9 is a Clarke-type clinical grid of all possible correlations obtained when each of the 24 glucose analyses of FIG. 7 were used for single point calibration of either implanted electrode.
  • FIG. 10 is a Clarke-type clinical grid testing improvement of the single point calibration through redundant electrodes, the readings of which were within the standard deviation calculated for all differences between simultaneous readings by a pair of implanted electrodes.
  • the present invention includes an insulated, non-corroding conducting metal (e.g., gold, platinum, palladium) or carbon wire-based small (e.g., 290 ⁇ m) O.D. subcutaneous glucose sensor, allowing one-point calibration in vivo. As shown in FIG.
  • a small (e.g., 250 ⁇ m) diameter non-corroding metal or carbon wire 2 with an electrically insulating material 4 , e.g., a polyimide, and, layering in a recess 6 formed by etching or removing a portion of the metal or carbon, the following active polymeric layers: an immobilized, “wired,” glucose oxidase layer 8 ; an electrically insulating and glucose diffusion limiting layer 10 formed, for example, by crosslinking a polyallylamine (PAL) with a polyaziridine (PAZ); optionally, an interference eliminating layer 12 , e.g., of crosslinked horseradish-peroxidase and lactate oxidase; and a biocompatible film 14 e.g., of poly(ethylene oxide) (PEO) derivatized to allow its photo-crosslinking.
  • an electrically insulating material 4 e.g., a polyimide
  • an electrically insulating material 4 e.g.
  • the outside diameter a of the wire 2 is preferably about 0.25 mm or less, and the outside diameter b of the insulated wire is preferably about 0.3 mm or less.
  • the recess 6 in the insulated electrode extends from the tip 16 of the electrode which is open to the surrounding environment, to the top 18 of the wire 2 in the insulating sheath, generally for a length c of less than about 0.150 mm, and preferably about 0.125 mm.
  • the electrodes have no leachable components.
  • the total amount of polymers and enzymes is preferably about 5 ⁇ g.
  • the glucose response through the physiologically relevant 2-20 mM concentration range is close to linear.
  • the electrodes do not respond to ascorbate, urate or acetaminophenol for at least about 36 hours.
  • Their 10-90% response time is about 90 seconds at 2 mM glucose and about 30 seconds at 20 mM glucose.
  • Their sensitivity, after about 30 minutes equilibration, is stable for about 72 hours at 37° C. in 10 mM glucose, the current deviating from the average by less than .+ ⁇ 0.5%.
  • the electrodes have substantially no signal output, e.g., current, charge, or potential, when the concentration of the analyte to be measured is zero.
  • Analysis of the correlation between the blood glucose levels in the tail vein and the current output of the sensors in the subcutaneous regions of the thorax and between the scapulae of the same rat showed that even when the probed sites and organs differed in the extreme, one point in vivo calibration was valid.
  • the analysis also showed the value of implanting redundant sensors. Had clinical decisions been made based on individual sensor readings, calibrated at one point, 94% would have been clinically correct. By using redundant sensors and accepting only those pairs of readings that were within one standard deviation, the percentage of the clinically correct decisions was increased to 99%.
  • the base electrode of the inventive sensor may be formed of a non-corroding metal or carbon wire, for example vitreous carbon, graphite, platinum, palladium, or gold. Gold is preferred, and is used in the following illustrative examples of the invention.
  • the conductive metal or carbon wire is coated with an electrically insulating material, which also forms a wall about the recess which houses the active polymeric components.
  • the insulating material may be, for example, polyurethane, teflon (fluorinated polymers), polyethyleneterephthalate (PET, Dacron) or polyimide.
  • the insulating material is preferably a biocompatible polymer containing less than about 5% water when in equilibrium with physiological body fluids, e.g., subcutaneous tissue.
  • the recess at the tip of the electrode is approximately 20 to 150 ⁇ m in length c, and preferably is approximately 50 to 125 ⁇ m.
  • Etching method The method for etching metal from the tip of the electrode described herein may utilize chloride, bromide or iodide in the bath in lieu of cyamide as described. Bromide is preferred, because it is less toxic and, like Au(CN) 2 —, AuBr 4 ⁇ is a water soluble anion.
  • the metal e.g., gold
  • glucose oxidase may be substituted with other redox enzymes to measure other relevant clinical compounds.
  • lactate oxidase may be used for the in vivo detection of lactate, important in determining if an organ is receiving sufficient oxygen through the blood.
  • Additional redox polymers include, for example, poly(1-vinyl imidazole); poly(4-vinyl pyridine); or copolymers of 1-vinyl imidazole such as poly (acrylamide co-1-vinyl imidazole) where the imidazole or pyridine complexes with [Os (bpy) 2 Cl]+/2 + ; [Os (4,4′-dimethyl bipyridine) 2 Cl]+/2 + ; [Os (4,4′-dimethyl phenanthroline) 2 Cl-]+/2 + ; [Os (4,4′-dimethyoxy phenanthroline) 2 Cl]+/2 + ; and [Os (4,4′-dimethoxy bipyridine) 2 Cl] +/2+ ; to imidazole rings
  • the imidazole ring compounds are preferred because their complexes have more reducing redox potentials, i.e., closer to that of the SCE potential. At these more reducing potentials, the rate of electrooxidation of interferants and the current generated thereby.
  • the polymeric barrier layer is electrically insulating and limits diffusion of glucose through to the sensing layer. It may be formed, for example, by crosslinking a polyallylamine (PAL) with a polyaziridine (PAZ). Alternatively, PAL may be replaced wholly or in part with a zwitterionic polymer obtained by quaternizing poly(vinylpyridine) with bromoacetate and dialyzing against 0.15M NaCl or by a polyanion such as a polysulfonic acid.
  • PAL polyallylamine
  • PAZ polyaziridine
  • PAL may be replaced wholly or in part with a zwitterionic polymer obtained by quaternizing poly(vinylpyridine) with bromoacetate and dialyzing against 0.15M NaCl or by a polyanion such as a polysulfonic acid.
  • the barrier layer may contain a polyanionic polymer, in which the rate of permeation of anionic interferants such as ascorbate and urate is slowed.
  • This layer may also contain a polycation that enhances the retention of the polyanion by electrostatic bonds and improves wetting by the biocompatable layer.
  • Interference Eliminating Layer As described above, this layer is optional, in that it is not required when a redox polymer having a more reducing potential is used, such as PVI 15 -dmeOs (Ohara et al., Analytical Chemistry, 1994, 64:2451-2457). At operating potentials of approximately ⁇ 0.10 to +0.25 for the glucose biosensor, the rate of electrooxidation of interferants such as ascorbate, urate and acetaminophen is very slow relative to that of glucose through its physiological concentration range.
  • a redox polymer having a more reducing potential such as PVI 15 -dmeOs
  • a separate interferant eliminating layer When a separate interferant eliminating layer is used, it preferably contains a peroxidase enzyme which may or may-not be preactivated.
  • a peroxidase enzyme which may or may-not be preactivated.
  • Such interferant eliminating layers are disclosed, for example, in U.S. Pat. No. 5,356,786, which discloses the structure and function of interferant eliminating biosensors.
  • the glucose biosensor preferably contains lactate oxidase (LOX) in combination with peroxidase in the interferant eliminating layer.
  • LOX lactate oxidase
  • glucose oxidase would be used with peroxidase.
  • the enzyme composition of the interferant eliminating layer may be altered for a specified function.
  • the biocompatable layer is comprised of hydrogels, e.g., polymeric compositions which contain more than about 20% by weight of water when in equilibrium with a physiological environment such as living tissue or blood.
  • hydrogels e.g., polymeric compositions which contain more than about 20% by weight of water when in equilibrium with a physiological environment such as living tissue or blood.
  • An example is crosslinked poly(ethylene oxide), e.g., poly(ethylene oxide) tetraacrylate.
  • the polymeric compositions must be non-toxic and compatible with living Systems.
  • Insulated non-corroding metal or carbon wires that have been etched as described above to contain a recess at the tip, are placed in a block that serves as an X-Y positioner.
  • the wires vertically traverse the block and are held in place, e.g., by pressure.
  • the blocks with the wires can be formed of elements, each element having multiple half-cylinder grooves running vertically.
  • the wires are placed in these grooves and the elements are assembled into the block using screws.
  • the block may be formed of aluminum having equally spaced holes, (900 for a 30 ⁇ 30 array of wires), each hole to contain one wire.
  • the block is positioned under a fixed micronozzle that ejects a fluid in to the recess of the insulated wire.
  • the nozzle is electrically charged, with the wire having an opposite charge, or the wire being grounded or at least having a potential such that there is a potential difference between the nozzle and the wire. Because the nozzle is charged, the microdroplets it ejects are also charged with the same type of charge (positive or negative) as the nozzle. The higher the potential on the nozzle (e.g., versus ground potential), the higher the charge on the ejected microdroplets.
  • the tip of the wire to be coated is at ground potential or has a charge of the opposite type, the charged microdroplets are guided into the recess to deposit on the electrode, even if the jet of microdroplets is not vertical, i.e., even if the micronozzle is not precisely aligned above the wire's tip.
  • the droplet breaks up into two or more smaller droplets because of electrostatic repulsion of charges on the droplet.
  • the very small droplets all “drift” (drift meaning transport assisted by an electrical field) to the recessed electrode surface and are collected on it, even if they did not originate in a nozzle precisely aligned with the electrode.
  • This coating method is useful in making any small biosensor, not only those in recessed zones.
  • the recessed biosensors of the present invention have sufficient sensitivity and stability to be used as very small, subcutaneous biosensors for the measurement of clinically relevant compounds such as glucose and lactate.
  • the electrodes accurately measure glucose in the range of about 2-30 ⁇ M and lactate in the range of about 0.5-10 mM.
  • One function of the implanted biosensor is to sound an alarm when, for example, a patient's glucose concentration is too low or too high. When pairs of implanted electrodes are used, there are three situations in which an alarm is triggered: low glucose concentration, high glucose concentration; sensor malfunction as determined by a discrepancy between paired readings of the two sensors.
  • a discrepancy sufficient to trigger the alarm may be, for example more than two or three times the standard deviation persisting for a defined period, e.g., not less than ten minutes. Such a system may be useful in sleeping patients, and also in emergency and intensive care hospital rooms, where vital functions are continuously monitored.
  • Another function of the inventive biosensors in to assist diabetics in maintaining their blood glucose levels near normal Many diabetics now maintain higher than normal blood glucose levels because of danger of coma and death in severe hypoglycemia. However, maintaining blood glucose levels substantially, e.g., approximately 40% or more above normal leads to retinopathy and blindness as well as to kidney failure.
  • Use of the subcutaneous biosensors to frequently, if not continuously, monitor glucose concentrations is desirable so that glucose concentrations can be maintained closer to an optimum level.
  • the subcutaneous biosensors can be used to measure the rate of rise and decline of glucose concentrations after a meal or the administration of glucose (e.g., a glucose tolerance test).
  • the sensors are also useful in feedback loops for automatic or manually controlled maintenance of glucose concentrations within a defined range. For example, when used in conjunction with an insulin pump, a specified amount of insulin is delivered from the pump if the sensor glucose reading is above a set value.
  • the ability to promptly confirm that the implanted sensor reading is accurate is essential. Prompt confirmation and rapid recalibration are possible only when one-point calibration is valid. Generally, even if a sensor's response is linear through the relevant concentration range, calibration requires at least two blood or fluid samples, withdrawn from the patient at times when the glucose concentration differs. It usually takes several hours for the glucose concentration to change sufficiently to validate proper functioning by two-point calibration. The ability to confirm and recalibrate using only one point is thus a highly desirable feature of the present invention.
  • Redundant sensors e.g., at least two are preferred in the clinical application of the subcutaneous biosensors. Such redundancy permits signaling of failure of any one sensor by recognition of an increase in the discrepancy between the readings of the sensors at one time point, e.g., more than two standard deviations apart.
  • the redundant sensors may be implanted near each other or at remote sites.
  • the biosensors be implanted in subcutaneous tissue so as to make the sensor relatively unobtrusive, and at a site where they would not be easily dislodged, e.g., with turning or movement. It is also preferred, when readings are not corrected for temperature (which they generally are) that the sensors be implanted where they are likely to be at body temperature, e.g., near 37° C., and preferably covered by clothing. Convenient sites include the abdomen, inner thigh, arm.
  • the electrical measurement by which the glucose concentration is monitored can be continuous or pulsed. It can be a current measurement, a potential measurement or a measurement of charge. It can be a steady state measurement, where a current or potential that does not substantially change during the measurement is monitored, or it can be a dynamic measurement, e.g., one in which the rate of current or potential change in a given time period is monitored.
  • These measurements require at least one electrode in addition to the sensing electrode.
  • This second electrode can be placed on the skin or can be implanted, e.g., subcutaneously.
  • a potentiostat in the circuit connecting the implanted sensing electrode and the second electrode that can be a reference electrode, such as an Ag/AgCl electrode.
  • the reference electrode may serve also as the counter electrode.
  • the counter electrode can also be a separate, third electrode, such as a platinum, carbon, palladium or gold electrode.
  • fluid from the body can be routed to an external sensor. It is preferred in this case to implant in the subcutaneous region a microfiltration giver and pull fluid to an evacuated container, the fluid traversing a cell containing the sensing electrode.
  • this cell also contains a second electrode, e.g., a reference electrode which may serve also as a counter electrode.
  • the reference and counter electrodes may be separate electrodes. In coulometric measurements only two electrodes, the sensing electrode and the counter electrode are required.
  • the flow of body fluid may be pulsed or continuous.
  • a microdialysis fiber may be used, preferably in conjunction with a pump.
  • a simple measure by which the life of the implanted electrodes can be extended and the frequency of their required recalibration reduced involves turning the electrodes “on” by applying a bias, i.e., a potential, only during the period of measurement, then turning the biasing potential off or reducing it, so that a lesser current will flow. It is generally sufficient to perform only one measurement every five or even ten minutes, or longer, because glucose concentrations do not change abruptly.
  • a bias i.e., a potential
  • Another measure is to lower the glucose flux to the sensing layer much as possible, consistent with maintaining adequate sensitivity and detectivity. Reduction of the glucose flux to the sensing layer reduces the current. Therefore, even though this stabilizes the electrodes, i.e., slows the loss in sensitivity, the flux dependent current must not be excessively reduced. Usually a current of 3-5 nA at 2 mM glucose concentration is adequate.
  • the glucose flux is lowered by using one or more glucose-flux reducing polymer slayers, such as the PAL/PAZ layer, the lifetime of the sensor is increased.
  • Electrodes were made of a polyamide-insulated 250 ⁇ m diameter gold wire, having an outer diameter (O.D.) of 290 ⁇ m (California Fine Wire Co., Grover City, Calif.). Heat shrinkable tubing (RNF 100 3/64” BK and 1/16” BK, Thermofit®, Raychem, Menlo Park, Calif.) and a two component silver epoxy (Epo-tek H 2 OE; Epoxy Tech, Inc., Billerica, Mass.) were used for electrode preparation.
  • the glucose sensing layer was made by crosslinking a genetically engineered glucose oxidase (rGOX) (35% purity, Chiron Corp., Emeryville, Calif.) with a polymer derived of poly(vinylimidazole) (PVI), made by complexing part of the imidazoles to [Os(bpy) 2 Cl] +/2+ .
  • rGOX glucose oxidase
  • PVI poly(vinylimidazole)
  • the barrier layer between the sensing and interference-eliminating layers was made of polyallylamine (PAL; Polysciences) crosslinked with a polyfunctional aziridine (PAZ) (XAMA-7; Virginia Chemicals, Portsmouth, Va.).
  • PAL polyallylamine
  • PAZ polyfunctional aziridine
  • the biocompatible layer was made of 10% aqueous poly(ethylene oxide) tetraacrylate (PEO-TA).
  • PEO poly(ethylene oxide) tetraacrylate
  • PEO-TA aqueous poly(ethylene oxide) tetraacrylate
  • the 18,500 g/mol PEO (Polysciences) is a tetrahydroxylated compound by virtue of two hydroxyl groups on a bisphenol A bisepoxide that linked two .alpha., .omega.-hydroxy-terminated 9,000 g/mol PEO units.
  • Acryloyl chloride Aldrich, Milwaukee, Wis.
  • Triethylamine (Mallinkrodt, Paris, Ky.) was used as a proton acceptor equimolar with the acryloyl chloride.
  • bovine serum albumin (BSA) fraction V (Cat. No. A-2153)
  • BSA bovine serum albumin
  • ascorbic acid uric acid
  • 4-acetaminophenol 4-acetaminophenol
  • L(+) lactic acid
  • hydrogen peroxide 30% all from Sigma. All chemicals were used as received. Solutions (if not otherwise specified) were made with distilled, deionized water. Glucose monitoring was performed in buffer, in bovine serum (Sigma, Cat. No. S-6648) containing antibiotic-antimycotic solution (Sigma, Cat. No. A-8909) at 37° C. and in rats.
  • a potentiostat/galvanostat (PAR Model 173, Princeton Applied Research, Princeton, N.J.) operated in a galvanostatic mode, and a sonicator (Fisher scientific, Pittsburgh, Pa.) were used. Cyclic voltammograms were recorded with a potentiostat (PAR Model 273A) and a conventional electrochemical cell having a Pt wire counter and a SCE reference electrode and were evaluated with PAR 270 software. Glucose signals were monitored with a bipotentiostat (Biometra EP 30) and a two channel strip-chart recorder.
  • the recessed electrodes were coated under a microscope (Bausch & Lomb) using a micromanipulator (Narishige, Seacliff, N.Y.). The micropipettes were pulled with a micropipette puller (Narishige). Temperature was controlled with an isothermal circulator (Fisher Scientific).
  • a recess 6 i.e., channel, in a polyamide insulated gold wire 2 is formed by electrochemical etching of the gold under galvanostatic control. By controlling the charge, the total amount of gold electrooxidized and dissolved as Au(CN) 2 is defined.
  • the process is reproducible, accurate and fast with 20 electrodes being processed in each batch in less than five minutes.
  • the recess-forming procedure was highly reproducible, with a deviation of +/ ⁇ 10 ⁇ m found (using an objective micrometer) for a batch of 30 recessed electrodes.
  • the electrodes were examined under a microscope for flatness of the gold surface and correct depth.
  • FIG. 1 shows a schematic side view in cross-section of an electrode of the present invention, showing the gold wire 2 , insulating coating 4 , and recess or channel 6 .
  • the recessed gold surfaces were coated by filling of the cavities or channels 6 with aqueous solutions containing the crosslinkable components of the different layers, and their crosslinkers.
  • the solutions were introduced under a microscope with a micropipette (connected to a microsyringe by polyethylene tubing and shrink tubing), using a micromanipulator. After application of each of the individual layers, the electrodes were cured overnight at room temperature, in air.
  • the sensing layer 8 was made by “wiring” rGOX to the gold electrode through a redox hydrogel to which the enzyme was covalently bound.
  • the electrodes were prepared as follows: 10 mg/ml solutions were made from
  • a redox hydrogel was formed by mixing the three solutions so that the final composition (by weight) was 52% redox polymer, 35% enzyme and 13% crosslinker.
  • the insulating layer 10 prevented electrical contact between the redox hydrogel and the interference eliminating enzymes (HRP and LOX).
  • PAL:PAZ was used as the insulating material.
  • the film was deposited from a solution obtained by mixing in volume ratio of 1/1, 1/2 or 1/3, a PAL solution (4.5 mg in 100 mM HEPES buffer at pH 7.0) and a freshly prepared PAZ solution (30 mg/ml). The PAZ solution was used within 15 minutes of preparation.
  • the interference-eliminating layer 12 was prepared according to a previously published protocol, Maidan and Heller, 1992, Anal. Chem., 64:2889-2896. 50 ⁇ l of a 12 mg/ml freshly prepared sodium periodate solution was added to 100 ⁇ l of a solution containing 20 mg/ml HRP (HRP-VI or HRP-BM) and 100 mg/ml LOX (LOX or rLOX) in 0.1 M sodium bicarbonate and the mixture was incubated in the dark for two hours. Alternatively, the oxidation of HRP could be carried out prior to adding LOX and crosslinking.
  • the biocompatible layer 14 films were photocrosslinked by exposure to UV light (UVP, Inc., San Gabriel, Calif.; Blak-Ray; spectral peak at 360 nM UV irradiance at the sample 200 mW/cm 2 ) for one minute.
  • the initiator used was 2,2-dimethoxy-2-phenylacetophenone (Aldrich).
  • a solution of 300 mg/ml of the initiator in 1-vinyl-2-pyrrolidinone (Aldrich) was added to the prepolymer mixtures.
  • Approximately 30 ⁇ l of the initiator solution was added per ml of 10% w/w aqueous solution of the tetraacrylated PEO.
  • the prepolymers were crosslinked in situ inside the recess of the electrode.
  • the films were prepared by filling the recess with the prepolymer solution twice and exposing the electrode to the UV light source after each time the cavity was filled.
  • the depth c of the channel 6 and the thickness of the polymer layers in it controls the mass transport, i.e., flux of glucose, to the sensing layer.
  • the apparent Michaelis constant (K m ) is adjusted to about 20-30 mM glucose.
  • the polyimide wall 4 of the channel 6 also protects the four polymer and polymer/enzyme layers 8 , 10 , 12 , 14 against mechanical damage and reduces the hazard of their loss in the body. Because the glucose electrooxidation current is limited by glucose mass transport through the recess 16 and its polymer films 8 , 10 , 12 , 14 , rather than by mass transport to the tissue-exposed tip 16 , the current is practically insensitive to motion. Evidently, the electrooxidation rate of glucose in the recessed sensing layer 8 is slower than the rate of glucose diffusion to the channel's outer fluid contacting interface.
  • PVI 5 -Os is preferred as the “wire” of the sensing layer when an interference eliminating layer of HRP and LOX is used, but not in the absence of this layer, i.e., when redox polymers with more reducing redox potential are preferred.
  • the subscript (5) is used to indicate that, on the average, every fifth vinylimidazole mer carries an electron-relaying osmium center.
  • Use of electrodes formed with PVI 5 -Os and PVI 3 -Os are compared in FIG. 2 , and show higher current density of glucose electrooxidation on electrodes made with PVI 5 -Os (open triangle) than on those made with PVI 3 -Os (filled triangles).
  • Depth of the recess and the sensing layer were investigated to assess the dependence of the current on the depth of the recess ( FIG. 3 ), with the total amount of PVI 5 -Os and rGOX being kept constant.
  • Much of the loss in current in the deeper cavities resulted not from reduced glucose mass transport, but from adsorptive retention of part of the enzyme and polymer on the polyamide wall when microdrops of the component solutions were introduced into the recess in the process of making the electrodes.
  • Some of the adsorbed polymer and enzyme on the walls were washed onto the electrode surface, increasing the current. The highest currents were seen after five washings.
  • the ratio of current to charge required to electroreduce or electrooxidize the redox polymer in the sensing layer reached a maximum, then dropped.
  • 10 coatings producing an approximately 13 ⁇ m thick wired-rGOX sensing layer, yielded sensors that had the desired characteristics for in vivo use.
  • the insulating layer This layer electrically insulates the redox enzymes of the interference eliminating layer (HRP and LOX) from the “wired” rGOX layer and limits the glucose flux to the sensing layer, thereby extending the useful life of the electrode.
  • PAL crosslinked with PAZ, forming a polycationic network at pH 7.09 is preferred. The best results, i.e., best stability of current outputs, were obtained using 1:2 PAL:PAZ ( FIG. 5 ), with three coatings applied to form an approximately 7 ⁇ m thick crosslinked film.
  • the interference eliminating layer Interferants, particularly ascorbate, urate, and acetaminophenol, are oxidized in the third layer, containing LOX and HRP.
  • lactate the typical concentration of which in blood is 1 mM, reacts with O 2 to form H 2 O 2 and pyruvate.
  • H 2 O 2 in the presence of HRP, oxidizes ascorbate, urate, and acetaminophenol, being reduced to water.
  • the preferred coimmobilization process involved two separate steps: periodate oxidation of oligosaccharide functions of HRP to aldehydes, followed by mixing with LOX and formation of multiple Schiff bases between HRP-aldehydes and LOX amines (e.g. lysines) and between HRP aldehydes and amines.
  • the thickness of the interference eliminating layer is approximately 85 ⁇ m and is made by applying successive coatings, e.g., about six coatings.
  • FIG. 6 shows that electrooxidizable interferants were eliminated in the presence of lactate at physiological levels.
  • LOX slowly lost its activity in the crosslinked HRP-LOX layer. This led to degradation of the ability of the layer to eliminate interferants. After 36 hours of operation at 37° C., a measurable current increment was noted when enough ascorbate was added to produce a 0.1 mM concentration.
  • a preferred biocompatible layer consists, for example, of photocrosslinked tetraacrylated 18,500 Da poly(ethylene oxide) (Pathak et al., 1993, J. Am. Chem. Soc., 114:8311-8312).
  • the thickness of this layer, made by sequential photo-crosslinking of two coatings, is about 20 ⁇ m.
  • One minute UV exposure required for the photocrosslinking process reduced the sensitivity by 16+/ ⁇ 2%.
  • the rat's body temperature was maintained at 37° C. by a homeostatic blanket.
  • the sensors were allowed to reach a basal signal level for at least one hour before blood sampling was started.
  • Blood samples were obtained from the tail vein and all blood samples were analyzed using a glucose analyzer (YSI, Inc., Yellow Springs, Ohio; Model 23A).
  • glucose infusion was started using a syringe pump (Harvard Apparatus, South Natick, Mass.) at a rate of 120 mg glucose/min kg rat wt. The glucose infusion was maintained for approximately one hour.
  • thermostable recombinant GOX (rGOX; Heller, 1992, J. Phys. Chem., 96:3579-3587) rather than GOX is used in the sensor and glucose transport is reduced to make the sensor current diffusion, not enzyme turnover, limited.
  • the glucose flux is attenuated by the three outer layers and the sensing layer itself. Because the sensing layer contains a large excess of glucose oxidase, its activity greatly exceeds that needed for electrooxidizing the attenuated glucose flux, and the sensor's stability is improved.
  • the stability can be tested by methods known, for example, tested in the presence of 0.1 mM ascorbate in 10 mM glucose at 37° C.
  • the current output of a typical optimized electrode was about 35 nA and the apparent K m , derived from an Eadie-Hofstee plot, was about 20 mM (Table 1).
  • the 10-90% response time was approximately one minute.
  • the sensitivity of the stabilized sensors does not change by more than +5% for 72 hours of operation at 37° C. After a small initial decrease in sensitivity, it increased to a maximum after 40 hours and the final 72 hour sensitivity was almost identical with the initial.
  • the characteristics of the electrodes of the present invention are summarized in Table 1. Each entry represents an average value for five tested electrodes.
  • Baseline currents are typically less than 0.5 nA and the noise less than 10 pA.
  • the currents observed throughout the physiological glucose concentration range (2-20 mM) exceed the noise equivalent current by at least a factor of 100.
  • the apparent K m is 20 mM, and the 10% to 90% response time is, for aged electrodes, about 90 seconds at the lowest physiologically relevant glucose concentration (2 mM) and 20 seconds at the highest (20 mM).
  • the baseline of nil at 0 mM glucose is stable for 36 hours in the presence of 0.1 mM ascorbate.
  • the stability observed and the existence of a valid zero-point in the presence of interferants suggest that the sensor can be used in vivo for 72 hours and tested/recalibrated in vivo through a single point calibration, i.e., by withdrawing only a single sample of blood for independent analysis.
  • K M app is the apparent Michaelis-Menton coefficient determined from an electrochemical Eadie-Hoffstee (EH) or Lineweaver-Burk (LB) plot -t r is the 10-90% risetime, 90s for 2 mM and 30 s for 20 mH glucose concentration.
  • EH electrochemical Eadie-Hoffstee
  • LB Lineweaver-Burk
  • -t r is the 10-90% risetime, 90s for 2 mM and 30 s for 20 mH glucose concentration.
  • -Current Variance is the maximum deviation from the mean value, measured during the 72 hours test, conducted in 10 mM glucose in the presence of interferants. The current was continuously monitored at 37 ° C.

Abstract

A small diameter flexible electrode designed for subcutaneous in vivo amperometric monitoring of glucose is described. The electrode is designed to allow “one-point” in vivo calibration, i.e., to have zero output current at zero glucose concentration, even in the presence of other electroreactive species of serum or blood. The electrode is preferably three or four-layered, with the layers serially deposited within a recess upon the tip of a polyamide insulated gold wire. A first glucose concentration-to-current transducing layer is overcoated with an electrically insulating and glucose flux limiting layer (second layer) on which, optionally, an immobilized interference-eliminating horseradish peroxidase based film is deposited (third layer). An outer (fourth) layer is biocompatible.

Description

    CROSS-REFERENCE TO RELATED APPLICATIONS
  • This application is a Continuation of application Ser. No. 11/109,379, filed on Apr. 19, 2005, which is a Continuation application of Ser. No. 10/353,341, filed Jan. 28, 2003, now U.S. Pat. No. 6,881,551, which is a Continuation application of Ser. No. 09/997,808, filed Nov. 29, 2001, now U.S. Pat. No. 6,514,718, which is a Continuation application of Ser. No. 09/668,221, filed Sep. 22, 2000, now U.S. Pat. No. 6,329,161, which is a Continuation of application Ser. No. 09/477,053, filed Jan. 3, 2000, now U.S. Pat. No. 6,162,611, which is a Continuation of application Ser. No. 09/356,102, filed Jul. 16, 1999, now U.S. Pat. No. 6,121,009, which is a Continuation of application Ser. No. 08/767,110, filed Dec. 4, 1996, now U.S. Pat. No. 6,284,478, which is a continuation of application Ser. No. 08/299,526, filed Sep. 1, 1994, now U.S. Pat. No. 5,593,852, which is a continuation-in-part of application Ser. No. 08/161,682, filed Dec. 2, 1993, now U.S. Pat. No. 5,356,786, which is a continuation of application Ser. No. 07/664,054, filed Mar. 4, 1991, now abandoned, which applications are incorporated herein by reference.
  • STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT
  • This work was supported in part by the National Institutes of Health (DK42015). Accordingly, the U.S. government may have rights in this invention.
  • FIELD OF THE INVENTION
  • The present invention relates to in vivo enzyme biosensors and more specifically to miniature glucose sensors for subcutaneous measurement of glucose with one-point calibration.
  • BACKGROUND
  • In response to the need for frequent or continuous in vivo monitoring of glucose in diabetics, particularly in brittle diabetes, a range of possible in vivo glucose electrodes have been studied. The desired characteristics of these electrodes include safety, clinical accuracy and reliability, feasibility of in vivo recalibration, stability for at least one hospital shift of eight hours, small size, ease of insertion and removal, and a sufficiently fast response to allow timely intervention. The in vivo recalibration should be based upon withdrawal of a single sample of body fluid, e.g., blood, and measuring its glucose concentration. This is termed “one point calibration”.
  • Keys to safety are absence of leachable components, biocompatibility, and limiting of the potentially hazardous foreign matter introduced into the body to an amount that is inconsequential in a worst case failure. The clinical accuracy must be such that even when the readings are least accurate, the clinical decisions based on these be still correct. Feasibility of prompt confirmation of proper functioning of the sensors and of periodic in vivo recalibration is of essence if a physician is to allow the treatment of a patient to depend on the readings of the sensor. This one-point calibration, relying on the signal at zero glucose concentration being zero and measuring the blood glucose concentration at one point in time, along with the signal, is of essence, but has heretofore been elusive. The sensitivity must be sufficiently stable for the frequency of required in vivo recalibration to not be excessive. The sensor must be small enough to be introduced and removed with minimal discomfort to the patient and for minimal tissue damage. It is preferred that the sensor be subcutaneous and that it be inserted and removed by the patient or by staff in a physician's office. Finally, its response time must be fast enough so that corrective measures, when needed, can be timely.
  • In response to some of these needs, needle type and other subcutaneous amperometric sensors were considered. The majority of these utilized platinum-iridium, or platinum black to electrooxidize H2O2 generated by the glucose oxidase (GOX) catalyzed reaction of glucose and oxygen. In these sensors, the GOX was usually in large excess and immobilized, often by crosslinking with albumin and glutaraldehyde. To exclude electrooxidizable interferants, membranes of cellulose acetate and sulfonated polymers including Nafion™ were used. Particular attention was paid to the exclusion of the most common electrooxidizable interferants: ascorbate, urate and acetaminophen. Also to cope with the interferants, two-electrode differential measurements were used, one electrode being sensitive to glucose and electrooxidizable interferants and the other only to interferants. One strategy for overcoming the problem of interferants, applicable also to the present invention, involves their preoxidation. Another strategy involves shifting, through chemical changes, the redox potential of the polymer in the sensing layer to more reducing potentials. When the redox potential of the polymer is in the region between about −0.15 V and +0.15 V versus the standard calomel electrode (SCE), and the electrodes are poised in their in vivo operation between about −0.10 and +0.25 V, the rate of electrooxidation of interferants such as ascorbate, urate, and acetaminophen is very slow relative to that of glucose through its physiological concentration range. Thus, also the currents from electrooxidation of interferants are small relative to those of glucose.
  • To make the electrodes more biocompatible, hydrophilic polyurethanes, poly(vinyl alcohol) and polyHEMA membranes have been used.
  • Several researchers tested GOX-based glucose sensors in vivo and obtained acceptable results in rats, rabbits, dogs, pigs, sheep and humans. These studies validated the subcutaneous tissue as an acceptable glucose sensing site. Good correlation was observed between intravascular and subcutaneous glucose concentrations. They also demonstrated the need for in vivo sensor calibration. Another approach to in vivo glucose monitoring was based on coupling subcutaneous microdialysis with electrochemical detection. To control and adjust the linear response range, electrodes have been made glucose-diffusion limited, usually through glucose transport limiting membranes.
  • Diffusional mediators, through which the O2 partial pressure dependence of the signals is reduced, are leached from sensors. Such leaching introduces an unwanted chemical into the body, and also leads to loss in sensitivity, particularly in small sensors. In microsensors, in which outward diffusion of the mediator is radial, the decline in sensitivity is rapid. This problem has been overcome in “wired” enzyme electrodes, i.e., electrodes made by connecting enzymes to electrodes through crosslinked electron-conducting redox hydrogels (“wires”). Glucose oxidase has been “wired” with polyelectrolytes having electron relaying [Os(bpy)2Cl]+/2+ redox centers in their backbones. Hydrogels were formed upon crosslinking the enzyme and its wire on electrodes. These electrodes had high current densities and operated at a potential of 0.3V vs. SCE. The electrooxidizable interferants are eliminated through peroxidase-catalyzed preoxidation in a second, nonwired, hydrogen peroxide generating layer on the “wired” enzyme electrode.
  • SUMMARY OF THE INVENTION
  • A small (e.g., 0.29 mm), recessed, non-corroding metal (e.g., gold, platinum, palladium) or carbon wire electrode for subcutaneous in vivo glucose monitoring, approaching in its performance all of the above listed requirements, including in vivo one-point calibration, has been produced. The electrode was constructed by depositing active polymer layers into a recess formed by etching away gold from an insulated gold wire.
  • The active polymer layers, including a sensing layer, a glucose flux-limiting layer, a biocompatable layer, and optionally a peroxidase-based interferant eliminating layer, were protected within the recess against mechanical damage. (The peroxidase-based interferant eliminating layer is not required when a lower redox potential polymer is used, as described above.) The recess and its polymer layers also reduced the transport of glucose to the wire electrode contacting sensing layer.
  • By limiting the glucose flux, the desired linear response range, spanning the clinically relevant glucose concentration range was obtained. The inventive biosensors are able to accurately measure, for example, approximately 2-30 mμ glucose and approximately 0.5-10 mμ lactate, in vivo. The sensor has no leachable components, and its four crosslinked polymer layers contain only about 5 μg of immobilized material, and only a few nanograms of polymer-bound osmium. Preoxidation of the interferants in one of the four layers makes possible one-point in vivo calibration of the sensor.
  • BRIEF DESCRIPTION OF THE FIGURES
  • FIG. 1 is a schematic drawing of an electrode of the present invention.
  • FIG. 2 is a graphical representation of data generated comparing current density of glucose electrooxidation on electrodes made with PVI5-Os (open triangles) with those made with PVI3-Os (filled triangles).
  • FIG. 3 is a graphical representation of data generated comparing dependency of current generated on the depth of the recess.
  • FIG. 4 is a graphical representation of data generated comparing dependency of the ratio of the current generated and the charge required to electoreduce or oxidize the polymer redox centers in the sensing layer on the thickness of the sensing layer.
  • FIG. 5 is a graphical representation of data generated comparing variation of current generated by electrodes having sensing layers of differing thickness and diffusion limiting layers of different compositions and thickness. Solid circles: 7.5 μm thick sensing layer of PVI5-Os (52%), rGOX (35%), PEGDGE (13%), coated with 4 μm PAL/PAZ (1:1 ratio). Open circles: 5.0 sensing layer. Solid triangles: 12.5 μm sensing layer and 7 μm PAL/PAZ (1:2 ratio). Open triangles: 7.5 μm sensing layer and 4.5 μm PAL/PAZ (1:2 ratio).
  • FIG. 6 is a graphical representation of data generated comparing dependency of current generated on the presence of ascorbate, in the absence and presence of lactate and glucose. The concentrations of ascorbate (A), lactate (L) and glucose (G) are shown. Ascorbate is an electrooxidzable interferant. Upon addition of lactate its electrooxidation current is suppressed while that of glucose is not suppressed.
  • FIG. 7 is a graphical representation of data showing current density and corresponding subcutaneous glucose concentration measured with the subcutaneously implanted electrodes of the present invention in a rat animal model. Large solid circles show blood glucose concentrations measured on withdrawn blood samples using a YSI analyzer.
  • FIG. 8 is a Clarke-type clinical grid analyzing the clinical relevance of the blood glucose measurements of FIG. 7.
  • FIG. 9 is a Clarke-type clinical grid of all possible correlations obtained when each of the 24 glucose analyses of FIG. 7 were used for single point calibration of either implanted electrode.
  • FIG. 10 is a Clarke-type clinical grid testing improvement of the single point calibration through redundant electrodes, the readings of which were within the standard deviation calculated for all differences between simultaneous readings by a pair of implanted electrodes.
  • DETAILED DESCRIPTION OF THE INVENTION
  • The present invention includes an insulated, non-corroding conducting metal (e.g., gold, platinum, palladium) or carbon wire-based small (e.g., 290 μm) O.D. subcutaneous glucose sensor, allowing one-point calibration in vivo. As shown in FIG. 1, its construction involves coating a small (e.g., 250 μm) diameter non-corroding metal or carbon wire 2 with an electrically insulating material 4, e.g., a polyimide, and, layering in a recess 6 formed by etching or removing a portion of the metal or carbon, the following active polymeric layers: an immobilized, “wired,” glucose oxidase layer 8; an electrically insulating and glucose diffusion limiting layer 10 formed, for example, by crosslinking a polyallylamine (PAL) with a polyaziridine (PAZ); optionally, an interference eliminating layer 12, e.g., of crosslinked horseradish-peroxidase and lactate oxidase; and a biocompatible film 14 e.g., of poly(ethylene oxide) (PEO) derivatized to allow its photo-crosslinking. The outside diameter a of the wire 2 is preferably about 0.25 mm or less, and the outside diameter b of the insulated wire is preferably about 0.3 mm or less. The recess 6 in the insulated electrode extends from the tip 16 of the electrode which is open to the surrounding environment, to the top 18 of the wire 2 in the insulating sheath, generally for a length c of less than about 0.150 mm, and preferably about 0.125 mm.
  • The electrodes have no leachable components. The total amount of polymers and enzymes is preferably about 5 μg. The glucose response through the physiologically relevant 2-20 mM concentration range is close to linear. The electrodes do not respond to ascorbate, urate or acetaminophenol for at least about 36 hours. Their 10-90% response time is about 90 seconds at 2 mM glucose and about 30 seconds at 20 mM glucose. Their sensitivity, after about 30 minutes equilibration, is stable for about 72 hours at 37° C. in 10 mM glucose, the current deviating from the average by less than .+−0.5%. The electrodes have substantially no signal output, e.g., current, charge, or potential, when the concentration of the analyte to be measured is zero.
  • Two electrodes implanted subcutaneously in a rat tracked blood glucose levels, and their absolute, uncorrected current output was proportional to the blood glucose concentration. Analysis of the correlation between the blood glucose levels in the tail vein and the current output of the sensors in the subcutaneous regions of the thorax and between the scapulae of the same rat showed that even when the probed sites and organs differed in the extreme, one point in vivo calibration was valid. The analysis also showed the value of implanting redundant sensors. Had clinical decisions been made based on individual sensor readings, calibrated at one point, 94% would have been clinically correct. By using redundant sensors and accepting only those pairs of readings that were within one standard deviation, the percentage of the clinically correct decisions was increased to 99%.
  • It is understood that one of skill in the art may substitute various components of the biosensor described above with known materials to obtain an modified biosensor using the principles outlined herein. For example, the following substitutions are contemplated:
  • Base electrode: The base electrode of the inventive sensor may be formed of a non-corroding metal or carbon wire, for example vitreous carbon, graphite, platinum, palladium, or gold. Gold is preferred, and is used in the following illustrative examples of the invention.
  • Insulator: The conductive metal or carbon wire is coated with an electrically insulating material, which also forms a wall about the recess which houses the active polymeric components. The insulating material may be, for example, polyurethane, teflon (fluorinated polymers), polyethyleneterephthalate (PET, Dacron) or polyimide. The insulating material is preferably a biocompatible polymer containing less than about 5% water when in equilibrium with physiological body fluids, e.g., subcutaneous tissue.
  • Recess: In general, the recess at the tip of the electrode is approximately 20 to 150 μm in length c, and preferably is approximately 50 to 125 μm.
  • Etching method: The method for etching metal from the tip of the electrode described herein may utilize chloride, bromide or iodide in the bath in lieu of cyamide as described. Bromide is preferred, because it is less toxic and, like Au(CN)2—, AuBr4 is a water soluble anion. Thus, in aqueous HBR, the metal, e.g., gold, an be etched by applying a sufficiently oxidizing potential where gold is electrolytically dissolved:
    Au+4HBr---->HAuBr4 +(3/2)H2
  • Wired Enzyme Layer: In the sensing enzyme-containing layer, glucose oxidase may be substituted with other redox enzymes to measure other relevant clinical compounds. For example, lactate oxidase may be used for the in vivo detection of lactate, important in determining if an organ is receiving sufficient oxygen through the blood.
  • Useful redox polymers and methods for producing the sensing layer are described, for example, in U.S. Pat. Nos. 5,264,104; 5,356,786; 5,262,035, and 5,320,725. Additional redox polymers include, for example, poly(1-vinyl imidazole); poly(4-vinyl pyridine); or copolymers of 1-vinyl imidazole such as poly (acrylamide co-1-vinyl imidazole) where the imidazole or pyridine complexes with [Os (bpy)2 Cl]+/2+; [Os (4,4′-dimethyl bipyridine)2Cl]+/2+; [Os (4,4′-dimethyl phenanthroline)2Cl-]+/2+; [Os (4,4′-dimethyoxy phenanthroline)2Cl]+/2+; and [Os (4,4′-dimethoxy bipyridine)2Cl]+/2+; to imidazole rings. The imidazole ring compounds are preferred because their complexes have more reducing redox potentials, i.e., closer to that of the SCE potential. At these more reducing potentials, the rate of electrooxidation of interferants and the current generated thereby.
  • Barrier Layer: The polymeric barrier layer is electrically insulating and limits diffusion of glucose through to the sensing layer. It may be formed, for example, by crosslinking a polyallylamine (PAL) with a polyaziridine (PAZ). Alternatively, PAL may be replaced wholly or in part with a zwitterionic polymer obtained by quaternizing poly(vinylpyridine) with bromoacetate and dialyzing against 0.15M NaCl or by a polyanion such as a polysulfonic acid.
  • The barrier layer may contain a polyanionic polymer, in which the rate of permeation of anionic interferants such as ascorbate and urate is slowed. This layer may also contain a polycation that enhances the retention of the polyanion by electrostatic bonds and improves wetting by the biocompatable layer.
  • Interference Eliminating Layer: As described above, this layer is optional, in that it is not required when a redox polymer having a more reducing potential is used, such as PVI15-dmeOs (Ohara et al., Analytical Chemistry, 1994, 64:2451-2457). At operating potentials of approximately −0.10 to +0.25 for the glucose biosensor, the rate of electrooxidation of interferants such as ascorbate, urate and acetaminophen is very slow relative to that of glucose through its physiological concentration range.
  • When a separate interferant eliminating layer is used, it preferably contains a peroxidase enzyme which may or may-not be preactivated. Such interferant eliminating layers are disclosed, for example, in U.S. Pat. No. 5,356,786, which discloses the structure and function of interferant eliminating biosensors. The glucose biosensor preferably contains lactate oxidase (LOX) in combination with peroxidase in the interferant eliminating layer. However, for biosensors used to detect lactate, glucose oxidase would be used with peroxidase. In a similar manner, the enzyme composition of the interferant eliminating layer may be altered for a specified function.
  • Biocompatable Layer: In general, the biocompatable layer is comprised of hydrogels, e.g., polymeric compositions which contain more than about 20% by weight of water when in equilibrium with a physiological environment such as living tissue or blood. An example is crosslinked poly(ethylene oxide), e.g., poly(ethylene oxide) tetraacrylate. The polymeric compositions must be non-toxic and compatible with living Systems.
  • Method for making multi-layered recessed biosensors: Insulated non-corroding metal or carbon wires that have been etched as described above to contain a recess at the tip, are placed in a block that serves as an X-Y positioner. The wires vertically traverse the block and are held in place, e.g., by pressure. The blocks with the wires can be formed of elements, each element having multiple half-cylinder grooves running vertically. The wires are placed in these grooves and the elements are assembled into the block using screws. For example, the block may be formed of aluminum having equally spaced holes, (900 for a 30×30 array of wires), each hole to contain one wire. The block is positioned under a fixed micronozzle that ejects a fluid in to the recess of the insulated wire.
  • To reduce the requirement of precision in the positioning of the block and the micronozzle, the nozzle is electrically charged, with the wire having an opposite charge, or the wire being grounded or at least having a potential such that there is a potential difference between the nozzle and the wire. Because the nozzle is charged, the microdroplets it ejects are also charged with the same type of charge (positive or negative) as the nozzle. The higher the potential on the nozzle (e.g., versus ground potential), the higher the charge on the ejected microdroplets. If the tip of the wire to be coated is at ground potential or has a charge of the opposite type, the charged microdroplets are guided into the recess to deposit on the electrode, even if the jet of microdroplets is not vertical, i.e., even if the micronozzle is not precisely aligned above the wire's tip.
  • Furthermore, the higher the electrical potential on the nozzle (relative to ground) the greater the charge on the ejected microdroplet. When the charge is high enough, the droplet breaks up into two or more smaller droplets because of electrostatic repulsion of charges on the droplet. Thus, the very small droplets all “drift” (drift meaning transport assisted by an electrical field) to the recessed electrode surface and are collected on it, even if they did not originate in a nozzle precisely aligned with the electrode.
  • This coating method is useful in making any small biosensor, not only those in recessed zones.
  • Clinical Use of the Recessed Biosensors:
  • The recessed biosensors of the present invention have sufficient sensitivity and stability to be used as very small, subcutaneous biosensors for the measurement of clinically relevant compounds such as glucose and lactate. The electrodes accurately measure glucose in the range of about 2-30 μM and lactate in the range of about 0.5-10 mM. One function of the implanted biosensor is to sound an alarm when, for example, a patient's glucose concentration is too low or too high. When pairs of implanted electrodes are used, there are three situations in which an alarm is triggered: low glucose concentration, high glucose concentration; sensor malfunction as determined by a discrepancy between paired readings of the two sensors. A discrepancy sufficient to trigger the alarm may be, for example more than two or three times the standard deviation persisting for a defined period, e.g., not less than ten minutes. Such a system may be useful in sleeping patients, and also in emergency and intensive care hospital rooms, where vital functions are continuously monitored.
  • Another function of the inventive biosensors in to assist diabetics in maintaining their blood glucose levels near normal. Many diabetics now maintain higher than normal blood glucose levels because of danger of coma and death in severe hypoglycemia. However, maintaining blood glucose levels substantially, e.g., approximately 40% or more above normal leads to retinopathy and blindness as well as to kidney failure. Use of the subcutaneous biosensors to frequently, if not continuously, monitor glucose concentrations is desirable so that glucose concentrations can be maintained closer to an optimum level.
  • The subcutaneous biosensors can be used to measure the rate of rise and decline of glucose concentrations after a meal or the administration of glucose (e.g., a glucose tolerance test). The sensors are also useful in feedback loops for automatic or manually controlled maintenance of glucose concentrations within a defined range. For example, when used in conjunction with an insulin pump, a specified amount of insulin is delivered from the pump if the sensor glucose reading is above a set value.
  • In all of these applications, the ability to promptly confirm that the implanted sensor reading is accurate is essential. Prompt confirmation and rapid recalibration are possible only when one-point calibration is valid. Generally, even if a sensor's response is linear through the relevant concentration range, calibration requires at least two blood or fluid samples, withdrawn from the patient at times when the glucose concentration differs. It usually takes several hours for the glucose concentration to change sufficiently to validate proper functioning by two-point calibration. The ability to confirm and recalibrate using only one point is thus a highly desirable feature of the present invention.
  • Redundant sensors (e.g., at least two) are preferred in the clinical application of the subcutaneous biosensors. Such redundancy permits signaling of failure of any one sensor by recognition of an increase in the discrepancy between the readings of the sensors at one time point, e.g., more than two standard deviations apart. The redundant sensors may be implanted near each other or at remote sites.
  • It is preferred that the biosensors be implanted in subcutaneous tissue so as to make the sensor relatively unobtrusive, and at a site where they would not be easily dislodged, e.g., with turning or movement. It is also preferred, when readings are not corrected for temperature (which they generally are) that the sensors be implanted where they are likely to be at body temperature, e.g., near 37° C., and preferably covered by clothing. Convenient sites include the abdomen, inner thigh, arm.
  • Although we describe here continuous current measurement for assaying glucose, the electrical measurement by which the glucose concentration is monitored can be continuous or pulsed. It can be a current measurement, a potential measurement or a measurement of charge. It can be a steady state measurement, where a current or potential that does not substantially change during the measurement is monitored, or it can be a dynamic measurement, e.g., one in which the rate of current or potential change in a given time period is monitored. These measurements require at least one electrode in addition to the sensing electrode. This second electrode can be placed on the skin or can be implanted, e.g., subcutaneously. When a current is measured it is useful to have a potentiostat in the circuit connecting the implanted sensing electrode and the second electrode, that can be a reference electrode, such as an Ag/AgCl electrode. When a current is measured the reference electrode may serve also as the counter electrode. The counter electrode can also be a separate, third electrode, such as a platinum, carbon, palladium or gold electrode.
  • In addition to implanting the sending electrode in the body, fluid from the body, particularly fluid from the subcutaneous region, can be routed to an external sensor. It is preferred in this case to implant in the subcutaneous region a microfiltration giver and pull fluid to an evacuated container, the fluid traversing a cell containing the sensing electrode. Preferably this cell also contains a second electrode, e.g., a reference electrode which may serve also as a counter electrode. Alternatively, the reference and counter electrodes may be separate electrodes. In coulometric measurements only two electrodes, the sensing electrode and the counter electrode are required. The flow of body fluid may be pulsed or continuous. Other than an implanted microfiltration fiber, also a microdialysis fiber may be used, preferably in conjunction with a pump.
  • Increased Stability of the Biosensors:
  • To increase the stability and useful life of the inventive biosensors, it is advantageous to use intrinsically more stable enzymes and redox polymers. However, even if the enzyme and redox polymer degrade in the glucose electrooxidation process by which the signal (current) is generated, it is possible to greatly extend the useful life of the implanted electrodes and reduce the frequency of their required recalibration after implantation.
  • A simple measure by which the life of the implanted electrodes can be extended and the frequency of their required recalibration reduced involves turning the electrodes “on” by applying a bias, i.e., a potential, only during the period of measurement, then turning the biasing potential off or reducing it, so that a lesser current will flow. It is generally sufficient to perform only one measurement every five or even ten minutes, or longer, because glucose concentrations do not change abruptly.
  • Another measure is to lower the glucose flux to the sensing layer much as possible, consistent with maintaining adequate sensitivity and detectivity. Reduction of the glucose flux to the sensing layer reduces the current. Therefore, even though this stabilizes the electrodes, i.e., slows the loss in sensitivity, the flux dependent current must not be excessively reduced. Usually a current of 3-5 nA at 2 mM glucose concentration is adequate. When the glucose flux is lowered by using one or more glucose-flux reducing polymer slayers, such as the PAL/PAZ layer, the lifetime of the sensor is increased.
  • EXAMPLES Example 1
  • Electrode Preparation
  • Electrodes were made of a polyamide-insulated 250 μm diameter gold wire, having an outer diameter (O.D.) of 290 μm (California Fine Wire Co., Grover City, Calif.). Heat shrinkable tubing (RNF 100 3/64” BK and 1/16” BK, Thermofit®, Raychem, Menlo Park, Calif.) and a two component silver epoxy (Epo-tek H2OE; Epoxy Tech, Inc., Billerica, Mass.) were used for electrode preparation.
  • The glucose sensing layer was made by crosslinking a genetically engineered glucose oxidase (rGOX) (35% purity, Chiron Corp., Emeryville, Calif.) with a polymer derived of poly(vinylimidazole) (PVI), made by complexing part of the imidazoles to [Os(bpy)2Cl]+/2+. The resulting redox polymer, termed PVI-Os, was synthesized according to a previously published protocol. (Ohara et al., 1993, Anal. Chem., 65:24). Poly(ethylene glycol) diglycidyl ether 400 (PEDGE; Polysciences, Warrington, Pa.) was used as the crosslinker.
  • The barrier layer between the sensing and interference-eliminating layers was made of polyallylamine (PAL; Polysciences) crosslinked with a polyfunctional aziridine (PAZ) (XAMA-7; Virginia Chemicals, Portsmouth, Va.).
  • The interference-eliminating layer was prepared by co-immobilizing horseradish peroxidase (HRP) type VI (Cat. No. P-8375, 310 U/mg, denoted herein as HRP-VI, Sigma, St. Louis, Mo.) and HRP for immunological assay (No. 814407, min 1000 U/mg, denoted HRP-BM, Boehringer-Mannheim, Indianapolis, Ind.) with lactate oxidase from Pediococcus sp. (Cat. No. 1361, 40 U/mg denoted LOX, Genzyme, Cambridge, Mass.) and a recombinant microbial source (Cat. No. 1381 denoted rLOX, Genzyme). Co-immobilization was performed using sodium periodate (Cat. No. S-1147, Sigma) according to the methods described in Maidan and Heller, 1992, Anal. Chem. 64:2889-2896.
  • The biocompatible layer was made of 10% aqueous poly(ethylene oxide) tetraacrylate (PEO-TA). To form the photocrosslinkable polymer, PEO was acrylated by reaction with acryloyl chloride. The 18,500 g/mol PEO (Polysciences) is a tetrahydroxylated compound by virtue of two hydroxyl groups on a bisphenol A bisepoxide that linked two .alpha., .omega.-hydroxy-terminated 9,000 g/mol PEO units. Acryloyl chloride (Aldrich, Milwaukee, Wis.) in a 2 to 5 molar excess was used to acrylate the polymer (10% w/v PEO in benzene). Triethylamine (Mallinkrodt, Paris, Ky.) was used as a proton acceptor equimolar with the acryloyl chloride.
  • Other chemicals used were bovine serum albumin (BSA) fraction V (Cat. No. A-2153), BSA, ascorbic acid, uric acid, 4-acetaminophenol, L(+)=lactic acid, and hydrogen peroxide 30%, all from Sigma. All chemicals were used as received. Solutions (if not otherwise specified) were made with distilled, deionized water. Glucose monitoring was performed in buffer, in bovine serum (Sigma, Cat. No. S-6648) containing antibiotic-antimycotic solution (Sigma, Cat. No. A-8909) at 37° C. and in rats.
  • Instrumentation
  • In making the recessed gold electrodes, a potentiostat/galvanostat (PAR Model 173, Princeton Applied Research, Princeton, N.J.) operated in a galvanostatic mode, and a sonicator (Fisher scientific, Pittsburgh, Pa.) were used. Cyclic voltammograms were recorded with a potentiostat (PAR Model 273A) and a conventional electrochemical cell having a Pt wire counter and a SCE reference electrode and were evaluated with PAR 270 software. Glucose signals were monitored with a bipotentiostat (Biometra EP 30) and a two channel strip-chart recorder. The recessed electrodes were coated under a microscope (Bausch & Lomb) using a micromanipulator (Narishige, Seacliff, N.Y.). The micropipettes were pulled with a micropipette puller (Narishige). Temperature was controlled with an isothermal circulator (Fisher Scientific).
  • Electrode Preparation:
  • Five cm lengths of polyamide insulated gold wire were cut with a sharp razor blade. Electrical contact was made at one end with silver epoxy to an insulated stainless steel wire and the junction was covered with insulating heat shrinkable tubing. The recess forming electrochemical etching process was carried out in 10 ml of 3M potassium cyamide, with the gold wire as the working electrode and a platinum or gold wire as the counter electrode. The wires were placed in contact with the bottom of the beaker, all electrodes being equidistant from the counter electrode. The beaker was sonicated during the etching procedure. The ends of the gold wires were bent upwards, so that agitation by the sonicator caused the oxygen bubbles formed during the etching process to rise and escape. The electrodes were then thoroughly washed and immersed in water for 30 minutes.
  • A recess 6, i.e., channel, in a polyamide insulated gold wire 2 is formed by electrochemical etching of the gold under galvanostatic control. By controlling the charge, the total amount of gold electrooxidized and dissolved as Au(CN)2 is defined.
  • When the conditions were set so that the CN—transport into the channel and the Au(CN)2-transport out of it are not rate limiting, (e.g., sonicated bath and high concentration of potassium cyamide, at least approximately 0.2M, and preferably 3M), a flat gold wire surface is produced at the bottom of channels with aspect ratios of 0.5 to 2.0. Thus, when the CN—concentration is high enough and the wires are ultrasonically vibrated, the tips of gold wires are flat. Passage of 1.5 coulombs per electrode at 8 mA current produced approximately 125 μm deep cavities or channels. At theoretical efficiency for one-electron oxidation, 3.08 mg of gold would have been etched. The amount of gold actually etched was only 0.076 mg, showing significant CN—or water oxidation.
  • Nevertheless, the process is reproducible, accurate and fast with 20 electrodes being processed in each batch in less than five minutes. The recess-forming procedure was highly reproducible, with a deviation of +/−10 μm found (using an objective micrometer) for a batch of 30 recessed electrodes. Before coating, the electrodes were examined under a microscope for flatness of the gold surface and correct depth.
  • FIG. 1 shows a schematic side view in cross-section of an electrode of the present invention, showing the gold wire 2, insulating coating 4, and recess or channel 6. The recessed gold surfaces were coated by filling of the cavities or channels 6 with aqueous solutions containing the crosslinkable components of the different layers, and their crosslinkers. The solutions were introduced under a microscope with a micropipette (connected to a microsyringe by polyethylene tubing and shrink tubing), using a micromanipulator. After application of each of the individual layers, the electrodes were cured overnight at room temperature, in air.
  • Electrode Structure:
  • The electrodes were prepared by sequentially depositing four layers within the recess or channel 6. The layers were: the sensing layer 8, the insulating layer 10, the interference-eliminating layer 12 and the biocompatible layer 14. The sensing layer, containing “wired” redox enzyme is positioned adjacent to and in contact with the gold wire 2. The insulating layer 10 is positioned between the sensing layer 8 and the peroxidase-based interferant-eliminating layer 12. The biocompatible layer 14 fills the remaining space in the recess 6 and is in contact with the environment outside the electrode. The thin polymer layers are well protected by containment within the polyamide sleeve 4.
  • The sensing layer 8 was made by “wiring” rGOX to the gold electrode through a redox hydrogel to which the enzyme was covalently bound. The electrodes were prepared as follows: 10 mg/ml solutions were made from
  • 1. the PVI-Os redox polymer in water,
  • 2. the crosslinker, PEGDGE, in water, and
  • 3. the enzyme, rGOX, in a 10 mM HEPES solution adjusted to pH 8.15.
  • A redox hydrogel was formed by mixing the three solutions so that the final composition (by weight) was 52% redox polymer, 35% enzyme and 13% crosslinker.
  • The insulating layer 10 prevented electrical contact between the redox hydrogel and the interference eliminating enzymes (HRP and LOX). PAL:PAZ was used as the insulating material. The film was deposited from a solution obtained by mixing in volume ratio of 1/1, 1/2 or 1/3, a PAL solution (4.5 mg in 100 mM HEPES buffer at pH 7.0) and a freshly prepared PAZ solution (30 mg/ml). The PAZ solution was used within 15 minutes of preparation.
  • The interference-eliminating layer 12 was prepared according to a previously published protocol, Maidan and Heller, 1992, Anal. Chem., 64:2889-2896. 50 μl of a 12 mg/ml freshly prepared sodium periodate solution was added to 100 μl of a solution containing 20 mg/ml HRP (HRP-VI or HRP-BM) and 100 mg/ml LOX (LOX or rLOX) in 0.1 M sodium bicarbonate and the mixture was incubated in the dark for two hours. Alternatively, the oxidation of HRP could be carried out prior to adding LOX and crosslinking.
  • The biocompatible layer 14 films were photocrosslinked by exposure to UV light (UVP, Inc., San Gabriel, Calif.; Blak-Ray; spectral peak at 360 nM UV irradiance at the sample 200 mW/cm2) for one minute. The initiator used was 2,2-dimethoxy-2-phenylacetophenone (Aldrich). A solution of 300 mg/ml of the initiator in 1-vinyl-2-pyrrolidinone (Aldrich) was added to the prepolymer mixtures. Approximately 30 μl of the initiator solution was added per ml of 10% w/w aqueous solution of the tetraacrylated PEO. The prepolymers were crosslinked in situ inside the recess of the electrode. The films were prepared by filling the recess with the prepolymer solution twice and exposing the electrode to the UV light source after each time the cavity was filled.
  • In Vitro Testing of Electrodes:
  • In vitro experiments were carried out in batch fashion at 250 and 37° C., using a conventional three electrode electrochemical cell with the enzyme-modified gold wire as the working electrode, a platinum wire as the counter electrode and a saturated calomel reference electrode (SCE). The electrolyte was a 20 mM phosphate buffered-saline solution containing 0.15 M NaCl at pH 7.15. Experiments in serum were performed at 37° C., adding 100 μL antibiotic-antimycotic solution to 10 ml serum. Phosphate buffered-saline and serum were agitated during the experiments. The working potential was +0.3 V versus SCE for experiments with the PVI-Os polymers.
  • Structure and Performance: The depth c of the channel 6 and the thickness of the polymer layers in it controls the mass transport, i.e., flux of glucose, to the sensing layer. By controlling these parameters, the apparent Michaelis constant (Km) is adjusted to about 20-30 mM glucose. The polyimide wall 4 of the channel 6 also protects the four polymer and polymer/enzyme layers 8, 10, 12, 14 against mechanical damage and reduces the hazard of their loss in the body. Because the glucose electrooxidation current is limited by glucose mass transport through the recess 16 and its polymer films 8, 10, 12, 14, rather than by mass transport to the tissue-exposed tip 16, the current is practically insensitive to motion. Evidently, the electrooxidation rate of glucose in the recessed sensing layer 8 is slower than the rate of glucose diffusion to the channel's outer fluid contacting interface.
  • PVI5-Os is preferred as the “wire” of the sensing layer when an interference eliminating layer of HRP and LOX is used, but not in the absence of this layer, i.e., when redox polymers with more reducing redox potential are preferred. The subscript (5) is used to indicate that, on the average, every fifth vinylimidazole mer carries an electron-relaying osmium center. Use of electrodes formed with PVI5-Os and PVI3-Os (every third 1-vinylimidazole mer carrying an osmium center) are compared in FIG. 2, and show higher current density of glucose electrooxidation on electrodes made with PVI5-Os (open triangle) than on those made with PVI3-Os (filled triangles).
  • Depth of the recess and the sensing layer: Channels of 125, 250, and 500 μm depth, were investigated to assess the dependence of the current on the depth of the recess (FIG. 3), with the total amount of PVI5-Os and rGOX being kept constant. Much of the loss in current in the deeper cavities resulted not from reduced glucose mass transport, but from adsorptive retention of part of the enzyme and polymer on the polyamide wall when microdrops of the component solutions were introduced into the recess in the process of making the electrodes. Through repeated rinsing with water, some of the adsorbed polymer and enzyme on the walls were washed onto the electrode surface, increasing the current. The highest currents were seen after five washings. When the thickness of the sensing layer was increased through increasing the number of coatings (FIG. 4) the ratio of current to charge required to electroreduce or electrooxidize the redox polymer in the sensing layer reached a maximum, then dropped. For the preferred 125 μm recess, 10 coatings, producing an approximately 13 μm thick wired-rGOX sensing layer, yielded sensors that had the desired characteristics for in vivo use.
  • The insulating layer: This layer electrically insulates the redox enzymes of the interference eliminating layer (HRP and LOX) from the “wired” rGOX layer and limits the glucose flux to the sensing layer, thereby extending the useful life of the electrode. PAL crosslinked with PAZ, forming a polycationic network at pH 7.09 is preferred. The best results, i.e., best stability of current outputs, were obtained using 1:2 PAL:PAZ (FIG. 5), with three coatings applied to form an approximately 7 μm thick crosslinked film.
  • The interference eliminating layer: Interferants, particularly ascorbate, urate, and acetaminophenol, are oxidized in the third layer, containing LOX and HRP. In this layer, lactate, the typical concentration of which in blood is 1 mM, reacts with O2 to form H2O2 and pyruvate. H2O2, in the presence of HRP, oxidizes ascorbate, urate, and acetaminophenol, being reduced to water. The preferred coimmobilization process involved two separate steps: periodate oxidation of oligosaccharide functions of HRP to aldehydes, followed by mixing with LOX and formation of multiple Schiff bases between HRP-aldehydes and LOX amines (e.g. lysines) and between HRP aldehydes and amines. The thickness of the interference eliminating layer is approximately 85 μm and is made by applying successive coatings, e.g., about six coatings. FIG. 6 shows that electrooxidizable interferants were eliminated in the presence of lactate at physiological levels. LOX slowly lost its activity in the crosslinked HRP-LOX layer. This led to degradation of the ability of the layer to eliminate interferants. After 36 hours of operation at 37° C., a measurable current increment was noted when enough ascorbate was added to produce a 0.1 mM concentration.
  • The biocompatible layer: A preferred biocompatible layer consists, for example, of photocrosslinked tetraacrylated 18,500 Da poly(ethylene oxide) (Pathak et al., 1993, J. Am. Chem. Soc., 114:8311-8312). The thickness of this layer, made by sequential photo-crosslinking of two coatings, is about 20 μm. One minute UV exposure required for the photocrosslinking process reduced the sensitivity by 16+/−2%.
  • Example 2
  • In Vivo Use of Sensor
  • The objective of this experiment was to establish the validity of a one-point in vivo calibration. Two sensors were simultaneously implanted subcutaneously in a rat, one on the thorax, the second between the scapulae. To make the difference between the blood sampled and the subcutaneous fluid proved with the sensors as extreme as possible, i.e., to probe whether the one-point calibration holds even if the organs sampled are different and the sampling sites are remote, blood was withdrawn from the tail vein. Blood glucose levels were periodically measured in withdrawn samples, while the absolute uncorrected sensor current output was continuously monitored.
  • In vivo experiments (6-10 hours) were carried out in 300 g male Sprague-Dawley rats. The rats were fasted overnight and prior to the experiment were anaesthetized with an intraperitoneal (i.p.) injection of sodium pentobarbital (65 mg/kg rat wt). An i.p. injection of atropine sulfate (166 mg/kg rat wt) was then administered to suppress respiratory depression. Once the rat was anaesthetized, a portion of the rat's abdomen was shaved, coated with a conductive gel, and an Ag/AgCl surface skin reference electrode was attached. This electrode served also as the counter electrode. Sensors were then implanted subcutaneously using a 22 gauge Per-Q-Cath Introducer (Gesco International, San Antonio, Tex.) on the rat's thorax, or subcutaneously in the intrascepular area through a small surgical incision. The sensors were taped to the skin to avoid sensor movement. The sensors, along with the reference electrode, were connected to an in-house built bipotentiostat. The operating potential of the sensors was 0.3 V vs. Ag/AgCl, with the Ag/AgCl electrode serving as both the reference counter electrode. Sensor readings were collected using a data logger (Rustrak Ranger, East Greenwich, R.I.) and at the end of the experiment were transferred to a computer. During the experiment, the rat's body temperature was maintained at 37° C. by a homeostatic blanket. The sensors were allowed to reach a basal signal level for at least one hour before blood sampling was started. Blood samples were obtained from the tail vein and all blood samples were analyzed using a glucose analyzer (YSI, Inc., Yellow Springs, Ohio; Model 23A).
  • Approximately thirty minutes after the start of blood sampling, an i.p. glucose infusion was started using a syringe pump (Harvard Apparatus, South Natick, Mass.) at a rate of 120 mg glucose/min kg rat wt. The glucose infusion was maintained for approximately one hour.
  • As seen in FIG. 7, at 410 min the current dropped precipitously. Such a drop was observed in other measurements with subcutaneously implanted electrodes between 400 and 600 min, but was never observed in electrodes operated in buffer at 37° C. When the failed electrodes were withdrawn and retested in buffer, most of their original sensitivity was found to be intact. The cause for this apparent deactivation was failure of the counter/reference Ag/AgCl electrode on the rat's skin to make good electrolytic contact, and was not due to any failure of the implanted sensor. Using an arbitrarily chosen point to calculate a calibration curve for each electrode, i.e., one blood glucose level determination and one current measurement to establish the scales, all the data from FIG. 7 were plotted in a Clarke-type, (Clarke et al., 1987, Diabetes Care, 5:622-627) clinical grid (FIG. 8), without further correction. In this analysis, points falling in region A of the grid are considered clinically accurate, while those in region B are considered clinically correct. Points falling in region C are not correct, but would not lead to improper treatment. Points in regions D and E are incorrect and if treatment would rely on these, it would be improper.
  • All of the points, from both electrodes, were in regions A and B, with 43 of the 48 points being in region A. The three points in region B near 100 mg/dl glucose, for the electrode implanted between the scapulae, were the last three points of the experiment, at about 410 min. Notwithstanding the failure mode at 400-600 min because of poor electrolytic contact of the counter/reference electrode with the skin and failure after 36 hours by deactivation of the lactate oxidase, resulting in loss of interference elimination, one-point calibration is shown here to be practical. After such calibration, the readings of the subcutaneous sensors provide, without any correction, clinically useful estimates of blood glucose levels.
  • FIG. 9 shows the distribution of all possible. correlations obtained when each of the 24 glucose analyses was used for single point calibration of either implanted electrode. There are 2×24×24=1152 points in the distribution. Of these, 78% are in region A, 15% are in region B, 1% in region C, 6% are in region D, and no points are in region E.
  • In FIG. 10, we tested for the improvement of the single point calibration through using redundant electrodes. First, the readings of electrode A were normalized with respect to those of electrode B by multiplying each reading by the average output of electrode B divided by the average output of electrode A. Next the standard deviation was calculated for the differences between the 24 sets of readings of implanted electrode B and corrected readings of implanted electrode A. Then, all those sets of readings that differed by more than the standard deviation were rejected. The number of sets was reduced thereby from 24 to 11; 82% of the points were in region A, 17% in region B, 1% in region D, and no points in regions C and E. The distribution demonstrates that the sensors can be calibrated through a single independent measurement of the glucose concentration in a withdrawn blood sample. They also demonstrate the improvement in clinical accuracy resulting from the use of redundant subcutaneous sensors. The selection of those data points that differed by less than the standard deviation for the entire set led to a sixfold reduction in the probability of clinically erring in a decision based on readings of the implanted sensors.
  • Stability and Other Characteristics:
  • In order to improve the stability, more thermostable recombinant GOX, (rGOX; Heller, 1992, J. Phys. Chem., 96:3579-3587) rather than GOX is used in the sensor and glucose transport is reduced to make the sensor current diffusion, not enzyme turnover, limited. The glucose flux is attenuated by the three outer layers and the sensing layer itself. Because the sensing layer contains a large excess of glucose oxidase, its activity greatly exceeds that needed for electrooxidizing the attenuated glucose flux, and the sensor's stability is improved.
  • The stability can be tested by methods known, for example, tested in the presence of 0.1 mM ascorbate in 10 mM glucose at 37° C. The current output of a typical optimized electrode was about 35 nA and the apparent Km, derived from an Eadie-Hofstee plot, was about 20 mM (Table 1). The 10-90% response time was approximately one minute.
  • As expected, and as can be seen in FIG. 5, with thinner films the glucose mass transport was increased, i.e., the current was higher, while for thicker films the stability was improved. Because of the high sensitivity of thin sensing film (approximately 1 μm) electrodes (less than 10−2A cm−2 M−1), an order of magnitude decrease in sensitivity could be traded for stability, while the currents remained high enough to be easily measured.
  • As seen in FIG. 5, the sensitivity of the stabilized sensors does not change by more than +5% for 72 hours of operation at 37° C. After a small initial decrease in sensitivity, it increased to a maximum after 40 hours and the final 72 hour sensitivity was almost identical with the initial.
  • The characteristics of the electrodes of the present invention are summarized in Table 1. Each entry represents an average value for five tested electrodes. Baseline currents are typically less than 0.5 nA and the noise less than 10 pA. The currents observed throughout the physiological glucose concentration range (2-20 mM) exceed the noise equivalent current by at least a factor of 100. The apparent Km is 20 mM, and the 10% to 90% response time is, for aged electrodes, about 90 seconds at the lowest physiologically relevant glucose concentration (2 mM) and 20 seconds at the highest (20 mM).
  • The baseline of nil at 0 mM glucose is stable for 36 hours in the presence of 0.1 mM ascorbate. The stability observed and the existence of a valid zero-point in the presence of interferants suggest that the sensor can be used in vivo for 72 hours and tested/recalibrated in vivo through a single point calibration, i.e., by withdrawing only a single sample of blood for independent analysis.
    TABLE 1
    SENSOR CHARACTERISTICS
    Km app(mM) Km app(mM) Current
    i(nA) j(μA/cm2) EH LB tr(s) Variance (%)
    33.9 69.1 18.5 33.4 30-90 5.0

    where:
    -I is the current measured at 37 ° C. and 10 mM glucose concentration
    -j is the current density measured at 37 ° C. at 10 mM glucose concentration
    KM app is the apparent Michaelis-Menton coefficient determined from an electrochemical Eadie-Hoffstee (EH) or Lineweaver-Burk (LB) plot
    -tr is the 10-90% risetime, 90s for 2 mM and 30 s for 20 mH glucose concentration.
    -Current Variance is the maximum deviation from the mean value, measured during the 72 hours test, conducted in 10 mM glucose in the presence of interferants. The current was continuously monitored at 37 ° C.
  • The foregoing examples are designed to illustrate certain aspects of the present invention. The examples are not intended to be comprehensive of all features and all embodiments of the present invention, and should not be construed as limiting the claims presented herein.

Claims (22)

1. A glucose monitoring device having a stacked construction comprising a first electrode, a second electrode, a glucose-responsive enzyme, and a substrate, wherein the first and second electrodes, and the substrate are positioned in a stacked construction, and further, wherein at least a portion of the device is configured for positioning below a skin surface.
2. The device of claim 1 further wherein the enzyme is a wired enzyme.
3. The device of claim 2 wherein the enzyme is adjacent at least one of the first and second electrodes.
4. The device of claim 1 comprising a membrane.
5. The device of claim 4 wherein the membrane is formed in situ.
6. The device of claim 5, wherein the membrane is a mass transport limiting membrane.
7. The device of claim 1 wherein the device includes a part that is connectable to a device to receive glucose data from the glucose monitoring device when connected.
8. The device of claim 1 wherein the first and the second electrodes include a working electrode, and a reference electrode or a reference/counter electrode, respectively.
9. The device of claim 1 including a third electrode.
10. The device of claim 9 wherein the first electrode, the second electrode and the third electrode include a working electrode, a reference electrode, and a counter electrode.
11. The device of claim 9 wherein the device includes two working electrodes.
12. A transcutaneous sensor, comprising:
a first layer;
a first conducting layer at least a portion of which is positioned in contact with at least a first portion of the first layer;
a second layer having a first surface and a second surface, at least a portion of the first surface positioned in contact with at least a first portion of the first conducting layer; and
a second conducting layer at least a portion of which is positioned in contact with at least a portion of the second surface of the second layer.
13. The sensor of claim 12 wherein the first and the second layers include nonconducting material.
14. The sensor of claim 12 wherein at least one of the conducting layers includes a working electrode.
15. The sensor of claim 12 wherein the second layer is substantially disposed between the first conducting layer and the second conducting layer.
16. The sensor of claim 12 comprising an analyte responsive enzyme.
17. The sensor of claim 16, wherein the enzyme is a wired enzyme.
18. The sensor of claim 12, comprising a redox compound.
19. The sensor of claim 18, wherein the redox compound includes a redox polymer.
20. The sensor of claim 18, comprising a mass transport limiting layer.
21. The sensor of claim 12, wherein at least another portion of the first conducting layer is in fluid contact with an analyte of a patient.
22. The sensor of claim 12, wherein the device comprises a portion connectable to a device for measurement of the signal generated by the sensor.
US11/695,611 1991-03-04 2007-04-03 Subcutaneous Glucose Electrode Abandoned US20070218097A1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US11/695,611 US20070218097A1 (en) 1991-03-04 2007-04-03 Subcutaneous Glucose Electrode

Applications Claiming Priority (11)

Application Number Priority Date Filing Date Title
US66405491A 1991-03-04 1991-03-04
US08/161,682 US5356786A (en) 1991-03-04 1993-12-02 Interferant eliminating biosensor
US08/299,526 US5593852A (en) 1993-12-02 1994-09-01 Subcutaneous glucose electrode
US08/767,110 US6284478B1 (en) 1993-12-02 1996-12-04 Subcutaneous glucose electrode
US09/356,102 US6121009A (en) 1993-12-02 1999-07-16 Electrochemical analyte measurement system
US09/477,053 US6162611A (en) 1993-12-02 2000-01-03 Subcutaneous glucose electrode
US09/668,221 US6329161B1 (en) 1993-12-02 2000-09-22 Subcutaneous glucose electrode
US09/997,808 US6514718B2 (en) 1991-03-04 2001-11-29 Subcutaneous glucose electrode
US10/353,341 US6881551B2 (en) 1991-03-04 2003-01-28 Subcutaneous glucose electrode
US11/109,379 US20050287620A1 (en) 1991-03-04 2005-04-19 Method of determining analyte level using subcutaneous electrode
US11/695,611 US20070218097A1 (en) 1991-03-04 2007-04-03 Subcutaneous Glucose Electrode

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US11/109,379 Continuation US20050287620A1 (en) 1991-03-04 2005-04-19 Method of determining analyte level using subcutaneous electrode

Publications (1)

Publication Number Publication Date
US20070218097A1 true US20070218097A1 (en) 2007-09-20

Family

ID=23155192

Family Applications (30)

Application Number Title Priority Date Filing Date
US08/299,526 Expired - Lifetime US5593852A (en) 1991-03-04 1994-09-01 Subcutaneous glucose electrode
US08/767,110 Expired - Lifetime US6284478B1 (en) 1991-03-04 1996-12-04 Subcutaneous glucose electrode
US09/229,235 Expired - Lifetime US5965380A (en) 1993-12-02 1999-01-12 Subcutaneous glucose electrode
US09/334,480 Expired - Lifetime US6083710A (en) 1993-12-02 1999-06-16 Electrochemical analyte measurement system
US09/356,102 Expired - Lifetime US6121009A (en) 1991-03-04 1999-07-16 Electrochemical analyte measurement system
US09/477,053 Expired - Lifetime US6162611A (en) 1991-03-04 2000-01-03 Subcutaneous glucose electrode
US09/668,221 Expired - Lifetime US6329161B1 (en) 1991-03-04 2000-09-22 Subcutaneous glucose electrode
US09/997,808 Expired - Fee Related US6514718B2 (en) 1991-03-04 2001-11-29 Subcutaneous glucose electrode
US10/353,341 Expired - Fee Related US6881551B2 (en) 1991-03-04 2003-01-28 Subcutaneous glucose electrode
US11/109,379 Abandoned US20050287620A1 (en) 1991-03-04 2005-04-19 Method of determining analyte level using subcutaneous electrode
US11/182,634 Expired - Fee Related US7462264B2 (en) 1991-03-04 2005-07-15 Subcutaneous glucose electrode
US11/681,713 Expired - Fee Related US8588881B2 (en) 1991-03-04 2007-03-02 Subcutaneous glucose electrode
US11/695,612 Expired - Fee Related US8741590B2 (en) 1991-03-04 2007-04-03 Subcutaneous glucose electrode
US11/695,611 Abandoned US20070218097A1 (en) 1991-03-04 2007-04-03 Subcutaneous Glucose Electrode
US12/551,448 Abandoned US20100030051A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,411 Abandoned US20100030047A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,497 Abandoned US20100059372A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,513 Abandoned US20100072064A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,504 Abandoned US20100059373A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,222 Abandoned US20100121166A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,491 Abandoned US20100059371A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,265 Abandoned US20100030046A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,283 Abandoned US20100030044A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,439 Abandoned US20100030050A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,192 Abandoned US20100121165A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,480 Abandoned US20100059370A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,419 Abandoned US20100030048A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,427 Abandoned US20100030049A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,510 Abandoned US20100072063A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/615,009 Abandoned US20100051479A1 (en) 1991-03-04 2009-11-09 Subcutaneous Glucose Electrode

Family Applications Before (13)

Application Number Title Priority Date Filing Date
US08/299,526 Expired - Lifetime US5593852A (en) 1991-03-04 1994-09-01 Subcutaneous glucose electrode
US08/767,110 Expired - Lifetime US6284478B1 (en) 1991-03-04 1996-12-04 Subcutaneous glucose electrode
US09/229,235 Expired - Lifetime US5965380A (en) 1993-12-02 1999-01-12 Subcutaneous glucose electrode
US09/334,480 Expired - Lifetime US6083710A (en) 1993-12-02 1999-06-16 Electrochemical analyte measurement system
US09/356,102 Expired - Lifetime US6121009A (en) 1991-03-04 1999-07-16 Electrochemical analyte measurement system
US09/477,053 Expired - Lifetime US6162611A (en) 1991-03-04 2000-01-03 Subcutaneous glucose electrode
US09/668,221 Expired - Lifetime US6329161B1 (en) 1991-03-04 2000-09-22 Subcutaneous glucose electrode
US09/997,808 Expired - Fee Related US6514718B2 (en) 1991-03-04 2001-11-29 Subcutaneous glucose electrode
US10/353,341 Expired - Fee Related US6881551B2 (en) 1991-03-04 2003-01-28 Subcutaneous glucose electrode
US11/109,379 Abandoned US20050287620A1 (en) 1991-03-04 2005-04-19 Method of determining analyte level using subcutaneous electrode
US11/182,634 Expired - Fee Related US7462264B2 (en) 1991-03-04 2005-07-15 Subcutaneous glucose electrode
US11/681,713 Expired - Fee Related US8588881B2 (en) 1991-03-04 2007-03-02 Subcutaneous glucose electrode
US11/695,612 Expired - Fee Related US8741590B2 (en) 1991-03-04 2007-04-03 Subcutaneous glucose electrode

Family Applications After (16)

Application Number Title Priority Date Filing Date
US12/551,448 Abandoned US20100030051A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,411 Abandoned US20100030047A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,497 Abandoned US20100059372A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,513 Abandoned US20100072064A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,504 Abandoned US20100059373A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,222 Abandoned US20100121166A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,491 Abandoned US20100059371A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,265 Abandoned US20100030046A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,283 Abandoned US20100030044A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,439 Abandoned US20100030050A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,192 Abandoned US20100121165A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,480 Abandoned US20100059370A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,419 Abandoned US20100030048A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,427 Abandoned US20100030049A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/551,510 Abandoned US20100072063A1 (en) 1991-03-04 2009-08-31 Subcutaneous Glucose Electrode
US12/615,009 Abandoned US20100051479A1 (en) 1991-03-04 2009-11-09 Subcutaneous Glucose Electrode

Country Status (7)

Country Link
US (30) US5593852A (en)
EP (1) EP0778897B1 (en)
JP (1) JP3679121B2 (en)
AU (1) AU3501695A (en)
DE (1) DE69533260T2 (en)
ES (1) ES2225845T3 (en)
WO (1) WO1996006947A1 (en)

Cited By (88)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080086042A1 (en) * 2006-10-04 2008-04-10 Dexcom, Inc. Analyte sensor
US7761130B2 (en) 2003-07-25 2010-07-20 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US7766829B2 (en) 2005-11-04 2010-08-03 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US7783333B2 (en) 2004-07-13 2010-08-24 Dexcom, Inc. Transcutaneous medical device with variable stiffness
US7792562B2 (en) 1997-03-04 2010-09-07 Dexcom, Inc. Device and method for determining analyte levels
US7811231B2 (en) 2002-12-31 2010-10-12 Abbott Diabetes Care Inc. Continuous glucose monitoring system and methods of use
US7828728B2 (en) 2003-07-25 2010-11-09 Dexcom, Inc. Analyte sensor
US7857760B2 (en) 2004-07-13 2010-12-28 Dexcom, Inc. Analyte sensor
US7860544B2 (en) 1998-04-30 2010-12-28 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US7885697B2 (en) 2004-07-13 2011-02-08 Dexcom, Inc. Transcutaneous analyte sensor
US7920907B2 (en) 2006-06-07 2011-04-05 Abbott Diabetes Care Inc. Analyte monitoring system and method
US7928850B2 (en) 2007-05-08 2011-04-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US7976778B2 (en) 2001-04-02 2011-07-12 Abbott Diabetes Care Inc. Blood glucose tracking apparatus
US7996054B2 (en) 1998-03-04 2011-08-09 Abbott Diabetes Care Inc. Electrochemical analyte sensor
US8050731B2 (en) 2002-05-22 2011-11-01 Dexcom, Inc. Techniques to improve polyurethane membranes for implantable glucose sensors
US8064977B2 (en) 2002-05-22 2011-11-22 Dexcom, Inc. Silicone based membranes for use in implantable glucose sensors
US8066639B2 (en) 2003-06-10 2011-11-29 Abbott Diabetes Care Inc. Glucose measuring device for use in personal area network
US8103456B2 (en) 2009-01-29 2012-01-24 Abbott Diabetes Care Inc. Method and device for early signal attenuation detection using blood glucose measurements
US8112240B2 (en) 2005-04-29 2012-02-07 Abbott Diabetes Care Inc. Method and apparatus for providing leak detection in data monitoring and management systems
US8123686B2 (en) 2007-03-01 2012-02-28 Abbott Diabetes Care Inc. Method and apparatus for providing rolling data in communication systems
US8149117B2 (en) 2007-05-08 2012-04-03 Abbott Diabetes Care Inc. Analyte monitoring system and methods
USRE43399E1 (en) 2003-07-25 2012-05-22 Dexcom, Inc. Electrode systems for electrochemical sensors
US8226891B2 (en) 2006-03-31 2012-07-24 Abbott Diabetes Care Inc. Analyte monitoring devices and methods therefor
US8255033B2 (en) 2003-07-25 2012-08-28 Dexcom, Inc. Oxygen enhancing membrane systems for implantable devices
US8275438B2 (en) 2006-10-04 2012-09-25 Dexcom, Inc. Analyte sensor
US8277713B2 (en) 2004-05-03 2012-10-02 Dexcom, Inc. Implantable analyte sensor
US8287454B2 (en) 1998-04-30 2012-10-16 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8298142B2 (en) 2006-10-04 2012-10-30 Dexcom, Inc. Analyte sensor
US8346337B2 (en) 1998-04-30 2013-01-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8364230B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US8364231B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US8364229B2 (en) 2003-07-25 2013-01-29 Dexcom, Inc. Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise
US8396528B2 (en) 2008-03-25 2013-03-12 Dexcom, Inc. Analyte sensor
US8425417B2 (en) 2003-12-05 2013-04-23 Dexcom, Inc. Integrated device for continuous in vivo analyte detection and simultaneous control of an infusion device
US8425416B2 (en) 2006-10-04 2013-04-23 Dexcom, Inc. Analyte sensor
US8447376B2 (en) 2006-10-04 2013-05-21 Dexcom, Inc. Analyte sensor
US8449464B2 (en) 2006-10-04 2013-05-28 Dexcom, Inc. Analyte sensor
US8456301B2 (en) 2007-05-08 2013-06-04 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8465425B2 (en) 1998-04-30 2013-06-18 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8478377B2 (en) 2006-10-04 2013-07-02 Dexcom, Inc. Analyte sensor
US8509871B2 (en) 2001-07-27 2013-08-13 Dexcom, Inc. Sensor head for use with implantable devices
US8560039B2 (en) 2008-09-19 2013-10-15 Dexcom, Inc. Particle-containing membrane and particulate electrode for analyte sensors
US8562528B2 (en) 2006-10-04 2013-10-22 Dexcom, Inc. Analyte sensor
US8562558B2 (en) 2007-06-08 2013-10-22 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US8583204B2 (en) 2008-03-28 2013-11-12 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US8588881B2 (en) 1991-03-04 2013-11-19 Abbott Diabetes Care Inc. Subcutaneous glucose electrode
US8593109B2 (en) 2006-03-31 2013-11-26 Abbott Diabetes Care Inc. Method and system for powering an electronic device
US8612159B2 (en) 1998-04-30 2013-12-17 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8626257B2 (en) 2003-08-01 2014-01-07 Dexcom, Inc. Analyte sensor
US8652043B2 (en) 2001-01-02 2014-02-18 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8665091B2 (en) 2007-05-08 2014-03-04 Abbott Diabetes Care Inc. Method and device for determining elapsed sensor life
US8682408B2 (en) 2008-03-28 2014-03-25 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US8688188B2 (en) 1998-04-30 2014-04-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8732188B2 (en) 2007-02-18 2014-05-20 Abbott Diabetes Care Inc. Method and system for providing contextual based medication dosage determination
US8744546B2 (en) 2005-05-05 2014-06-03 Dexcom, Inc. Cellulosic-based resistance domain for an analyte sensor
US8771183B2 (en) 2004-02-17 2014-07-08 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US8828201B2 (en) 2009-07-02 2014-09-09 Dexcom, Inc. Analyte sensors and methods of manufacturing same
US8886273B2 (en) 2003-08-01 2014-11-11 Dexcom, Inc. Analyte sensor
US8900431B2 (en) 2008-08-27 2014-12-02 Edwards Lifesciences Corporation Analyte sensor
US8930203B2 (en) 2007-02-18 2015-01-06 Abbott Diabetes Care Inc. Multi-function analyte test device and methods therefor
US8929968B2 (en) 2003-12-05 2015-01-06 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8974386B2 (en) 1998-04-30 2015-03-10 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8993331B2 (en) 2009-08-31 2015-03-31 Abbott Diabetes Care Inc. Analyte monitoring system and methods for managing power and noise
US9066695B2 (en) 1998-04-30 2015-06-30 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9226701B2 (en) 2009-04-28 2016-01-05 Abbott Diabetes Care Inc. Error detection in critical repeating data in a wireless sensor system
US9314195B2 (en) 2009-08-31 2016-04-19 Abbott Diabetes Care Inc. Analyte signal processing device and methods
US9320461B2 (en) 2009-09-29 2016-04-26 Abbott Diabetes Care Inc. Method and apparatus for providing notification function in analyte monitoring systems
US9351677B2 (en) 2009-07-02 2016-05-31 Dexcom, Inc. Analyte sensor with increased reference capacity
US9549692B2 (en) 2011-08-26 2017-01-24 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US9763609B2 (en) 2003-07-25 2017-09-19 Dexcom, Inc. Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise
US9968306B2 (en) 2012-09-17 2018-05-15 Abbott Diabetes Care Inc. Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems
US9980669B2 (en) 2011-11-07 2018-05-29 Abbott Diabetes Care Inc. Analyte monitoring device and methods
US9986942B2 (en) 2004-07-13 2018-06-05 Dexcom, Inc. Analyte sensor
US10610135B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10791928B2 (en) 2007-05-18 2020-10-06 Dexcom, Inc. Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise
US10813577B2 (en) 2005-06-21 2020-10-27 Dexcom, Inc. Analyte sensor
US10835672B2 (en) 2004-02-26 2020-11-17 Dexcom, Inc. Integrated insulin delivery system with continuous glucose sensor
US10966609B2 (en) 2004-02-26 2021-04-06 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US10980461B2 (en) 2008-11-07 2021-04-20 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US11000215B1 (en) 2003-12-05 2021-05-11 Dexcom, Inc. Analyte sensor
US11246990B2 (en) 2004-02-26 2022-02-15 Dexcom, Inc. Integrated delivery device for continuous glucose sensor
US11331022B2 (en) 2017-10-24 2022-05-17 Dexcom, Inc. Pre-connected analyte sensors
US11350862B2 (en) 2017-10-24 2022-06-07 Dexcom, Inc. Pre-connected analyte sensors
US11399745B2 (en) 2006-10-04 2022-08-02 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US11633133B2 (en) 2003-12-05 2023-04-25 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US11730407B2 (en) 2008-03-28 2023-08-22 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US11793936B2 (en) 2009-05-29 2023-10-24 Abbott Diabetes Care Inc. Medical device antenna systems having external antenna configurations
US11918354B2 (en) 2019-12-31 2024-03-05 Dexcom, Inc. Particle-containing membrane and particulate electrode for analyte sensors

Families Citing this family (899)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH04278450A (en) 1991-03-04 1992-10-05 Adam Heller Biosensor and method for analyzing subject
US5956501A (en) * 1997-01-10 1999-09-21 Health Hero Network, Inc. Disease simulation system and method
US20040062759A1 (en) * 1995-07-12 2004-04-01 Cygnus, Inc. Hydrogel formulations for use in electroosmotic extraction and detection of glucose
US6261440B1 (en) * 1995-12-18 2001-07-17 Abbott Laboratories Interference free biosensor
SE9700384D0 (en) * 1997-02-04 1997-02-04 Biacore Ab Analytical method and apparatus
ATE227844T1 (en) 1997-02-06 2002-11-15 Therasense Inc SMALL VOLUME SENSOR FOR IN-VITRO DETERMINATION
US6862465B2 (en) 1997-03-04 2005-03-01 Dexcom, Inc. Device and method for determining analyte levels
US7192450B2 (en) * 2003-05-21 2007-03-20 Dexcom, Inc. Porous membranes for use with implantable devices
US20050033132A1 (en) 1997-03-04 2005-02-10 Shults Mark C. Analyte measuring device
US7657297B2 (en) 2004-05-03 2010-02-02 Dexcom, Inc. Implantable analyte sensor
US7899511B2 (en) 2004-07-13 2011-03-01 Dexcom, Inc. Low oxygen in vivo analyte sensor
US8527026B2 (en) 1997-03-04 2013-09-03 Dexcom, Inc. Device and method for determining analyte levels
US6741877B1 (en) 1997-03-04 2004-05-25 Dexcom, Inc. Device and method for determining analyte levels
US9155496B2 (en) * 1997-03-04 2015-10-13 Dexcom, Inc. Low oxygen in vivo analyte sensor
US6060327A (en) 1997-05-14 2000-05-09 Keensense, Inc. Molecular wire injection sensors
US6699667B2 (en) 1997-05-14 2004-03-02 Keensense, Inc. Molecular wire injection sensors
US7220550B2 (en) * 1997-05-14 2007-05-22 Keensense, Inc. Molecular wire injection sensors
US6071391A (en) * 1997-09-12 2000-06-06 Nok Corporation Enzyme electrode structure
WO1999017095A1 (en) 1997-09-30 1999-04-08 M-Biotech, Inc. Biosensor
US6036924A (en) 1997-12-04 2000-03-14 Hewlett-Packard Company Cassette of lancet cartridges for sampling blood
US6579690B1 (en) * 1997-12-05 2003-06-17 Therasense, Inc. Blood analyte monitoring through subcutaneous measurement
US8071384B2 (en) 1997-12-22 2011-12-06 Roche Diagnostics Operations, Inc. Control and calibration solutions and methods for their use
US7407811B2 (en) * 1997-12-22 2008-08-05 Roche Diagnostics Operations, Inc. System and method for analyte measurement using AC excitation
US7390667B2 (en) * 1997-12-22 2008-06-24 Roche Diagnostics Operations, Inc. System and method for analyte measurement using AC phase angle measurements
US6479015B1 (en) 1998-03-03 2002-11-12 Pepex Biomedical, Llc Apparatus for monitoring a level of a chemical species in a body fluid
US6103033A (en) * 1998-03-04 2000-08-15 Therasense, Inc. Process for producing an electrochemical biosensor
US6391005B1 (en) 1998-03-30 2002-05-21 Agilent Technologies, Inc. Apparatus and method for penetration with shaft having a sensor for sensing penetration depth
US6294281B1 (en) 1998-06-17 2001-09-25 Therasense, Inc. Biological fuel cell and method
US6251260B1 (en) 1998-08-24 2001-06-26 Therasense, Inc. Potentiometric sensors for analytic determination
US20060202859A1 (en) * 1998-10-08 2006-09-14 Mastrototaro John J Telemetered characteristic monitor system and method of using the same
ATE514372T1 (en) * 1998-10-08 2011-07-15 Medtronic Minimed Inc LICENSE PLATE MONITORING SYSTEM WITH REMOTE MEASUREMENT
US6591125B1 (en) 2000-06-27 2003-07-08 Therasense, Inc. Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator
US6338790B1 (en) * 1998-10-08 2002-01-15 Therasense, Inc. Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator
US7766873B2 (en) 1998-10-29 2010-08-03 Medtronic Minimed, Inc. Method and apparatus for detecting occlusions in an ambulatory infusion pump
US7621893B2 (en) 1998-10-29 2009-11-24 Medtronic Minimed, Inc. Methods and apparatuses for detecting occlusions in an ambulatory infusion pump
US6424847B1 (en) 1999-02-25 2002-07-23 Medtronic Minimed, Inc. Glucose monitor calibration methods
JP2002542498A (en) * 1999-04-22 2002-12-10 シグナス, インコーポレイテッド Methods and devices for removing interfering species
US6514689B2 (en) 1999-05-11 2003-02-04 M-Biotech, Inc. Hydrogel biosensor
US6475750B1 (en) 1999-05-11 2002-11-05 M-Biotech, Inc. Glucose biosensor
US7806886B2 (en) 1999-06-03 2010-10-05 Medtronic Minimed, Inc. Apparatus and method for controlling insulin infusion with state variable feedback
AU5747100A (en) * 1999-06-18 2001-01-09 Therasense, Inc. Mass transport limited in vivo analyte sensor
GB9918839D0 (en) * 1999-08-11 1999-10-13 Univ Manchester Sensor devices and analytical methods for their use
US7045054B1 (en) 1999-09-20 2006-05-16 Roche Diagnostics Corporation Small volume biosensor for continuous analyte monitoring
US20050103624A1 (en) * 1999-10-04 2005-05-19 Bhullar Raghbir S. Biosensor and method of making
WO2001025474A2 (en) * 1999-10-07 2001-04-12 Pepex Biomedical, Llc Sensor for measuring a bioanalyte such as lactate
US20060091006A1 (en) * 1999-11-04 2006-05-04 Yi Wang Analyte sensor with insertion monitor, and methods
US6616819B1 (en) * 1999-11-04 2003-09-09 Therasense, Inc. Small volume in vitro analyte sensor and methods
DK1230249T3 (en) 1999-11-15 2004-08-30 Therasense Inc Transition metal complexes with bidentate ligand having an imidazole ring
US8444834B2 (en) 1999-11-15 2013-05-21 Abbott Diabetes Care Inc. Redox polymers for use in analyte monitoring
US8268143B2 (en) * 1999-11-15 2012-09-18 Abbott Diabetes Care Inc. Oxygen-effect free analyte sensor
US6484045B1 (en) 2000-02-10 2002-11-19 Medtronic Minimed, Inc. Analyte sensor and method of making the same
US7003336B2 (en) 2000-02-10 2006-02-21 Medtronic Minimed, Inc. Analyte sensor method of making the same
US20030060765A1 (en) * 2000-02-16 2003-03-27 Arthur Campbell Infusion device menu structure and method of using the same
US7890295B2 (en) * 2000-02-23 2011-02-15 Medtronic Minimed, Inc. Real time self-adjusting calibration algorithm
EP1309856A2 (en) * 2000-03-01 2003-05-14 Nmi Naturwissenschaftliches Und Medizinisches Institut An Der Universität Tübingen Use of an electrode array
DE10010081A1 (en) * 2000-03-02 2001-09-13 Nmi Univ Tuebingen Apparatus for an electro-physiological study of biological material comprises an array of measurement electrodes on the carrier and a counter electrode within the sample vessel
WO2001069222A2 (en) 2000-03-17 2001-09-20 F. Hoffmann-La Roche Ag Implantable analyte sensor
US6405066B1 (en) 2000-03-17 2002-06-11 The Regents Of The University Of California Implantable analyte sensor
AU2001263022A1 (en) * 2000-05-12 2001-11-26 Therasense, Inc. Electrodes with multilayer membranes and methods of using and making the electrodes
US6340421B1 (en) * 2000-05-16 2002-01-22 Minimed Inc. Microelectrogravimetric method for plating a biosensor
US6540675B2 (en) 2000-06-27 2003-04-01 Rosedale Medical, Inc. Analyte monitor
DE10057832C1 (en) * 2000-11-21 2002-02-21 Hartmann Paul Ag Blood analysis device has syringe mounted in casing, annular mounting carrying needles mounted behind test strip and being swiveled so that needle can be pushed through strip and aperture in casing to take blood sample
US8641644B2 (en) * 2000-11-21 2014-02-04 Sanofi-Aventis Deutschland Gmbh Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means
US6642015B2 (en) 2000-12-29 2003-11-04 Minimed Inc. Hydrophilic polymeric material for coating biosensors
US20030003436A1 (en) * 2001-02-05 2003-01-02 Willson C. Grant Use of mesoscale self-assembly and recognition to effect delivery of sensing reagent for arrayed sensors
TW522127B (en) * 2001-02-21 2003-03-01 Daifuku Kk Cargo storage facility
US6572745B2 (en) 2001-03-23 2003-06-03 Virotek, L.L.C. Electrochemical sensor and method thereof
US7310543B2 (en) 2001-03-26 2007-12-18 Kumetrix, Inc. Silicon microprobe with integrated biosensor
US8070934B2 (en) 2001-05-11 2011-12-06 Abbott Diabetes Care Inc. Transition metal complexes with (pyridyl)imidazole ligands
US6676816B2 (en) * 2001-05-11 2004-01-13 Therasense, Inc. Transition metal complexes with (pyridyl)imidazole ligands and sensors using said complexes
US8226814B2 (en) * 2001-05-11 2012-07-24 Abbott Diabetes Care Inc. Transition metal complexes with pyridyl-imidazole ligands
US6932894B2 (en) * 2001-05-15 2005-08-23 Therasense, Inc. Biosensor membranes composed of polymers containing heterocyclic nitrogens
US7005273B2 (en) * 2001-05-16 2006-02-28 Therasense, Inc. Method for the determination of glycated hemoglobin
US6674635B1 (en) 2001-06-11 2004-01-06 Avx Corporation Protective coating for electrolytic capacitors
US9427532B2 (en) 2001-06-12 2016-08-30 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8337419B2 (en) 2002-04-19 2012-12-25 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
ES2357887T3 (en) 2001-06-12 2011-05-03 Pelikan Technologies Inc. APPARATUS FOR IMPROVING THE BLOOD OBTAINING SUCCESS RATE FROM A CAPILLARY PUNCTURE.
US9226699B2 (en) * 2002-04-19 2016-01-05 Sanofi-Aventis Deutschland Gmbh Body fluid sampling module with a continuous compression tissue interface surface
US20070100255A1 (en) * 2002-04-19 2007-05-03 Pelikan Technologies, Inc. Method and apparatus for body fluid sampling and analyte sensing
US9795747B2 (en) 2010-06-02 2017-10-24 Sanofi-Aventis Deutschland Gmbh Methods and apparatus for lancet actuation
CA2448902C (en) * 2001-06-12 2010-09-07 Pelikan Technologies, Inc. Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties
US6501976B1 (en) 2001-06-12 2002-12-31 Lifescan, Inc. Percutaneous biological fluid sampling and analyte measurement devices and methods
US7682318B2 (en) 2001-06-12 2010-03-23 Pelikan Technologies, Inc. Blood sampling apparatus and method
US7981056B2 (en) * 2002-04-19 2011-07-19 Pelikan Technologies, Inc. Methods and apparatus for lancet actuation
US6793632B2 (en) 2001-06-12 2004-09-21 Lifescan, Inc. Percutaneous biological fluid constituent sampling and measurement devices and methods
US6875613B2 (en) 2001-06-12 2005-04-05 Lifescan, Inc. Biological fluid constituent sampling and measurement devices and methods
US7344507B2 (en) 2002-04-19 2008-03-18 Pelikan Technologies, Inc. Method and apparatus for lancet actuation
WO2002100254A2 (en) * 2001-06-12 2002-12-19 Pelikan Technologies, Inc. Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge
EP1395185B1 (en) * 2001-06-12 2010-10-27 Pelikan Technologies Inc. Electric lancet actuator
US6837988B2 (en) * 2001-06-12 2005-01-04 Lifescan, Inc. Biological fluid sampling and analyte measurement devices and methods
US7041068B2 (en) 2001-06-12 2006-05-09 Pelikan Technologies, Inc. Sampling module device and method
US6721586B2 (en) 2001-06-12 2004-04-13 Lifescan, Inc. Percutaneous biological fluid sampling and analyte measurement devices and methods
DE10133363A1 (en) * 2001-07-10 2003-01-30 Infineon Technologies Ag Measuring cell and measuring field with such measuring cells as well as using a measuring cell and using a measuring field
US6702857B2 (en) 2001-07-27 2004-03-09 Dexcom, Inc. Membrane for use with implantable devices
AT410223B (en) * 2001-08-09 2003-03-25 Adlassnig Alexander Mag Dr BIOSENSORS IN THICK FILM TECHNOLOGY
US8227240B2 (en) * 2001-08-14 2012-07-24 The Washington University Systems for screening pharmaceutical chemicals
IL145182A (en) * 2001-08-29 2005-11-20 Yissum Res Dev Co Self-powered biosensor
US8506550B2 (en) * 2001-09-07 2013-08-13 Medtronic Minimed, Inc. Method and system for non-vascular sensor implantation
US7323142B2 (en) * 2001-09-07 2008-01-29 Medtronic Minimed, Inc. Sensor substrate and method of fabricating same
US6671554B2 (en) 2001-09-07 2003-12-30 Medtronic Minimed, Inc. Electronic lead for a medical implant device, method of making same, and method and apparatus for inserting same
US6827702B2 (en) 2001-09-07 2004-12-07 Medtronic Minimed, Inc. Safety limits for closed-loop infusion pump control
US7025760B2 (en) * 2001-09-07 2006-04-11 Medtronic Minimed, Inc. Method and system for non-vascular sensor implantation
US6915147B2 (en) * 2001-09-07 2005-07-05 Medtronic Minimed, Inc. Sensing apparatus and process
USRE44522E1 (en) 2001-09-14 2013-10-08 Arkray, Inc. Concentration measuring method, concentration test instrument, and concentration measuring apparatus
US7192766B2 (en) * 2001-10-23 2007-03-20 Medtronic Minimed, Inc. Sensor containing molded solidified protein
US8465466B2 (en) 2001-10-23 2013-06-18 Medtronic Minimed, Inc Method and system for non-vascular sensor implantation
US6809507B2 (en) * 2001-10-23 2004-10-26 Medtronic Minimed, Inc. Implantable sensor electrodes and electronic circuitry
EP1448489B1 (en) * 2001-11-16 2010-08-25 Stefan Ufer Flexible sensor and method of fabrication
US6952604B2 (en) 2001-12-21 2005-10-04 Becton, Dickinson And Company Minimally-invasive system and method for monitoring analyte levels
US20040137547A1 (en) * 2001-12-28 2004-07-15 Medtronic Minimed, Inc. Method for formulating a glucose oxidase enzyme with a desired property or properties and a glucose oxidase enzyme with the desired property
US20030216628A1 (en) * 2002-01-28 2003-11-20 Bortz Jonathan David Methods and systems for assessing glycemic control using predetermined pattern label analysis of blood glucose readings
US7004928B2 (en) 2002-02-08 2006-02-28 Rosedale Medical, Inc. Autonomous, ambulatory analyte monitor or drug delivery device
US8260393B2 (en) 2003-07-25 2012-09-04 Dexcom, Inc. Systems and methods for replacing signal data artifacts in a glucose sensor data stream
US9282925B2 (en) 2002-02-12 2016-03-15 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US9247901B2 (en) 2003-08-22 2016-02-02 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US8010174B2 (en) 2003-08-22 2011-08-30 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US7101472B2 (en) * 2002-03-13 2006-09-05 The Charles Stark Draper Laboratory, Inc. Microfluidic ion-selective electrode sensor system
US7407570B2 (en) * 2002-03-13 2008-08-05 The Charles Stark Draper Laboratory, Inc. Disposable, self-administered electrolyte test
US7563232B2 (en) * 2002-04-19 2009-07-21 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7901362B2 (en) 2002-04-19 2011-03-08 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7232451B2 (en) 2002-04-19 2007-06-19 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7141058B2 (en) * 2002-04-19 2006-11-28 Pelikan Technologies, Inc. Method and apparatus for a body fluid sampling device using illumination
US7547287B2 (en) 2002-04-19 2009-06-16 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7524293B2 (en) * 2002-04-19 2009-04-28 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7976476B2 (en) 2002-04-19 2011-07-12 Pelikan Technologies, Inc. Device and method for variable speed lancet
US20070142748A1 (en) * 2002-04-19 2007-06-21 Ajay Deshmukh Tissue penetration device
US8702624B2 (en) 2006-09-29 2014-04-22 Sanofi-Aventis Deutschland Gmbh Analyte measurement device with a single shot actuator
US7892183B2 (en) * 2002-04-19 2011-02-22 Pelikan Technologies, Inc. Method and apparatus for body fluid sampling and analyte sensing
US7717863B2 (en) * 2002-04-19 2010-05-18 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7648468B2 (en) * 2002-04-19 2010-01-19 Pelikon Technologies, Inc. Method and apparatus for penetrating tissue
US8784335B2 (en) * 2002-04-19 2014-07-22 Sanofi-Aventis Deutschland Gmbh Body fluid sampling device with a capacitive sensor
US7297122B2 (en) 2002-04-19 2007-11-20 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7485128B2 (en) * 2002-04-19 2009-02-03 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8221334B2 (en) * 2002-04-19 2012-07-17 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7909778B2 (en) * 2002-04-19 2011-03-22 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8360992B2 (en) * 2002-04-19 2013-01-29 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US8372016B2 (en) 2002-04-19 2013-02-12 Sanofi-Aventis Deutschland Gmbh Method and apparatus for body fluid sampling and analyte sensing
US9795334B2 (en) 2002-04-19 2017-10-24 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US8267870B2 (en) * 2002-04-19 2012-09-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for body fluid sampling with hybrid actuation
US7331931B2 (en) * 2002-04-19 2008-02-19 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7291117B2 (en) * 2002-04-19 2007-11-06 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7229458B2 (en) 2002-04-19 2007-06-12 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8579831B2 (en) 2002-04-19 2013-11-12 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7244265B2 (en) * 2002-04-19 2007-07-17 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9248267B2 (en) 2002-04-19 2016-02-02 Sanofi-Aventis Deustchland Gmbh Tissue penetration device
US7410468B2 (en) * 2002-04-19 2008-08-12 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7481776B2 (en) 2002-04-19 2009-01-27 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7674232B2 (en) * 2002-04-19 2010-03-09 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7491178B2 (en) * 2002-04-19 2009-02-17 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9314194B2 (en) 2002-04-19 2016-04-19 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US7371247B2 (en) 2002-04-19 2008-05-13 Pelikan Technologies, Inc Method and apparatus for penetrating tissue
US7198606B2 (en) 2002-04-19 2007-04-03 Pelikan Technologies, Inc. Method and apparatus for a multi-use body fluid sampling device with analyte sensing
US7813780B2 (en) * 2005-12-13 2010-10-12 Medtronic Minimed, Inc. Biosensors and methods for making and using them
US7153265B2 (en) * 2002-04-22 2006-12-26 Medtronic Minimed, Inc. Anti-inflammatory biosensor for reduced biofouling and enhanced sensor performance
US20070227907A1 (en) * 2006-04-04 2007-10-04 Rajiv Shah Methods and materials for controlling the electrochemistry of analyte sensors
US9492111B2 (en) * 2002-04-22 2016-11-15 Medtronic Minimed, Inc. Methods and materials for stabilizing analyte sensors
US7368190B2 (en) * 2002-05-02 2008-05-06 Abbott Diabetes Care Inc. Miniature biological fuel cell that is operational under physiological conditions, and associated devices and methods
KR100464141B1 (en) * 2002-05-10 2005-01-06 주식회사 엘바이오 Biosensor
US20060258761A1 (en) * 2002-05-22 2006-11-16 Robert Boock Silicone based membranes for use in implantable glucose sensors
US6864147B1 (en) 2002-06-11 2005-03-08 Avx Corporation Protective coating for electrolytic capacitors
US20040067481A1 (en) * 2002-06-12 2004-04-08 Leslie Leonard Thermal sensor for fluid detection
US8512276B2 (en) 2002-07-24 2013-08-20 Medtronic Minimed, Inc. System for providing blood glucose measurements to an infusion device
US20040068230A1 (en) 2002-07-24 2004-04-08 Medtronic Minimed, Inc. System for providing blood glucose measurements to an infusion device
US7278983B2 (en) 2002-07-24 2007-10-09 Medtronic Minimed, Inc. Physiological monitoring device for controlling a medication infusion device
US7150975B2 (en) * 2002-08-19 2006-12-19 Animas Technologies, Llc Hydrogel composition for measuring glucose flux
US7291256B2 (en) * 2002-09-12 2007-11-06 Lifescan, Inc. Mediator stabilized reagent compositions and methods for their use in electrochemical analyte detection assays
US8003513B2 (en) * 2002-09-27 2011-08-23 Medtronic Minimed, Inc. Multilayer circuit devices and manufacturing methods using electroplated sacrificial structures
US20040061232A1 (en) * 2002-09-27 2004-04-01 Medtronic Minimed, Inc. Multilayer substrate
US7736309B2 (en) * 2002-09-27 2010-06-15 Medtronic Minimed, Inc. Implantable sensor method and system
CA2501825C (en) * 2002-10-09 2009-12-01 Therasense, Inc. Fluid delivery device, system and method
US7727181B2 (en) * 2002-10-09 2010-06-01 Abbott Diabetes Care Inc. Fluid delivery device with autocalibration
US7993108B2 (en) * 2002-10-09 2011-08-09 Abbott Diabetes Care Inc. Variable volume, shape memory actuated insulin dispensing pump
US20050272989A1 (en) * 2004-06-04 2005-12-08 Medtronic Minimed, Inc. Analyte sensors and methods for making and using them
US9237865B2 (en) * 2002-10-18 2016-01-19 Medtronic Minimed, Inc. Analyte sensors and methods for making and using them
US7501053B2 (en) * 2002-10-23 2009-03-10 Abbott Laboratories Biosensor having improved hematocrit and oxygen biases
US7381184B2 (en) 2002-11-05 2008-06-03 Abbott Diabetes Care Inc. Sensor inserter assembly
AU2003291250A1 (en) * 2002-11-05 2004-06-07 Therasense, Inc. Assay device, system and method
US7638228B2 (en) * 2002-11-27 2009-12-29 Saint Louis University Enzyme immobilization for use in biofuel cells and sensors
US7025791B2 (en) 2002-12-02 2006-04-11 Gi Dynamics, Inc. Bariatric sleeve
AU2003297205A1 (en) * 2002-12-13 2004-07-09 Pelikan Technologies, Inc. Method and apparatus for measuring analytes
US7175897B2 (en) * 2002-12-17 2007-02-13 Avery Dennison Corporation Adhesive articles which contain at least one hydrophilic or hydrophobic layer, method for making and uses for same
US20040122353A1 (en) * 2002-12-19 2004-06-24 Medtronic Minimed, Inc. Relay device for transferring information between a sensor system and a fluid delivery system
US7265881B2 (en) * 2002-12-20 2007-09-04 Hewlett-Packard Development Company, L.P. Method and apparatus for measuring assembly and alignment errors in sensor assemblies
US7514250B2 (en) 2002-12-24 2009-04-07 Ikeda Food Research Co., Ltd. Coenzyme-binding glucose dehydrogenase
US8574895B2 (en) 2002-12-30 2013-11-05 Sanofi-Aventis Deutschland Gmbh Method and apparatus using optical techniques to measure analyte levels
US20040126831A1 (en) * 2002-12-31 2004-07-01 Medtronic Minimed, Inc. Functionalization of immobilized proteins
WO2004060174A2 (en) * 2002-12-31 2004-07-22 Pelikan Technologies Inc. Method and apparatus for loading penetrating members
US20040132167A1 (en) * 2003-01-06 2004-07-08 Peter Rule Cartridge lance
US7120483B2 (en) * 2003-01-13 2006-10-10 Isense Corporation Methods for analyte sensing and measurement
US7312197B2 (en) * 2003-02-24 2007-12-25 University Of Maryland, Baltimore Method of modifying glucose activity using polypeptides selectively expressed in fat tissue
US7052652B2 (en) 2003-03-24 2006-05-30 Rosedale Medical, Inc. Analyte concentration detection devices and methods
US6965791B1 (en) 2003-03-26 2005-11-15 Sorenson Medical, Inc. Implantable biosensor system, apparatus and method
US20050177201A1 (en) * 2003-03-31 2005-08-11 Freeman Gary A. Probe insertion pain reduction method and device
US7134999B2 (en) * 2003-04-04 2006-11-14 Dexcom, Inc. Optimized sensor geometry for an implantable glucose sensor
US7587287B2 (en) 2003-04-04 2009-09-08 Abbott Diabetes Care Inc. Method and system for transferring analyte test data
US20050037384A1 (en) * 2003-04-15 2005-02-17 Braig James R. Analyte detection system
WO2004097371A2 (en) * 2003-04-25 2004-11-11 Board Of Regents, The University Of Texas System System and method for the detection of analytes
US7679407B2 (en) * 2003-04-28 2010-03-16 Abbott Diabetes Care Inc. Method and apparatus for providing peak detection circuitry for data communication systems
WO2004104922A2 (en) * 2003-05-16 2004-12-02 Board Of Regents, The University Of Texas System Image and part recognition technology
US9317922B2 (en) 2003-05-16 2016-04-19 Board Of Regents The University Of Texas System Image and part recognition technology
EP2460881B1 (en) * 2003-05-16 2017-05-03 Acorda Therapeutics, Inc. Proteoglycan degrading mutants for treatment of CNS
US7862519B1 (en) * 2003-05-21 2011-01-04 Isense Corporation Easy-to-use multi-use body fluid specimen collection and analyte sensing assembly
US7875293B2 (en) * 2003-05-21 2011-01-25 Dexcom, Inc. Biointerface membranes incorporating bioactive agents
EP1628567B1 (en) 2003-05-30 2010-08-04 Pelikan Technologies Inc. Method and apparatus for fluid injection
US7258673B2 (en) * 2003-06-06 2007-08-21 Lifescan, Inc Devices, systems and methods for extracting bodily fluid and monitoring an analyte therein
US20040253736A1 (en) * 2003-06-06 2004-12-16 Phil Stout Analytical device with prediction module and related methods
ES2490740T3 (en) * 2003-06-06 2014-09-04 Sanofi-Aventis Deutschland Gmbh Apparatus for blood fluid sampling and analyte detection
US20040249254A1 (en) * 2003-06-06 2004-12-09 Joel Racchini Devices, systems and methods for extracting bodily fluid and monitoring an analyte therein
US20060241666A1 (en) * 2003-06-11 2006-10-26 Briggs Barry D Method and apparatus for body fluid sampling and analyte sensing
WO2006001797A1 (en) 2004-06-14 2006-01-05 Pelikan Technologies, Inc. Low pain penetrating
US7645421B2 (en) 2003-06-20 2010-01-12 Roche Diagnostics Operations, Inc. System and method for coding information on a biosensor test strip
US7452457B2 (en) 2003-06-20 2008-11-18 Roche Diagnostics Operations, Inc. System and method for analyte measurement using dose sufficiency electrodes
US8148164B2 (en) 2003-06-20 2012-04-03 Roche Diagnostics Operations, Inc. System and method for determining the concentration of an analyte in a sample fluid
US8071030B2 (en) 2003-06-20 2011-12-06 Roche Diagnostics Operations, Inc. Test strip with flared sample receiving chamber
US7645373B2 (en) 2003-06-20 2010-01-12 Roche Diagnostic Operations, Inc. System and method for coding information on a biosensor test strip
ES2683013T3 (en) 2003-06-20 2018-09-24 F. Hoffmann-La Roche Ag Reagent band for test strip
US8679853B2 (en) 2003-06-20 2014-03-25 Roche Diagnostics Operations, Inc. Biosensor with laser-sealed capillary space and method of making
US8206565B2 (en) 2003-06-20 2012-06-26 Roche Diagnostics Operation, Inc. System and method for coding information on a biosensor test strip
US7718439B2 (en) 2003-06-20 2010-05-18 Roche Diagnostics Operations, Inc. System and method for coding information on a biosensor test strip
US8058077B2 (en) 2003-06-20 2011-11-15 Roche Diagnostics Operations, Inc. Method for coding information on a biosensor test strip
US7488601B2 (en) 2003-06-20 2009-02-10 Roche Diagnostic Operations, Inc. System and method for determining an abused sensor during analyte measurement
US7097788B2 (en) 2003-06-30 2006-08-29 The Board Of Trustees Of The University Of Illinois Conducting inks
US7695239B2 (en) * 2003-07-14 2010-04-13 Fortrend Engineering Corporation End effector gripper arms having corner grippers which reorient reticle during transfer
WO2005010518A1 (en) * 2003-07-23 2005-02-03 Dexcom, Inc. Rolled electrode array and its method for manufacture
US7366556B2 (en) 2003-12-05 2008-04-29 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US20050176136A1 (en) * 2003-11-19 2005-08-11 Dexcom, Inc. Afinity domain for analyte sensor
US7467003B2 (en) * 2003-12-05 2008-12-16 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US7460898B2 (en) * 2003-12-05 2008-12-02 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8423113B2 (en) 2003-07-25 2013-04-16 Dexcom, Inc. Systems and methods for processing sensor data
WO2005019795A2 (en) * 2003-07-25 2005-03-03 Dexcom, Inc. Electrochemical sensors including electrode systems with increased oxygen generation
US7424318B2 (en) 2003-12-05 2008-09-09 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US20050056552A1 (en) * 2003-07-25 2005-03-17 Simpson Peter C. Increasing bias for oxygen production in an electrode system
US8285354B2 (en) 2003-08-01 2012-10-09 Dexcom, Inc. System and methods for processing analyte sensor data
US8275437B2 (en) * 2003-08-01 2012-09-25 Dexcom, Inc. Transcutaneous analyte sensor
US8845536B2 (en) 2003-08-01 2014-09-30 Dexcom, Inc. Transcutaneous analyte sensor
US7774145B2 (en) * 2003-08-01 2010-08-10 Dexcom, Inc. Transcutaneous analyte sensor
US9135402B2 (en) 2007-12-17 2015-09-15 Dexcom, Inc. Systems and methods for processing sensor data
US8369919B2 (en) 2003-08-01 2013-02-05 Dexcom, Inc. Systems and methods for processing sensor data
US6931327B2 (en) 2003-08-01 2005-08-16 Dexcom, Inc. System and methods for processing analyte sensor data
US8160669B2 (en) 2003-08-01 2012-04-17 Dexcom, Inc. Transcutaneous analyte sensor
US8761856B2 (en) 2003-08-01 2014-06-24 Dexcom, Inc. System and methods for processing analyte sensor data
US7519408B2 (en) 2003-11-19 2009-04-14 Dexcom, Inc. Integrated receiver for continuous analyte sensor
US8676287B2 (en) 2003-08-01 2014-03-18 Dexcom, Inc. System and methods for processing analyte sensor data
US20070066873A1 (en) 2003-08-22 2007-03-22 Apurv Kamath Systems and methods for processing analyte sensor data
US20140121989A1 (en) 2003-08-22 2014-05-01 Dexcom, Inc. Systems and methods for processing analyte sensor data
US7306641B2 (en) * 2003-09-12 2007-12-11 Hewlett-Packard Development Company, L.P. Integral fuel cartridge and filter
US7150820B2 (en) * 2003-09-22 2006-12-19 Semitool, Inc. Thiourea- and cyanide-free bath and process for electrolytic etching of gold
US7433727B2 (en) * 2003-09-24 2008-10-07 Legacy Good Samaritan Hospital And Medical Center Implantable biosensor
EP1671096A4 (en) * 2003-09-29 2009-09-16 Pelikan Technologies Inc Method and apparatus for an improved sample capture device
EP1680014A4 (en) 2003-10-14 2009-01-21 Pelikan Technologies Inc Method and apparatus for a variable user interface
US20050090607A1 (en) * 2003-10-28 2005-04-28 Dexcom, Inc. Silicone composition for biocompatible membrane
US7299082B2 (en) 2003-10-31 2007-11-20 Abbott Diabetes Care, Inc. Method of calibrating an analyte-measurement device, and associated methods, devices and systems
US8859151B2 (en) 2003-11-05 2014-10-14 St. Louis University Immobilized enzymes in biocathodes
USD902408S1 (en) 2003-11-05 2020-11-17 Abbott Diabetes Care Inc. Analyte sensor control unit
US20080197024A1 (en) * 2003-12-05 2008-08-21 Dexcom, Inc. Analyte sensor
US8287453B2 (en) 2003-12-05 2012-10-16 Dexcom, Inc. Analyte sensor
ATE474219T1 (en) 2003-12-08 2010-07-15 Dexcom Inc SYSTEMS AND METHODS FOR IMPROVING ELECTROCHEMICAL ANALYT SENSORS
WO2005057175A2 (en) 2003-12-09 2005-06-23 Dexcom, Inc. Signal processing for continuous analyte sensor
US7822454B1 (en) 2005-01-03 2010-10-26 Pelikan Technologies, Inc. Fluid sampling device with improved analyte detecting member configuration
WO2005065414A2 (en) 2003-12-31 2005-07-21 Pelikan Technologies, Inc. Method and apparatus for improving fluidic flow and sample capture
US7637868B2 (en) * 2004-01-12 2009-12-29 Dexcom, Inc. Composite material for implantable device
DE102004004031B4 (en) * 2004-01-27 2019-03-28 Disetronic Licensing Ag Adjustment of sensors or measuring systems
CA2568032C (en) * 2004-02-05 2016-04-12 Dermal Therapy (Barbados) Inc. Method and apparatus for measuring glucose in body fluids using sub-dermal body tissue impedance measurements
BRPI0507376A (en) 2004-02-06 2007-07-10 Bayer Healthcare Llc oxidizable species as an internal reference for biosensors and method of use
US7699964B2 (en) * 2004-02-09 2010-04-20 Abbott Diabetes Care Inc. Membrane suitable for use in an analyte sensor, analyte sensor, and associated method
US8165651B2 (en) * 2004-02-09 2012-04-24 Abbott Diabetes Care Inc. Analyte sensor, and associated system and method employing a catalytic agent
US7807043B2 (en) * 2004-02-23 2010-10-05 Oakville Hong Kong Company Limited Microfluidic test device
ITVI20040046A1 (en) * 2004-03-10 2004-06-10 Bona Gian Domenico Dalla ELECTRODE FOR ELECTROSTIMULATORS
US8936560B2 (en) * 2004-03-10 2015-01-20 Vision Quest Industries Incorporated Bracing and electrostimulation for arthritis
CA2560022A1 (en) * 2004-03-15 2005-10-13 St. Louis University Microfluidic biofuel cell
US8792955B2 (en) 2004-05-03 2014-07-29 Dexcom, Inc. Transcutaneous analyte sensor
US8828203B2 (en) * 2004-05-20 2014-09-09 Sanofi-Aventis Deutschland Gmbh Printable hydrogels for biosensors
WO2005120365A1 (en) 2004-06-03 2005-12-22 Pelikan Technologies, Inc. Method and apparatus for a fluid sampling device
US9775553B2 (en) * 2004-06-03 2017-10-03 Sanofi-Aventis Deutschland Gmbh Method and apparatus for a fluid sampling device
CA3090413C (en) 2004-06-04 2023-10-10 Abbott Diabetes Care Inc. Glucose monitoring and graphical representations in a data management system
US20070100222A1 (en) * 2004-06-14 2007-05-03 Metronic Minimed, Inc. Analyte sensing apparatus for hospital use
US7569126B2 (en) 2004-06-18 2009-08-04 Roche Diagnostics Operations, Inc. System and method for quality assurance of a biosensor test strip
US7556723B2 (en) * 2004-06-18 2009-07-07 Roche Diagnostics Operations, Inc. Electrode design for biosensor
US20060001551A1 (en) 2004-06-30 2006-01-05 Ulrich Kraft Analyte monitoring system with wireless alarm
US20060001538A1 (en) * 2004-06-30 2006-01-05 Ulrich Kraft Methods of monitoring the concentration of an analyte
US8452368B2 (en) 2004-07-13 2013-05-28 Dexcom, Inc. Transcutaneous analyte sensor
US8565848B2 (en) 2004-07-13 2013-10-22 Dexcom, Inc. Transcutaneous analyte sensor
EP2335584B1 (en) 2004-07-13 2015-06-17 DexCom, Inc. Transcutaneous analyte sensor
US20060016700A1 (en) * 2004-07-13 2006-01-26 Dexcom, Inc. Transcutaneous analyte sensor
US7344500B2 (en) 2004-07-27 2008-03-18 Medtronic Minimed, Inc. Sensing system with auxiliary display
US7109271B2 (en) * 2004-07-28 2006-09-19 Lifescan, Inc. Redox polymers for use in electrochemical-based sensors
WO2006127023A2 (en) * 2004-08-24 2006-11-30 University Of South Florida Epoxy enhanced polymer membrane to increase durability of biosensors
US7572356B2 (en) * 2004-08-31 2009-08-11 Lifescan Scotland Limited Electrochemical-based sensor with a redox polymer and redox enzyme entrapped by a dialysis membrane
WO2006027702A2 (en) * 2004-09-09 2006-03-16 Albatros Technologies Gmbh & Co. Kg Analyte detecting member with a 3d hydrogel
US7351770B2 (en) 2004-09-30 2008-04-01 Lifescan, Inc. Ionic hydrophilic high molecular weight redox polymers for use in enzymatic electrochemical-based sensors
JP5502279B2 (en) * 2004-10-28 2014-05-28 エコー セラピューティクス, インコーポレイテッド System and method for analyte sampling and analysis using hydrogels
US7303543B1 (en) * 2004-12-03 2007-12-04 Medtronic Minimed, Inc. Medication infusion set
RU2430264C2 (en) * 2004-12-16 2011-09-27 Индепендент Нэчурэл Ресорсиз, Инк. Power system built around float-type pump
US20090105569A1 (en) 2006-04-28 2009-04-23 Abbott Diabetes Care, Inc. Introducer Assembly and Methods of Use
US10226207B2 (en) 2004-12-29 2019-03-12 Abbott Diabetes Care Inc. Sensor inserter having introducer
US7697967B2 (en) 2005-12-28 2010-04-13 Abbott Diabetes Care Inc. Method and apparatus for providing analyte sensor insertion
US7731657B2 (en) * 2005-08-30 2010-06-08 Abbott Diabetes Care Inc. Analyte sensor introducer and methods of use
US9398882B2 (en) 2005-09-30 2016-07-26 Abbott Diabetes Care Inc. Method and apparatus for providing analyte sensor and data processing device
US8029441B2 (en) 2006-02-28 2011-10-04 Abbott Diabetes Care Inc. Analyte sensor transmitter unit configuration for a data monitoring and management system
US9351669B2 (en) 2009-09-30 2016-05-31 Abbott Diabetes Care Inc. Interconnect for on-body analyte monitoring device
US9788771B2 (en) 2006-10-23 2017-10-17 Abbott Diabetes Care Inc. Variable speed sensor insertion devices and methods of use
US8512243B2 (en) 2005-09-30 2013-08-20 Abbott Diabetes Care Inc. Integrated introducer and transmitter assembly and methods of use
US9259175B2 (en) 2006-10-23 2016-02-16 Abbott Diabetes Care, Inc. Flexible patch for fluid delivery and monitoring body analytes
US9572534B2 (en) 2010-06-29 2017-02-21 Abbott Diabetes Care Inc. Devices, systems and methods for on-skin or on-body mounting of medical devices
US9636450B2 (en) 2007-02-19 2017-05-02 Udo Hoss Pump system modular components for delivering medication and analyte sensing at seperate insertion sites
US8333714B2 (en) 2006-09-10 2012-12-18 Abbott Diabetes Care Inc. Method and system for providing an integrated analyte sensor insertion device and data processing unit
US8571624B2 (en) 2004-12-29 2013-10-29 Abbott Diabetes Care Inc. Method and apparatus for mounting a data transmission device in a communication system
US7883464B2 (en) 2005-09-30 2011-02-08 Abbott Diabetes Care Inc. Integrated transmitter unit and sensor introducer mechanism and methods of use
US9743862B2 (en) 2011-03-31 2017-08-29 Abbott Diabetes Care Inc. Systems and methods for transcutaneously implanting medical devices
US20080214917A1 (en) * 2004-12-30 2008-09-04 Dirk Boecker Method and apparatus for analyte measurement test time
US8652831B2 (en) 2004-12-30 2014-02-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for analyte measurement test time
US20060166629A1 (en) * 2005-01-24 2006-07-27 Therasense, Inc. Method and apparatus for providing EMC Class-B compliant RF transmitter for data monitoring an detection systems
US7704229B2 (en) 2005-02-03 2010-04-27 Medtronic Minimed, Inc. Insertion device
US7545272B2 (en) 2005-02-08 2009-06-09 Therasense, Inc. RF tag on test strips, test strip vials and boxes
US20060184065A1 (en) * 2005-02-10 2006-08-17 Ajay Deshmukh Method and apparatus for storing an analyte sampling and measurement device
US20060184104A1 (en) * 2005-02-15 2006-08-17 Medtronic Minimed, Inc. Needle guard
US8133178B2 (en) 2006-02-22 2012-03-13 Dexcom, Inc. Analyte sensor
US20090076360A1 (en) 2007-09-13 2009-03-19 Dexcom, Inc. Transcutaneous analyte sensor
EP1863559A4 (en) 2005-03-21 2008-07-30 Abbott Diabetes Care Inc Method and system for providing integrated medication infusion and analyte monitoring system
DE502005005099D1 (en) * 2005-03-23 2008-10-02 Roche Diagnostics Gmbh Method for determining the glucose concentration by fluorescence polarization
EP2380980B1 (en) 2005-03-25 2014-11-05 Ikeda Food Research Co. Ltd. Coenzyme-linked glucose dehydrogenase and polynucleotide encoding the same
US20060249381A1 (en) * 2005-05-05 2006-11-09 Petisce James R Cellulosic-based resistance domain for an analyte sensor
WO2006110193A2 (en) 2005-04-08 2006-10-19 Dexcom, Inc. Cellulosic-based interference domain for an analyte sensor
AU2006201333A1 (en) 2005-04-12 2006-11-02 Lifescan Scotland Limited Water-miscible conductive ink for use in enzymatic electrochemical-based sensors
US20060226007A1 (en) * 2005-04-12 2006-10-12 Rodgers James I Method for manufacturing an enzymatic electrochemical-based sensor
US7588670B2 (en) * 2005-04-12 2009-09-15 Lifescan Scotland Limited Enzymatic electrochemical-based sensor
US7465380B2 (en) * 2005-04-12 2008-12-16 Lifescan Scotland, Ltd. Water-miscible conductive ink for use in enzymatic electrochemical-based sensors
MX2007013483A (en) * 2005-04-29 2008-01-22 Norman R Byrne Center connect single-sided junction block.
US7768408B2 (en) 2005-05-17 2010-08-03 Abbott Diabetes Care Inc. Method and system for providing data management in data monitoring system
US7620437B2 (en) 2005-06-03 2009-11-17 Abbott Diabetes Care Inc. Method and apparatus for providing rechargeable power in data monitoring and management systems
US20060272652A1 (en) * 2005-06-03 2006-12-07 Medtronic Minimed, Inc. Virtual patient software system for educating and treating individuals with diabetes
US20070033074A1 (en) * 2005-06-03 2007-02-08 Medtronic Minimed, Inc. Therapy management system
US20060281187A1 (en) 2005-06-13 2006-12-14 Rosedale Medical, Inc. Analyte detection devices and methods with hematocrit/volume correction and feedback control
US20070016449A1 (en) * 2005-06-29 2007-01-18 Gary Cohen Flexible glucose analysis using varying time report deltas and configurable glucose target ranges
ES2717135T3 (en) 2005-07-20 2019-06-19 Ascensia Diabetes Care Holdings Ag Method to signal the user to add an additional sample to a test strip, method to measure the temperature of a sample and methods to determine the concentration of an analyte based on controlled amperometry
US20070066956A1 (en) * 2005-07-27 2007-03-22 Medtronic Minimed, Inc. Systems and methods for entering temporary basal rate pattern in an infusion device
US20070036770A1 (en) * 2005-08-12 2007-02-15 Wagner Darrell O Biologic device for regulation of gene expression and method therefor
US20070060869A1 (en) * 2005-08-16 2007-03-15 Tolle Mike C V Controller device for an infusion pump
US7737581B2 (en) * 2005-08-16 2010-06-15 Medtronic Minimed, Inc. Method and apparatus for predicting end of battery life
US20070093786A1 (en) * 2005-08-16 2007-04-26 Medtronic Minimed, Inc. Watch controller for a medical device
US20090227855A1 (en) * 2005-08-16 2009-09-10 Medtronic Minimed, Inc. Controller device for an infusion pump
US20070060870A1 (en) * 2005-08-16 2007-03-15 Tolle Mike Charles V Controller device for an infusion pump
CA2620586A1 (en) 2005-08-31 2007-03-08 Boris P. Kovatchev Improving the accuracy of continuous glucose sensors
US7713240B2 (en) 2005-09-13 2010-05-11 Medtronic Minimed, Inc. Modular external infusion device
GB2430749B (en) * 2005-09-21 2007-11-28 Schlumberger Holdings Electro-chemical sensor
US9072476B2 (en) 2005-09-23 2015-07-07 Medtronic Minimed, Inc. Flexible sensor apparatus
US7725148B2 (en) * 2005-09-23 2010-05-25 Medtronic Minimed, Inc. Sensor with layered electrodes
US7704704B2 (en) * 2005-09-28 2010-04-27 The Texas A&M University System Implantable system for glucose monitoring using fluorescence quenching
US8801631B2 (en) 2005-09-30 2014-08-12 Intuity Medical, Inc. Devices and methods for facilitating fluid transport
EP2989981B8 (en) 2005-09-30 2018-09-05 Intuity Medical, Inc. Multi-site body fluid sampling and analysis cartridge
US8880138B2 (en) * 2005-09-30 2014-11-04 Abbott Diabetes Care Inc. Device for channeling fluid and methods of use
KR101577176B1 (en) 2005-09-30 2015-12-14 바이엘 헬스케어 엘엘씨 Gated voltammetry analyte determination
US9521968B2 (en) 2005-09-30 2016-12-20 Abbott Diabetes Care Inc. Analyte sensor retention mechanism and methods of use
US7756561B2 (en) 2005-09-30 2010-07-13 Abbott Diabetes Care Inc. Method and apparatus for providing rechargeable power in data monitoring and management systems
US20070276290A1 (en) * 2005-10-04 2007-11-29 Dirk Boecker Tissue Penetrating Apparatus
US20070191736A1 (en) * 2005-10-04 2007-08-16 Don Alden Method for loading penetrating members in a collection device
US20090196580A1 (en) * 2005-10-06 2009-08-06 Freeman Dominique M Method and apparatus for an analyte detecting device
US20090054747A1 (en) * 2005-10-31 2009-02-26 Abbott Diabetes Care, Inc. Method and system for providing analyte sensor tester isolation
US7583190B2 (en) 2005-10-31 2009-09-01 Abbott Diabetes Care Inc. Method and apparatus for providing data communication in data monitoring and management systems
CA2627650A1 (en) * 2005-11-02 2007-07-26 St. Louis University Direct electron transfer using enzymes in bioanodes, biocathodes, and biofuel cells
KR20080086977A (en) * 2005-11-02 2008-09-29 세인트 루이스 유니버시티 Enzymes immobilized in hydrophobically modified polysaccharides
US8455088B2 (en) 2005-12-23 2013-06-04 Boston Scientific Scimed, Inc. Spun nanofiber, medical devices, and methods
US7674864B2 (en) * 2005-12-23 2010-03-09 Boston Scientific Scimed, Inc. Polymeric hybrid precursors, polymeric hybrid precursor composite matrices, medical devices, and methods
US8160670B2 (en) 2005-12-28 2012-04-17 Abbott Diabetes Care Inc. Analyte monitoring: stabilizer for subcutaneous glucose sensor with incorporated antiglycolytic agent
CA2636034A1 (en) * 2005-12-28 2007-10-25 Abbott Diabetes Care Inc. Medical device insertion
US8515518B2 (en) * 2005-12-28 2013-08-20 Abbott Diabetes Care Inc. Analyte monitoring
US8353881B2 (en) * 2005-12-28 2013-01-15 Abbott Diabetes Care Inc. Infusion sets for the delivery of a therapeutic substance to a patient
US11298058B2 (en) 2005-12-28 2022-04-12 Abbott Diabetes Care Inc. Method and apparatus for providing analyte sensor insertion
US8114268B2 (en) * 2005-12-30 2012-02-14 Medtronic Minimed, Inc. Method and system for remedying sensor malfunctions detected by electrochemical impedance spectroscopy
US7774038B2 (en) 2005-12-30 2010-08-10 Medtronic Minimed, Inc. Real-time self-calibrating sensor system and method
US20070169533A1 (en) * 2005-12-30 2007-07-26 Medtronic Minimed, Inc. Methods and systems for detecting the hydration of sensors
US7985330B2 (en) 2005-12-30 2011-07-26 Medtronic Minimed, Inc. Method and system for detecting age, hydration, and functional states of sensors using electrochemical impedance spectroscopy
US8114269B2 (en) 2005-12-30 2012-02-14 Medtronic Minimed, Inc. System and method for determining the point of hydration and proper time to apply potential to a glucose sensor
US20070173712A1 (en) * 2005-12-30 2007-07-26 Medtronic Minimed, Inc. Method of and system for stabilization of sensors
US9757061B2 (en) 2006-01-17 2017-09-12 Dexcom, Inc. Low oxygen in vivo analyte sensor
EP1973464B1 (en) 2006-01-17 2018-03-14 DexCom, Inc. Low oxygen in vivo analyte sensor
EP2004796B1 (en) * 2006-01-18 2015-04-08 DexCom, Inc. Membranes for an analyte sensor
US7736310B2 (en) * 2006-01-30 2010-06-15 Abbott Diabetes Care Inc. On-body medical device securement
US8344966B2 (en) 2006-01-31 2013-01-01 Abbott Diabetes Care Inc. Method and system for providing a fault tolerant display unit in an electronic device
WO2007093981A2 (en) * 2006-02-15 2007-08-23 Medingo Ltd. Systems and methods for sensing analyte and dispensing therapeutic fluid
EP3649925A1 (en) 2006-02-22 2020-05-13 DexCom, Inc. Analyte sensor
US20090143658A1 (en) * 2006-02-27 2009-06-04 Edwards Lifesciences Corporation Analyte sensor
US7885698B2 (en) 2006-02-28 2011-02-08 Abbott Diabetes Care Inc. Method and system for providing continuous calibration of implantable analyte sensors
US7826879B2 (en) * 2006-02-28 2010-11-02 Abbott Diabetes Care Inc. Analyte sensors and methods of use
US7981034B2 (en) 2006-02-28 2011-07-19 Abbott Diabetes Care Inc. Smart messages and alerts for an infusion delivery and management system
EP4218548A1 (en) 2006-03-09 2023-08-02 Dexcom, Inc. Systems and methods for processing analyte sensor data
US7801582B2 (en) 2006-03-31 2010-09-21 Abbott Diabetes Care Inc. Analyte monitoring and management system and methods therefor
US7618369B2 (en) 2006-10-02 2009-11-17 Abbott Diabetes Care Inc. Method and system for dynamically updating calibration parameters for an analyte sensor
US8374668B1 (en) 2007-10-23 2013-02-12 Abbott Diabetes Care Inc. Analyte sensor with lag compensation
US8224415B2 (en) 2009-01-29 2012-07-17 Abbott Diabetes Care Inc. Method and device for providing offset model based calibration for analyte sensor
US8473022B2 (en) * 2008-01-31 2013-06-25 Abbott Diabetes Care Inc. Analyte sensor with time lag compensation
US9326709B2 (en) 2010-03-10 2016-05-03 Abbott Diabetes Care Inc. Systems, devices and methods for managing glucose levels
US7630748B2 (en) 2006-10-25 2009-12-08 Abbott Diabetes Care Inc. Method and system for providing analyte monitoring
US9392969B2 (en) 2008-08-31 2016-07-19 Abbott Diabetes Care Inc. Closed loop control and signal attenuation detection
US8346335B2 (en) 2008-03-28 2013-01-01 Abbott Diabetes Care Inc. Analyte sensor calibration management
US8140312B2 (en) 2007-05-14 2012-03-20 Abbott Diabetes Care Inc. Method and system for determining analyte levels
US7653425B2 (en) 2006-08-09 2010-01-26 Abbott Diabetes Care Inc. Method and system for providing calibration of an analyte sensor in an analyte monitoring system
US9339217B2 (en) 2011-11-25 2016-05-17 Abbott Diabetes Care Inc. Analyte monitoring system and methods of use
US9675290B2 (en) 2012-10-30 2017-06-13 Abbott Diabetes Care Inc. Sensitivity calibration of in vivo sensors used to measure analyte concentration
US8219173B2 (en) 2008-09-30 2012-07-10 Abbott Diabetes Care Inc. Optimizing analyte sensor calibration
WO2007127616A2 (en) * 2006-04-12 2007-11-08 Benjamin Pless Cavitation heating system and method
US20070255126A1 (en) * 2006-04-28 2007-11-01 Moberg Sheldon B Data communication in networked fluid infusion systems
US20070254593A1 (en) * 2006-04-28 2007-11-01 Medtronic Minimed, Inc. Wireless data communication for a medical device network that supports a plurality of data communication modes
US20070253380A1 (en) * 2006-04-28 2007-11-01 James Jollota Data translation device with nonvolatile memory for a networked medical device system
US20070255125A1 (en) * 2006-04-28 2007-11-01 Moberg Sheldon B Monitor devices for networked fluid infusion systems
US8073008B2 (en) * 2006-04-28 2011-12-06 Medtronic Minimed, Inc. Subnetwork synchronization and variable transmit synchronization techniques for a wireless medical device network
US20090054749A1 (en) * 2006-05-31 2009-02-26 Abbott Diabetes Care, Inc. Method and System for Providing Data Transmission in a Data Management System
WO2007147475A1 (en) * 2006-06-19 2007-12-27 Roche Diagnostics Gmbh Amperometric sensor and method for its manufacturing
US9700252B2 (en) 2006-06-19 2017-07-11 Roche Diabetes Care, Inc. Amperometric sensor and method for its manufacturing
US20080004601A1 (en) * 2006-06-28 2008-01-03 Abbott Diabetes Care, Inc. Analyte Monitoring and Therapy Management System and Methods Therefor
US8492130B2 (en) * 2006-06-29 2013-07-23 Ikeda Food Research Co., Ltd. FAD-conjugated glucose dehydrogenase gene
US20090105571A1 (en) * 2006-06-30 2009-04-23 Abbott Diabetes Care, Inc. Method and System for Providing Data Communication in Data Management Systems
US9119582B2 (en) * 2006-06-30 2015-09-01 Abbott Diabetes Care, Inc. Integrated analyte sensor and infusion device and methods therefor
US7699973B2 (en) * 2006-06-30 2010-04-20 Abbott Diabetes Care Inc. Rapid analyte measurement assay
GB0613500D0 (en) * 2006-07-07 2006-08-16 Lectus Therapeutics Ltd Apparatus and Methods
WO2008082694A2 (en) * 2006-07-14 2008-07-10 Akermin, Inc. Organelles in bioanodes, biocathodes, and biofuel cells
US7943385B2 (en) 2006-07-25 2011-05-17 General Atomics Methods for assaying percentage of glycated hemoglobin
WO2008013874A1 (en) 2006-07-25 2008-01-31 General Atomics Methods for assaying percentage of glycated hemoglobin
US20110054391A1 (en) * 2006-07-28 2011-03-03 Ward W Kenneth Analyte sensing and response system
US8206296B2 (en) 2006-08-07 2012-06-26 Abbott Diabetes Care Inc. Method and system for providing integrated analyte monitoring and infusion system therapy management
US8932216B2 (en) 2006-08-07 2015-01-13 Abbott Diabetes Care Inc. Method and system for providing data management in integrated analyte monitoring and infusion system
GB0616566D0 (en) * 2006-08-19 2006-09-27 Rolls Royce Plc An alloy and method of treating titanium aluminide
DE602006004043D1 (en) * 2006-08-25 2009-01-15 Alcatel Lucent Digital signal receiver with Q-factor monitoring
US20080076836A1 (en) * 2006-09-01 2008-03-27 Cardiac Pacemakers, Inc Method and apparatus for using light to enhance cell growth and survival
GB0617276D0 (en) * 2006-09-04 2006-10-11 Suresensors Device
EP2063762A1 (en) * 2006-09-06 2009-06-03 Medingo Ltd. Fluid delivery system with optical sensing of analyte concentration levels
DK2083673T3 (en) 2006-09-29 2012-09-24 Medingo Ltd FLUID DISTRIBUTION SYSTEM WITH ELECTROCHEMICAL DETECTION OF ANALYTIC CONCENTRATION LEVELS
CA2664528A1 (en) 2006-10-04 2008-04-10 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US7831287B2 (en) * 2006-10-04 2010-11-09 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8790819B1 (en) 2006-10-06 2014-07-29 Greatbatch Ltd. Implantable medical assembly
AU2007308804A1 (en) 2006-10-26 2008-05-02 Abbott Diabetes Care, Inc. Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors
US8158081B2 (en) * 2006-10-31 2012-04-17 Abbott Diabetes Care Inc. Analyte monitoring devices
US20080119710A1 (en) * 2006-10-31 2008-05-22 Abbott Diabetes Care, Inc. Medical devices and methods of using the same
US20080119702A1 (en) * 2006-10-31 2008-05-22 Abbott Diabetes Care, Inc. Analyte meter having alert, alarm and test reminder capabilities and methods of use
US7740580B2 (en) * 2006-10-31 2010-06-22 Abbott Diabetes Care Inc. Analyte monitoring
US8579853B2 (en) * 2006-10-31 2013-11-12 Abbott Diabetes Care Inc. Infusion devices and methods
CA2668685A1 (en) * 2006-11-06 2008-05-15 Akermin, Inc. Bioanode and biocathode stack assemblies
US8255034B2 (en) * 2006-11-30 2012-08-28 Abbott Diabetes Care Inc. Lyotropic liquid crystal coated analyte monitoring device and methods of use
US20080139910A1 (en) * 2006-12-06 2008-06-12 Metronic Minimed, Inc. Analyte sensor and method of using the same
WO2008082987A2 (en) * 2006-12-26 2008-07-10 Abbott Diabetes Care Inc Analyte meter protectors and methods
US20080214912A1 (en) * 2007-01-10 2008-09-04 Glucose Sensing Technologies, Llc Blood Glucose Monitoring System And Method
US20080177166A1 (en) * 2007-01-18 2008-07-24 Provex Technologies, Llc Ultrasensitive amperometric saliva glucose sensor strip
US8808515B2 (en) * 2007-01-31 2014-08-19 Abbott Diabetes Care Inc. Heterocyclic nitrogen containing polymers coated analyte monitoring device and methods of use
US10154804B2 (en) * 2007-01-31 2018-12-18 Medtronic Minimed, Inc. Model predictive method and system for controlling and supervising insulin infusion
US20080199894A1 (en) 2007-02-15 2008-08-21 Abbott Diabetes Care, Inc. Device and method for automatic data acquisition and/or detection
US8121857B2 (en) * 2007-02-15 2012-02-21 Abbott Diabetes Care Inc. Device and method for automatic data acquisition and/or detection
CA2681412A1 (en) 2007-03-26 2008-10-02 Dexcom, Inc. Analyte sensor
JP2010523227A (en) * 2007-04-04 2010-07-15 アイセンス コーポレーション Analyte sensing device having one or more sensing electrodes
CA2683959C (en) 2007-04-14 2017-08-29 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US9008743B2 (en) * 2007-04-14 2015-04-14 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
WO2009096992A1 (en) 2007-04-14 2009-08-06 Abbott Diabetes Care, Inc. Method and apparatus for providing data processing and control in medical communication system
CA2683930A1 (en) 2007-04-14 2008-10-23 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US7768387B2 (en) 2007-04-14 2010-08-03 Abbott Diabetes Care Inc. Method and apparatus for providing dynamic multi-stage signal amplification in a medical device
WO2008130896A1 (en) * 2007-04-14 2008-10-30 Abbott Diabetes Care, Inc. Method and apparatus for providing data processing and control in medical communication system
US20080269714A1 (en) 2007-04-25 2008-10-30 Medtronic Minimed, Inc. Closed loop/semi-closed loop therapy modification system
US20080269723A1 (en) * 2007-04-25 2008-10-30 Medtronic Minimed, Inc. Closed loop/semi-closed loop therapy modification system
US8080385B2 (en) * 2007-05-03 2011-12-20 Abbott Diabetes Care Inc. Crosslinked adduct of polyaniline and polymer acid containing redox enzyme for electrochemical sensor
US20080281179A1 (en) * 2007-05-08 2008-11-13 Abbott Diabetes Care, Inc. Analyte monitoring system and methods
US8260558B2 (en) 2007-05-14 2012-09-04 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US7996158B2 (en) 2007-05-14 2011-08-09 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8600681B2 (en) 2007-05-14 2013-12-03 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US20080312845A1 (en) * 2007-05-14 2008-12-18 Abbott Diabetes Care, Inc. Method and apparatus for providing data processing and control in a medical communication system
US10002233B2 (en) * 2007-05-14 2018-06-19 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8103471B2 (en) 2007-05-14 2012-01-24 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8444560B2 (en) * 2007-05-14 2013-05-21 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US9125548B2 (en) 2007-05-14 2015-09-08 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8560038B2 (en) 2007-05-14 2013-10-15 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8239166B2 (en) * 2007-05-14 2012-08-07 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
WO2008150917A1 (en) 2007-05-31 2008-12-11 Abbott Diabetes Care, Inc. Insertion devices and methods
US20080300572A1 (en) * 2007-06-01 2008-12-04 Medtronic Minimed, Inc. Wireless monitor for a personal medical device system
EP2157907B1 (en) 2007-06-07 2013-03-27 MicroCHIPS, Inc. Electrochemical biosensors and arrays
US20080319294A1 (en) * 2007-06-21 2008-12-25 Abbott Diabetes Care, Inc. Health management devices and methods
CA2690870C (en) * 2007-06-21 2017-07-11 Abbott Diabetes Care Inc. Health monitor
EP3533387A3 (en) 2007-06-21 2019-11-13 Abbott Diabetes Care, Inc. Health management devices and methods
US8641618B2 (en) * 2007-06-27 2014-02-04 Abbott Diabetes Care Inc. Method and structure for securing a monitoring device element
US8085151B2 (en) 2007-06-28 2011-12-27 Abbott Diabetes Care Inc. Signal converting cradle for medical condition monitoring and management system
US8160900B2 (en) 2007-06-29 2012-04-17 Abbott Diabetes Care Inc. Analyte monitoring and management device and method to analyze the frequency of user interaction with the device
EP2017350A1 (en) * 2007-07-19 2009-01-21 F. Hoffmann-La Roche AG Electrochemical sensor with covalent-bound enzyme
US20090036760A1 (en) * 2007-07-31 2009-02-05 Abbott Diabetes Care, Inc. Method and apparatus for providing data processing and control in a medical communication system
US20090038004A1 (en) * 2007-07-31 2009-02-05 Gabor Blasko Role change based on coupling or docking of information handling apparatus and method for same
US8834366B2 (en) 2007-07-31 2014-09-16 Abbott Diabetes Care Inc. Method and apparatus for providing analyte sensor calibration
US7768386B2 (en) * 2007-07-31 2010-08-03 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US20090043183A1 (en) * 2007-08-08 2009-02-12 Lifescan, Inc. Integrated stent and blood analyte monitoring system
US7747302B2 (en) * 2007-08-08 2010-06-29 Lifescan, Inc. Method for integrating facilitated blood flow and blood analyte monitoring
US20120046533A1 (en) 2007-08-29 2012-02-23 Medtronic Minimed, Inc. Combined sensor and infusion sets
US9968742B2 (en) 2007-08-29 2018-05-15 Medtronic Minimed, Inc. Combined sensor and infusion set using separated sites
WO2009051901A2 (en) 2007-08-30 2009-04-23 Pepex Biomedical, Llc Electrochemical sensor and method for manufacturing
WO2009032760A2 (en) 2007-08-30 2009-03-12 Pepex Biomedical Llc Electrochmical sensor and method for manufacturing
US11385226B2 (en) * 2007-09-17 2022-07-12 Red Ivory Llc Self-actuating signal producing detection devices and methods
US8163146B2 (en) 2007-10-12 2012-04-24 Abbott Diabetes Care Inc. Mediator stabilized reagent compositions for use in biosensor electrodes
US8000918B2 (en) 2007-10-23 2011-08-16 Edwards Lifesciences Corporation Monitoring and compensating for temperature-related error in an electrochemical sensor
US8377031B2 (en) 2007-10-23 2013-02-19 Abbott Diabetes Care Inc. Closed loop control system with safety parameters and methods
US8216138B1 (en) 2007-10-23 2012-07-10 Abbott Diabetes Care Inc. Correlation of alternative site blood and interstitial fluid glucose concentrations to venous glucose concentration
US8409093B2 (en) 2007-10-23 2013-04-02 Abbott Diabetes Care Inc. Assessing measures of glycemic variability
WO2009055736A1 (en) 2007-10-25 2009-04-30 Dexcom, Inc. Systems and methods for processing sensor data
US8417312B2 (en) 2007-10-25 2013-04-09 Dexcom, Inc. Systems and methods for processing sensor data
US20090112626A1 (en) * 2007-10-30 2009-04-30 Cary Talbot Remote wireless monitoring, processing, and communication of patient data
US7783442B2 (en) * 2007-10-31 2010-08-24 Medtronic Minimed, Inc. System and methods for calibrating physiological characteristic sensors
JP2011504129A (en) * 2007-11-21 2011-02-03 メディンゴ・リミテッド Analyte monitoring and fluid dispensing system
US8615281B2 (en) * 2007-11-21 2013-12-24 Medingo Ltd. Hypodermic optical monitoring of bodily analyte
US20090188811A1 (en) 2007-11-28 2009-07-30 Edwards Lifesciences Corporation Preparation and maintenance of sensors
WO2009076302A1 (en) 2007-12-10 2009-06-18 Bayer Healthcare Llc Control markers for auto-detection of control solution and methods of use
US9839395B2 (en) 2007-12-17 2017-12-12 Dexcom, Inc. Systems and methods for processing sensor data
US20090164239A1 (en) * 2007-12-19 2009-06-25 Abbott Diabetes Care, Inc. Dynamic Display Of Glucose Information
US20090164190A1 (en) * 2007-12-19 2009-06-25 Abbott Diabetes Care, Inc. Physiological condition simulation device and method
US8313467B2 (en) 2007-12-27 2012-11-20 Medtronic Minimed, Inc. Reservoir pressure equalization systems and methods
US8986253B2 (en) 2008-01-25 2015-03-24 Tandem Diabetes Care, Inc. Two chamber pumps and related methods
US8431011B2 (en) 2008-01-31 2013-04-30 Abbott Diabetes Care Inc. Method for automatically and rapidly distinguishing between control and sample solutions in a biosensor strip
WO2009100082A1 (en) 2008-02-04 2009-08-13 Bayer Healthcare Llc Semiconductor based analyte sensors and methods
GB2457660A (en) * 2008-02-19 2009-08-26 Sphere Medical Ltd Methods of calibrating a sensor in a patient monitoring system
EP2252196A4 (en) 2008-02-21 2013-05-15 Dexcom Inc Systems and methods for processing, transmitting and displaying sensor data
WO2009108836A1 (en) * 2008-02-29 2009-09-03 Path Scientific, Llc Unitized painfree blood glucose measuring device
RU2500349C2 (en) * 2008-03-17 2013-12-10 Айсенс Корпорейшн Auxiliary unit of analyte sensor and methods and devices for introduction of analyte sensor, connected with auxiliary unit
US20090275815A1 (en) * 2008-03-21 2009-11-05 Nova Biomedical Corporation Temperature-compensated in-vivo sensor
US20090240121A1 (en) * 2008-03-21 2009-09-24 Nova Biomedical Corporation Intravascular sensor and insertion set combination
US20090242399A1 (en) * 2008-03-25 2009-10-01 Dexcom, Inc. Analyte sensor
US20090247855A1 (en) * 2008-03-28 2009-10-01 Dexcom, Inc. Polymer membranes for continuous analyte sensors
WO2009124095A1 (en) * 2008-03-31 2009-10-08 Abbott Diabetes Care Inc. Shallow implantable analyte sensor with rapid physiological response
US8241616B2 (en) * 2008-04-03 2012-08-14 Rohm And Haas Company Hair styling composition
EP2982383B1 (en) 2008-04-10 2019-05-15 Abbott Diabetes Care, Inc. Method for sterilizing an analyte sensor
WO2009126900A1 (en) 2008-04-11 2009-10-15 Pelikan Technologies, Inc. Method and apparatus for analyte detecting device
US8262874B2 (en) * 2008-04-14 2012-09-11 Abbott Diabetes Care Inc. Biosensor coating composition and methods thereof
EP2283149A1 (en) * 2008-05-13 2011-02-16 General Atomics Electrochemical biosensor for direct determination of percentage of glycated hemoglobin
US9295786B2 (en) * 2008-05-28 2016-03-29 Medtronic Minimed, Inc. Needle protective device for subcutaneous sensors
US8924159B2 (en) 2008-05-30 2014-12-30 Abbott Diabetes Care Inc. Method and apparatus for providing glycemic control
US7826382B2 (en) 2008-05-30 2010-11-02 Abbott Diabetes Care Inc. Close proximity communication device and methods
US20090300616A1 (en) * 2008-05-30 2009-12-03 Abbott Diabetes Care, Inc. Automated task execution for an analyte monitoring system
EP2293719B1 (en) 2008-05-30 2015-09-09 Intuity Medical, Inc. Body fluid sampling device -- sampling site interface
US8591410B2 (en) * 2008-05-30 2013-11-26 Abbott Diabetes Care Inc. Method and apparatus for providing glycemic control
US8620398B2 (en) * 2008-06-02 2013-12-31 Abbott Diabetes Care Inc. Reference electrodes having an extended lifetime for use in long term amperometric sensors
US20090294307A1 (en) * 2008-06-02 2009-12-03 Zenghe Liu Redox polymer based reference electrodes having an extended lifetime for use in long term amperometric sensors
US8155722B2 (en) * 2008-06-02 2012-04-10 Abbott Diabetes Care Inc. Reference electrodes having an extended lifetime for use in long term amperometric sensors
US8280474B2 (en) 2008-06-02 2012-10-02 Abbott Diabetes Care Inc. Reference electrodes having an extended lifetime for use in long term amperometric sensors
EP2299904B1 (en) 2008-06-06 2019-09-11 Intuity Medical, Inc. Medical measurement method
WO2009148624A1 (en) 2008-06-06 2009-12-10 Intuity Medical, Inc. Detection meter and mode of operation
JP5405916B2 (en) * 2008-06-24 2014-02-05 パナソニック株式会社 Biosensor, method for manufacturing the same, and detection system including the same
US8876755B2 (en) 2008-07-14 2014-11-04 Abbott Diabetes Care Inc. Closed loop control system interface and methods
US7896703B2 (en) * 2008-07-17 2011-03-01 Abbott Diabetes Care Inc. Strip connectors for measurement devices
EP2149957B1 (en) * 2008-07-30 2017-06-14 Harman Becker Automotive Systems GmbH Priority based power distribution arrangement
US8700114B2 (en) * 2008-07-31 2014-04-15 Medtronic Minmed, Inc. Analyte sensor apparatuses comprising multiple implantable sensor elements and methods for making and using them
US20100030052A1 (en) * 2008-07-31 2010-02-04 Bommakanti Balasubrahmanya S Analyte sensors comprising plasticizers
US8622988B2 (en) 2008-08-31 2014-01-07 Abbott Diabetes Care Inc. Variable rate closed loop control and methods
US8734422B2 (en) 2008-08-31 2014-05-27 Abbott Diabetes Care Inc. Closed loop control with improved alarm functions
US20100057040A1 (en) 2008-08-31 2010-03-04 Abbott Diabetes Care, Inc. Robust Closed Loop Control And Methods
US9943644B2 (en) * 2008-08-31 2018-04-17 Abbott Diabetes Care Inc. Closed loop control with reference measurement and methods thereof
EP2355865A2 (en) 2008-09-02 2011-08-17 Medingo Ltd. Remote control for fluid dispensing device with a rechargeable power source
US8637194B2 (en) 2008-09-02 2014-01-28 Bio-Nano Power, Llc Bio-nano power cells and their uses
US8636884B2 (en) 2008-09-15 2014-01-28 Abbott Diabetes Care Inc. Cationic polymer based wired enzyme formulations for use in analyte sensors
US8408421B2 (en) 2008-09-16 2013-04-02 Tandem Diabetes Care, Inc. Flow regulating stopcocks and related methods
EP2341830A4 (en) 2008-09-19 2012-10-31 Bayer Healthcare Llc Analyte sensors, systems, testing apparatus and manufacturing methods
WO2010033748A1 (en) 2008-09-19 2010-03-25 Bayer Healthcare Llc Electrical devices with enhanced electrochemical activity and manufacturing methods thereof
WO2010033878A2 (en) 2008-09-19 2010-03-25 David Brown Solute concentration measurement device and related methods
US8986208B2 (en) 2008-09-30 2015-03-24 Abbott Diabetes Care Inc. Analyte sensor sensitivity attenuation mitigation
US20100082364A1 (en) * 2008-09-30 2010-04-01 Abbott Diabetes Care, Inc. Medical Information Management
US8983568B2 (en) 2008-09-30 2015-03-17 Abbott Diabetes Care Inc. Analyte sensors comprising leveling agents
US8208973B2 (en) * 2008-11-05 2012-06-26 Medtronic Minimed, Inc. System and method for variable beacon timing with wireless devices
US9326707B2 (en) 2008-11-10 2016-05-03 Abbott Diabetes Care Inc. Alarm characterization for analyte monitoring devices and systems
US20110282172A1 (en) 2008-11-11 2011-11-17 Isense Corporation Long-term implantable biosensor
US8506740B2 (en) 2008-11-14 2013-08-13 Pepex Biomedical, Llc Manufacturing electrochemical sensor module
WO2010056878A2 (en) 2008-11-14 2010-05-20 Pepex Biomedical, Llc Electrochemical sensor module
US8951377B2 (en) 2008-11-14 2015-02-10 Pepex Biomedical, Inc. Manufacturing electrochemical sensor module
US20100161346A1 (en) * 2008-12-24 2010-06-24 Kristen Getschmann Systems and Methods for Providing Bolus Dosage Recommendations
US9330237B2 (en) * 2008-12-24 2016-05-03 Medtronic Minimed, Inc. Pattern recognition and filtering in a therapy management system
US20100160756A1 (en) * 2008-12-24 2010-06-24 Edwards Lifesciences Corporation Membrane Layer for Electrochemical Biosensor and Method of Accommodating Electromagnetic and Radiofrequency Fields
US20100160740A1 (en) * 2008-12-24 2010-06-24 Gary Cohen Use of Patterns in a Therapy Management System
US20100187132A1 (en) * 2008-12-29 2010-07-29 Don Alden Determination of the real electrochemical surface areas of screen printed electrodes
US20100185517A1 (en) * 2009-01-21 2010-07-22 Yahoo! Inc. User interface for interest-based targeted marketing
US9375169B2 (en) * 2009-01-30 2016-06-28 Sanofi-Aventis Deutschland Gmbh Cam drive for managing disposable penetrating member actions with a single motor and motor and control system
US20100198196A1 (en) * 2009-01-30 2010-08-05 Abbott Diabetes Care, Inc. Therapy Delivery Device Programming Tool
US8560082B2 (en) 2009-01-30 2013-10-15 Abbott Diabetes Care Inc. Computerized determination of insulin pump therapy parameters using real time and retrospective data processing
US9402544B2 (en) * 2009-02-03 2016-08-02 Abbott Diabetes Care Inc. Analyte sensor and apparatus for insertion of the sensor
WO2011034629A1 (en) * 2009-02-05 2011-03-24 Abbott Diabetes Care Inc. Devices and methods for metering insoluble active agent particles
CN102308204B (en) 2009-02-09 2014-07-09 爱科来株式会社 Electrochemical sensor and method for manufacturing same
US20100213079A1 (en) * 2009-02-24 2010-08-26 Ultradian Diagnostics, Llc Microsecond response electrochemical sensors and methods thereof
US20100213057A1 (en) 2009-02-26 2010-08-26 Benjamin Feldman Self-Powered Analyte Sensor
US9339229B2 (en) 2009-02-26 2016-05-17 Abbott Diabetes Care Inc. Analyte monitoring devices and methods
DK3912551T3 (en) 2009-02-26 2023-10-30 Abbott Diabetes Care Inc Procedure for calibrating an analyte sensor
RU2489089C2 (en) 2009-03-16 2013-08-10 АРКРЭЙ, Инк. Method of continuous measurement of substrate concentration
US9446194B2 (en) 2009-03-27 2016-09-20 Dexcom, Inc. Methods and systems for promoting glucose management
WO2010114942A1 (en) * 2009-03-31 2010-10-07 Abbott Diabetes Care Inc. Precise fluid dispensing method and device
US8497777B2 (en) * 2009-04-15 2013-07-30 Abbott Diabetes Care Inc. Analyte monitoring system having an alert
WO2010121229A1 (en) 2009-04-16 2010-10-21 Abbott Diabetes Care Inc. Analyte sensor calibration management
WO2010123521A1 (en) 2009-04-21 2010-10-28 The Trustees Of Columbia University In The City Of New York Sensors for long-term and continuous monitoring of biochemicals
US8758583B2 (en) 2009-04-28 2014-06-24 Abbott Diabetes Care Inc. Smart sensor ports and methods of using same
US8467972B2 (en) * 2009-04-28 2013-06-18 Abbott Diabetes Care Inc. Closed loop blood glucose control algorithm analysis
US8359081B2 (en) * 2009-04-28 2013-01-22 Abbott Diabetes Care Inc. Service-detectable analyte sensors and methods of using and making same
US20100274515A1 (en) * 2009-04-28 2010-10-28 Abbott Diabetes Care Inc. Dynamic Analyte Sensor Calibration Based On Sensor Stability Profile
EP2424426B1 (en) 2009-04-29 2020-01-08 Abbott Diabetes Care, Inc. Method and system for providing data communication in continuous glucose monitoring and management system
EP2425209A4 (en) 2009-04-29 2013-01-09 Abbott Diabetes Care Inc Method and system for providing real time analyte sensor calibration with retrospective backfill
US20100278738A1 (en) * 2009-05-04 2010-11-04 Sitzman Thomas J Method to detect and monitor ischemia in transplanted organs and tissues
US8236254B2 (en) * 2009-05-14 2012-08-07 Abbott Diabetes Care Inc. Cap-linked test strip carrier for vial augmentation
EP2434944B1 (en) 2009-05-29 2014-12-03 Abbott Diabetes Care, Inc. Glucose monitoring system with wireless communications
EP2438527B1 (en) 2009-06-04 2018-05-02 Abbott Diabetes Care, Inc. Method and system for updating a medical device
US8000763B2 (en) * 2009-06-30 2011-08-16 Abbott Diabetes Care Inc. Integrated devices having extruded electrode structures and methods of using same
US8437827B2 (en) * 2009-06-30 2013-05-07 Abbott Diabetes Care Inc. Extruded analyte sensors and methods of using same
US8613892B2 (en) 2009-06-30 2013-12-24 Abbott Diabetes Care Inc. Analyte meter with a moveable head and methods of using the same
US10376213B2 (en) * 2009-06-30 2019-08-13 Waveform Technologies, Inc. System, method and apparatus for sensor insertion
MX337978B (en) 2009-07-01 2016-03-29 Fresenius Med Care Hldg Inc Drug delivery devices and related systems and methods.
FR2947634B1 (en) * 2009-07-06 2012-07-27 Otv Sa DEVICE FOR MEASURING AT LEAST ONE PROPERTY OF WATER
US8344847B2 (en) 2009-07-09 2013-01-01 Medtronic Minimed, Inc. Coordination of control commands in a medical device system having at least one therapy delivery device and at least one wireless controller device
US20110009813A1 (en) * 2009-07-09 2011-01-13 Medtronic Minimed, Inc. Panning a display of a portable medical device
US20110006880A1 (en) * 2009-07-09 2011-01-13 Medtronic Minimed, Inc. Fingerprint-linked control of a portable medical device
EP3932309A1 (en) 2009-07-23 2022-01-05 Abbott Diabetes Care, Inc. Continuous analyte measurement system
EP3173014B1 (en) * 2009-07-23 2021-08-18 Abbott Diabetes Care, Inc. Real time management of data relating to physiological control of glucose levels
US8641671B2 (en) 2009-07-30 2014-02-04 Tandem Diabetes Care, Inc. Infusion pump system with disposable cartridge having pressure venting and pressure feedback
WO2011014851A1 (en) 2009-07-31 2011-02-03 Abbott Diabetes Care Inc. Method and apparatus for providing analyte monitoring system calibration accuracy
US20110023878A1 (en) * 2009-07-31 2011-02-03 Nellcor Puritan Bennett Llc Method And System For Delivering A Single-Breath, Low Flow Recruitment Maneuver
JP2013501532A (en) 2009-08-08 2013-01-17 サノフィ−アベンティス・ドイチュラント・ゲゼルシャフト・ミット・ベシュレンクテル・ハフツング Implantable sensor device and pharmaceutical delivery device connectable to such sensor device
US9125603B2 (en) 2009-08-11 2015-09-08 Abbott Diabetes Care Inc. Analyte sensor ports
US20110046466A1 (en) * 2009-08-19 2011-02-24 Feldman Benjamin J Analyte Sensors Including Nanomaterials and Methods of Using Same
WO2011025999A1 (en) * 2009-08-29 2011-03-03 Abbott Diabetes Care Inc. Analyte sensor
WO2011026130A1 (en) * 2009-08-31 2011-03-03 Abbott Diabetes Care Inc. Inserter device including rotor subassembly
ES2912584T3 (en) 2009-08-31 2022-05-26 Abbott Diabetes Care Inc A glucose monitoring system and method
US8357276B2 (en) 2009-08-31 2013-01-22 Abbott Diabetes Care Inc. Small volume test strips with large sample fill ports, supported test strips, and methods of making and using same
AU2010286917B2 (en) 2009-08-31 2016-03-10 Abbott Diabetes Care Inc. Medical devices and methods
US8487758B2 (en) * 2009-09-02 2013-07-16 Medtronic Minimed, Inc. Medical device having an intelligent alerting scheme, and related operating methods
EP2478350B1 (en) 2009-09-15 2021-06-16 Agamatrix, Inc. Implantable electrochemical biosensor system and method
US20120172773A1 (en) * 2009-09-22 2012-07-05 David Combs Durable electrode construction for an orthotic device
WO2011041449A1 (en) * 2009-09-29 2011-04-07 Abbott Diabetes Care Inc. Sensor inserter having introducer
US20110082356A1 (en) 2009-10-01 2011-04-07 Medtronic Minimed, Inc. Analyte sensor apparatuses having interference rejection membranes and methods for making and using them
WO2011044386A1 (en) * 2009-10-07 2011-04-14 Abbott Diabetes Care Inc. Sensor inserter assembly having rotatable trigger
US8741591B2 (en) * 2009-10-09 2014-06-03 The Research Foundation For The State University Of New York pH-insensitive glucose indicator protein
WO2011053881A1 (en) 2009-10-30 2011-05-05 Abbott Diabetes Care Inc. Method and apparatus for detecting false hypoglycemic conditions
US8386042B2 (en) * 2009-11-03 2013-02-26 Medtronic Minimed, Inc. Omnidirectional accelerometer device and medical device incorporating same
WO2011061733A1 (en) * 2009-11-17 2011-05-26 Israel Shamir Lebovitz A method and device for remote controlled application of medical monitoring and attention
US20110288388A1 (en) 2009-11-20 2011-11-24 Medtronic Minimed, Inc. Multi-conductor lead configurations useful with medical device systems and methods for making and using them
US20110124993A1 (en) * 2009-11-24 2011-05-26 Abbott Diabetes Care Inc. Analyte Sensors Comprising Self-Polymerizing Hydrogels
US8354013B2 (en) 2009-11-24 2013-01-15 Abbott Diabetes Care Inc. Analyte sensors comprising high-boiling point solvents
US9042954B2 (en) * 2009-11-24 2015-05-26 Abbott Diabetes Care Inc. Analyte sensors comprising hydrogel membranes
US8919605B2 (en) 2009-11-30 2014-12-30 Intuity Medical, Inc. Calibration material delivery devices and methods
WO2011064780A2 (en) 2009-11-30 2011-06-03 Medingo Ltd. Analyte monitoring and fluid dispensing system
WO2011075575A1 (en) 2009-12-17 2011-06-23 Bayer Healthcare Llc Transdermal systems, devices, and methods to optically analyze an analyte
US8660628B2 (en) 2009-12-21 2014-02-25 Medtronic Minimed, Inc. Analyte sensors comprising blended membrane compositions and methods for making and using them
US8574201B2 (en) 2009-12-22 2013-11-05 Medtronic Minimed, Inc. Syringe piston with check valve seal
US20110152970A1 (en) * 2009-12-23 2011-06-23 Medtronic Minimed, Inc. Location-based ranking and switching of wireless channels in a body area network of medical devices
US8755269B2 (en) * 2009-12-23 2014-06-17 Medtronic Minimed, Inc. Ranking and switching of wireless channels in a body area network of medical devices
US8803688B2 (en) * 2010-01-07 2014-08-12 Lisa Halff System and method responsive to an event detected at a glucose monitoring device
US20110163880A1 (en) * 2010-01-07 2011-07-07 Lisa Halff System and method responsive to an alarm event detected at an insulin delivery device
US8828330B2 (en) 2010-01-28 2014-09-09 Abbott Diabetes Care Inc. Universal test strip port
US20110184258A1 (en) * 2010-01-28 2011-07-28 Abbott Diabetes Care Inc. Balloon Catheter Analyte Measurement Sensors and Methods for Using the Same
USD924406S1 (en) 2010-02-01 2021-07-06 Abbott Diabetes Care Inc. Analyte sensor inserter
EP2545853B1 (en) * 2010-03-09 2017-10-25 ARKRAY, Inc. Electrochemical sensor
US10448872B2 (en) 2010-03-16 2019-10-22 Medtronic Minimed, Inc. Analyte sensor apparatuses having improved electrode configurations and methods for making and using them
CN102548476A (en) 2010-03-24 2012-07-04 雅培糖尿病护理公司 Medical device inserters and processes of inserting and using medical devices
US8965476B2 (en) 2010-04-16 2015-02-24 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
WO2013066362A1 (en) 2011-02-17 2013-05-10 Abbott Diabetes Care Inc. Analyte meter communication module
CA2766947A1 (en) 2010-04-16 2011-10-20 Abbott Diabetes Care Inc. Analyte monitoring device and methods
JP5753720B2 (en) 2010-04-22 2015-07-22 アークレイ株式会社 Biosensor
US9198623B2 (en) 2010-04-22 2015-12-01 Abbott Diabetes Care Inc. Devices, systems, and methods related to analyte monitoring and management
WO2011149857A1 (en) 2010-05-24 2011-12-01 Abbott Diabetes Care Inc. Method and system for updating a medical device
US8636711B2 (en) 2010-06-14 2014-01-28 Legacy Emanuel Hospital & Health Center Stabilized glucagon solutions and uses therefor
US9215995B2 (en) * 2010-06-23 2015-12-22 Medtronic Minimed, Inc. Sensor systems having multiple probes and electrode arrays
US8635046B2 (en) 2010-06-23 2014-01-21 Abbott Diabetes Care Inc. Method and system for evaluating analyte sensor response characteristics
CA2803797A1 (en) 2010-06-25 2011-12-29 Intuity Medical, Inc. Analyte monitoring methods and systems
US10092229B2 (en) 2010-06-29 2018-10-09 Abbott Diabetes Care Inc. Calibration of analyte measurement system
US11064921B2 (en) 2010-06-29 2021-07-20 Abbott Diabetes Care Inc. Devices, systems and methods for on-skin or on-body mounting of medical devices
DK2598021T3 (en) 2010-07-28 2015-09-28 Abbott Diabetes Care Inc Analyte sensors with temperature-independent membranes
EP2624745A4 (en) 2010-10-07 2018-05-23 Abbott Diabetes Care, Inc. Analyte monitoring devices and methods
US8562565B2 (en) 2010-10-15 2013-10-22 Medtronic Minimed, Inc. Battery shock absorber for a portable medical device
US8603033B2 (en) 2010-10-15 2013-12-10 Medtronic Minimed, Inc. Medical device and related assembly having an offset element for a piezoelectric speaker
US8603032B2 (en) 2010-10-15 2013-12-10 Medtronic Minimed, Inc. Medical device with membrane keypad sealing element, and related manufacturing method
US8479595B2 (en) 2010-10-20 2013-07-09 Medtronic Minimed, Inc. Sensor assembly and medical device incorporating same
US8474332B2 (en) 2010-10-20 2013-07-02 Medtronic Minimed, Inc. Sensor assembly and medical device incorporating same
US8495918B2 (en) 2010-10-20 2013-07-30 Medtronic Minimed, Inc. Sensor assembly and medical device incorporating same
WO2012058237A1 (en) 2010-10-26 2012-05-03 Abbott Diabetes Care Inc. Analyte measurement devices and systems, and components and methods related thereto
EP2455748A1 (en) 2010-11-17 2012-05-23 Max-Planck-Gesellschaft zur Förderung der Wissenschaften e.V. Sensor device, in particular for substance sensing, measuring apparatus, and method of manufacturing the sensor device
US8702928B2 (en) 2010-11-22 2014-04-22 Abbott Diabetes Care Inc. Modular analyte measurement system with extendable strip port
US9713440B2 (en) 2010-12-08 2017-07-25 Abbott Diabetes Care Inc. Modular analyte measurement systems, modular components thereof and related methods
AU2011338255B2 (en) 2010-12-09 2016-06-02 Abbott Diabetes Care Inc. Analyte sensors with a sensing surface having small sensing spots
US8469942B2 (en) 2010-12-22 2013-06-25 Medtronic Minimed, Inc. Occlusion detection for a fluid infusion device
US8690855B2 (en) 2010-12-22 2014-04-08 Medtronic Minimed, Inc. Fluid reservoir seating procedure for a fluid infusion device
US8589106B2 (en) * 2010-12-22 2013-11-19 Roche Diagnostics Operations, Inc. Calibration of a handheld diabetes managing device that receives data from a continuous glucose monitor
US8628510B2 (en) 2010-12-22 2014-01-14 Medtronic Minimed, Inc. Monitoring the operating health of a force sensor in a fluid infusion device
US8197444B1 (en) 2010-12-22 2012-06-12 Medtronic Minimed, Inc. Monitoring the seating status of a fluid reservoir in a fluid infusion device
US10064987B2 (en) 2011-01-31 2018-09-04 Fresenius Medical Care Holdings, Inc. Preventing over-delivery of drug
JP5819183B2 (en) 2011-02-03 2015-11-18 アークレイ株式会社 Analysis device, sensor inspection device, inspection method, and inspection program
CN106902406B (en) 2011-02-08 2019-11-08 弗雷塞尼斯医疗保健控股公司 Magnetic sensor and related system and method
WO2012108936A1 (en) 2011-02-11 2012-08-16 Abbott Diabetes Care Inc. Data synchronization between two or more analyte detecting devices in a database
WO2012108938A1 (en) 2011-02-11 2012-08-16 Abbott Diabetes Care Inc. Software applications residing on handheld analyte determining devices
US20140088392A1 (en) 2011-02-11 2014-03-27 Abbott Diabetes Care Inc. Feedback from Cloud or HCP to Payer or Patient via Meter or Cell Phone
US20120211946A1 (en) 2011-02-22 2012-08-23 Medtronic Minimed, Inc. Sealing element for a hollow needle of a fluid infusion device
US9463309B2 (en) 2011-02-22 2016-10-11 Medtronic Minimed, Inc. Sealing assembly and structure for a fluid infusion device having a needled fluid reservoir
US9393399B2 (en) 2011-02-22 2016-07-19 Medtronic Minimed, Inc. Sealing assembly for a fluid reservoir of a fluid infusion device
US9283318B2 (en) 2011-02-22 2016-03-15 Medtronic Minimed, Inc. Flanged sealing element and needle guide pin assembly for a fluid infusion device having a needled fluid reservoir
US8614596B2 (en) 2011-02-28 2013-12-24 Medtronic Minimed, Inc. Systems and methods for initializing a voltage bus and medical devices incorporating same
US10136845B2 (en) 2011-02-28 2018-11-27 Abbott Diabetes Care Inc. Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same
EP3583901A3 (en) 2011-02-28 2020-01-15 Abbott Diabetes Care, Inc. Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same
US9101305B2 (en) 2011-03-09 2015-08-11 Medtronic Minimed, Inc. Glucose sensor product and related manufacturing and packaging methods
US10010273B2 (en) 2011-03-10 2018-07-03 Abbott Diabetes Care, Inc. Multi-function analyte monitor device and methods of use
US8564447B2 (en) 2011-03-18 2013-10-22 Medtronic Minimed, Inc. Battery life indication techniques for an electronic device
US9018893B2 (en) 2011-03-18 2015-04-28 Medtronic Minimed, Inc. Power control techniques for an electronic device
KR101952468B1 (en) * 2011-04-18 2019-02-26 노비오센스 비.브이. Electrochemical biosensor based on hollow coils
US9008744B2 (en) 2011-05-06 2015-04-14 Medtronic Minimed, Inc. Method and apparatus for continuous analyte monitoring
US9585605B2 (en) 2011-05-19 2017-03-07 Pepex Biomedical, Inc. Fluid management and patient monitoring system
US9380965B2 (en) 2011-05-20 2016-07-05 Abbott Diabetes Care Inc. Analyte sensors having a membrane with low temperature sensitivity
US9504162B2 (en) 2011-05-20 2016-11-22 Pepex Biomedical, Inc. Manufacturing electrochemical sensor modules
EP3556285B1 (en) 2011-06-16 2022-08-31 Abbott Diabetes Care, Inc. Temperature-compensated analyte monitoring devices, systems, and methods thereof
CA3105324A1 (en) 2011-06-17 2012-12-20 Abbott Diabetes Care Inc. Connectors for making connections between analyte sensors and other devices
WO2013003735A1 (en) * 2011-06-30 2013-01-03 Abbott Diabetes Care Inc. Methods for generating hybrid analyte level output, and devices and systems related thereto
EP2736588A4 (en) 2011-07-27 2015-06-10 Vision Quest Ind Inc Dba Vq Orthocare Electrostimulation system
WO2013019714A1 (en) 2011-07-29 2013-02-07 The Trustees Of Columbia University In The City Of New York Mems affinity sensor for continuous monitoring of analytes
CA3154143A1 (en) 2011-08-03 2013-02-07 Intuity Medical, Inc. Devices and methods for body fluid sampling and analysis
EP3689235A1 (en) 2011-09-28 2020-08-05 Abbott Diabetes Care, Inc. Methods for analyte monitoring management and analyte measurement data management, and articles of manufacture related thereto
EP2760336B1 (en) 2011-09-28 2018-09-19 Abbott Diabetes Care Inc. Methods, devices and systems for analyte monitoring management
US9662243B2 (en) 2011-09-30 2017-05-30 Zoll Circulation, Inc. Heat exchange catheters with bi-directional fluid flow and their methods of manufacture and use
USD680454S1 (en) 2011-10-25 2013-04-23 Abbott Diabetes Care Inc. Analyte meter and strip port
US9069536B2 (en) 2011-10-31 2015-06-30 Abbott Diabetes Care Inc. Electronic devices having integrated reset systems and methods thereof
US9622691B2 (en) 2011-10-31 2017-04-18 Abbott Diabetes Care Inc. Model based variable risk false glucose threshold alarm prevention mechanism
ES2637799T3 (en) 2011-11-15 2017-10-17 Ashwin-Ushas Corporation, Inc. Electrochromic device with complementary polymers
US8710993B2 (en) 2011-11-23 2014-04-29 Abbott Diabetes Care Inc. Mitigating single point failure of devices in an analyte monitoring system and methods thereof
US9317656B2 (en) 2011-11-23 2016-04-19 Abbott Diabetes Care Inc. Compatibility mechanisms for devices in a continuous analyte monitoring system and methods thereof
US8887911B2 (en) 2011-12-09 2014-11-18 Abbott Diabetes Care Inc. Packages and kits for analyte monitoring devices, and methods related thereto
FI4056105T3 (en) 2011-12-11 2023-12-28 Abbott Diabetes Care Inc Analyte sensor devices
EP3662965A1 (en) 2011-12-30 2020-06-10 Abbott Diabetes Care, Inc. Method and apparatus for determining medication dose information
US9610401B2 (en) 2012-01-13 2017-04-04 Medtronic Minimed, Inc. Infusion set component with modular fluid channel element
CA2806765C (en) 2012-03-08 2020-09-22 Isense Corporation Method and apparatus for insertion of a sensor
WO2013138369A1 (en) 2012-03-16 2013-09-19 Dexcom, Inc. Systems and methods for processing analyte sensor data
US8603027B2 (en) 2012-03-20 2013-12-10 Medtronic Minimed, Inc. Occlusion detection using pulse-width modulation and medical device incorporating same
US8603026B2 (en) 2012-03-20 2013-12-10 Medtronic Minimed, Inc. Dynamic pulse-width modulation motor control and medical device incorporating same
US8523803B1 (en) 2012-03-20 2013-09-03 Medtronic Minimed, Inc. Motor health monitoring and medical device incorporating same
US9462970B2 (en) 2012-04-24 2016-10-11 Abbott Diabetes Care Inc. Methods of lag-compensation for analyte measurements, and devices related thereto
US9144646B2 (en) 2012-04-25 2015-09-29 Fresenius Medical Care Holdings, Inc. Vial spiking devices and related assemblies and methods
US9180242B2 (en) 2012-05-17 2015-11-10 Tandem Diabetes Care, Inc. Methods and devices for multiple fluid transfer
US9493807B2 (en) 2012-05-25 2016-11-15 Medtronic Minimed, Inc. Foldover sensors and methods for making and using them
US20130338630A1 (en) 2012-06-07 2013-12-19 Medtronic Minimed, Inc. Diabetes therapy management system for recommending adjustments to an insulin infusion device
US9333292B2 (en) 2012-06-26 2016-05-10 Medtronic Minimed, Inc. Mechanically actuated fluid infusion device
US20140012115A1 (en) 2012-07-03 2014-01-09 Medtronic Minimed, Inc. Plasma deposited adhesion promoter layers for use with analyte sensors
US8808269B2 (en) 2012-08-21 2014-08-19 Medtronic Minimed, Inc. Reservoir plunger position monitoring and medical device incorporating same
US10132793B2 (en) 2012-08-30 2018-11-20 Abbott Diabetes Care Inc. Dropout detection in continuous analyte monitoring data during data excursions
US9662445B2 (en) 2012-08-30 2017-05-30 Medtronic Minimed, Inc. Regulating entry into a closed-loop operating mode of an insulin infusion system
US9623179B2 (en) 2012-08-30 2017-04-18 Medtronic Minimed, Inc. Safeguarding techniques for a closed-loop insulin infusion system
US10130767B2 (en) 2012-08-30 2018-11-20 Medtronic Minimed, Inc. Sensor model supervisor for a closed-loop insulin infusion system
US20140066884A1 (en) 2012-08-30 2014-03-06 Medtronic Minimed, Inc. Sensor model supervisor for a closed-loop insulin infusion system
US9849239B2 (en) 2012-08-30 2017-12-26 Medtronic Minimed, Inc. Generation and application of an insulin limit for a closed-loop operating mode of an insulin infusion system
US10496797B2 (en) 2012-08-30 2019-12-03 Medtronic Minimed, Inc. Blood glucose validation for a closed-loop operating mode of an insulin infusion system
US9878096B2 (en) 2012-08-30 2018-01-30 Medtronic Minimed, Inc. Generation of target glucose values for a closed-loop operating mode of an insulin infusion system
WO2014047484A1 (en) 2012-09-21 2014-03-27 Abbott Diabetes Care Inc. Test strips having ceria nanoparticle electrodes
US9907492B2 (en) 2012-09-26 2018-03-06 Abbott Diabetes Care Inc. Method and apparatus for improving lag correction during in vivo measurement of analyte concentration with analyte concentration variability and range data
US9788765B2 (en) 2012-09-28 2017-10-17 Dexcom, Inc. Zwitterion surface modifications for continuous sensors
US9801756B2 (en) 2012-09-28 2017-10-31 Zoll Circulation, Inc. Intravascular heat exchange catheter and system with RFID coupling
US9433528B2 (en) 2012-09-28 2016-09-06 Zoll Circulation, Inc. Intravascular heat exchange catheter with rib cage-like coolant path
US10108781B2 (en) 2012-09-28 2018-10-23 Abbott Diabetes Care Inc. Glucose or ketone body analyte monitoring in vivo
US8870818B2 (en) 2012-11-15 2014-10-28 Medtronic Minimed, Inc. Systems and methods for alignment and detection of a consumable component
US10466247B2 (en) 2012-11-20 2019-11-05 Becton, Dickinson And Company System and method for diagnosing sensor performance using analyte-independent ratiometric signals
EP4331659A2 (en) 2012-11-29 2024-03-06 Abbott Diabetes Care, Inc. Methods, devices, and systems related to analyte monitoring
BR112015012958B1 (en) 2012-12-03 2022-03-15 Pepex Biomedical, Inc Sensor module to detect an analyte in a blood sample
US10194840B2 (en) 2012-12-06 2019-02-05 Medtronic Minimed, Inc. Microarray electrodes useful with analyte sensors and methods for making and using them
US9522223B2 (en) 2013-01-18 2016-12-20 Medtronic Minimed, Inc. Systems for fluid reservoir retention
US9107994B2 (en) 2013-01-18 2015-08-18 Medtronic Minimed, Inc. Systems for fluid reservoir retention
US9033924B2 (en) 2013-01-18 2015-05-19 Medtronic Minimed, Inc. Systems for fluid reservoir retention
US10426383B2 (en) 2013-01-22 2019-10-01 Medtronic Minimed, Inc. Muting glucose sensor oxygen response and reducing electrode edge growth with pulsed current plating
US9308321B2 (en) 2013-02-18 2016-04-12 Medtronic Minimed, Inc. Infusion device having gear assembly initialization
US9173998B2 (en) 2013-03-14 2015-11-03 Tandem Diabetes Care, Inc. System and method for detecting occlusions in an infusion pump
US8858884B2 (en) 2013-03-15 2014-10-14 American Sterilizer Company Coupled enzyme-based method for electronic monitoring of biological indicator
US9207515B2 (en) 2013-03-15 2015-12-08 Ashwin-Ushas Corporation, Inc. Variable-emittance electrochromic devices and methods of preparing the same
US10433773B1 (en) 2013-03-15 2019-10-08 Abbott Diabetes Care Inc. Noise rejection methods and apparatus for sparsely sampled analyte sensor data
US9486171B2 (en) 2013-03-15 2016-11-08 Tandem Diabetes Care, Inc. Predictive calibration
WO2014152034A1 (en) 2013-03-15 2014-09-25 Abbott Diabetes Care Inc. Sensor fault detection using analyte sensor data pattern comparison
CN105377118B (en) 2013-03-15 2019-09-17 雅培糖尿病护理公司 Equipment, system and method associated with analyte supervision equipment and the equipment comprising it
US9474475B1 (en) 2013-03-15 2016-10-25 Abbott Diabetes Care Inc. Multi-rate analyte sensor data collection with sample rate configurable signal processing
US9121050B2 (en) 2013-03-15 2015-09-01 American Sterilizer Company Non-enzyme based detection method for electronic monitoring of biological indicator
US8920381B2 (en) 2013-04-12 2014-12-30 Medtronic Minimed, Inc. Infusion set with improved bore configuration
EP2991552A4 (en) 2013-04-30 2017-01-11 Abbott Diabetes Care Inc. Systems, devices, and methods for energy efficient electrical device activation
WO2014205412A1 (en) 2013-06-21 2014-12-24 Intuity Medical, Inc. Analyte monitoring system with audible feedback
US9433731B2 (en) 2013-07-19 2016-09-06 Medtronic Minimed, Inc. Detecting unintentional motor motion and infusion device incorporating same
CN105555345B (en) 2013-08-05 2018-03-30 费雪派克医疗保健有限公司 Combination for the interface used in positive pressure respiration treatment is provided and its with face shield assembly
US9402949B2 (en) 2013-08-13 2016-08-02 Medtronic Minimed, Inc. Detecting conditions associated with medical device operations using matched filters
US9880528B2 (en) 2013-08-21 2018-01-30 Medtronic Minimed, Inc. Medical devices and related updating methods and systems
US9889257B2 (en) 2013-08-21 2018-02-13 Medtronic Minimed, Inc. Systems and methods for updating medical devices
US9259528B2 (en) 2013-08-22 2016-02-16 Medtronic Minimed, Inc. Fluid infusion device with safety coupling
US20150122647A1 (en) 2013-11-07 2015-05-07 Medtronic Minimed, Inc. Enzyme matrices for use with ethylene oxide sterilization
US9750877B2 (en) 2013-12-11 2017-09-05 Medtronic Minimed, Inc. Predicted time to assess and/or control a glycemic state
US9750878B2 (en) 2013-12-11 2017-09-05 Medtronic Minimed, Inc. Closed-loop control of glucose according to a predicted blood glucose trajectory
US10105488B2 (en) 2013-12-12 2018-10-23 Medtronic Minimed, Inc. Predictive infusion device operations and related methods and systems
US9849240B2 (en) 2013-12-12 2017-12-26 Medtronic Minimed, Inc. Data modification for predictive operations and devices incorporating same
US9694132B2 (en) 2013-12-19 2017-07-04 Medtronic Minimed, Inc. Insertion device for insertion set
US9834805B2 (en) 2013-12-23 2017-12-05 Verily Life Sciences Llc Two-layer analyte sensor
US9739746B1 (en) 2013-12-23 2017-08-22 Google Inc. Analyte sensor incorporating negatively charged moieties
US9855359B2 (en) 2013-12-23 2018-01-02 Verily Life Sciences Llc Analyte sensors with ethylene oxide immunity
US10379125B2 (en) 2013-12-27 2019-08-13 Becton, Dickinson And Company System and method for dynamically calibrating and measuring analyte concentration in diabetes management monitors
WO2015102745A1 (en) 2013-12-31 2015-07-09 Abbott Diabetes Care Inc. Self-powered analyte sensor and devices using the same
US9399096B2 (en) 2014-02-06 2016-07-26 Medtronic Minimed, Inc. Automatic closed-loop control adjustments and infusion systems incorporating same
US9861748B2 (en) 2014-02-06 2018-01-09 Medtronic Minimed, Inc. User-configurable closed-loop notifications and infusion systems incorporating same
US9610402B2 (en) 2014-03-24 2017-04-04 Medtronic Minimed, Inc. Transcutaneous conduit insertion mechanism with a living hinge for use with a fluid infusion patch pump device
WO2015153482A1 (en) 2014-03-30 2015-10-08 Abbott Diabetes Care Inc. Method and apparatus for determining meal start and peak events in analyte monitoring systems
US10001450B2 (en) 2014-04-18 2018-06-19 Medtronic Minimed, Inc. Nonlinear mapping technique for a physiological characteristic sensor
US10232113B2 (en) 2014-04-24 2019-03-19 Medtronic Minimed, Inc. Infusion devices and related methods and systems for regulating insulin on board
US10275572B2 (en) 2014-05-01 2019-04-30 Medtronic Minimed, Inc. Detecting blockage of a reservoir cavity during a seating operation of a fluid infusion device
US9681828B2 (en) 2014-05-01 2017-06-20 Medtronic Minimed, Inc. Physiological characteristic sensors and methods for forming such sensors
US10274349B2 (en) 2014-05-19 2019-04-30 Medtronic Minimed, Inc. Calibration factor adjustments for infusion devices and related methods and systems
US10152049B2 (en) 2014-05-19 2018-12-11 Medtronic Minimed, Inc. Glucose sensor health monitoring and related methods and systems
US10007765B2 (en) 2014-05-19 2018-06-26 Medtronic Minimed, Inc. Adaptive signal processing for infusion devices and related methods and systems
EP3146746B1 (en) 2014-05-21 2019-07-03 Abbott Diabetes Care Inc. Management of multiple devices within an analyte monitoring environment
US11045124B2 (en) 2014-06-04 2021-06-29 Pepex Biomedical, Inc. Electrochemical sensors and methods for making electrochemical sensors using advanced printing technology
WO2016022696A1 (en) 2014-08-05 2016-02-11 The Trustees Of Columbia University In The City Of New York Method of isolating aptamers for minimal residual disease detection
EP3179915A4 (en) 2014-08-15 2018-03-21 Abbott Diabetes Care Inc. Temperature insensitive in vivo analyte devices, methods and systems
US9833563B2 (en) 2014-09-26 2017-12-05 Medtronic Minimed, Inc. Systems for managing reservoir chamber pressure
US9839753B2 (en) 2014-09-26 2017-12-12 Medtronic Minimed, Inc. Systems for managing reservoir chamber pressure
US10279126B2 (en) 2014-10-07 2019-05-07 Medtronic Minimed, Inc. Fluid conduit assembly with gas trapping filter in the fluid flow path
WO2016065190A1 (en) 2014-10-23 2016-04-28 Abbott Diabetes Care Inc. Electrodes having at least one sensing structure and methods for making and using the same
US9833564B2 (en) 2014-11-25 2017-12-05 Medtronic Minimed, Inc. Fluid conduit assembly with air venting features
US9987420B2 (en) 2014-11-26 2018-06-05 Medtronic Minimed, Inc. Systems and methods for fluid infusion device with automatic reservoir fill
US10195341B2 (en) 2014-11-26 2019-02-05 Medtronic Minimed, Inc. Systems and methods for fluid infusion device with automatic reservoir fill
US10987039B2 (en) 2014-12-03 2021-04-27 Stmicroelectronics S.R.L. Microneedle array device and method of making
US9636453B2 (en) 2014-12-04 2017-05-02 Medtronic Minimed, Inc. Advance diagnosis of infusion device operating mode viability
US9943645B2 (en) 2014-12-04 2018-04-17 Medtronic Minimed, Inc. Methods for operating mode transitions and related infusion devices and systems
US9937292B2 (en) 2014-12-09 2018-04-10 Medtronic Minimed, Inc. Systems for filling a fluid infusion device reservoir
US10307535B2 (en) 2014-12-19 2019-06-04 Medtronic Minimed, Inc. Infusion devices and related methods and systems for preemptive alerting
US10265031B2 (en) 2014-12-19 2019-04-23 Medtronic Minimed, Inc. Infusion devices and related methods and systems for automatic alert clearing
US10307528B2 (en) 2015-03-09 2019-06-04 Medtronic Minimed, Inc. Extensible infusion devices and related methods
US10449298B2 (en) 2015-03-26 2019-10-22 Medtronic Minimed, Inc. Fluid injection devices and related methods
US10254265B1 (en) * 2015-04-10 2019-04-09 Mohsen Rezayat Sealed container sensor device
US10674944B2 (en) 2015-05-14 2020-06-09 Abbott Diabetes Care Inc. Compact medical device inserters and related systems and methods
US10213139B2 (en) 2015-05-14 2019-02-26 Abbott Diabetes Care Inc. Systems, devices, and methods for assembling an applicator and sensor control device
US10137243B2 (en) 2015-05-26 2018-11-27 Medtronic Minimed, Inc. Infusion devices with distributed motor control and related operating methods
GB2538731B (en) 2015-05-26 2019-05-22 Imperial Innovations Ltd Methods
US9999721B2 (en) 2015-05-26 2018-06-19 Medtronic Minimed, Inc. Error handling in infusion devices with distributed motor control and related operating methods
US10575767B2 (en) 2015-05-29 2020-03-03 Medtronic Minimed, Inc. Method for monitoring an analyte, analyte sensor and analyte monitoring apparatus
EP3307164B1 (en) 2015-06-15 2021-05-12 Abbott Diabetes Care Inc. Stabilized lactate responsive enzymes, electrodes and sensors, and methods for making and using the same
EP3311150A1 (en) 2015-06-18 2018-04-25 Ultradian Diagnostics LLC Methods and devices for determining metabolic states
US9987425B2 (en) 2015-06-22 2018-06-05 Medtronic Minimed, Inc. Occlusion detection techniques for a fluid infusion device having a rotary pump mechanism and sensor contact elements
US9878095B2 (en) 2015-06-22 2018-01-30 Medtronic Minimed, Inc. Occlusion detection techniques for a fluid infusion device having a rotary pump mechanism and multiple sensor contact elements
US10010668B2 (en) 2015-06-22 2018-07-03 Medtronic Minimed, Inc. Occlusion detection techniques for a fluid infusion device having a rotary pump mechanism and a force sensor
US9993594B2 (en) 2015-06-22 2018-06-12 Medtronic Minimed, Inc. Occlusion detection techniques for a fluid infusion device having a rotary pump mechanism and rotor position sensors
US9879668B2 (en) 2015-06-22 2018-01-30 Medtronic Minimed, Inc. Occlusion detection techniques for a fluid infusion device having a rotary pump mechanism and an optical sensor
US11553883B2 (en) 2015-07-10 2023-01-17 Abbott Diabetes Care Inc. System, device and method of dynamic glucose profile response to physiological parameters
US10888272B2 (en) 2015-07-10 2021-01-12 Abbott Diabetes Care Inc. Systems, devices, and methods for meal information collection, meal assessment, and analyte data correlation
US10578785B2 (en) * 2015-08-18 2020-03-03 Corning Incorporated Blocking coating with adhesion layer for ultraviolet optics
US10459134B2 (en) * 2015-08-18 2019-10-29 Corning Incorporated UV-blocking coating with capping layer in optical assembly having UV light source
US10293108B2 (en) 2015-08-21 2019-05-21 Medtronic Minimed, Inc. Infusion devices and related patient ratio adjustment methods
US20170053552A1 (en) 2015-08-21 2017-02-23 Medtronic Minimed, Inc. Management and prioritization of the delivery of glycemic insight messages
US10201657B2 (en) 2015-08-21 2019-02-12 Medtronic Minimed, Inc. Methods for providing sensor site rotation feedback and related infusion devices and systems
US10478557B2 (en) 2015-08-21 2019-11-19 Medtronic Minimed, Inc. Personalized parameter modeling methods and related devices and systems
US10463297B2 (en) 2015-08-21 2019-11-05 Medtronic Minimed, Inc. Personalized event detection methods and related devices and systems
US9632059B2 (en) 2015-09-03 2017-04-25 Ashwin-Ushas Corporation, Inc. Potentiostat/galvanostat with digital interface
US9482880B1 (en) 2015-09-15 2016-11-01 Ashwin-Ushas Corporation, Inc. Electrochromic eyewear
US10117992B2 (en) 2015-09-29 2018-11-06 Medtronic Minimed, Inc. Infusion devices and related rescue detection methods
US11666702B2 (en) 2015-10-19 2023-06-06 Medtronic Minimed, Inc. Medical devices and related event pattern treatment recommendation methods
US11501867B2 (en) 2015-10-19 2022-11-15 Medtronic Minimed, Inc. Medical devices and related event pattern presentation methods
US10146911B2 (en) 2015-10-23 2018-12-04 Medtronic Minimed, Inc. Medical devices and related methods and systems for data transfer
US10037722B2 (en) 2015-11-03 2018-07-31 Medtronic Minimed, Inc. Detecting breakage in a display element
US10449306B2 (en) 2015-11-25 2019-10-22 Medtronics Minimed, Inc. Systems for fluid delivery with wicking membrane
US20170188905A1 (en) 2015-12-30 2017-07-06 Dexcom, Inc. Biointerface layer for analyte sensors
US11091788B2 (en) 2016-03-04 2021-08-17 Abbott Diabetes Care Inc. NAD(P)- dependent responsive enzymes, electrodes and sensors, and methods for making and using the same
SI3220137T1 (en) 2016-03-14 2019-05-31 F. Hoffmann-La Roche Ag Method for detecting an interferent contribution in a biosensor
US10589038B2 (en) 2016-04-27 2020-03-17 Medtronic Minimed, Inc. Set connector systems for venting a fluid reservoir
US10324058B2 (en) 2016-04-28 2019-06-18 Medtronic Minimed, Inc. In-situ chemistry stack for continuous glucose sensors
US11179078B2 (en) 2016-06-06 2021-11-23 Medtronic Minimed, Inc. Polycarbonate urea/urethane polymers for use with analyte sensors
US20180221636A1 (en) * 2016-06-16 2018-08-09 These Three Medical Inc. Artificial Pancreas System and Method Therefor
US11617832B2 (en) 2016-08-17 2023-04-04 International Business Machines Corporation Portal system-based bionic pancreas
WO2018064471A1 (en) 2016-09-29 2018-04-05 The Regents Of The University Of California Tracheotomy tube-based monitoring systems and methods
US11097051B2 (en) 2016-11-04 2021-08-24 Medtronic Minimed, Inc. Methods and apparatus for detecting and reacting to insufficient hypoglycemia response
CN106725470B (en) * 2016-11-22 2023-12-19 南通九诺医疗科技有限公司 Continuous or discontinuous physiological parameter analysis system
US10238030B2 (en) 2016-12-06 2019-03-26 Medtronic Minimed, Inc. Wireless medical device with a complementary split ring resonator arrangement for suppression of electromagnetic interference
US10272201B2 (en) 2016-12-22 2019-04-30 Medtronic Minimed, Inc. Insertion site monitoring methods and related infusion devices and systems
US10758406B2 (en) 2016-12-30 2020-09-01 Zoll Circulation, Inc. High efficiency heat exchange catheters for control of patient body temperature
US10561528B2 (en) 2016-12-30 2020-02-18 Zoll Circulation, Inc. Fluid-circulating catheters useable for endovascular heat exchange
WO2018136898A1 (en) 2017-01-23 2018-07-26 Abbott Diabetes Care Inc. Systems, devices and methods for analyte sensor insertion
US10532165B2 (en) 2017-01-30 2020-01-14 Medtronic Minimed, Inc. Fluid reservoir and systems for filling a fluid reservoir of a fluid infusion device
US10500135B2 (en) 2017-01-30 2019-12-10 Medtronic Minimed, Inc. Fluid reservoir and systems for filling a fluid reservoir of a fluid infusion device
US10363365B2 (en) 2017-02-07 2019-07-30 Medtronic Minimed, Inc. Infusion devices and related consumable calibration methods
US10552580B2 (en) 2017-02-07 2020-02-04 Medtronic Minimed, Inc. Infusion system consumables and related calibration methods
US10646649B2 (en) 2017-02-21 2020-05-12 Medtronic Minimed, Inc. Infusion devices and fluid identification apparatuses and methods
US11207463B2 (en) 2017-02-21 2021-12-28 Medtronic Minimed, Inc. Apparatuses, systems, and methods for identifying an infusate in a reservoir of an infusion device
US11134868B2 (en) 2017-03-17 2021-10-05 Medtronic Minimed, Inc. Metal pillar device structures and methods for making and using them in electrochemical and/or electrocatalytic applications
US11596330B2 (en) 2017-03-21 2023-03-07 Abbott Diabetes Care Inc. Methods, devices and system for providing diabetic condition diagnosis and therapy
WO2018172619A1 (en) * 2017-03-22 2018-09-27 Aalto University Foundation Sr Electrochemical assay for the detection of opioids
US10856784B2 (en) 2017-06-30 2020-12-08 Medtronic Minimed, Inc. Sensor initialization methods for faster body sensor response
DE202018006591U1 (en) 2017-08-18 2021-07-21 Abbott Diabetes Care, Inc. Systems and devices relating to the individualized calibration and / or manufacture of medical devices
US20190223771A1 (en) 2018-01-23 2019-07-25 Medtronic Minimed, Inc. Implantable polymer surfaces exhibiting reduced in vivo inflammatory responses
WO2019152966A1 (en) 2018-02-05 2019-08-08 Abbott Diabetes Care Inc. Notes and event log information associated with analyte sensors
US11186859B2 (en) 2018-02-07 2021-11-30 Medtronic Minimed, Inc. Multilayer electrochemical analyte sensors and methods for making and using them
US11583213B2 (en) 2018-02-08 2023-02-21 Medtronic Minimed, Inc. Glucose sensor electrode design
US11220735B2 (en) 2018-02-08 2022-01-11 Medtronic Minimed, Inc. Methods for controlling physical vapor deposition metal film adhesion to substrates and surfaces
WO2019222499A1 (en) 2018-05-16 2019-11-21 Medtronic Minimed, Inc. Thermally stable glucose limiting membrane for glucose sensors
US11424435B2 (en) 2019-05-09 2022-08-23 New Jersey Institute Of Technology High oxidation state periodate battery
USD1002852S1 (en) 2019-06-06 2023-10-24 Abbott Diabetes Care Inc. Analyte sensor device
US11718865B2 (en) 2019-07-26 2023-08-08 Medtronic Minimed, Inc. Methods to improve oxygen delivery to implantable sensors
US11523757B2 (en) 2019-08-01 2022-12-13 Medtronic Minimed, Inc. Micro-pillar working electrodes design to reduce backflow of hydrogen peroxide in glucose sensor
US11637328B2 (en) 2019-12-18 2023-04-25 New Jersey Institute Of Technology Methods and devices for high-capacity flexible, printable, and conformal periodate and iodate batteries
USD957438S1 (en) 2020-07-29 2022-07-12 Abbott Diabetes Care Inc. Display screen or portion thereof with graphical user interface
US20220031205A1 (en) 2020-07-31 2022-02-03 Medtronic Minimed, Inc. Sensor identification and integrity check design
US20220133190A1 (en) 2020-10-29 2022-05-05 Medtronic Minimed, Inc. Glucose biosensors comprising direct electron transfer enzymes and methods of making and using them
USD999913S1 (en) 2020-12-21 2023-09-26 Abbott Diabetes Care Inc Analyte sensor inserter
US20220233116A1 (en) 2021-01-26 2022-07-28 Abbott Diabetes Care Inc. Systems, devices, and methods related to ketone sensors
US20220240823A1 (en) 2021-01-29 2022-08-04 Medtronic Minimed, Inc. Interference rejection membranes useful with analyte sensors
AU2022238919A1 (en) 2021-03-19 2023-10-19 Dexcom, Inc. Drug releasing membrane for analyte sensor
AU2022249311A1 (en) 2021-03-31 2023-11-02 Dexcom, Inc. Filtering of continuous glucose monitor (cgm) signals with a kalman filter
WO2022212867A1 (en) 2021-04-02 2022-10-06 Dexcom, Inc. Personalized modeling of blood glucose concentration impacted by individualized sensor characteristics and individualized physiological characteristics
US20220338768A1 (en) 2021-04-09 2022-10-27 Medtronic Minimed, Inc. Hexamethyldisiloxane membranes for analyte sensors
US20230053254A1 (en) 2021-08-13 2023-02-16 Medtronic Minimed, Inc. Dry electrochemical impedance spectroscopy metrology for conductive chemical layers
WO2023043908A1 (en) 2021-09-15 2023-03-23 Dexcom, Inc. Bioactive releasing membrane for analyte sensor
US20230113175A1 (en) 2021-10-08 2023-04-13 Medtronic Minimed, Inc. Immunosuppressant releasing coatings
US20230123613A1 (en) 2021-10-14 2023-04-20 Medtronic Minimed, Inc. Sensors for 3-hydroxybutyrate detection
US20230172497A1 (en) 2021-12-02 2023-06-08 Medtronic Minimed, Inc. Ketone limiting membrane and dual layer membrane approach for ketone sensing
WO2023110190A1 (en) 2021-12-13 2023-06-22 Heraeus Medical Gmbh Tests and methods for detecting bacterial infection
DE102022000897A1 (en) 2022-03-15 2023-09-21 Ruhr-Universität Bochum, Körperschaft des öffentlichen Rechts Implantable biosensor
WO2023177896A1 (en) 2022-03-18 2023-09-21 Dexcom, Inc. Continuous multi-analyte sensor systems
US20240023849A1 (en) 2022-07-20 2024-01-25 Medtronic Minimed, Inc. Acrylate hydrogel membrane for dual function of diffusion limiting membrane as well as attenuation to the foreign body response

Citations (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4699157A (en) * 1985-08-27 1987-10-13 Electro-Catheter Corporation Pacing catheter and method of making same
US4986271A (en) * 1989-07-19 1991-01-22 The University Of New Mexico Vivo refillable glucose sensor
US5103816A (en) * 1989-09-11 1992-04-14 Biomedical Device Consultants, Inc. Composite for use in making protective articles for use in laser surgery
US5122244A (en) * 1990-02-03 1992-06-16 Boehringer Mannheim Gmbh Method and sensor electrode system for the electrochemical determination of an analyte or an oxidoreductase as well as the use of suitable compounds therefor
US5525511A (en) * 1990-09-01 1996-06-11 Environmental & Medical Products Ltd. Electrochemical biosensor stability
US5696314A (en) * 1996-07-12 1997-12-09 Chiron Diagnostics Corporation Multilayer enzyme electrode membranes and methods of making same
US5776324A (en) * 1996-05-17 1998-07-07 Encelle, Inc. Electrochemical biosensors
US6060176A (en) * 1995-11-30 2000-05-09 International Business Machines Corporation Corrosion protection for metallic features
US6387048B1 (en) * 1997-10-20 2002-05-14 Alfred E. Mann Foundation Implantable sensor and integrity tests therefor
US20050215871A1 (en) * 2004-02-09 2005-09-29 Feldman Benjamin J Analyte sensor, and associated system and method employing a catalytic agent
US20070042377A1 (en) * 2003-10-29 2007-02-22 Zhiqiang Gao Biosensor

Family Cites Families (452)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US470290A (en) * 1892-03-08 Automatic counter and alarm
US177743A (en) * 1876-05-23 Improvement in expanding well-curbs
US278647A (en) * 1883-05-29 Wood-polishing machine
US255291A (en) * 1882-03-21 Revolving hay-rake
US241309A (en) * 1881-05-10 davis
US400918A (en) * 1889-04-09 Walter s
US32947A (en) * 1861-07-30 Machine for bending fifth-wheels fob
US125139A (en) * 1872-04-02 Improvement in coolers for soda-water and other liquids
US136362A (en) * 1873-03-04 Improvement in box-plaiting machines
US2073801A (en) * 1934-10-08 1937-03-16 Herbert E Linden Renewable cutting edge
US3260656A (en) 1962-09-27 1966-07-12 Corning Glass Works Method and apparatus for electrolytically determining a species in a fluid
US3653841A (en) 1969-12-19 1972-04-04 Hoffmann La Roche Methods and compositions for determining glucose in blood
US3934299A (en) * 1970-04-24 1976-01-27 Regester Willard D Tooth cleaning device
US3776832A (en) 1970-11-10 1973-12-04 Energetics Science Electrochemical detection cell
US3719564A (en) 1971-05-10 1973-03-06 Philip Morris Inc Method of determining a reducible gas concentration and sensor therefor
US3775832A (en) * 1971-11-01 1973-12-04 Ladish Co Method of manufacturing shrouded gaskets
US3943918A (en) 1971-12-02 1976-03-16 Tel-Pac, Inc. Disposable physiological telemetric device
US3837339A (en) 1972-02-03 1974-09-24 Whittaker Corp Blood glucose level monitoring-alarm system and method therefor
US4184429A (en) * 1972-02-09 1980-01-22 Max Datwyler & Co. Constant bevel doctor blade and method and apparatus using same
US3908657A (en) 1973-01-15 1975-09-30 Univ Johns Hopkins System for continuous withdrawal of blood
GB1394171A (en) 1973-05-16 1975-05-14 Whittaker Corp Blood glucose level monitoring-alarm system and method therefor
US4100048A (en) 1973-09-20 1978-07-11 U.S. Philips Corporation Polarographic cell
US3926760A (en) * 1973-09-28 1975-12-16 Du Pont Process for electrophoretic deposition of polymer
US3991770A (en) 1974-01-24 1976-11-16 Leveen Harry H Method for treating benign and malignant tumors utilizing radio frequency, electromagnetic radiation
US3972320A (en) 1974-08-12 1976-08-03 Gabor Ujhelyi Kalman Patient monitoring system
DE2504206C3 (en) * 1975-02-01 1981-10-01 Robert Bosch Gmbh, 7000 Stuttgart Electrochemical measuring sensor for the determination of the oxygen content in exhaust gases, in particular in exhaust gases from internal combustion engines
US4036749A (en) 1975-04-30 1977-07-19 Anderson Donald R Purification of saline water
US3979274A (en) 1975-09-24 1976-09-07 The Yellow Springs Instrument Company, Inc. Membrane for enzyme electrodes
US4016866A (en) 1975-12-18 1977-04-12 General Electric Company Implantable electrochemical sensor
US4055175A (en) 1976-05-07 1977-10-25 Miles Laboratories, Inc. Blood glucose control apparatus
DE2625834B2 (en) 1976-06-09 1978-10-12 Boehringer Mannheim Gmbh, 6800 Mannheim Method for the determination of substrates or enzyme activities
US4059406A (en) 1976-07-12 1977-11-22 E D T Supplies Limited Electrochemical detector system
US4076596A (en) 1976-10-07 1978-02-28 Leeds & Northrup Company Apparatus for electrolytically determining a species in a fluid and method of use
US4129128A (en) 1977-02-23 1978-12-12 Mcfarlane Richard H Securing device for catheter placement assembly
FR2387659A1 (en) 1977-04-21 1978-11-17 Armines GLYCEMIA CONTROL AND REGULATION DEVICE
US4098574A (en) 1977-08-01 1978-07-04 Eastman Kodak Company Glucose detection system free from fluoride-ion interference
US4178916A (en) 1977-09-26 1979-12-18 Mcnamara Elger W Diabetic insulin alarm system
JPS5912135B2 (en) 1977-09-28 1984-03-21 松下電器産業株式会社 enzyme electrode
US4151845A (en) 1977-11-25 1979-05-01 Miles Laboratories, Inc. Blood glucose control apparatus
JPS5921500B2 (en) 1978-01-28 1984-05-21 東洋紡績株式会社 Enzyme membrane for oxygen electrode
DK151000C (en) 1978-02-17 1988-06-13 Radiometer As PROCEDURE AND APPARATUS FOR DETERMINING A PATIENT'S IN VIVO PLASMA-PH VALUE
US4172770A (en) 1978-03-27 1979-10-30 Technicon Instruments Corporation Flow-through electrochemical system analytical method
DE2817363C2 (en) 1978-04-20 1984-01-26 Siemens AG, 1000 Berlin und 8000 München Method for determining the concentration of sugar and a suitable electrocatalytic sugar sensor
DE2827918A1 (en) * 1978-06-26 1980-01-10 Vdo Schindling DEVICE FOR ADJUSTING AN ELECTRIC CLOCK
US4344438A (en) 1978-08-02 1982-08-17 The United States Of America As Represented By The Department Of Health, Education And Welfare Optical sensor of plasma constituents
HU177369B (en) 1978-09-08 1981-09-28 Radelkis Electrokemiai Industrial molecule-selective sensing device and method for producing same
US4240438A (en) 1978-10-02 1980-12-23 Wisconsin Alumni Research Foundation Method for monitoring blood glucose levels and elements
EP0010375B1 (en) 1978-10-02 1983-07-20 Xerox Corporation Electrostatographic processing system
US4247297A (en) 1979-02-23 1981-01-27 Miles Laboratories, Inc. Test means and method for interference resistant determination of oxidizing substances
US4573994A (en) 1979-04-27 1986-03-04 The Johns Hopkins University Refillable medication infusion apparatus
US4365637A (en) 1979-07-05 1982-12-28 Dia-Med, Inc. Perspiration indicating alarm for diabetics
US4401122A (en) 1979-08-02 1983-08-30 Children's Hospital Medical Center Cutaneous methods of measuring body substances
US4458686A (en) 1979-08-02 1984-07-10 Children's Hospital Medical Center Cutaneous methods of measuring body substances
US4293396A (en) 1979-09-27 1981-10-06 Prototech Company Thin carbon-cloth-based electrocatalytic gas diffusion electrodes, and electrochemical cells comprising the same
DE3114441A1 (en) 1980-04-11 1982-03-04 Radiometer A/S, 2400 Koebenhavn ELECTROCHEMICAL MEASURING ELECTRODE DEVICE
US4450842A (en) 1980-04-25 1984-05-29 Cordis Corporation Solid state reference electrode
US4340458A (en) 1980-06-02 1982-07-20 Joslin Diabetes Center, Inc. Glucose sensor
US4404066A (en) 1980-08-25 1983-09-13 The Yellow Springs Instrument Company Method for quantitatively determining a particular substrate catalyzed by a multisubstrate enzyme
US4356074A (en) 1980-08-25 1982-10-26 The Yellow Springs Instrument Company, Inc. Substrate specific galactose oxidase enzyme electrodes
USRE32947E (en) 1980-09-30 1989-06-13 Baptist Medical Center Of Oklahoma, Inc. Magnetic transcutaneous mount for external device of an associated implant
US4352960A (en) 1980-09-30 1982-10-05 Baptist Medical Center Of Oklahoma, Inc. Magnetic transcutaneous mount for external device of an associated implant
US4425920A (en) * 1980-10-24 1984-01-17 Purdue Research Foundation Apparatus and method for measurement and control of blood pressure
US4327725A (en) 1980-11-25 1982-05-04 Alza Corporation Osmotic device with hydrogel driving member
US4390621A (en) 1980-12-15 1983-06-28 Miles Laboratories, Inc. Method and device for detecting glucose concentration
US4436094A (en) 1981-03-09 1984-03-13 Evreka, Inc. Monitor for continuous in vivo measurement of glucose concentration
AT369254B (en) 1981-05-07 1982-12-27 Otto Dipl Ing Dr Tech Prohaska MEDICAL PROBE
FR2508305B1 (en) 1981-06-25 1986-04-11 Slama Gerard DEVICE FOR CAUSING A LITTLE BITE TO COLLECT A BLOOD DROP
US4440175A (en) 1981-08-10 1984-04-03 University Patents, Inc. Membrane electrode for non-ionic species
DE3138194A1 (en) * 1981-09-25 1983-04-14 Basf Ag, 6700 Ludwigshafen WATER-INSOLUBLE POROESES PROTEIN MATERIAL, THEIR PRODUCTION AND USE
DE3278334D1 (en) 1981-10-23 1988-05-19 Genetics Int Inc Sensor for components of a liquid mixture
US4431004A (en) 1981-10-27 1984-02-14 Bessman Samuel P Implantable glucose sensor
US4418148A (en) 1981-11-05 1983-11-29 Miles Laboratories, Inc. Multilayer enzyme electrode membrane
JPS5886083A (en) 1981-11-12 1983-05-23 Wako Pure Chem Ind Ltd Stabilizing agent for glycerol-3-phosphoric acid oxidase
US4494950A (en) * 1982-01-19 1985-01-22 The Johns Hopkins University Plural module medication delivery system
JPS58153154A (en) 1982-03-09 1983-09-12 Ajinomoto Co Inc Qualified electrode
US4581336A (en) 1982-04-26 1986-04-08 Uop Inc. Surface-modified electrodes
FI831399L (en) 1982-04-29 1983-10-30 Agripat Sa KONTAKTLINS AV HAERDAD POLYVINYL ALCOHOL
DD227029A3 (en) * 1982-05-13 1985-09-04 Zentralinst F Diabetiker G Kat ENZYME ELECTRODE FOR GLUCOSE MEASUREMENT
DE3221339A1 (en) 1982-06-05 1983-12-08 Basf Ag, 6700 Ludwigshafen METHOD FOR THE ELECTROCHEMICAL HYDRATION OF NICOTINAMIDADENINE-DINUCLEOTIDE
US4427770A (en) 1982-06-14 1984-01-24 Miles Laboratories, Inc. High glucose-determining analytical element
EP0098592A3 (en) 1982-07-06 1985-08-21 Fujisawa Pharmaceutical Co., Ltd. Portable artificial pancreas
US4534356A (en) 1982-07-30 1985-08-13 Diamond Shamrock Chemicals Company Solid state transcutaneous blood gas sensors
DE3228551A1 (en) 1982-07-30 1984-02-02 Siemens AG, 1000 Berlin und 8000 München METHOD FOR DETERMINING SUGAR CONCENTRATION
US4571292A (en) 1982-08-12 1986-02-18 Case Western Reserve University Apparatus for electrochemical measurements
US4552840A (en) 1982-12-02 1985-11-12 California And Hawaiian Sugar Company Enzyme electrode and method for dextran analysis
US4461691A (en) 1983-02-10 1984-07-24 The United States Of America As Represented By The United States Department Of Energy Organic conductive films for semiconductor electrodes
US4679562A (en) 1983-02-16 1987-07-14 Cardiac Pacemakers, Inc. Glucose sensor
EP0136362B1 (en) 1983-03-11 1990-12-19 Matsushita Electric Industrial Co., Ltd. Biosensor
IT1170375B (en) 1983-04-19 1987-06-03 Giuseppe Bombardieri Implantable device for measuring body fluid parameters
CA1226036A (en) 1983-05-05 1987-08-25 Irving J. Higgins Analytical equipment and sensor electrodes therefor
US5509410A (en) 1983-06-06 1996-04-23 Medisense, Inc. Strip electrode including screen printing of a single layer
CA1218704A (en) 1983-05-05 1987-03-03 Graham Davis Assay systems using more than one enzyme
CA1220818A (en) 1983-05-05 1987-04-21 Hugh A.O. Hill Assay techniques utilising specific binding agents
US5682884A (en) 1983-05-05 1997-11-04 Medisense, Inc. Strip electrode with screen printing
GB2154003B (en) 1983-12-16 1988-02-17 Genetics Int Inc Diagnostic aid
CA1219040A (en) 1983-05-05 1987-03-10 Elliot V. Plotkin Measurement of enzyme-catalysed reactions
US4484987A (en) 1983-05-19 1984-11-27 The Regents Of The University Of California Method and membrane applicable to implantable sensor
US4650547A (en) 1983-05-19 1987-03-17 The Regents Of The University Of California Method and membrane applicable to implantable sensor
US4524114A (en) 1983-07-05 1985-06-18 Allied Corporation Bifunctional air electrode
US4538616A (en) 1983-07-25 1985-09-03 Robert Rogoff Blood sugar level sensing and monitoring transducer
US4655880A (en) 1983-08-01 1987-04-07 Case Western Reserve University Apparatus and method for sensing species, substances and substrates using oxidase
US4543955A (en) 1983-08-01 1985-10-01 Cordis Corporation System for controlling body implantable action device
SE8305704D0 (en) 1983-10-18 1983-10-18 Leo Ab Cuvette
US4560534A (en) * 1983-11-02 1985-12-24 Miles Laboratories, Inc. Polymer catalyst transducers
US4522690A (en) 1983-12-01 1985-06-11 Honeywell Inc. Electrochemical sensing of carbon monoxide
AU583258B2 (en) 1983-12-16 1989-04-27 Medisense Inc. Assay for nucleic acids
SU1281988A1 (en) 1984-03-15 1987-01-07 Институт биохимии АН ЛитССР Electrochemical transducer for measuring glucose concentration
JPS61502402A (en) 1984-04-30 1986-10-23 エル エ− シユテイツフツング Sensitization method for oxidation/reduction photoreaction catalyst and photoreaction catalyst
WO1986000135A1 (en) 1984-06-13 1986-01-03 Unilever Plc Photometric instruments, their use in methods of optical analyses, and ancillary devices therefor
US5141868A (en) 1984-06-13 1992-08-25 Internationale Octrooi Maatschappij "Octropa" Bv Device for use in chemical test procedures
DK8601218A (en) 1984-07-18 1986-03-17
DE3429596A1 (en) 1984-08-10 1986-02-20 Siemens AG, 1000 Berlin und 8000 München DEVICE FOR THE PHYSIOLOGICAL FREQUENCY CONTROL OF A PACEMAKER PROVIDED WITH A PICTURE ELECTRODE
US4820399A (en) 1984-08-31 1989-04-11 Shimadzu Corporation Enzyme electrodes
CA1254091A (en) 1984-09-28 1989-05-16 Vladimir Feingold Implantable medication infusion system
GB2168815A (en) 1984-11-13 1986-06-25 Genetics Int Inc Bioelectrochemical assay electrode
US4936956A (en) 1984-11-23 1990-06-26 Massachusetts Institute Of Technology Microelectrochemical devices based on inorganic redox active material and method for sensing
US4717673A (en) 1984-11-23 1988-01-05 Massachusetts Institute Of Technology Microelectrochemical devices
US4721601A (en) 1984-11-23 1988-01-26 Massachusetts Institute Of Technology Molecule-based microelectronic devices
JPH0617889B2 (en) 1984-11-27 1994-03-09 株式会社日立製作所 Biochemical sensor
EP0186210B1 (en) * 1984-12-28 1992-04-22 TERUMO KABUSHIKI KAISHA trading as TERUMO CORPORATION Ion sensor
GB8500729D0 (en) 1985-01-11 1985-02-13 Hill H A O Surface-modified electrode
AU5481786A (en) 1985-03-20 1986-09-25 Hochmair, E.S. Transcutaneous power and signal transmission system
US5279294A (en) 1985-04-08 1994-01-18 Cascade Medical, Inc. Medical diagnostic system
US4627445A (en) 1985-04-08 1986-12-09 Garid, Inc. Glucose medical monitoring system
US4781798A (en) 1985-04-19 1988-11-01 The Regents Of The University Of California Transparent multi-oxygen sensor array and method of using same
US4671288A (en) 1985-06-13 1987-06-09 The Regents Of The University Of California Electrochemical cell sensor for continuous short-term use in tissues and blood
DE3687646T3 (en) 1985-06-21 2001-05-31 Matsushita Electric Ind Co Ltd BIOSENSOR AND THEIR PRODUCTION.
US4938860A (en) 1985-06-28 1990-07-03 Miles Inc. Electrode for electrochemical sensors
US4796634A (en) 1985-08-09 1989-01-10 Lawrence Medical Systems, Inc. Methods and apparatus for monitoring cardiac output
US4805624A (en) 1985-09-09 1989-02-21 The Montefiore Hospital Association Of Western Pa Low-potential electrochemical redox sensors
US4680268A (en) 1985-09-18 1987-07-14 Children's Hospital Medical Center Implantable gas-containing biosensor and method for measuring an analyte such as glucose
US4890620A (en) 1985-09-20 1990-01-02 The Regents Of The University Of California Two-dimensional diffusion glucose substrate sensing electrode
US4627908A (en) 1985-10-24 1986-12-09 Chevron Research Company Process for stabilizing lube base stocks derived from bright stock
CA1254616A (en) 1985-11-11 1989-05-23 Calum J. Mcneil Electrochemical enzymic assay procedures
GB8529300D0 (en) 1985-11-28 1986-01-02 Ici Plc Membrane
US4776944A (en) 1986-03-20 1988-10-11 Jiri Janata Chemical selective sensors utilizing admittance modulated membranes
US4685463A (en) 1986-04-03 1987-08-11 Williams R Bruce Device for continuous in vivo measurement of blood glucose concentrations
GB8608700D0 (en) 1986-04-10 1986-05-14 Genetics Int Inc Measurement of electroactive species in solution
US4726378A (en) 1986-04-11 1988-02-23 Minnesota Mining And Manufacturing Company Adjustable magnetic supercutaneous device and transcutaneous coupling apparatus
US4994167A (en) 1986-04-15 1991-02-19 Markwell Medical Institute, Inc. Biological fluid measuring device
US4757022A (en) 1986-04-15 1988-07-12 Markwell Medical Institute, Inc. Biological fluid measuring device
US4795542A (en) * 1986-04-24 1989-01-03 St. Jude Medical, Inc. Electrochemical concentration detector device
US4909908A (en) 1986-04-24 1990-03-20 Pepi Ross Electrochemical cncentration detector method
DE3614821A1 (en) 1986-05-02 1987-11-05 Siemens Ag IMPLANTABLE, CALIBRABLE MEASURING DEVICE FOR A BODY SUBSTANCE AND CALIBRATION METHOD
US4703756A (en) 1986-05-06 1987-11-03 The Regents Of The University Of California Complete glucose monitoring system with an implantable, telemetered sensor module
US4731726A (en) * 1986-05-19 1988-03-15 Healthware Corporation Patient-operated glucose monitor and diabetes management system
GB8612861D0 (en) 1986-05-27 1986-07-02 Cambridge Life Sciences Immobilised enzyme biosensors
US4969468A (en) 1986-06-17 1990-11-13 Alfred E. Mann Foundation For Scientific Research Electrode array for use in connection with a living body and method of manufacture
US4911794A (en) 1986-06-20 1990-03-27 Molecular Devices Corporation Measuring with zero volume cell
US5001054A (en) 1986-06-26 1991-03-19 Becton, Dickinson And Company Method for monitoring glucose
JPS636451A (en) 1986-06-27 1988-01-12 Terumo Corp Enzyme sensor
US4764416A (en) 1986-07-01 1988-08-16 Mitsubishi Denki Kabushiki Kaisha Electric element circuit using oxidation-reduction substances
US4784736A (en) 1986-07-07 1988-11-15 Bend Research, Inc. Functional, photochemically active, and chemically asymmetric membranes by interfacial polymerization of derivatized multifunctional prepolymers
US4917800A (en) 1986-07-07 1990-04-17 Bend Research, Inc. Functional, photochemically active, and chemically asymmetric membranes by interfacial polymerization of derivatized multifunctional prepolymers
US4726716A (en) 1986-07-21 1988-02-23 Mcguire Thomas V Fastener for catheter
GB8618022D0 (en) 1986-07-23 1986-08-28 Unilever Plc Electrochemical measurements
US4787837A (en) 1986-08-07 1988-11-29 Union Carbide Corporation Wear-resistant ceramic, cermet or metallic embossing surfaces, methods for producing same, methods of embossing articles by same and novel embossed articles
US4894137A (en) 1986-09-12 1990-01-16 Omron Tateisi Electronics Co. Enzyme electrode
US5055171A (en) 1986-10-06 1991-10-08 T And G Corporation Ionic semiconductor materials and applications thereof
US5184619A (en) * 1986-11-10 1993-02-09 Peritronics Medical, Inc. Intrauterine pressure and fetal heart rate sensor
US4897162A (en) 1986-11-14 1990-01-30 The Cleveland Clinic Foundation Pulse voltammetry
DE3700119A1 (en) 1987-01-03 1988-07-14 Inst Diabetestechnologie Gemei IMPLANTABLE ELECTROCHEMICAL SENSOR
US4934369A (en) 1987-01-30 1990-06-19 Minnesota Mining And Manufacturing Company Intravascular blood parameter measurement system
EP0278647A3 (en) 1987-02-09 1989-09-20 AT&T Corp. Electronchemical processes involving enzymes
GB2201248B (en) 1987-02-24 1991-04-17 Ici Plc Enzyme electrode sensors
US4777953A (en) 1987-02-25 1988-10-18 Ash Medical Systems, Inc. Capillary filtration and collection method for long-term monitoring of blood constituents
US5002054A (en) 1987-02-25 1991-03-26 Ash Medical Systems, Inc. Interstitial filtration and collection device and method for long-term monitoring of physiological constituents of the body
US4854322A (en) 1987-02-25 1989-08-08 Ash Medical Systems, Inc. Capillary filtration and collection device for long-term monitoring of blood constituents
US4848351A (en) 1987-03-04 1989-07-18 Sentry Medical Products, Inc. Medical electrode assembly
GB2204408A (en) 1987-03-04 1988-11-09 Plessey Co Plc Biosensor device
US4923586A (en) 1987-03-31 1990-05-08 Daikin Industries, Ltd. Enzyme electrode unit
US4935345A (en) * 1987-04-07 1990-06-19 Arizona Board Of Regents Implantable microelectronic biochemical sensor incorporating thin film thermopile
US4759828A (en) 1987-04-09 1988-07-26 Nova Biomedical Corporation Glucose electrode and method of determining glucose
US5352348A (en) 1987-04-09 1994-10-04 Nova Biomedical Corporation Method of using enzyme electrode
US4749985A (en) 1987-04-13 1988-06-07 United States Of America As Represented By The United States Department Of Energy Functional relationship-based alarm processing
EP0290683A3 (en) 1987-05-01 1988-12-14 Diva Medical Systems B.V. Diabetes management system and apparatus
US5286364A (en) 1987-06-08 1994-02-15 Rutgers University Surface-modified electochemical biosensor
US4822337A (en) 1987-06-22 1989-04-18 Stanley Newhouse Insulin delivery method and apparatus
JPH07122624B2 (en) 1987-07-06 1995-12-25 ダイキン工業株式会社 Biosensor
US4805625A (en) * 1987-07-08 1989-02-21 Ad-Tech Medical Instrument Corporation Sphenoidal electrode and insertion method
US4874500A (en) * 1987-07-15 1989-10-17 Sri International Microelectrochemical sensor and sensor array
GB8718430D0 (en) 1987-08-04 1987-09-09 Ici Plc Sensor
JPS6423155A (en) 1987-07-17 1989-01-25 Daikin Ind Ltd Electrode refreshing device for biosensor
EP0378683B1 (en) 1987-08-11 1995-11-02 Terumo Kabushiki Kaisha Automatic sphygmomanometer
US4974929A (en) 1987-09-22 1990-12-04 Baxter International, Inc. Fiber optical probe connector for physiologic measurement devices
NL8702370A (en) 1987-10-05 1989-05-01 Groningen Science Park METHOD AND SYSTEM FOR GLUCOSE DETERMINATION AND USEABLE MEASURING CELL ASSEMBLY.
US4815469A (en) 1987-10-08 1989-03-28 Siemens-Pacesetter, Inc. Implantable blood oxygen sensor and method of use
GB8725936D0 (en) 1987-11-05 1987-12-09 Genetics Int Inc Sensing system
JPH01140054A (en) 1987-11-26 1989-06-01 Nec Corp Glucose sensor
US4813424A (en) 1987-12-23 1989-03-21 University Of New Mexico Long-life membrane electrode for non-ionic species
US5108564A (en) 1988-03-15 1992-04-28 Tall Oak Ventures Method and apparatus for amperometric diagnostic analysis
DE68924026T3 (en) 1988-03-31 2008-01-10 Matsushita Electric Industrial Co., Ltd., Kadoma BIOSENSOR AND ITS MANUFACTURE.
GB8817421D0 (en) 1988-07-21 1988-08-24 Medisense Inc Bioelectrochemical electrodes
US4954129A (en) 1988-07-25 1990-09-04 Abbott Laboratories Hydrodynamic clot flushing
US4925268A (en) 1988-07-25 1990-05-15 Abbott Laboratories Fiber-optic physiological probes
EP0353328A1 (en) 1988-08-03 1990-02-07 Dräger Nederland B.V. A polarographic-amperometric three-electrode sensor
US4898591A (en) * 1988-08-09 1990-02-06 Mallinckrodt, Inc. Nylon-PEBA copolymer catheter
US5340722A (en) 1988-08-24 1994-08-23 Avl Medical Instruments Ag Method for the determination of the concentration of an enzyme substrate and a sensor for carrying out the method
US5264106A (en) 1988-10-07 1993-11-23 Medisense, Inc. Enhanced amperometric sensor
US5108889A (en) * 1988-10-12 1992-04-28 Thorne, Smith, Astill Technologies, Inc. Assay for determining analyte using mercury release followed by detection via interaction with aluminum
JPH02128152A (en) 1988-11-08 1990-05-16 Nec Corp Immobilization of enzyme and biosensor
US5205920A (en) 1989-03-03 1993-04-27 Noboru Oyama Enzyme sensor and method of manufacturing the same
US5269891A (en) 1989-03-09 1993-12-14 Novo Nordisk A/S Method and apparatus for determination of a constituent in a fluid
US5089112A (en) 1989-03-20 1992-02-18 Associated Universities, Inc. Electrochemical biosensor based on immobilized enzymes and redox polymers
JPH02298855A (en) * 1989-03-20 1990-12-11 Assoc Univ Inc Electrochemical biosensor using immobilized enzyme and redox polymer
US4953552A (en) 1989-04-21 1990-09-04 Demarzo Arthur P Blood glucose monitoring system
EP0396788A1 (en) 1989-05-08 1990-11-14 Dräger Nederland B.V. Process and sensor for measuring the glucose content of glucosecontaining fluids
US5236567A (en) 1989-05-31 1993-08-17 Nakano Vinegar Co., Ltd. Enzyme sensor
US5198367A (en) 1989-06-09 1993-03-30 Masuo Aizawa Homogeneous amperometric immunoassay
FR2648353B1 (en) 1989-06-16 1992-03-27 Europhor Sa MICRODIALYSIS PROBE
CH677149A5 (en) 1989-07-07 1991-04-15 Disetronic Ag
US5431160A (en) 1989-07-19 1995-07-11 University Of New Mexico Miniature implantable refillable glucose sensor and material therefor
US5320725A (en) * 1989-08-02 1994-06-14 E. Heller & Company Electrode and method for the detection of hydrogen peroxide
US5264104A (en) * 1989-08-02 1993-11-23 Gregg Brian A Enzyme electrodes
US5264105A (en) * 1989-08-02 1993-11-23 Gregg Brian A Enzyme electrodes
US5262035A (en) * 1989-08-02 1993-11-16 E. Heller And Company Enzyme electrodes
US4944299A (en) 1989-08-08 1990-07-31 Siemens-Pacesetter, Inc. High speed digital telemetry system for implantable device
US5190041A (en) 1989-08-11 1993-03-02 Palti Yoram Prof System for monitoring and controlling blood glucose
US5101814A (en) 1989-08-11 1992-04-07 Palti Yoram Prof System for monitoring and controlling blood glucose
US5095904A (en) 1989-09-08 1992-03-17 Cochlear Pty. Ltd. Multi-peak speech procession
US5050612A (en) 1989-09-12 1991-09-24 Matsumura Kenneth N Device for computer-assisted monitoring of the body
FR2652736A1 (en) 1989-10-06 1991-04-12 Neftel Frederic IMPLANTABLE DEVICE FOR EVALUATING THE RATE OF GLUCOSE.
DE3934299C1 (en) 1989-10-13 1990-10-25 Gesellschaft Fuer Biotechnologische Forschung Mbh (Gbf), 3300 Braunschweig, De
EP0429076B1 (en) 1989-11-24 1996-01-31 Matsushita Electric Industrial Co., Ltd. Preparation of biosensor
US5082550A (en) * 1989-12-11 1992-01-21 The United States Of America As Represented By The Department Of Energy Enzyme electrochemical sensor electrode and method of making it
US5342789A (en) 1989-12-14 1994-08-30 Sensor Technologies, Inc. Method and device for detecting and quantifying glucose in body fluids
KR0171222B1 (en) 1989-12-15 1999-02-18 스티브 올드함 Redox mediator reagent and biosensor
US5286362A (en) 1990-02-03 1994-02-15 Boehringer Mannheim Gmbh Method and sensor electrode system for the electrochemical determination of an analyte or an oxidoreductase as well as the use of suitable compounds therefor
US5109850A (en) 1990-02-09 1992-05-05 Massachusetts Institute Of Technology Automatic blood monitoring for medication delivery method and apparatus
US5108819A (en) 1990-02-14 1992-04-28 Eli Lilly And Company Thin film electrical component
US5161532A (en) 1990-04-19 1992-11-10 Teknekron Sensor Development Corporation Integral interstitial fluid sensor
US5165407A (en) * 1990-04-19 1992-11-24 The University Of Kansas Implantable glucose sensor
DE4014109A1 (en) * 1990-05-02 1991-11-07 Siemens Ag ELECROCHEMICAL DETERMINATION OF THE OXYGEN CONCENTRATION
GB2245665A (en) 1990-06-30 1992-01-08 Draftex Ind Ltd Flexible protective bellows.
SE506135C2 (en) 1990-07-11 1997-11-17 Radi Medical Systems Sensor and conductor construction
US5250439A (en) * 1990-07-19 1993-10-05 Miles Inc. Use of conductive sensors in diagnostic assays
US5202261A (en) * 1990-07-19 1993-04-13 Miles Inc. Conductive sensors and their use in diagnostic assays
US5395332A (en) 1990-08-28 1995-03-07 Scimed Life Systems, Inc. Intravascualr catheter with distal tip guide wire lumen
US5431806A (en) 1990-09-17 1995-07-11 Fujitsu Limited Oxygen electrode and temperature sensor
ATE106015T1 (en) 1990-09-28 1994-06-15 Pfizer METER DELIVERY DEVICE CONTAINING A HYDROPHOBIC AGENT.
US5520731A (en) 1990-10-20 1996-05-28 Zanders Feinpapiere Ag Doctor blade for use in coating continuous strips of material or similar substrates
US5058592A (en) 1990-11-02 1991-10-22 Whisler G Douglas Adjustable mountable doppler ultrasound transducer device
AU1356792A (en) * 1991-01-25 1992-08-27 Markwell Medical Institute, Inc. Implantable biological fluid measuring device
FR2673289B1 (en) 1991-02-21 1994-06-17 Asulab Sa SENSOR FOR MEASURING THE QUANTITY OF A COMPONENT IN SOLUTION.
US5262305A (en) * 1991-03-04 1993-11-16 E. Heller & Company Interferant eliminating biosensors
US5593852A (en) * 1993-12-02 1997-01-14 Heller; Adam Subcutaneous glucose electrode
JPH04278450A (en) * 1991-03-04 1992-10-05 Adam Heller Biosensor and method for analyzing subject
GB9107193D0 (en) 1991-04-05 1991-05-22 Wilson Robert Analytical devices
US5208154A (en) 1991-04-08 1993-05-04 The United States Of America As Represented By The Department Of Energy Reversibly immobilized biological materials in monolayer films on electrodes
US5192416A (en) 1991-04-09 1993-03-09 New Mexico State University Technology Transfer Corporation Method and apparatus for batch injection analysis
US5293546A (en) * 1991-04-17 1994-03-08 Martin Marietta Corporation Oxide coated metal grid electrode structure in display devices
JP3118015B2 (en) 1991-05-17 2000-12-18 アークレイ株式会社 Biosensor and separation and quantification method using the same
US5209229A (en) 1991-05-20 1993-05-11 Telectronics Pacing Systems, Inc. Apparatus and method employing plural electrode configurations for cardioversion of atrial fibrillation in an arrhythmia control system
JP2816262B2 (en) * 1991-07-09 1998-10-27 工業技術院長 Carbon microsensor electrode and method of manufacturing the same
GB9120144D0 (en) 1991-09-20 1991-11-06 Imperial College A dialysis electrode device
US5264092A (en) 1991-10-02 1993-11-23 Moltech Corporation Redox polymer modified electrode for the electrochemical regeneration of coenzyme
US5322063A (en) 1991-10-04 1994-06-21 Eli Lilly And Company Hydrophilic polyurethane membranes for electrochemical glucose sensors
US5264103A (en) 1991-10-18 1993-11-23 Matsushita Electric Industrial Co., Ltd. Biosensor and a method for measuring a concentration of a substrate in a sample
US5217595A (en) 1991-10-25 1993-06-08 The Yellow Springs Instrument Company, Inc. Electrochemical gas sensor
US5415164A (en) 1991-11-04 1995-05-16 Biofield Corp. Apparatus and method for screening and diagnosing trauma or disease in body tissues
US5271815A (en) 1991-12-26 1993-12-21 Via Medical Corporation Method for measuring glucose
US5336388A (en) 1991-12-26 1994-08-09 Ppg Industries, Inc. Analyte and pH measuring sensor assembly and method
US5285792A (en) * 1992-01-10 1994-02-15 Physio-Control Corporation System for producing prioritized alarm messages in a medical instrument
US5246867A (en) 1992-01-17 1993-09-21 University Of Maryland At Baltimore Determination and quantification of saccharides by luminescence lifetimes and energy transfer
NL9200207A (en) 1992-02-05 1993-09-01 Nedap Nv IMPLANTABLE BIOMEDICAL SENSOR DEVICE, IN PARTICULAR FOR MEASUREMENT OF THE GLUCOSE CONCENTRATION.
US5278279A (en) * 1992-03-11 1994-01-11 Daicel Chemical Industries, Ltd. Process for producing (co)polycarbonate with transesterification catalyst and compound
DE69319771T2 (en) 1992-03-31 1999-04-22 Dainippon Printing Co Ltd Immobilized enzyme electrode, composition for its production and electrically conductive enzymes
US5496772A (en) 1992-04-07 1996-03-05 Nissin Electric Co., Ltd. Method of manufacturing film carrier type substrate
US5324322A (en) 1992-04-20 1994-06-28 Case Western Reserve University Thin film implantable electrode and method of manufacture
US5711001A (en) * 1992-05-08 1998-01-20 Motorola, Inc. Method and circuit for acquisition by a radio receiver
GB9211402D0 (en) 1992-05-29 1992-07-15 Univ Manchester Sensor devices
US5421816A (en) 1992-10-14 1995-06-06 Endodermic Medical Technologies Company Ultrasonic transdermal drug delivery system
US5387327A (en) 1992-10-19 1995-02-07 Duquesne University Of The Holy Ghost Implantable non-enzymatic electrochemical glucose sensor
US5320098A (en) 1992-10-20 1994-06-14 Sun Microsystems, Inc. Optical transdermal link
WO1994010553A1 (en) * 1992-10-23 1994-05-11 Optex Biomedical, Inc. Fibre-optic probe for the measurement of fluid parameters
US5899855A (en) 1992-11-17 1999-05-04 Health Hero Network, Inc. Modular microprocessor-based health monitoring system
US5956501A (en) 1997-01-10 1999-09-21 Health Hero Network, Inc. Disease simulation system and method
ZA938555B (en) 1992-11-23 1994-08-02 Lilly Co Eli Technique to improve the performance of electrochemical sensors
DK148592D0 (en) 1992-12-10 1992-12-10 Novo Nordisk As APPARATUS
US5375604A (en) 1992-12-11 1994-12-27 Siemens Medical Electronics, Inc. Transportable modular patient monitor
FR2701117B1 (en) 1993-02-04 1995-03-10 Asulab Sa Electrochemical measurement system with multizone sensor, and its application to glucose measurement.
GB9304306D0 (en) * 1993-03-03 1993-04-21 Univ Alberta Glucose sensor
DE4318519C2 (en) 1993-06-03 1996-11-28 Fraunhofer Ges Forschung Electrochemical sensor
US5403462A (en) 1993-06-24 1995-04-04 Yissum Research Development Company Of The Hebrew Univeristy Of Jerusalem Electrochemical electrodes and methods for the preparation thereof
DE4329898A1 (en) 1993-09-04 1995-04-06 Marcus Dr Besson Wireless medical diagnostic and monitoring device
US5582184A (en) 1993-10-13 1996-12-10 Integ Incorporated Interstitial fluid collection and constituent measurement
US5512406A (en) * 1993-10-14 1996-04-30 Canon Kabushiki Kaisha Toners of different size for electrophotography
US5791344A (en) 1993-11-19 1998-08-11 Alfred E. Mann Foundation For Scientific Research Patient monitoring system
US5497772A (en) 1993-11-19 1996-03-12 Alfred E. Mann Foundation For Scientific Research Glucose monitoring system
US5589326A (en) 1993-12-30 1996-12-31 Boehringer Mannheim Corporation Osmium-containing redox mediator
DE4401400A1 (en) 1994-01-19 1995-07-20 Ernst Prof Dr Pfeiffer Method and arrangement for continuously monitoring the concentration of a metabolite
US5437999A (en) 1994-02-22 1995-08-01 Boehringer Mannheim Corporation Electrochemical sensor
US5391250A (en) 1994-03-15 1995-02-21 Minimed Inc. Method of fabricating thin film sensors
US5390671A (en) 1994-03-15 1995-02-21 Minimed Inc. Transcutaneous sensor insertion set
US5510583A (en) * 1994-03-18 1996-04-23 Eaton Corporation Assembly for sequential switching
JP3061351B2 (en) 1994-04-25 2000-07-10 松下電器産業株式会社 Method and apparatus for quantifying specific compounds
US5569186A (en) 1994-04-25 1996-10-29 Minimed Inc. Closed loop infusion pump system with removable glucose sensor
DE4415896A1 (en) * 1994-05-05 1995-11-09 Boehringer Mannheim Gmbh Analysis system for monitoring the concentration of an analyte in the blood of a patient
US5545191A (en) 1994-05-06 1996-08-13 Alfred E. Mann Foundation For Scientific Research Method for optimally positioning and securing the external unit of a transcutaneous transducer of the skin of a living body
US5510581A (en) * 1994-05-18 1996-04-23 Angel; Shlomo Mass-produced flat multiple-beam load cell and scales incorporating it
GB9412789D0 (en) * 1994-06-24 1994-08-17 Environmental Sensors Ltd Improvements to electrodes
US5429735A (en) 1994-06-27 1995-07-04 Miles Inc. Method of making and amperometric electrodes
US5494562A (en) 1994-06-27 1996-02-27 Ciba Corning Diagnostics Corp. Electrochemical sensors
US5462051A (en) 1994-08-31 1995-10-31 Colin Corporation Medical communication system
IE72524B1 (en) 1994-11-04 1997-04-23 Elan Med Tech Analyte-controlled liquid delivery device and analyte monitor
US20050043596A1 (en) * 1996-07-12 2005-02-24 Non-Invasive Technology, Inc., A Delaware Corporation Optical examination device, system and method
US5586553A (en) 1995-02-16 1996-12-24 Minimed Inc. Transcutaneous sensor insertion set
US5568806A (en) 1995-02-16 1996-10-29 Minimed Inc. Transcutaneous sensor insertion set
US5651869A (en) 1995-02-28 1997-07-29 Matsushita Electric Industrial Co., Ltd. Biosensor
US5510584A (en) * 1995-03-07 1996-04-23 Itt Corporation Sequentially operated snap action membrane switches
US5596150A (en) 1995-03-08 1997-01-21 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Capacitance probe for fluid flow and volume measurements
JPH08247987A (en) 1995-03-15 1996-09-27 Omron Corp Portable measuring instrument
US5582697A (en) 1995-03-17 1996-12-10 Matsushita Electric Industrial Co., Ltd. Biosensor, and a method and a device for quantifying a substrate in a sample liquid using the same
US5882494A (en) 1995-03-27 1999-03-16 Minimed, Inc. Polyurethane/polyurea compositions containing silicone for biosensor membranes
US5628310A (en) 1995-05-19 1997-05-13 Joseph R. Lakowicz Method and apparatus to perform trans-cutaneous analyte monitoring
US5567302A (en) 1995-06-07 1996-10-22 Molecular Devices Corporation Electrochemical system for rapid detection of biochemical agents that catalyze a redox potential change
US5743262A (en) 1995-06-07 1998-04-28 Masimo Corporation Blood glucose monitoring system
CN1192680A (en) * 1995-06-07 1998-09-09 苏根公司 Method and compositions for inhibition of adaptor protein/tyrosine kinase interactions
US5995860A (en) 1995-07-06 1999-11-30 Thomas Jefferson University Implantable sensor and system for measurement and control of blood constituent levels
DE19530376C2 (en) 1995-08-18 1999-09-02 Fresenius Ag Biosensor
US5682233A (en) 1995-09-08 1997-10-28 Integ, Inc. Interstitial fluid sampler
US5735273A (en) 1995-09-12 1998-04-07 Cygnus, Inc. Chemical signal-impermeable mask
US5628890A (en) 1995-09-27 1997-05-13 Medisense, Inc. Electrochemical sensor
US5972199A (en) 1995-10-11 1999-10-26 E. Heller & Company Electrochemical analyte sensors using thermostable peroxidase
US5741211A (en) 1995-10-26 1998-04-21 Medtronic, Inc. System and method for continuous monitoring of diabetes-related blood constituents
DE19541619A1 (en) 1995-11-08 1997-05-15 Bosch Gmbh Robert Electrochemical sensor and method for producing an electrochemical sensor
US5711861A (en) 1995-11-22 1998-01-27 Ward; W. Kenneth Device for monitoring changes in analyte concentration
US6428489B1 (en) 1995-12-07 2002-08-06 Precision Vascular Systems, Inc. Guidewire system
US5747669A (en) 1995-12-28 1998-05-05 Fujitsu Limited Oxygen electrode and its manufacture
US5917320A (en) 1996-01-17 1999-06-29 Allegro Microsystems, Inc. Detection of passing magnetic articles while periodically adapting detection threshold
FI118509B (en) 1996-02-12 2007-12-14 Nokia Oyj A method and apparatus for predicting blood glucose levels in a patient
US5708247A (en) 1996-02-14 1998-01-13 Selfcare, Inc. Disposable glucose test strips, and methods and compositions for making same
JP3028752U (en) 1996-03-05 1996-09-13 株式会社オフィス・オートメーション・システム Telepromotion system
US5942443A (en) 1996-06-28 1999-08-24 Caliper Technologies Corporation High throughput screening assay systems in microscale fluidic devices
US5954685A (en) 1996-05-24 1999-09-21 Cygnus, Inc. Electrochemical sensor with dual purpose electrode
EP0906563A1 (en) 1996-06-17 1999-04-07 Mercury Diagnostics Inc. Electrochemical test device and related methods
ES2195151T3 (en) * 1996-06-18 2003-12-01 Alza Corp IMPROVEMENT OR SAMPLING DEVICE FOR TRANSDERMAL AGENTS.
JP3357247B2 (en) 1996-08-23 2002-12-16 アルプス電気株式会社 Temperature sensing element and radiation sensor
US5964993A (en) 1996-12-19 1999-10-12 Implanted Biosystems Inc. Glucose sensor
US5914026A (en) 1997-01-06 1999-06-22 Implanted Biosystems Inc. Implantable sensor employing an auxiliary electrode
US6122351A (en) 1997-01-21 2000-09-19 Med Graph, Inc. Method and system aiding medical diagnosis and treatment
US6093172A (en) 1997-02-05 2000-07-25 Minimed Inc. Injector for a subcutaneous insertion set
US6001067A (en) 1997-03-04 1999-12-14 Shults; Mark C. Device and method for determining analyte levels
US6741877B1 (en) 1997-03-04 2004-05-25 Dexcom, Inc. Device and method for determining analyte levels
US6558321B1 (en) 1997-03-04 2003-05-06 Dexcom, Inc. Systems and methods for remote monitoring and modulation of medical devices
US20050033132A1 (en) 1997-03-04 2005-02-10 Shults Mark C. Analyte measuring device
US7657297B2 (en) 2004-05-03 2010-02-02 Dexcom, Inc. Implantable analyte sensor
US6862465B2 (en) 1997-03-04 2005-03-01 Dexcom, Inc. Device and method for determining analyte levels
US7899511B2 (en) 2004-07-13 2011-03-01 Dexcom, Inc. Low oxygen in vivo analyte sensor
US7192450B2 (en) 2003-05-21 2007-03-20 Dexcom, Inc. Porous membranes for use with implantable devices
US6059946A (en) 1997-04-14 2000-05-09 Matsushita Electric Industrial Co., Ltd. Biosensor
US5759364A (en) 1997-05-02 1998-06-02 Bayer Corporation Electrochemical biosensor
JP2002505008A (en) 1997-06-16 2002-02-12 エラン コーポレーション ピーエルシー Methods for calibrating and testing sensors for in vivo measurement of analytes and devices for use in such methods
US6336845B1 (en) * 1997-11-12 2002-01-08 Lam Research Corporation Method and apparatus for polishing semiconductor wafers
US6579690B1 (en) 1997-12-05 2003-06-17 Therasense, Inc. Blood analyte monitoring through subcutaneous measurement
US6074725A (en) 1997-12-10 2000-06-13 Caliper Technologies Corp. Fabrication of microfluidic circuits by printing techniques
US6134461A (en) 1998-03-04 2000-10-17 E. Heller & Company Electrochemical analyte
US6024699A (en) * 1998-03-13 2000-02-15 Healthware Corporation Systems, methods and computer program products for monitoring, diagnosing and treating medical conditions of remotely located patients
US6175752B1 (en) 1998-04-30 2001-01-16 Therasense, Inc. Analyte monitoring device and methods of use
JP2000077477A (en) 1998-09-02 2000-03-14 Shinko Electric Ind Co Ltd Semiconductor device, its manufacture, and metallic substrate used therefor
DE69924749T2 (en) * 1998-11-20 2006-04-27 The University Of Connecticut, Farmington Generically integrated implantable potentiostat remote sensing device for electrochemical probes
US6360888B1 (en) * 1999-02-25 2002-03-26 Minimed Inc. Glucose sensor package system
US6285897B1 (en) * 1999-04-07 2001-09-04 Endonetics, Inc. Remote physiological monitoring system
US6669663B1 (en) 1999-04-30 2003-12-30 Medtronic, Inc. Closed loop medicament pump
US6974437B2 (en) 2000-01-21 2005-12-13 Medtronic Minimed, Inc. Microprocessor controlled ambulatory medical apparatus with hand held communication device
US6753143B2 (en) * 2000-05-01 2004-06-22 Clinical Micro Sensors, Inc. Target analyte detection using asymmetrical self-assembled monolayers
CN1329719C (en) 2000-12-12 2007-08-01 迷你米特公司 Digital sensor for miniature medical thermometer and body temp. monitor
US6702857B2 (en) 2001-07-27 2004-03-09 Dexcom, Inc. Membrane for use with implantable devices
US20030032874A1 (en) * 2001-07-27 2003-02-13 Dexcom, Inc. Sensor head for use with implantable devices
US8364229B2 (en) 2003-07-25 2013-01-29 Dexcom, Inc. Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise
US7613491B2 (en) 2002-05-22 2009-11-03 Dexcom, Inc. Silicone based membranes for use in implantable glucose sensors
US8260393B2 (en) * 2003-07-25 2012-09-04 Dexcom, Inc. Systems and methods for replacing signal data artifacts in a glucose sensor data stream
US8010174B2 (en) 2003-08-22 2011-08-30 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US9282925B2 (en) 2002-02-12 2016-03-15 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US7226978B2 (en) 2002-05-22 2007-06-05 Dexcom, Inc. Techniques to improve polyurethane membranes for implantable glucose sensors
US7134999B2 (en) 2003-04-04 2006-11-14 Dexcom, Inc. Optimized sensor geometry for an implantable glucose sensor
US7875293B2 (en) * 2003-05-21 2011-01-25 Dexcom, Inc. Biointerface membranes incorporating bioactive agents
US7467003B2 (en) 2003-12-05 2008-12-16 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US20050176136A1 (en) 2003-11-19 2005-08-11 Dexcom, Inc. Afinity domain for analyte sensor
US7366556B2 (en) 2003-12-05 2008-04-29 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US7424318B2 (en) 2003-12-05 2008-09-09 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
EP1649260A4 (en) 2003-07-25 2010-07-07 Dexcom Inc Electrode systems for electrochemical sensors
WO2005019795A2 (en) 2003-07-25 2005-03-03 Dexcom, Inc. Electrochemical sensors including electrode systems with increased oxygen generation
US8423113B2 (en) 2003-07-25 2013-04-16 Dexcom, Inc. Systems and methods for processing sensor data
WO2007120442A2 (en) 2003-07-25 2007-10-25 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
EP1648298A4 (en) 2003-07-25 2010-01-13 Dexcom Inc Oxygen enhancing membrane systems for implantable devices
US7460898B2 (en) 2003-12-05 2008-12-02 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US7591801B2 (en) 2004-02-26 2009-09-22 Dexcom, Inc. Integrated delivery device for continuous glucose sensor
US8285354B2 (en) 2003-08-01 2012-10-09 Dexcom, Inc. System and methods for processing analyte sensor data
US8626257B2 (en) 2003-08-01 2014-01-07 Dexcom, Inc. Analyte sensor
US7519408B2 (en) * 2003-11-19 2009-04-14 Dexcom, Inc. Integrated receiver for continuous analyte sensor
US8275437B2 (en) 2003-08-01 2012-09-25 Dexcom, Inc. Transcutaneous analyte sensor
US9135402B2 (en) 2007-12-17 2015-09-15 Dexcom, Inc. Systems and methods for processing sensor data
US8369919B2 (en) 2003-08-01 2013-02-05 Dexcom, Inc. Systems and methods for processing sensor data
US8845536B2 (en) 2003-08-01 2014-09-30 Dexcom, Inc. Transcutaneous analyte sensor
US8160669B2 (en) 2003-08-01 2012-04-17 Dexcom, Inc. Transcutaneous analyte sensor
US20070208245A1 (en) 2003-08-01 2007-09-06 Brauker James H Transcutaneous analyte sensor
US7774145B2 (en) 2003-08-01 2010-08-10 Dexcom, Inc. Transcutaneous analyte sensor
US8886273B2 (en) 2003-08-01 2014-11-11 Dexcom, Inc. Analyte sensor
US8676287B2 (en) 2003-08-01 2014-03-18 Dexcom, Inc. System and methods for processing analyte sensor data
US6931327B2 (en) 2003-08-01 2005-08-16 Dexcom, Inc. System and methods for processing analyte sensor data
US20070066873A1 (en) 2003-08-22 2007-03-22 Apurv Kamath Systems and methods for processing analyte sensor data
US7920906B2 (en) 2005-03-10 2011-04-05 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US20050090607A1 (en) 2003-10-28 2005-04-28 Dexcom, Inc. Silicone composition for biocompatible membrane
US8425416B2 (en) 2006-10-04 2013-04-23 Dexcom, Inc. Analyte sensor
US8364230B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US8425417B2 (en) 2003-12-05 2013-04-23 Dexcom, Inc. Integrated device for continuous in vivo analyte detection and simultaneous control of an infusion device
US8287453B2 (en) 2003-12-05 2012-10-16 Dexcom, Inc. Analyte sensor
US20080200788A1 (en) 2006-10-04 2008-08-21 Dexcorn, Inc. Analyte sensor
US20100185071A1 (en) 2003-12-05 2010-07-22 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8423114B2 (en) 2006-10-04 2013-04-16 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US20080197024A1 (en) 2003-12-05 2008-08-21 Dexcom, Inc. Analyte sensor
US8532730B2 (en) 2006-10-04 2013-09-10 Dexcom, Inc. Analyte sensor
US8364231B2 (en) * 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
ATE480761T1 (en) 2003-12-05 2010-09-15 Dexcom Inc CALIBRATION METHODS FOR A CONTINUOUSLY WORKING ANALYTICAL SENSOR
ATE474219T1 (en) 2003-12-08 2010-07-15 Dexcom Inc SYSTEMS AND METHODS FOR IMPROVING ELECTROCHEMICAL ANALYT SENSORS
WO2005057175A2 (en) * 2003-12-09 2005-06-23 Dexcom, Inc. Signal processing for continuous analyte sensor
US7637868B2 (en) 2004-01-12 2009-12-29 Dexcom, Inc. Composite material for implantable device
WO2005079257A2 (en) 2004-02-12 2005-09-01 Dexcom, Inc. Biointerface with macro- and micro- architecture
US8808228B2 (en) 2004-02-26 2014-08-19 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US8277713B2 (en) * 2004-05-03 2012-10-02 Dexcom, Inc. Implantable analyte sensor
US20050245799A1 (en) 2004-05-03 2005-11-03 Dexcom, Inc. Implantable analyte sensor
US20060015020A1 (en) * 2004-07-06 2006-01-19 Dexcom, Inc. Systems and methods for manufacture of an analyte-measuring device including a membrane system
US8565848B2 (en) 2004-07-13 2013-10-22 Dexcom, Inc. Transcutaneous analyte sensor
WO2006127694A2 (en) * 2004-07-13 2006-11-30 Dexcom, Inc. Analyte sensor
US20080242961A1 (en) 2004-07-13 2008-10-02 Dexcom, Inc. Transcutaneous analyte sensor
US7783333B2 (en) 2004-07-13 2010-08-24 Dexcom, Inc. Transcutaneous medical device with variable stiffness
US7640048B2 (en) 2004-07-13 2009-12-29 Dexcom, Inc. Analyte sensor
US8452368B2 (en) 2004-07-13 2013-05-28 Dexcom, Inc. Transcutaneous analyte sensor
US20060016700A1 (en) * 2004-07-13 2006-01-26 Dexcom, Inc. Transcutaneous analyte sensor
US20060020192A1 (en) * 2004-07-13 2006-01-26 Dexcom, Inc. Transcutaneous analyte sensor
JP5072171B2 (en) 2004-09-03 2012-11-14 エスケー化研株式会社 Interior paint composition
US20090076360A1 (en) 2007-09-13 2009-03-19 Dexcom, Inc. Transcutaneous analyte sensor
WO2006110193A2 (en) * 2005-04-08 2006-10-19 Dexcom, Inc. Cellulosic-based interference domain for an analyte sensor
US8447376B2 (en) 2006-10-04 2013-05-21 Dexcom, Inc. Analyte sensor
US8562528B2 (en) 2006-10-04 2013-10-22 Dexcom, Inc. Analyte sensor
US8449464B2 (en) 2006-10-04 2013-05-28 Dexcom, Inc. Analyte sensor
US8298142B2 (en) 2006-10-04 2012-10-30 Dexcom, Inc. Analyte sensor
US8275438B2 (en) 2006-10-04 2012-09-25 Dexcom, Inc. Analyte sensor
US7831287B2 (en) 2006-10-04 2010-11-09 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8478377B2 (en) 2006-10-04 2013-07-02 Dexcom, Inc. Analyte sensor
WO2008154312A1 (en) 2007-06-08 2008-12-18 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US8417312B2 (en) 2007-10-25 2013-04-09 Dexcom, Inc. Systems and methods for processing sensor data
US9839395B2 (en) 2007-12-17 2017-12-12 Dexcom, Inc. Systems and methods for processing sensor data
US20090299155A1 (en) 2008-01-30 2009-12-03 Dexcom, Inc. Continuous cardiac marker sensor system
CA2715624A1 (en) 2008-02-20 2009-08-27 Dexcom, Inc. Continuous medicament sensor system for in vivo use
EP2252196A4 (en) 2008-02-21 2013-05-15 Dexcom Inc Systems and methods for processing, transmitting and displaying sensor data
US20090242399A1 (en) 2008-03-25 2009-10-01 Dexcom, Inc. Analyte sensor
US8396528B2 (en) 2008-03-25 2013-03-12 Dexcom, Inc. Analyte sensor
US20090247855A1 (en) 2008-03-28 2009-10-01 Dexcom, Inc. Polymer membranes for continuous analyte sensors
EP2326944B1 (en) 2008-09-19 2020-08-19 Dexcom, Inc. Particle-containing membrane and particulate electrode for analyte sensors
JP5196595B2 (en) 2010-03-15 2013-05-15 Necアクセステクニカ株式会社 Optical signal redundancy system, optical signal distribution device, and optical signal redundancy method

Patent Citations (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4699157A (en) * 1985-08-27 1987-10-13 Electro-Catheter Corporation Pacing catheter and method of making same
US4986271A (en) * 1989-07-19 1991-01-22 The University Of New Mexico Vivo refillable glucose sensor
US5103816A (en) * 1989-09-11 1992-04-14 Biomedical Device Consultants, Inc. Composite for use in making protective articles for use in laser surgery
US5122244A (en) * 1990-02-03 1992-06-16 Boehringer Mannheim Gmbh Method and sensor electrode system for the electrochemical determination of an analyte or an oxidoreductase as well as the use of suitable compounds therefor
US5525511A (en) * 1990-09-01 1996-06-11 Environmental & Medical Products Ltd. Electrochemical biosensor stability
US6060176A (en) * 1995-11-30 2000-05-09 International Business Machines Corporation Corrosion protection for metallic features
US5776324A (en) * 1996-05-17 1998-07-07 Encelle, Inc. Electrochemical biosensors
US5696314A (en) * 1996-07-12 1997-12-09 Chiron Diagnostics Corporation Multilayer enzyme electrode membranes and methods of making same
US6387048B1 (en) * 1997-10-20 2002-05-14 Alfred E. Mann Foundation Implantable sensor and integrity tests therefor
US20070042377A1 (en) * 2003-10-29 2007-02-22 Zhiqiang Gao Biosensor
US20050215871A1 (en) * 2004-02-09 2005-09-29 Feldman Benjamin J Analyte sensor, and associated system and method employing a catalytic agent

Cited By (309)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8741590B2 (en) 1991-03-04 2014-06-03 Abbott Diabetes Care Inc. Subcutaneous glucose electrode
US8588881B2 (en) 1991-03-04 2013-11-19 Abbott Diabetes Care Inc. Subcutaneous glucose electrode
US7970448B2 (en) 1997-03-04 2011-06-28 Dexcom, Inc. Device and method for determining analyte levels
US9339223B2 (en) 1997-03-04 2016-05-17 Dexcom, Inc. Device and method for determining analyte levels
US8676288B2 (en) 1997-03-04 2014-03-18 Dexcom, Inc. Device and method for determining analyte levels
US7792562B2 (en) 1997-03-04 2010-09-07 Dexcom, Inc. Device and method for determining analyte levels
US8527025B1 (en) 1997-03-04 2013-09-03 Dexcom, Inc. Device and method for determining analyte levels
US7835777B2 (en) 1997-03-04 2010-11-16 Dexcom, Inc. Device and method for determining analyte levels
US7974672B2 (en) 1997-03-04 2011-07-05 Dexcom, Inc. Device and method for determining analyte levels
US8706180B2 (en) 1998-03-04 2014-04-22 Abbott Diabetes Care Inc. Electrochemical analyte sensor
US8463351B2 (en) 1998-03-04 2013-06-11 Abbott Diabetes Care Inc. Electrochemical analyte sensor
US7996054B2 (en) 1998-03-04 2011-08-09 Abbott Diabetes Care Inc. Electrochemical analyte sensor
US9072477B2 (en) 1998-04-30 2015-07-07 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9042953B2 (en) 1998-04-30 2015-05-26 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8612159B2 (en) 1998-04-30 2013-12-17 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8617071B2 (en) 1998-04-30 2013-12-31 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US7885699B2 (en) 1998-04-30 2011-02-08 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US7869853B1 (en) 1998-04-30 2011-01-11 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8622906B2 (en) 1998-04-30 2014-01-07 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US7860544B2 (en) 1998-04-30 2010-12-28 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8641619B2 (en) 1998-04-30 2014-02-04 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8649841B2 (en) 1998-04-30 2014-02-11 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8660627B2 (en) 1998-04-30 2014-02-25 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8666469B2 (en) 1998-04-30 2014-03-04 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8670815B2 (en) 1998-04-30 2014-03-11 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8672844B2 (en) 1998-04-30 2014-03-18 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8688188B2 (en) 1998-04-30 2014-04-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8480580B2 (en) 1998-04-30 2013-07-09 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8162829B2 (en) 1998-04-30 2012-04-24 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8175673B2 (en) 1998-04-30 2012-05-08 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8177716B2 (en) 1998-04-30 2012-05-15 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8734348B2 (en) 1998-04-30 2014-05-27 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US10478108B2 (en) 1998-04-30 2019-11-19 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8224413B2 (en) 1998-04-30 2012-07-17 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8226558B2 (en) 1998-04-30 2012-07-24 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8226555B2 (en) 1998-04-30 2012-07-24 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8226557B2 (en) 1998-04-30 2012-07-24 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8734346B2 (en) 1998-04-30 2014-05-27 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8231532B2 (en) 1998-04-30 2012-07-31 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8473021B2 (en) 1998-04-30 2013-06-25 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8235896B2 (en) 1998-04-30 2012-08-07 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9326714B2 (en) 1998-04-30 2016-05-03 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8465425B2 (en) 1998-04-30 2013-06-18 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8255031B2 (en) 1998-04-30 2012-08-28 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9066694B2 (en) 1998-04-30 2015-06-30 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8260392B2 (en) 1998-04-30 2012-09-04 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8265726B2 (en) 1998-04-30 2012-09-11 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8738109B2 (en) 1998-04-30 2014-05-27 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9066695B2 (en) 1998-04-30 2015-06-30 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8275439B2 (en) 1998-04-30 2012-09-25 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8273022B2 (en) 1998-04-30 2012-09-25 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9066697B2 (en) 1998-04-30 2015-06-30 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8287454B2 (en) 1998-04-30 2012-10-16 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8597189B2 (en) 1998-04-30 2013-12-03 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8306598B2 (en) 1998-04-30 2012-11-06 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8346336B2 (en) 1998-04-30 2013-01-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8346337B2 (en) 1998-04-30 2013-01-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8353829B2 (en) 1998-04-30 2013-01-15 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8357091B2 (en) 1998-04-30 2013-01-22 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8744545B2 (en) 1998-04-30 2014-06-03 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9014773B2 (en) 1998-04-30 2015-04-21 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9011331B2 (en) 1998-04-30 2015-04-21 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8974386B2 (en) 1998-04-30 2015-03-10 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8366614B2 (en) 1998-04-30 2013-02-05 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8372005B2 (en) 1998-04-30 2013-02-12 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8380273B2 (en) 1998-04-30 2013-02-19 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8391945B2 (en) 1998-04-30 2013-03-05 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8880137B2 (en) 1998-04-30 2014-11-04 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8409131B2 (en) 1998-04-30 2013-04-02 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8774887B2 (en) 1998-04-30 2014-07-08 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8840553B2 (en) 1998-04-30 2014-09-23 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9011332B2 (en) 2001-01-02 2015-04-21 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8652043B2 (en) 2001-01-02 2014-02-18 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9610034B2 (en) 2001-01-02 2017-04-04 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8668645B2 (en) 2001-01-02 2014-03-11 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9498159B2 (en) 2001-01-02 2016-11-22 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8236242B2 (en) 2001-04-02 2012-08-07 Abbott Diabetes Care Inc. Blood glucose tracking apparatus and methods
US8268243B2 (en) 2001-04-02 2012-09-18 Abbott Diabetes Care Inc. Blood glucose tracking apparatus and methods
US7976778B2 (en) 2001-04-02 2011-07-12 Abbott Diabetes Care Inc. Blood glucose tracking apparatus
US9477811B2 (en) 2001-04-02 2016-10-25 Abbott Diabetes Care Inc. Blood glucose tracking apparatus and methods
US8765059B2 (en) 2001-04-02 2014-07-01 Abbott Diabetes Care Inc. Blood glucose tracking apparatus
US8509871B2 (en) 2001-07-27 2013-08-13 Dexcom, Inc. Sensor head for use with implantable devices
US9328371B2 (en) 2001-07-27 2016-05-03 Dexcom, Inc. Sensor head for use with implantable devices
US9804114B2 (en) 2001-07-27 2017-10-31 Dexcom, Inc. Sensor head for use with implantable devices
US8064977B2 (en) 2002-05-22 2011-11-22 Dexcom, Inc. Silicone based membranes for use in implantable glucose sensors
US8543184B2 (en) 2002-05-22 2013-09-24 Dexcom, Inc. Silicone based membranes for use in implantable glucose sensors
US9179869B2 (en) 2002-05-22 2015-11-10 Dexcom, Inc. Techniques to improve polyurethane membranes for implantable glucose sensors
US10052051B2 (en) 2002-05-22 2018-08-21 Dexcom, Inc. Silicone based membranes for use in implantable glucose sensors
US9549693B2 (en) 2002-05-22 2017-01-24 Dexcom, Inc. Silicone based membranes for use in implantable glucose sensors
US11020026B2 (en) 2002-05-22 2021-06-01 Dexcom, Inc. Silicone based membranes for use in implantable glucose sensors
US8053018B2 (en) 2002-05-22 2011-11-08 Dexcom, Inc. Techniques to improve polyurethane membranes for implantable glucose sensors
US8050731B2 (en) 2002-05-22 2011-11-01 Dexcom, Inc. Techniques to improve polyurethane membranes for implantable glucose sensors
US8865249B2 (en) 2002-05-22 2014-10-21 Dexcom, Inc. Techniques to improve polyurethane membranes for implantable glucose sensors
US9801574B2 (en) 2002-05-22 2017-10-31 Dexcom, Inc. Techniques to improve polyurethane membranes for implantable glucose sensors
US10154807B2 (en) 2002-05-22 2018-12-18 Dexcom, Inc. Techniques to improve polyurethane membranes for implantable glucose sensors
US10750952B2 (en) 2002-12-31 2020-08-25 Abbott Diabetes Care Inc. Continuous glucose monitoring system and methods of use
US8187183B2 (en) 2002-12-31 2012-05-29 Abbott Diabetes Care Inc. Continuous glucose monitoring system and methods of use
US8622903B2 (en) 2002-12-31 2014-01-07 Abbott Diabetes Care Inc. Continuous glucose monitoring system and methods of use
US10039881B2 (en) 2002-12-31 2018-08-07 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US7811231B2 (en) 2002-12-31 2010-10-12 Abbott Diabetes Care Inc. Continuous glucose monitoring system and methods of use
US9962091B2 (en) 2002-12-31 2018-05-08 Abbott Diabetes Care Inc. Continuous glucose monitoring system and methods of use
US8066639B2 (en) 2003-06-10 2011-11-29 Abbott Diabetes Care Inc. Glucose measuring device for use in personal area network
US9730584B2 (en) 2003-06-10 2017-08-15 Abbott Diabetes Care Inc. Glucose measuring device for use in personal area network
US8512239B2 (en) 2003-06-10 2013-08-20 Abbott Diabetes Care Inc. Glucose measuring device for use in personal area network
US8647269B2 (en) 2003-06-10 2014-02-11 Abbott Diabetes Care Inc. Glucose measuring device for use in personal area network
US9597027B2 (en) 2003-07-25 2017-03-21 Dexcom, Inc. Oxygen enhancing membrane systems for implantable devices
US8255033B2 (en) 2003-07-25 2012-08-28 Dexcom, Inc. Oxygen enhancing membrane systems for implantable devices
US8909314B2 (en) 2003-07-25 2014-12-09 Dexcom, Inc. Oxygen enhancing membrane systems for implantable devices
US9993186B2 (en) 2003-07-25 2018-06-12 Dexcom, Inc. Oxygen enhancing membrane systems for implantable devices
US8255032B2 (en) 2003-07-25 2012-08-28 Dexcom, Inc. Oxygen enhancing membrane systems for implantable devices
USRE43399E1 (en) 2003-07-25 2012-05-22 Dexcom, Inc. Electrode systems for electrochemical sensors
US7828728B2 (en) 2003-07-25 2010-11-09 Dexcom, Inc. Analyte sensor
US10610140B2 (en) 2003-07-25 2020-04-07 Dexcom, Inc. Oxygen enhancing membrane systems for implantable devices
US10376143B2 (en) 2003-07-25 2019-08-13 Dexcom, Inc. Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise
US9763609B2 (en) 2003-07-25 2017-09-19 Dexcom, Inc. Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise
US7761130B2 (en) 2003-07-25 2010-07-20 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8255030B2 (en) 2003-07-25 2012-08-28 Dexcom, Inc. Oxygen enhancing membrane systems for implantable devices
US8364229B2 (en) 2003-07-25 2013-01-29 Dexcom, Inc. Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise
US10052055B2 (en) 2003-08-01 2018-08-21 Dexcom, Inc. Analyte sensor
US8886273B2 (en) 2003-08-01 2014-11-11 Dexcom, Inc. Analyte sensor
US8626257B2 (en) 2003-08-01 2014-01-07 Dexcom, Inc. Analyte sensor
US10188333B2 (en) 2003-12-05 2019-01-29 Dexcom, Inc. Calibration techniques for a continuous analyte sensor
US11020031B1 (en) 2003-12-05 2021-06-01 Dexcom, Inc. Analyte sensor
US11000215B1 (en) 2003-12-05 2021-05-11 Dexcom, Inc. Analyte sensor
US8929968B2 (en) 2003-12-05 2015-01-06 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US11633133B2 (en) 2003-12-05 2023-04-25 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8425417B2 (en) 2003-12-05 2013-04-23 Dexcom, Inc. Integrated device for continuous in vivo analyte detection and simultaneous control of an infusion device
US8771183B2 (en) 2004-02-17 2014-07-08 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US11246990B2 (en) 2004-02-26 2022-02-15 Dexcom, Inc. Integrated delivery device for continuous glucose sensor
US10835672B2 (en) 2004-02-26 2020-11-17 Dexcom, Inc. Integrated insulin delivery system with continuous glucose sensor
US10966609B2 (en) 2004-02-26 2021-04-06 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US8277713B2 (en) 2004-05-03 2012-10-02 Dexcom, Inc. Implantable analyte sensor
US10918313B2 (en) 2004-07-13 2021-02-16 Dexcom, Inc. Analyte sensor
US10799159B2 (en) 2004-07-13 2020-10-13 Dexcom, Inc. Analyte sensor
US11064917B2 (en) 2004-07-13 2021-07-20 Dexcom, Inc. Analyte sensor
US10524703B2 (en) 2004-07-13 2020-01-07 Dexcom, Inc. Transcutaneous analyte sensor
US9986942B2 (en) 2004-07-13 2018-06-05 Dexcom, Inc. Analyte sensor
US10918314B2 (en) 2004-07-13 2021-02-16 Dexcom, Inc. Analyte sensor
US8792953B2 (en) 2004-07-13 2014-07-29 Dexcom, Inc. Transcutaneous analyte sensor
US11045120B2 (en) 2004-07-13 2021-06-29 Dexcom, Inc. Analyte sensor
US11883164B2 (en) 2004-07-13 2024-01-30 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10827956B2 (en) 2004-07-13 2020-11-10 Dexcom, Inc. Analyte sensor
US10932700B2 (en) 2004-07-13 2021-03-02 Dexcom, Inc. Analyte sensor
US10813576B2 (en) 2004-07-13 2020-10-27 Dexcom, Inc. Analyte sensor
US11026605B1 (en) 2004-07-13 2021-06-08 Dexcom, Inc. Analyte sensor
US9414777B2 (en) 2004-07-13 2016-08-16 Dexcom, Inc. Transcutaneous analyte sensor
US7857760B2 (en) 2004-07-13 2010-12-28 Dexcom, Inc. Analyte sensor
US10709362B2 (en) 2004-07-13 2020-07-14 Dexcom, Inc. Analyte sensor
US10799158B2 (en) 2004-07-13 2020-10-13 Dexcom, Inc. Analyte sensor
US10980452B2 (en) 2004-07-13 2021-04-20 Dexcom, Inc. Analyte sensor
US10918315B2 (en) 2004-07-13 2021-02-16 Dexcom, Inc. Analyte sensor
US7783333B2 (en) 2004-07-13 2010-08-24 Dexcom, Inc. Transcutaneous medical device with variable stiffness
US10709363B2 (en) 2004-07-13 2020-07-14 Dexcom, Inc. Analyte sensor
US7885697B2 (en) 2004-07-13 2011-02-08 Dexcom, Inc. Transcutaneous analyte sensor
US10993641B2 (en) 2004-07-13 2021-05-04 Dexcom, Inc. Analyte sensor
US10993642B2 (en) 2004-07-13 2021-05-04 Dexcom, Inc. Analyte sensor
US10722152B2 (en) 2004-07-13 2020-07-28 Dexcom, Inc. Analyte sensor
US10617336B2 (en) 2005-03-10 2020-04-14 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10709364B2 (en) 2005-03-10 2020-07-14 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10716498B2 (en) 2005-03-10 2020-07-21 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10898114B2 (en) 2005-03-10 2021-01-26 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10743801B2 (en) 2005-03-10 2020-08-18 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10918317B2 (en) 2005-03-10 2021-02-16 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10925524B2 (en) 2005-03-10 2021-02-23 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US11000213B2 (en) 2005-03-10 2021-05-11 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10918316B2 (en) 2005-03-10 2021-02-16 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10610136B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10610135B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10918318B2 (en) 2005-03-10 2021-02-16 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10610137B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US11051726B2 (en) 2005-03-10 2021-07-06 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10856787B2 (en) 2005-03-10 2020-12-08 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US8112240B2 (en) 2005-04-29 2012-02-07 Abbott Diabetes Care Inc. Method and apparatus for providing leak detection in data monitoring and management systems
US8744546B2 (en) 2005-05-05 2014-06-03 Dexcom, Inc. Cellulosic-based resistance domain for an analyte sensor
US10300507B2 (en) 2005-05-05 2019-05-28 Dexcom, Inc. Cellulosic-based resistance domain for an analyte sensor
US10813577B2 (en) 2005-06-21 2020-10-27 Dexcom, Inc. Analyte sensor
US11363975B2 (en) 2005-11-01 2022-06-21 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9078607B2 (en) 2005-11-01 2015-07-14 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US11911151B1 (en) 2005-11-01 2024-02-27 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US10952652B2 (en) 2005-11-01 2021-03-23 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8915850B2 (en) 2005-11-01 2014-12-23 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9326716B2 (en) 2005-11-01 2016-05-03 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8920319B2 (en) 2005-11-01 2014-12-30 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US11399748B2 (en) 2005-11-01 2022-08-02 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US10231654B2 (en) 2005-11-01 2019-03-19 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US10201301B2 (en) 2005-11-01 2019-02-12 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US11272867B2 (en) 2005-11-01 2022-03-15 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US11103165B2 (en) 2005-11-01 2021-08-31 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US7766829B2 (en) 2005-11-04 2010-08-03 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US9323898B2 (en) 2005-11-04 2016-04-26 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US8585591B2 (en) 2005-11-04 2013-11-19 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US11538580B2 (en) 2005-11-04 2022-12-27 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US9669162B2 (en) 2005-11-04 2017-06-06 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US9380971B2 (en) 2006-03-31 2016-07-05 Abbott Diabetes Care Inc. Method and system for powering an electronic device
US8597575B2 (en) 2006-03-31 2013-12-03 Abbott Diabetes Care Inc. Analyte monitoring devices and methods therefor
US9743863B2 (en) 2006-03-31 2017-08-29 Abbott Diabetes Care Inc. Method and system for powering an electronic device
US9625413B2 (en) 2006-03-31 2017-04-18 Abbott Diabetes Care Inc. Analyte monitoring devices and methods therefor
US9039975B2 (en) 2006-03-31 2015-05-26 Abbott Diabetes Care Inc. Analyte monitoring devices and methods therefor
US8593109B2 (en) 2006-03-31 2013-11-26 Abbott Diabetes Care Inc. Method and system for powering an electronic device
US8933664B2 (en) 2006-03-31 2015-01-13 Abbott Diabetes Care Inc. Method and system for powering an electronic device
US8226891B2 (en) 2006-03-31 2012-07-24 Abbott Diabetes Care Inc. Analyte monitoring devices and methods therefor
US7920907B2 (en) 2006-06-07 2011-04-05 Abbott Diabetes Care Inc. Analyte monitoring system and method
US8911367B2 (en) 2006-10-04 2014-12-16 Dexcom, Inc. Analyte sensor
US20080086042A1 (en) * 2006-10-04 2008-04-10 Dexcom, Inc. Analyte sensor
US7775975B2 (en) 2006-10-04 2010-08-17 Dexcom, Inc. Analyte sensor
US10349873B2 (en) 2006-10-04 2019-07-16 Dexcom, Inc. Analyte sensor
US8275438B2 (en) 2006-10-04 2012-09-25 Dexcom, Inc. Analyte sensor
US8774886B2 (en) 2006-10-04 2014-07-08 Dexcom, Inc. Analyte sensor
US8562528B2 (en) 2006-10-04 2013-10-22 Dexcom, Inc. Analyte sensor
US8532730B2 (en) 2006-10-04 2013-09-10 Dexcom, Inc. Analyte sensor
US11399745B2 (en) 2006-10-04 2022-08-02 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8298142B2 (en) 2006-10-04 2012-10-30 Dexcom, Inc. Analyte sensor
US8478377B2 (en) 2006-10-04 2013-07-02 Dexcom, Inc. Analyte sensor
US11382539B2 (en) 2006-10-04 2022-07-12 Dexcom, Inc. Analyte sensor
US8364230B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US8449464B2 (en) 2006-10-04 2013-05-28 Dexcom, Inc. Analyte sensor
US8447376B2 (en) 2006-10-04 2013-05-21 Dexcom, Inc. Analyte sensor
US8425416B2 (en) 2006-10-04 2013-04-23 Dexcom, Inc. Analyte sensor
US8364231B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US9451908B2 (en) 2006-10-04 2016-09-27 Dexcom, Inc. Analyte sensor
US8930203B2 (en) 2007-02-18 2015-01-06 Abbott Diabetes Care Inc. Multi-function analyte test device and methods therefor
US8732188B2 (en) 2007-02-18 2014-05-20 Abbott Diabetes Care Inc. Method and system for providing contextual based medication dosage determination
US9095290B2 (en) 2007-03-01 2015-08-04 Abbott Diabetes Care Inc. Method and apparatus for providing rolling data in communication systems
US8123686B2 (en) 2007-03-01 2012-02-28 Abbott Diabetes Care Inc. Method and apparatus for providing rolling data in communication systems
US9801545B2 (en) 2007-03-01 2017-10-31 Abbott Diabetes Care Inc. Method and apparatus for providing rolling data in communication systems
US9035767B2 (en) 2007-05-08 2015-05-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8456301B2 (en) 2007-05-08 2013-06-04 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US10952611B2 (en) 2007-05-08 2021-03-23 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8593287B2 (en) 2007-05-08 2013-11-26 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8665091B2 (en) 2007-05-08 2014-03-04 Abbott Diabetes Care Inc. Method and device for determining elapsed sensor life
US9574914B2 (en) 2007-05-08 2017-02-21 Abbott Diabetes Care Inc. Method and device for determining elapsed sensor life
US8362904B2 (en) 2007-05-08 2013-01-29 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US9949678B2 (en) 2007-05-08 2018-04-24 Abbott Diabetes Care Inc. Method and device for determining elapsed sensor life
US7928850B2 (en) 2007-05-08 2011-04-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US11696684B2 (en) 2007-05-08 2023-07-11 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US10178954B2 (en) 2007-05-08 2019-01-15 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8149117B2 (en) 2007-05-08 2012-04-03 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US9000929B2 (en) 2007-05-08 2015-04-07 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US9314198B2 (en) 2007-05-08 2016-04-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US10653317B2 (en) 2007-05-08 2020-05-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8461985B2 (en) 2007-05-08 2013-06-11 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US9177456B2 (en) 2007-05-08 2015-11-03 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US9649057B2 (en) 2007-05-08 2017-05-16 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US10791928B2 (en) 2007-05-18 2020-10-06 Dexcom, Inc. Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise
US10403012B2 (en) 2007-06-08 2019-09-03 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US11373347B2 (en) 2007-06-08 2022-06-28 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US9741139B2 (en) 2007-06-08 2017-08-22 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US8562558B2 (en) 2007-06-08 2013-10-22 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US11744943B2 (en) 2007-10-09 2023-09-05 Dexcom, Inc. Integrated insulin delivery system with continuous glucose sensor
US11160926B1 (en) 2007-10-09 2021-11-02 Dexcom, Inc. Pre-connected analyte sensors
US10602968B2 (en) 2008-03-25 2020-03-31 Dexcom, Inc. Analyte sensor
US8396528B2 (en) 2008-03-25 2013-03-12 Dexcom, Inc. Analyte sensor
US11896374B2 (en) 2008-03-25 2024-02-13 Dexcom, Inc. Analyte sensor
US9173606B2 (en) 2008-03-28 2015-11-03 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US9173607B2 (en) 2008-03-28 2015-11-03 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US11730407B2 (en) 2008-03-28 2023-08-22 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US11147483B2 (en) 2008-03-28 2021-10-19 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US8954128B2 (en) 2008-03-28 2015-02-10 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US9572523B2 (en) 2008-03-28 2017-02-21 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US8583204B2 (en) 2008-03-28 2013-11-12 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US8682408B2 (en) 2008-03-28 2014-03-25 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US10143410B2 (en) 2008-03-28 2018-12-04 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US9566026B2 (en) 2008-03-28 2017-02-14 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US9549699B2 (en) 2008-03-28 2017-01-24 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US9693721B2 (en) 2008-03-28 2017-07-04 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US8900431B2 (en) 2008-08-27 2014-12-02 Edwards Lifesciences Corporation Analyte sensor
US9339222B2 (en) 2008-09-19 2016-05-17 Dexcom, Inc. Particle-containing membrane and particulate electrode for analyte sensors
US10561352B2 (en) 2008-09-19 2020-02-18 Dexcom, Inc. Particle-containing membrane and particulate electrode for analyte sensors
US8560039B2 (en) 2008-09-19 2013-10-15 Dexcom, Inc. Particle-containing membrane and particulate electrode for analyte sensors
US10028683B2 (en) 2008-09-19 2018-07-24 Dexcom, Inc. Particle-containing membrane and particulate electrode for analyte sensors
US10028684B2 (en) 2008-09-19 2018-07-24 Dexcom, Inc. Particle-containing membrane and particulate electrode for analyte sensors
US10980461B2 (en) 2008-11-07 2021-04-20 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US8473220B2 (en) 2009-01-29 2013-06-25 Abbott Diabetes Care Inc. Method and device for early signal attenuation detection using blood glucose measurements
US9066709B2 (en) 2009-01-29 2015-06-30 Abbott Diabetes Care Inc. Method and device for early signal attenuation detection using blood glucose measurements
US8676513B2 (en) 2009-01-29 2014-03-18 Abbott Diabetes Care Inc. Method and device for early signal attenuation detection using blood glucose measurements
US8103456B2 (en) 2009-01-29 2012-01-24 Abbott Diabetes Care Inc. Method and device for early signal attenuation detection using blood glucose measurements
US9226701B2 (en) 2009-04-28 2016-01-05 Abbott Diabetes Care Inc. Error detection in critical repeating data in a wireless sensor system
US11872370B2 (en) 2009-05-29 2024-01-16 Abbott Diabetes Care Inc. Medical device antenna systems having external antenna configurations
US11793936B2 (en) 2009-05-29 2023-10-24 Abbott Diabetes Care Inc. Medical device antenna systems having external antenna configurations
US9351677B2 (en) 2009-07-02 2016-05-31 Dexcom, Inc. Analyte sensor with increased reference capacity
US9517025B2 (en) 2009-07-02 2016-12-13 Dexcom, Inc. Analyte sensor with increased reference capacity
US9320466B2 (en) 2009-07-02 2016-04-26 Dexcom, Inc. Analyte sensor
US9763608B2 (en) 2009-07-02 2017-09-19 Dexcom, Inc. Analyte sensors and methods of manufacturing same
US8828201B2 (en) 2009-07-02 2014-09-09 Dexcom, Inc. Analyte sensors and methods of manufacturing same
US9907497B2 (en) 2009-07-02 2018-03-06 Dexcom, Inc. Analyte sensor
US10470691B2 (en) 2009-07-02 2019-11-12 Dexcom, Inc. Analyte sensor with increased reference capacity
US11559229B2 (en) 2009-07-02 2023-01-24 Dexcom, Inc. Analyte sensor
US9131885B2 (en) 2009-07-02 2015-09-15 Dexcom, Inc. Analyte sensors and methods of manufacturing same
US9237864B2 (en) 2009-07-02 2016-01-19 Dexcom, Inc. Analyte sensors and methods of manufacturing same
US10420494B2 (en) 2009-07-02 2019-09-24 Dexcom, Inc. Analyte sensor
US10429250B2 (en) 2009-08-31 2019-10-01 Abbott Diabetes Care, Inc. Analyte monitoring system and methods for managing power and noise
US11045147B2 (en) 2009-08-31 2021-06-29 Abbott Diabetes Care Inc. Analyte signal processing device and methods
US9968302B2 (en) 2009-08-31 2018-05-15 Abbott Diabetes Care Inc. Analyte signal processing device and methods
US8993331B2 (en) 2009-08-31 2015-03-31 Abbott Diabetes Care Inc. Analyte monitoring system and methods for managing power and noise
US11635332B2 (en) 2009-08-31 2023-04-25 Abbott Diabetes Care Inc. Analyte monitoring system and methods for managing power and noise
US9314195B2 (en) 2009-08-31 2016-04-19 Abbott Diabetes Care Inc. Analyte signal processing device and methods
US11150145B2 (en) 2009-08-31 2021-10-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods for managing power and noise
US9320461B2 (en) 2009-09-29 2016-04-26 Abbott Diabetes Care Inc. Method and apparatus for providing notification function in analyte monitoring systems
US10349874B2 (en) 2009-09-29 2019-07-16 Abbott Diabetes Care Inc. Method and apparatus for providing notification function in analyte monitoring systems
US9750439B2 (en) 2009-09-29 2017-09-05 Abbott Diabetes Care Inc. Method and apparatus for providing notification function in analyte monitoring systems
US9549692B2 (en) 2011-08-26 2017-01-24 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US9980669B2 (en) 2011-11-07 2018-05-29 Abbott Diabetes Care Inc. Analyte monitoring device and methods
US11612363B2 (en) 2012-09-17 2023-03-28 Abbott Diabetes Care Inc. Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems
US9968306B2 (en) 2012-09-17 2018-05-15 Abbott Diabetes Care Inc. Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems
US11706876B2 (en) 2017-10-24 2023-07-18 Dexcom, Inc. Pre-connected analyte sensors
US11382540B2 (en) 2017-10-24 2022-07-12 Dexcom, Inc. Pre-connected analyte sensors
US11350862B2 (en) 2017-10-24 2022-06-07 Dexcom, Inc. Pre-connected analyte sensors
US11331022B2 (en) 2017-10-24 2022-05-17 Dexcom, Inc. Pre-connected analyte sensors
US11918354B2 (en) 2019-12-31 2024-03-05 Dexcom, Inc. Particle-containing membrane and particulate electrode for analyte sensors

Also Published As

Publication number Publication date
US5593852A (en) 1997-01-14
US20070151869A1 (en) 2007-07-05
US20100059370A1 (en) 2010-03-11
US20100072063A1 (en) 2010-03-25
US20100030046A1 (en) 2010-02-04
US20070215491A1 (en) 2007-09-20
US20030134347A1 (en) 2003-07-17
US20100030050A1 (en) 2010-02-04
US6083710A (en) 2000-07-04
DE69533260T2 (en) 2005-08-04
US20050287620A1 (en) 2005-12-29
US20100059373A1 (en) 2010-03-11
US6162611A (en) 2000-12-19
US20100030051A1 (en) 2010-02-04
EP0778897A1 (en) 1997-06-18
US20100059371A1 (en) 2010-03-11
JP3679121B2 (en) 2005-08-03
AU3501695A (en) 1996-03-22
US20100030049A1 (en) 2010-02-04
US6881551B2 (en) 2005-04-19
US20100030044A1 (en) 2010-02-04
US20100121166A1 (en) 2010-05-13
US6121009A (en) 2000-09-19
US8588881B2 (en) 2013-11-19
DE69533260D1 (en) 2004-08-19
US7462264B2 (en) 2008-12-09
US20100072064A1 (en) 2010-03-25
US6514718B2 (en) 2003-02-04
US5965380A (en) 1999-10-12
US20100059372A1 (en) 2010-03-11
US20100051479A1 (en) 2010-03-04
US20100121165A1 (en) 2010-05-13
EP0778897B1 (en) 2004-07-14
US6284478B1 (en) 2001-09-04
US6329161B1 (en) 2001-12-11
WO1996006947A1 (en) 1996-03-07
US20060003398A1 (en) 2006-01-05
JPH10505421A (en) 1998-05-26
EP0778897A4 (en) 2000-03-22
US20020042090A1 (en) 2002-04-11
US20100030048A1 (en) 2010-02-04
ES2225845T3 (en) 2005-03-16
US8741590B2 (en) 2014-06-03
US20100030047A1 (en) 2010-02-04

Similar Documents

Publication Publication Date Title
US8414749B2 (en) Subcutaneous glucose electrode
US7462264B2 (en) Subcutaneous glucose electrode
Csoeregi et al. Design, characterization, and one-point in vivo calibration of a subcutaneously implanted glucose electrode

Legal Events

Date Code Title Description
STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION