CA2351734A1 - Generic integrated implantable potentiostat telemetry unit for electrochemical sensors - Google Patents
Generic integrated implantable potentiostat telemetry unit for electrochemical sensors Download PDFInfo
- Publication number
- CA2351734A1 CA2351734A1 CA002351734A CA2351734A CA2351734A1 CA 2351734 A1 CA2351734 A1 CA 2351734A1 CA 002351734 A CA002351734 A CA 002351734A CA 2351734 A CA2351734 A CA 2351734A CA 2351734 A1 CA2351734 A1 CA 2351734A1
- Authority
- CA
- Canada
- Prior art keywords
- electrode
- set forth
- electrochemical system
- circuit
- electrochemical
- 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
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L27/54—Biologically active materials, e.g. therapeutic substances
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
- A61B5/0031—Implanted circuitry
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/08—Materials for coatings
- A61L31/10—Macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L31/16—Biologically active materials, e.g. therapeutic substances
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
Abstract
A generic implantable puck (300) that can be used with a number of biosensor configurations. This generic implantable potentiostat telemetry unit (the puck) can also be part of a system to detect glucose concentrations. An electrochemical system partially implantable into a body for detecting gluco se concentrations therein is presented. The system comprises an electrochemical sensor (200), a transmitting puck including an electric circuit connected to the electrochemical sensor for transmitting a signal indicative of the gluco se concentrations in the body. There is at least one receiver (800) for receivi ng the signal from the transmitting puck and a computer system coupled to the a t least one receiver for processing the signal for patient diagnosis and treatment.
Description
-I-GENERIC INTEGRATED IMPLANTAIBLE POTENTIOSTAT
TELEMETRY UNIT FOR ELECTROCHEMICAL SENSORS
TECHNICAL FIELD
This invention relates to an electrochemical system partly implantable into a body for detecting glucose concentrations therein arid in a similar fashion, other elements, compounds or analytes.
BACKGROUND OF THE INVENTION
There is a need for an implantable generic device that can be used with different types of electrochemical sensors to facilitate real time monitoring during sensor development. Such a device would be an integrated potentiostat telemetry transmitting unit allowing researchers to test various biosensor configurations for 1o multiple possible uses. In an effort to regulate their glucose levels,,diabetic patients monitor their glycemia by repeatedly obtaining a sample of capillary blood by finger-pricking. Since these tests are frequent, painful and time consuming, diabetic patients resist performing an adequate number of these daily glucose measurements. This low compliance, plus the intrinsically discontinuous nature of the technique, leads to the 15 extensive pathology seen in diabetic patients. Thus, a great deal of research is being directed toward the development of new glucose sensors capable of replacing finger-pricking. Such glucose sensors are ideally implant~able in the patient, though pain free, as well as small, light-weight and capable of reliiable and continuous operation over extended periods of time. In addition it is desire;able that such sensors be a part of a system capable of continuous and real time procc;ssing of data from the sensors for diagnosis and patient treatment. It is also desirealble that the system be easily adaptable to use with various arnperometric glucose ;sensors without the need for redesigning the system for each new sensor. Such a system should be flexible, reliable, stable and easy to use in a telemetried system.
Previous telemetried systems require the development of designs taylored to a specific use and set of requirements. Typical telemetried systems utilize voltage-to-1o frequency conversion to increase frequency stability during frequency modulation of a carrier signal. This method expends objectionable amounts of power, limiting battery lifetime. The transmitted radio frequency carrier andl modulation thereof are continuous battery consuming processes. However, this requires the additional step of demodulation and additional signal shaping circuits in order to recover the data.
15 This requires additional power consumption and increased package size. In addition, data accuracy can be tainted by drift in the transmitter and the receiver components.
Typical telemetried systems also required dual battery configurations to provide power, thus adding to size.
It is desireable in a telemetried system to convert glucose sensor data to digital 2o values in vivo, in order to avoid conversion and modlulation errors. Once in digital format, a radio transmitter can utilize a serial data transmission protocol to a receiver thence directly to a computer for processing. An on-off keyed(OOK) asynchronous serial binary character data transmission method expends battery power only for the brief duration of each digital "one" bit. It expends zero power for each digital "zero"
25 bit. In addition to the glucose sensor data, an individual sensor identification code, and error preventive codes are included in each transmission, termed a "packet."
These data packets uniquely identify one of any number of sensors and provide a means to verify fidelity of the received data. Stored programs can allow direct conversion to glucose concentrations for immediate readout.
_3_ lVlonitoring glucose concentrations in diabetic patients is seen in U.S.
Patent No. 4,633,878 which relates to feedback controlled or "closed-loop" insulin pumps known also as "artificial pancreases". These devices provide a continuous glucose determination in the diabetic patient. Data is transnutted from a glucose sensor to a ~ microprocessor unit, which controls a pump for insulin, or glucose, infusion in order to maintain blood glucose levels within physiological range. In U.S. Patent No.
4,703,756 an electrochemical system includes a sensor module suitable for implantation in the body to monitor glucose and oxygen levels therein. In U.S.
Patent No. 5,914,026 an implautable sensor comprising a biocompatable electroconductive case which houses a measuring electrode, a reference electrode, an auxiliary electrode, and an electronic circuit for measuring the response of the measuring electrode where the measuring electrode, reference electrode and au:~iliary electrode are not in direct electrical contact with one another is provided.
International Application Number PCTlCTS9~6118724 discloses an 1 ~ electrochemical sensor system for measuring analyte concentrations in a fluid sample.
The invention is particularly useful for measuring aJnalytes such as glucose in a patient. An implantable glucose sensor includes a disc shaped body containing multiple anodes on opposing sides of the body. Electrodes are connected to a transmitter which transmits radio signals to an external receiver and computer where data is processed to yield glucose concentration figures.
SUMMARY OF THE INVENTION
This invention describes a generic implantable puck that can be used with a number of biosensor configurations. This generic i~nplantable potentiostat telemetry unit(the puck) can also be part of a system to detect glucose concentrations.
An electrochemical system partially implantable into a'body for detecting glucose concentrations therein is presented. The system comprises an electrochemical sensor, a transmitting puck including an electric circuit connected to the electrochemical sensor for transmitting a signal indicative of the glucose concentrations in the body.
There is at least one receiver for receiving the signal from the transmitting puck and a AMENDED SHEET
-3a-computer system coupled to the at least one receiver for processing the signal for patient diagnosis and treatment.
EXPLANATION OF THE DRAWINGS
Referring now to the drawings wherein like elements and features are numbered alike in the several figures:
Fig. 1 is a schematic representation of the electrochemical system of the present invention as it is generally comprised of an ~~Iectrochemical sensor, a AMENDED SHEET
transmitting puck, at least one receiver and a computer system;
Fig. 2 is a schematic representation of the electric circuit of the transmitting puck;
Fig. 3 is a first schematic representation of the potentiostat circuit of the transmitting puck;
Fig. 4 is a schematic representation of the electric filter circuit of the electric circuit of the transmitting puck;
Fig. 5 is a second schematic representation of the potentiostat circuit of the transmitting puck.
io DESCRIPTION OF THE PREFERRED EMBODIIVJfENTS
A description of the preferred embodiment oiPthe present invention will now be had, by way of exemplification and not limitation, with reference to Figs.
l, 2, 3, 4 and 5 of the drawing. Fig. 1 is a schematic represenl;ation of the electrochemical system 100 of the present invention as it is generally comprised of an electrochemical 15 sensor 200, including at least one electrode 202, 204, 206 connected to a transmitting puck 300. The electrochemical sensor 200 and the transmitting puck 300 are implantable into a body. The transmitting puck 300 is operative to generate a sensor current, IS, through the electrochemical sensor 200 which is proportional to the glucose concentrations in the body. The transmitting puck 300 thence transmits a 2o serial digital signal, VT, which is based upon the sensor current, IS, and is indicative of the glucose concentrations. The electrochemical system 100 further includes at least one receiver 800 for receiving the signal, VT. The at least one receiver 800 may comprise a portable receiver 800 worn by a patient implanted with the electrochemical sensor 200 and the transmitting puck 300. Such a portable receiver 25 800 would contain an onboard microprocessor having the capability of providing a continuous or, if desired, periodic readout of the patients glucose concentration, as well as the ability to retain such information in memory and to warn the patient when glucose concentrations are too high or too Iow. The. at least one receiver 800 may also comprise a larger office version connected to a computer system 1000 for processing 3o the serial digital signal, VT, for patient diagnosis and treatment.
Reference will now be had to Fig. 2. Therein depicted is a schematic representation of the transmitting puck 300 including; an electric circuit connected to the electrochemical sensor 200. The electrochemical sensor 200 includes at least one electrode, 202, 204, 206. The first electrode 202 of the at least one electrode is commonly referred to as the auxiliary electrode and provides a driving voltage to the electrochemical sensor 200. The second electrode 204 is commonly referred to as the reference electrode and allows for compensation of circuit and solution losses. The third electrode 206 is commonly referred to as the w~~rking electrode wherein the electrochemical reaction occurs.
The electric circuit of the transmitting puck 300 includes a power supply 680 for energizing the elements of the electric circuit. A potentiostat circuit 400 is connected to at the least one electrode 202, 204, 206 of the electrochemical sensor 200. The potentiostat circuit 400 is further connected to a first digital-to-analog converter 610, a second digital-to-analog converter Ei20, to a microprocessor 600 and to at least one filter circuit 500. The first digital-to-analog converter 610 provides an excitation voltage, V;, to the electrochemical sensor :200. The nature of the excitation voltage, V;, is controlled by the microprocessor G00 through the first analog-to-digital converter 610 and may, for example, be a constant voltage or a ramped voltage or a sinusoidal voltage or a sawtooth voltage signal. Such cyclic voltammetry allows for the characterization and testing of the electrochemical sensor 200. The second digital-to-analog converter 620 provides an adjustable reference voltage, V~, to the potentiostat circuit 400 in order to allow for bipolar functioning of the electrochemical sensor 200. The microprocessor 600 is directly comzected to the potentiostat circuit 400 to provide gain adjustment of the potentiostat circuit 400 and also to the at least one filter circuit 500 to provide adjustments of filter characteristics.
Continuing in Fig. 2, the potentiostat circuit 400 is operative to generate the sensor current, IS, through the electrochemical sensor 200 and to thence convert IS into an output voltage, Vo, proportional to glucose concentrations. The output voltage, Vo, is then passed through the at least one filter circuit 5~00 for filtering of unwanted WO 00/30532 PCT/gJS99/27543 signals. A filtered signal, Vf, is then converted into digital form by an analog-to-digital converter 640 and thence conveyed to the microprocessor 600, whereupon a serial data signal, VT, is conveyed to the transmitter '700.
Reference will now be had to Fig. 3. Therein depicted is a schematic representation of the potentiostaf circuit 400 of the transmitting puck 300.
The potentiostat circuit 400 comprises a first operational amplifier 402 having a first output terminal 404 connected to a first electrode 202 of the at least one electrode 202, 204, 206. The first operational amplifier 402 also includes a first input terminal 406 connected to a single pole-double throw first switch 414, and a second input to terminal 408. The first operational amplifier 402 includes a first feedback circuit 410 connected firstly to a selected one electrode of the at least one electrode 202, 204, 206 and secondly to the second input terminal 408 and a single pole-single throw second switch 416. The first and second switches 414, 416 are thrown simultaneously and controlled by the microprocessor 600 by way of signal path 660. The first feedback ~5 circuit 410 comprises a direct connection between the selected one electrode and the second input terminal 408 and a first resistor 412, R.,, between the second input terminal 408 and the second switch 416. The direct connection between the second input terminal 408 and the selected one electrode may be of one of three configurations as designated by the reference numerals 410a, 410b and 410c. In a 2o first configuration 410a, the first feedback circuit 410 is connected to the auxiliary electrode 202, thus providing a driving voltage at the auxiliary electrode 202. In a second configuration 4IOb, the first feedback circuit 410 is connected to the reference electrode 204, thus providing compensation far circuit and solution losses. In a third configuration 410c, the first feedback circuit 410 is connected to the working 25 electrode 206. The potentiostat circuit 400 further comprises a second operational amplifier 418 having a third input terminal 420 connected to a third electrode 206 of the at least one electrode 202, 204, 206, a fourth input terminal 422 connected to the second digital-to-analog converter 620 of the first at least one signal converter, a second output terminal 424 and a second feedback circuit 426 connected to the second WO 00/30532 PCT/US99/~7543 output terminal 424, the third input terminal 420 and the microprocessor 600.
The second feedback circuit 426 comprises a second resi:>tor, R2, which may be a digital resistor controlled by the microprocessor 600.
Continuing in Fig. 3, the potentiostat circuit 400 is connected to the first digital-to-analog converter 610 and a second digital-to-analog converter 620 which are biased by a first reference voltage,Vr, 630. The first digital-to-analog converter 610 is connected to the microprocessor 600 and operative thereby to accept as input therefrom a digital signal. The first digital-to-analog converter 610 thereby provides as output an analog excitation voltage, V;, at node 67.2 which may be, for example, a constant voltage or a ramped voltage or a sawtooth voltage or a sinusoidal voltage.
The second digital-to-analog converter 620 is connected to the microprocessor and operative thereby to accept as input therefrom a digital signal. The second digital-to-analog converter 620 thereby provides as output a second reference voltage, Vg, at the fourth input terminal 422 thus allowing for the bipolar functioning of the electrochemical sensor 200.
The function of the potentiostat circuit 400 may be accomplished in one of several modes, i.e., by the aforementioned selection of the configuration of the first feedback circuit 410 coupled with the simultaneous switching of the first switch 414 and the second switch 416 to a first position, "A"(as shown in Fig. 3), or a second 2o position, "B." As an example, if the first switch 414E and the second switch 416 are in position "A" and the first feedback circuit 410 is connected to the auxiliary electrode 202, then the potentiostat circuit 400 functions as a l:wo-wire potentiostat.
If the first switch 414 and the second switch 416 are in position "A" and the first feedback circuit 410 is connected to the reference electrode 2t74, then the potentiostat circuit 400 functions as a three-wire potentiostat. If the fir:>t switch 414 and the second switch 416 are in position "B" and the first feedback circuit 410 is connected to the working electrode 206, then the potentiostat circuit 400 functions as a two-wire galvanostat. It will be appreciated that when functioning as such a two-wire _g_ galvanostat the third ixrput texminal 420 is disconnected from the worldng electrode 206.
Reference will now be had to Fig. 4. Therein depicted is a generalized schematic representation of the filter circuit 500. The filter circuit 500 is compxised of a third operational amplifier 502 having a third output terminal 504, a fifth input terminal 506 and a sixth input terminal 508. The third operational amplifier further includes a third feedback circuit 510 connected to the third output terminal 504 and the fifth. input terminal 506. The third operational. amplifier 502 includes a fourth feedback circuit S 10a. Therein, the sixth input terminal 508 is connected to a third reference voltage 520 by way of a first capacitor 5 i6. A third resistor 512 and a fourth resistor 514 are connected to the sixth input tE:rminal 508. The third output terminal 504 is connected to a node point 522 between the third resistor 512 and fourth resistor 514 by way of a second capacitor 518.. Such a filter circuit 500 is a second order filter and its filtering capabilities are established by a judicious selection of the values of the third resistor 512, fourth resistor S I4, first capacitor 516 and second capacitor 5I8. In addition the operative natt,~re of the filter circuit 500 may be enhanced by placing the filter circuit 500 either in sfries or parallel with the same or like filters. Such filters may also be controlled by tree microprocessor 600.
The filter circuit 500 is thus operative to accept as input thereto, the output voltage, Vo, of the potentiostat circuit 400 and provide as output therefrom an appropriately filtered signal, Vf. The filtered signal, V~ is indicative of th.e glucose concentrations and is conveyed to a first anaolD to-digital converter 640 v~rhere it is converted into a digital form and thence conveyed to the microprocessor 600 whereupon a serial digital signal, VT, is conveyed to the transmitter 700. The transmitter 700 then in turn conveys VT to the aforesaid at least one receiver 800.
Reference will now be had to Fig. 5. Therein depicted is a schematic representation of an alternate to the potentiostat circuit 400 of Fig. 3 connected to a two electrode electrochemical sensor 200. The positive terminal of a battery 604 is connected to a third switch 602 and the negative terminal thereof is connected to electrical ground 606: The power supply 600f is thereby operative to energize the first operational amplifier 402 and the second operations amplifier 418 with the supply AMENDED SHEET
_g_ voltage, +V~ when the third switch 602 is in the closed position(as shown). A
voltage converter 608 supplies =~~ to the second operational amplifier 418. It is contemplated that +/ V~ is approximately +/-3.7 volts. When the third switch 602 is in the open position, the first operational amplifier 402 and second operational amplifier 418, are deenergized. The first input terminal 408 of the first operational amplifier 402 is an inverting terminal and the second input terminal 406 is a non-inverting terminal. The first feedback circuit 410 is a direct connection between the first output terminaz 404 and the fast input terminal 408. A potentiometer 438 comprises a voltage divider 436 connected to a fourth reference voltage 442, held at a i 0 potential of +VIi volts, and a fifth reference voltage 440, held at electrical ground.
The voltage divider 436 is also connected to the non-inverting terminal 406.
Thus, the first operational amplifier 402 is operative to maintain the first output terminal 404, and thus the first electrode 202 of the electrochemical sensor 200, at the substantially constant excitation voltage, Vi. In particular, by adjusting the voltage divider 436, the excitation voltage, V;, may be varied from 0 volts to VIl volts. Thus, the first operational amplifier 402 acts, for example;, in a fashion that is commonly referred to as a voltage follower. It is contemplated that Vrl is approximately +1.2 volts and the potentiometer 436 is adjusted so as to make excitation voltage, V;, approximately +0.7 volts to provide glucose concentration related data.
Continuing in Fig. 5, the third input terminal 420 of the second operational axnpli_fier 4I8 is an inverting terminal and the fourth input terminal 422 is a non-inverting terminal connected to electrical ground 4f.4. A third switch 446 is a two position switch that connects the second electrode 206 of the electrochemical sensor 200 to the third input terminal 420 and turns the electrochemical sensor 200 On or C)ff. The voltage at the second electrode 206, V~" varies with the glucose concentration thus resulting in a voltage drop, dV == Vi - Vw, across the first electrode 202 and the second electrode 206. The voltage drop, ~V coupled with the impedance of the glucose, Zg, generate the aforesaid sensor current, Is. The second feedback circuit 426 comprises a capacitor 426a in parallel v~~ith a resistor 426b. The resistor 426b acts to set the amplifier gain and in conjuuction with the capacitor 426a, acts as a low pass filter in order to dampen high frequency noise. An offset current AMENDED SHEET
compensation circuit 428 comprises a variable resistor 428a connected to a fourth switch 432 and the sixth reference voltage 430 held at a potential of Vrz volts. The fourth switch 432 is a two position switch that engal;es or disengages the offset current compensation circuit 428. With the fourth switch 432 in the closed position(as shown) and by adjusting the variable resistor 428a, an offset bias current, IB, is established at third input terminal 420. Continuing in Fig. 5, a fifth switch 434 is a two position switch that turns an optocoupler 900 On or Off. The second operational amplifier 418 is thereby operative to convert the sensor current, IS + Ie, into an output voltage, Va, at the second output terminal 424 and thus acts, for io example, in a fashion that is referred to as a transim~pedence amplifier.
Continuing in Fig. 5, the second operational amplifier 4I8 is connected to the optocoupler 900 by way of the fifth switch 434. The: optocoupler 900 comprises a first optical device 902, such as a light emitting diode. 'fhe first optical device 902 is optically coupled to a second optical device 904 such as a photocell, a photosensitive 15 resistor or a phototransistor. The cathode of the first optical device 902 is connected to the fifth switch 434 and the anode is connected to electrical ground 906.
As such, when the output voltage, Vo, at the second output terminal 424 or the fifth switch 434 is negative, the first optical device 902 emits an optical signal 908 to which the second optical device 904 is responsive. The operative nature of the first optical 2o device 902 is such that the optical signal 908 emitted therefrom is consistent with the output voltage, Vo, at the second output terminal 424 when the third switch 434 is closed{as shown). The optocoupler 900 is connected to the microprocessor 600 via the second optical device 904. However, the nature: of the coupling of the first optical device 902 and the second optical device 904 via the optical signal 908 is such as to 25 provide electrical isolation of the microprocessor 600 from the potentiostat circuit 400. As a result of the aforesaid responsivity of the second optical device 904 to the optical signal 908, a changing resistance, 0R, is developed across the second optical device 904. The output, DR, of the second optical device 904 is conveyed to the microprocessor 600 for conversion to a digital serial data signal, VT, which is then 3o conveyed to the transmitter 700. The transmitter 700 is operative to transmit a digital serial data signal VT, indicative of the changing resiistance, DR, in the optocoupler 900 WO 00/30532 PCT/US99i27543 to the at least one receiver 800. VT is then conveyed to the computer system 1000 for processing thereof by appropriate controlling software, e.g., screen readout and data logging to a storage disk. It is contemplated that the aforesaid transmittal of the serial data signal, VT, is by a radio frequency electromagnetic wave at a carrier frequency of about 303.85 Mhz. In particular, VT is in the nature of digital counts whereby digital count = 10 ~R ohms. The serial data signal, VT, includes, for example, the transmitter serial number, the resistance value in the number of digital counts and a timing scheme governing data transmission rates, data logging rates and received data error prevention information. VT is conveyed from t:he at least one receiver 800 to the 1o computer system 1000 whereat actual glucose conce:ntratifln values are displayed on a computer screen for immediate readout provided by real time conversion of digital counts based upon earlier calibration, curve fitting and tables. The computer system 1000 is operative to initialize the status of the transrr~itting puck 300, deactivate the transmitting puck 300, error check VT, process VT for display to a screen, log VT to a 15 disk file and commands the transmitting puck 300 to~ set transmission intervals over a range from 5 seconds to 10 minutes.
Thus it will be appreciated that the electrochemical system provides real time continuous and reliable data related to the glucose concentrations in a body.
The microprocessor 600 controls the status of the potentiostat circuit 400 by controlling 2o the first and second switches 414, 416, controls the bias voltage, Vg, the excitation voltage, V;, establishes alarm levels and directs the transmission of VT. The transmitter 700, including a near field receiver, accepts as input from the microprocessor 600 the serial data value, VT, in a serial data protocol and by digital signal processing converts VT into a binary stream to be conveyed to the at least one 25 receiver 800. The at least one receiver 800 accepts as input the binary stream and recovers therefrom the serial data signal, VT, for conveyance to either the computer system 1000 for processing thereof or immediate di:>play to a patient. The at least one receiver 800 includes a near field transmitter operative to initialize the transmitting puck 300 and place the transmitting puck 300 in standby mode.
While preferred embodiments have been shown and described, various modifications and substitutions may be made thereto without departing from the true spirit and scope of the invention. Accordingly, it is understood that the present invention has been described by way of illustrations and not limitation.
What is claimed is:
TELEMETRY UNIT FOR ELECTROCHEMICAL SENSORS
TECHNICAL FIELD
This invention relates to an electrochemical system partly implantable into a body for detecting glucose concentrations therein arid in a similar fashion, other elements, compounds or analytes.
BACKGROUND OF THE INVENTION
There is a need for an implantable generic device that can be used with different types of electrochemical sensors to facilitate real time monitoring during sensor development. Such a device would be an integrated potentiostat telemetry transmitting unit allowing researchers to test various biosensor configurations for 1o multiple possible uses. In an effort to regulate their glucose levels,,diabetic patients monitor their glycemia by repeatedly obtaining a sample of capillary blood by finger-pricking. Since these tests are frequent, painful and time consuming, diabetic patients resist performing an adequate number of these daily glucose measurements. This low compliance, plus the intrinsically discontinuous nature of the technique, leads to the 15 extensive pathology seen in diabetic patients. Thus, a great deal of research is being directed toward the development of new glucose sensors capable of replacing finger-pricking. Such glucose sensors are ideally implant~able in the patient, though pain free, as well as small, light-weight and capable of reliiable and continuous operation over extended periods of time. In addition it is desire;able that such sensors be a part of a system capable of continuous and real time procc;ssing of data from the sensors for diagnosis and patient treatment. It is also desirealble that the system be easily adaptable to use with various arnperometric glucose ;sensors without the need for redesigning the system for each new sensor. Such a system should be flexible, reliable, stable and easy to use in a telemetried system.
Previous telemetried systems require the development of designs taylored to a specific use and set of requirements. Typical telemetried systems utilize voltage-to-1o frequency conversion to increase frequency stability during frequency modulation of a carrier signal. This method expends objectionable amounts of power, limiting battery lifetime. The transmitted radio frequency carrier andl modulation thereof are continuous battery consuming processes. However, this requires the additional step of demodulation and additional signal shaping circuits in order to recover the data.
15 This requires additional power consumption and increased package size. In addition, data accuracy can be tainted by drift in the transmitter and the receiver components.
Typical telemetried systems also required dual battery configurations to provide power, thus adding to size.
It is desireable in a telemetried system to convert glucose sensor data to digital 2o values in vivo, in order to avoid conversion and modlulation errors. Once in digital format, a radio transmitter can utilize a serial data transmission protocol to a receiver thence directly to a computer for processing. An on-off keyed(OOK) asynchronous serial binary character data transmission method expends battery power only for the brief duration of each digital "one" bit. It expends zero power for each digital "zero"
25 bit. In addition to the glucose sensor data, an individual sensor identification code, and error preventive codes are included in each transmission, termed a "packet."
These data packets uniquely identify one of any number of sensors and provide a means to verify fidelity of the received data. Stored programs can allow direct conversion to glucose concentrations for immediate readout.
_3_ lVlonitoring glucose concentrations in diabetic patients is seen in U.S.
Patent No. 4,633,878 which relates to feedback controlled or "closed-loop" insulin pumps known also as "artificial pancreases". These devices provide a continuous glucose determination in the diabetic patient. Data is transnutted from a glucose sensor to a ~ microprocessor unit, which controls a pump for insulin, or glucose, infusion in order to maintain blood glucose levels within physiological range. In U.S. Patent No.
4,703,756 an electrochemical system includes a sensor module suitable for implantation in the body to monitor glucose and oxygen levels therein. In U.S.
Patent No. 5,914,026 an implautable sensor comprising a biocompatable electroconductive case which houses a measuring electrode, a reference electrode, an auxiliary electrode, and an electronic circuit for measuring the response of the measuring electrode where the measuring electrode, reference electrode and au:~iliary electrode are not in direct electrical contact with one another is provided.
International Application Number PCTlCTS9~6118724 discloses an 1 ~ electrochemical sensor system for measuring analyte concentrations in a fluid sample.
The invention is particularly useful for measuring aJnalytes such as glucose in a patient. An implantable glucose sensor includes a disc shaped body containing multiple anodes on opposing sides of the body. Electrodes are connected to a transmitter which transmits radio signals to an external receiver and computer where data is processed to yield glucose concentration figures.
SUMMARY OF THE INVENTION
This invention describes a generic implantable puck that can be used with a number of biosensor configurations. This generic i~nplantable potentiostat telemetry unit(the puck) can also be part of a system to detect glucose concentrations.
An electrochemical system partially implantable into a'body for detecting glucose concentrations therein is presented. The system comprises an electrochemical sensor, a transmitting puck including an electric circuit connected to the electrochemical sensor for transmitting a signal indicative of the glucose concentrations in the body.
There is at least one receiver for receiving the signal from the transmitting puck and a AMENDED SHEET
-3a-computer system coupled to the at least one receiver for processing the signal for patient diagnosis and treatment.
EXPLANATION OF THE DRAWINGS
Referring now to the drawings wherein like elements and features are numbered alike in the several figures:
Fig. 1 is a schematic representation of the electrochemical system of the present invention as it is generally comprised of an ~~Iectrochemical sensor, a AMENDED SHEET
transmitting puck, at least one receiver and a computer system;
Fig. 2 is a schematic representation of the electric circuit of the transmitting puck;
Fig. 3 is a first schematic representation of the potentiostat circuit of the transmitting puck;
Fig. 4 is a schematic representation of the electric filter circuit of the electric circuit of the transmitting puck;
Fig. 5 is a second schematic representation of the potentiostat circuit of the transmitting puck.
io DESCRIPTION OF THE PREFERRED EMBODIIVJfENTS
A description of the preferred embodiment oiPthe present invention will now be had, by way of exemplification and not limitation, with reference to Figs.
l, 2, 3, 4 and 5 of the drawing. Fig. 1 is a schematic represenl;ation of the electrochemical system 100 of the present invention as it is generally comprised of an electrochemical 15 sensor 200, including at least one electrode 202, 204, 206 connected to a transmitting puck 300. The electrochemical sensor 200 and the transmitting puck 300 are implantable into a body. The transmitting puck 300 is operative to generate a sensor current, IS, through the electrochemical sensor 200 which is proportional to the glucose concentrations in the body. The transmitting puck 300 thence transmits a 2o serial digital signal, VT, which is based upon the sensor current, IS, and is indicative of the glucose concentrations. The electrochemical system 100 further includes at least one receiver 800 for receiving the signal, VT. The at least one receiver 800 may comprise a portable receiver 800 worn by a patient implanted with the electrochemical sensor 200 and the transmitting puck 300. Such a portable receiver 25 800 would contain an onboard microprocessor having the capability of providing a continuous or, if desired, periodic readout of the patients glucose concentration, as well as the ability to retain such information in memory and to warn the patient when glucose concentrations are too high or too Iow. The. at least one receiver 800 may also comprise a larger office version connected to a computer system 1000 for processing 3o the serial digital signal, VT, for patient diagnosis and treatment.
Reference will now be had to Fig. 2. Therein depicted is a schematic representation of the transmitting puck 300 including; an electric circuit connected to the electrochemical sensor 200. The electrochemical sensor 200 includes at least one electrode, 202, 204, 206. The first electrode 202 of the at least one electrode is commonly referred to as the auxiliary electrode and provides a driving voltage to the electrochemical sensor 200. The second electrode 204 is commonly referred to as the reference electrode and allows for compensation of circuit and solution losses. The third electrode 206 is commonly referred to as the w~~rking electrode wherein the electrochemical reaction occurs.
The electric circuit of the transmitting puck 300 includes a power supply 680 for energizing the elements of the electric circuit. A potentiostat circuit 400 is connected to at the least one electrode 202, 204, 206 of the electrochemical sensor 200. The potentiostat circuit 400 is further connected to a first digital-to-analog converter 610, a second digital-to-analog converter Ei20, to a microprocessor 600 and to at least one filter circuit 500. The first digital-to-analog converter 610 provides an excitation voltage, V;, to the electrochemical sensor :200. The nature of the excitation voltage, V;, is controlled by the microprocessor G00 through the first analog-to-digital converter 610 and may, for example, be a constant voltage or a ramped voltage or a sinusoidal voltage or a sawtooth voltage signal. Such cyclic voltammetry allows for the characterization and testing of the electrochemical sensor 200. The second digital-to-analog converter 620 provides an adjustable reference voltage, V~, to the potentiostat circuit 400 in order to allow for bipolar functioning of the electrochemical sensor 200. The microprocessor 600 is directly comzected to the potentiostat circuit 400 to provide gain adjustment of the potentiostat circuit 400 and also to the at least one filter circuit 500 to provide adjustments of filter characteristics.
Continuing in Fig. 2, the potentiostat circuit 400 is operative to generate the sensor current, IS, through the electrochemical sensor 200 and to thence convert IS into an output voltage, Vo, proportional to glucose concentrations. The output voltage, Vo, is then passed through the at least one filter circuit 5~00 for filtering of unwanted WO 00/30532 PCT/gJS99/27543 signals. A filtered signal, Vf, is then converted into digital form by an analog-to-digital converter 640 and thence conveyed to the microprocessor 600, whereupon a serial data signal, VT, is conveyed to the transmitter '700.
Reference will now be had to Fig. 3. Therein depicted is a schematic representation of the potentiostaf circuit 400 of the transmitting puck 300.
The potentiostat circuit 400 comprises a first operational amplifier 402 having a first output terminal 404 connected to a first electrode 202 of the at least one electrode 202, 204, 206. The first operational amplifier 402 also includes a first input terminal 406 connected to a single pole-double throw first switch 414, and a second input to terminal 408. The first operational amplifier 402 includes a first feedback circuit 410 connected firstly to a selected one electrode of the at least one electrode 202, 204, 206 and secondly to the second input terminal 408 and a single pole-single throw second switch 416. The first and second switches 414, 416 are thrown simultaneously and controlled by the microprocessor 600 by way of signal path 660. The first feedback ~5 circuit 410 comprises a direct connection between the selected one electrode and the second input terminal 408 and a first resistor 412, R.,, between the second input terminal 408 and the second switch 416. The direct connection between the second input terminal 408 and the selected one electrode may be of one of three configurations as designated by the reference numerals 410a, 410b and 410c. In a 2o first configuration 410a, the first feedback circuit 410 is connected to the auxiliary electrode 202, thus providing a driving voltage at the auxiliary electrode 202. In a second configuration 4IOb, the first feedback circuit 410 is connected to the reference electrode 204, thus providing compensation far circuit and solution losses. In a third configuration 410c, the first feedback circuit 410 is connected to the working 25 electrode 206. The potentiostat circuit 400 further comprises a second operational amplifier 418 having a third input terminal 420 connected to a third electrode 206 of the at least one electrode 202, 204, 206, a fourth input terminal 422 connected to the second digital-to-analog converter 620 of the first at least one signal converter, a second output terminal 424 and a second feedback circuit 426 connected to the second WO 00/30532 PCT/US99/~7543 output terminal 424, the third input terminal 420 and the microprocessor 600.
The second feedback circuit 426 comprises a second resi:>tor, R2, which may be a digital resistor controlled by the microprocessor 600.
Continuing in Fig. 3, the potentiostat circuit 400 is connected to the first digital-to-analog converter 610 and a second digital-to-analog converter 620 which are biased by a first reference voltage,Vr, 630. The first digital-to-analog converter 610 is connected to the microprocessor 600 and operative thereby to accept as input therefrom a digital signal. The first digital-to-analog converter 610 thereby provides as output an analog excitation voltage, V;, at node 67.2 which may be, for example, a constant voltage or a ramped voltage or a sawtooth voltage or a sinusoidal voltage.
The second digital-to-analog converter 620 is connected to the microprocessor and operative thereby to accept as input therefrom a digital signal. The second digital-to-analog converter 620 thereby provides as output a second reference voltage, Vg, at the fourth input terminal 422 thus allowing for the bipolar functioning of the electrochemical sensor 200.
The function of the potentiostat circuit 400 may be accomplished in one of several modes, i.e., by the aforementioned selection of the configuration of the first feedback circuit 410 coupled with the simultaneous switching of the first switch 414 and the second switch 416 to a first position, "A"(as shown in Fig. 3), or a second 2o position, "B." As an example, if the first switch 414E and the second switch 416 are in position "A" and the first feedback circuit 410 is connected to the auxiliary electrode 202, then the potentiostat circuit 400 functions as a l:wo-wire potentiostat.
If the first switch 414 and the second switch 416 are in position "A" and the first feedback circuit 410 is connected to the reference electrode 2t74, then the potentiostat circuit 400 functions as a three-wire potentiostat. If the fir:>t switch 414 and the second switch 416 are in position "B" and the first feedback circuit 410 is connected to the working electrode 206, then the potentiostat circuit 400 functions as a two-wire galvanostat. It will be appreciated that when functioning as such a two-wire _g_ galvanostat the third ixrput texminal 420 is disconnected from the worldng electrode 206.
Reference will now be had to Fig. 4. Therein depicted is a generalized schematic representation of the filter circuit 500. The filter circuit 500 is compxised of a third operational amplifier 502 having a third output terminal 504, a fifth input terminal 506 and a sixth input terminal 508. The third operational amplifier further includes a third feedback circuit 510 connected to the third output terminal 504 and the fifth. input terminal 506. The third operational. amplifier 502 includes a fourth feedback circuit S 10a. Therein, the sixth input terminal 508 is connected to a third reference voltage 520 by way of a first capacitor 5 i6. A third resistor 512 and a fourth resistor 514 are connected to the sixth input tE:rminal 508. The third output terminal 504 is connected to a node point 522 between the third resistor 512 and fourth resistor 514 by way of a second capacitor 518.. Such a filter circuit 500 is a second order filter and its filtering capabilities are established by a judicious selection of the values of the third resistor 512, fourth resistor S I4, first capacitor 516 and second capacitor 5I8. In addition the operative natt,~re of the filter circuit 500 may be enhanced by placing the filter circuit 500 either in sfries or parallel with the same or like filters. Such filters may also be controlled by tree microprocessor 600.
The filter circuit 500 is thus operative to accept as input thereto, the output voltage, Vo, of the potentiostat circuit 400 and provide as output therefrom an appropriately filtered signal, Vf. The filtered signal, V~ is indicative of th.e glucose concentrations and is conveyed to a first anaolD to-digital converter 640 v~rhere it is converted into a digital form and thence conveyed to the microprocessor 600 whereupon a serial digital signal, VT, is conveyed to the transmitter 700. The transmitter 700 then in turn conveys VT to the aforesaid at least one receiver 800.
Reference will now be had to Fig. 5. Therein depicted is a schematic representation of an alternate to the potentiostat circuit 400 of Fig. 3 connected to a two electrode electrochemical sensor 200. The positive terminal of a battery 604 is connected to a third switch 602 and the negative terminal thereof is connected to electrical ground 606: The power supply 600f is thereby operative to energize the first operational amplifier 402 and the second operations amplifier 418 with the supply AMENDED SHEET
_g_ voltage, +V~ when the third switch 602 is in the closed position(as shown). A
voltage converter 608 supplies =~~ to the second operational amplifier 418. It is contemplated that +/ V~ is approximately +/-3.7 volts. When the third switch 602 is in the open position, the first operational amplifier 402 and second operational amplifier 418, are deenergized. The first input terminal 408 of the first operational amplifier 402 is an inverting terminal and the second input terminal 406 is a non-inverting terminal. The first feedback circuit 410 is a direct connection between the first output terminaz 404 and the fast input terminal 408. A potentiometer 438 comprises a voltage divider 436 connected to a fourth reference voltage 442, held at a i 0 potential of +VIi volts, and a fifth reference voltage 440, held at electrical ground.
The voltage divider 436 is also connected to the non-inverting terminal 406.
Thus, the first operational amplifier 402 is operative to maintain the first output terminal 404, and thus the first electrode 202 of the electrochemical sensor 200, at the substantially constant excitation voltage, Vi. In particular, by adjusting the voltage divider 436, the excitation voltage, V;, may be varied from 0 volts to VIl volts. Thus, the first operational amplifier 402 acts, for example;, in a fashion that is commonly referred to as a voltage follower. It is contemplated that Vrl is approximately +1.2 volts and the potentiometer 436 is adjusted so as to make excitation voltage, V;, approximately +0.7 volts to provide glucose concentration related data.
Continuing in Fig. 5, the third input terminal 420 of the second operational axnpli_fier 4I8 is an inverting terminal and the fourth input terminal 422 is a non-inverting terminal connected to electrical ground 4f.4. A third switch 446 is a two position switch that connects the second electrode 206 of the electrochemical sensor 200 to the third input terminal 420 and turns the electrochemical sensor 200 On or C)ff. The voltage at the second electrode 206, V~" varies with the glucose concentration thus resulting in a voltage drop, dV == Vi - Vw, across the first electrode 202 and the second electrode 206. The voltage drop, ~V coupled with the impedance of the glucose, Zg, generate the aforesaid sensor current, Is. The second feedback circuit 426 comprises a capacitor 426a in parallel v~~ith a resistor 426b. The resistor 426b acts to set the amplifier gain and in conjuuction with the capacitor 426a, acts as a low pass filter in order to dampen high frequency noise. An offset current AMENDED SHEET
compensation circuit 428 comprises a variable resistor 428a connected to a fourth switch 432 and the sixth reference voltage 430 held at a potential of Vrz volts. The fourth switch 432 is a two position switch that engal;es or disengages the offset current compensation circuit 428. With the fourth switch 432 in the closed position(as shown) and by adjusting the variable resistor 428a, an offset bias current, IB, is established at third input terminal 420. Continuing in Fig. 5, a fifth switch 434 is a two position switch that turns an optocoupler 900 On or Off. The second operational amplifier 418 is thereby operative to convert the sensor current, IS + Ie, into an output voltage, Va, at the second output terminal 424 and thus acts, for io example, in a fashion that is referred to as a transim~pedence amplifier.
Continuing in Fig. 5, the second operational amplifier 4I8 is connected to the optocoupler 900 by way of the fifth switch 434. The: optocoupler 900 comprises a first optical device 902, such as a light emitting diode. 'fhe first optical device 902 is optically coupled to a second optical device 904 such as a photocell, a photosensitive 15 resistor or a phototransistor. The cathode of the first optical device 902 is connected to the fifth switch 434 and the anode is connected to electrical ground 906.
As such, when the output voltage, Vo, at the second output terminal 424 or the fifth switch 434 is negative, the first optical device 902 emits an optical signal 908 to which the second optical device 904 is responsive. The operative nature of the first optical 2o device 902 is such that the optical signal 908 emitted therefrom is consistent with the output voltage, Vo, at the second output terminal 424 when the third switch 434 is closed{as shown). The optocoupler 900 is connected to the microprocessor 600 via the second optical device 904. However, the nature: of the coupling of the first optical device 902 and the second optical device 904 via the optical signal 908 is such as to 25 provide electrical isolation of the microprocessor 600 from the potentiostat circuit 400. As a result of the aforesaid responsivity of the second optical device 904 to the optical signal 908, a changing resistance, 0R, is developed across the second optical device 904. The output, DR, of the second optical device 904 is conveyed to the microprocessor 600 for conversion to a digital serial data signal, VT, which is then 3o conveyed to the transmitter 700. The transmitter 700 is operative to transmit a digital serial data signal VT, indicative of the changing resiistance, DR, in the optocoupler 900 WO 00/30532 PCT/US99i27543 to the at least one receiver 800. VT is then conveyed to the computer system 1000 for processing thereof by appropriate controlling software, e.g., screen readout and data logging to a storage disk. It is contemplated that the aforesaid transmittal of the serial data signal, VT, is by a radio frequency electromagnetic wave at a carrier frequency of about 303.85 Mhz. In particular, VT is in the nature of digital counts whereby digital count = 10 ~R ohms. The serial data signal, VT, includes, for example, the transmitter serial number, the resistance value in the number of digital counts and a timing scheme governing data transmission rates, data logging rates and received data error prevention information. VT is conveyed from t:he at least one receiver 800 to the 1o computer system 1000 whereat actual glucose conce:ntratifln values are displayed on a computer screen for immediate readout provided by real time conversion of digital counts based upon earlier calibration, curve fitting and tables. The computer system 1000 is operative to initialize the status of the transrr~itting puck 300, deactivate the transmitting puck 300, error check VT, process VT for display to a screen, log VT to a 15 disk file and commands the transmitting puck 300 to~ set transmission intervals over a range from 5 seconds to 10 minutes.
Thus it will be appreciated that the electrochemical system provides real time continuous and reliable data related to the glucose concentrations in a body.
The microprocessor 600 controls the status of the potentiostat circuit 400 by controlling 2o the first and second switches 414, 416, controls the bias voltage, Vg, the excitation voltage, V;, establishes alarm levels and directs the transmission of VT. The transmitter 700, including a near field receiver, accepts as input from the microprocessor 600 the serial data value, VT, in a serial data protocol and by digital signal processing converts VT into a binary stream to be conveyed to the at least one 25 receiver 800. The at least one receiver 800 accepts as input the binary stream and recovers therefrom the serial data signal, VT, for conveyance to either the computer system 1000 for processing thereof or immediate di:>play to a patient. The at least one receiver 800 includes a near field transmitter operative to initialize the transmitting puck 300 and place the transmitting puck 300 in standby mode.
While preferred embodiments have been shown and described, various modifications and substitutions may be made thereto without departing from the true spirit and scope of the invention. Accordingly, it is understood that the present invention has been described by way of illustrations and not limitation.
What is claimed is:
Claims
3. An electrochemical system for detecting glucose concentrations in a body, the system comprising:
an electrochemical sensor (200) for implantation into the body including at least one electrode (202, 204, 206);
a telemetry unit (300) for implantation into the body including an electric circuit (400) convertable between a potentiostat circuit and a galvanostat circuit connected to the electrochemical sensor for providing an excitation voltage to a first electrode of the at least one electrode of the electrochemical sensor and generating thereby a first signal indicative of glucose concentrations;
at least one signal converter (610, 620) connected to the potentiostat circuit;
a microprocessor (600) connected to the potentiostat circuit and the at least one signal converter;
at least one receiver (800) for receiving the signal from the telemetry unit;
and a power supply (680) for energizing the electric circuit.
4. The electrochemical system as set forth in Claim 3 wherein the convertable electric circuit comprises a first operational amplifier (402) having a first output terminal (404) connected to a first electrode (202) of the at least one electrode, a first switch (414) having at least one position connected to the at least one signal converter, a second switch (416) having at least one position connected to the at least one signal converter, a first input terminal (406) connected to the first switch, a second input terminal (408), a first feedback circuit (410) having at least one electric device therein connected to a second electrode (204) of the at least one electrode, the second input terminal (408) and the second switch (416); and a second operational amplifier (418) having a third input terminal (420) connected to a third electrode (206) of the at least one electrode, a fourth input terminal (422) connected to the at least one signal converter, a second output terminal (424) and a second feedback circuit (426) having at least one electric device therein connected to the second output terminal (424), the third input terminal (420) and the microprocessor (600).
5. The electrochemical system as set forth is Claim 4 wherein the first feedback circuit (410) is a negative feedback circuit including a direct connection from the first output terminal (404) to the second input terminal (408).
6. The electrochemical system as set forth in Claim 4 wherein the first feedback circuit (410) is a negative feedback circuit including a first resistor (412) connected to the second input terminal (408) and the second switch (416).
7. The electrochemical system as set forth in Claim 4 wherein the second feedback circuit is a negative feedback circuit including a second resistor (426) connected to the second output terminal (424) and the third input terminal (420).
8. The electrochemical system as set forth in Claim 7 wherein the second resistor (426) is controlled by the microprocessor (600).
9. The electrochemical system as set forth in Claim 4 wherein the second electrode (204) of the at least one electrode is an auxiliary electrode.
10. The electrochemical system as set forth in Claim 4 wherein the second electrode (204) of the at least one electrode is a reference electrode.
11. The electrochemical system as set forth in Claim 4 wherein the second electrode (204) of the at least one electrode is a working electrode and the third input terminal (420) is disconnected from the third electrode (206).
12. The electrochemical system as set forth in claim 3 wherein the electric circuit further comprises a filter circuit (500) connected to the convertable electric circuit (400) and an analog to digital converter (640).
13. The electrochemical system as set forth in claim 3 wherein the electric circuit (400) further comprises a transmitter (700) connected to the microprocessor {600) for transmitting a signal indicative of glucose concentrations.
14. The electrochemical system as set forth in claim 13 further comprising a computer system (1000) coupled to the at least one receiver (800) for processing the signal indicative of glucose concentrations.
15. The electrochemical system as set forth in. Claim 12 wherein the filter circuit (500) is a low pass filter circuit.
16. The electrochemical system as set forth in Claim 15 wherein the filter circuit comprises:
a third operational (502) amplifier having a third output terminal (504) connected to the analog to digital converter (640);
a fifth input terminal (506);
a sixth input terminal (508);
a third feedback circuit (510) having at least one electrical device therein connected to the third output terminal (504) and the fifth input terminal (506);
a fourth feedback circuit (510a) having at least one electrical device (518) therein connected to the third output terminal (504) and the sixth input terminal (508).
17. The electrochemical system as set forth in Claim 16 wherein the third feedback circuit (510) is a negative feedback circuit.
18. The electrochemical system as set forth inn Claim 16 wherein the third feedback circuit (510) comprises a direct connection.
19. The electrochemical system as set forth in Claim 16 wherein the fourth feedback circuit (510a) is a positive feedback circuit.
20. The electrochemical system as set forth in Claim 16 wherein the fourth feedback circuit comprises:
a first capacitor (516) connected to the sixth input terminal (508) and a third reference voltage (520);
a fourth resistor (514) connected to the sixth input terminal (508);
a second capacitor (518) connected to the third output terminal (504) and the fourth resistor (514);
a third resistor (512) connected to the first resistor, the second capacitor (518).
21. The electrochemical system as set forth in Claim 3 wherein the convertable electric circuit comprises:
a power supply (650) for energizing the electric circuit;
a first operational amplifier (402) connected to the power supply (650) and the electrochemical sensor (200) for maintaining the first electrode (202) of the electrochemical sensor at a substantially constant excitation voltage;
a second operational amplifier (418) connected to the power supply (650) and the electrochemical sensor (200) for converting the sensor current into an output voltage; and an optocoupler (900) connected to the second operational amplifier (418) and a transmitter for converting the output voltage into a changing resistance.
22. The electrochemical system as set forth in Claim 21 wherein the power supply comprises:
a third switch (602) having an open and closed position;
a battery (604) connected to the third switch (602) and a first reference voltage (606); and a voltage converter (608) connected to a first and second reference voltage (602a, 652).
23. The electrochemical system as set forth in Claim 21 wherein the first operational amplifier comprises a first input lead (408);
a second input lead (406);
a first output lead (404) connected to a first electrode (202) of the electrochemical sensor;
a first feedback circuit (410) connected to the first input lead (408) and the first output lead (404); and a first potentiometer (438) connected to a fourth reference voltage (442), the second input lead (406) and a fifth reference voltage (440).
24. The electrochemical system as set forth in Claim 22 wherein the first feedback circuit (410) comprises a direct connection.
25. The electrochemical system as set fore in Claim 23 wherein the first potentiometer (438) comprises a voltage divider (436) connected to the fourth reference voltage (442), the second input lead (406) and the fifth reference voltage (440).
26. The electrochemical system as set forth in Claim 23 wherein the fourth reference voltage (442) is approximately 1.2 volts and the fifth reference voltage (440) is electrical ground.
27. The electrochemical system as set forth in Claim 23 wherein the first input lead (408) is an inverting input lead and the second input lead (406) is a noninverting lead.
28. The electrochemical system as set forth in Claim 22 wherein the second operational amplifier (418) comprises a third input lead (420);
a fourth input lead (422) connected to a fourth reference voltage (444);
a second output lead (424);
a third switch (446) connected to the third input lead (420) and a second electrode (206) of the electrochemical sensor (200);
the third switch (446) having an open and closed position;
a fifth switch (434) connected to the second output lead (424) and the optocoupler (900);
the fifth switch (434) having an open and closed position;
a second feedback circuit (426) connected to the second output lead (424) and the third input lead (420);
an offset voltage compensation circuit (428) connected to the third input lead (420); and a sixth reference voltage (430).
29. The electrochemical system as set forth in Claim 28 wherein the second feedback circuit (426) comprises a first electrical device (426a) in parallel with a second electrical device (426b).
30. The electrochemical system as set forth in Claim 29 wherein the first electrical device is a capacitor (426a).
31. The electrochemical system as set forth in Claim 29 wherein the second electrical device is a resistor (426b).
32. The electrochemical system as set forth in Claim 28 wherein the offset voltage compensation (428) circuit comprises:
a fourth switch (432) connected to the third input lead (420); and a variable resistor (428a) connected to the fourth switch (432) and the sixth reference voltage (430).
33. The electrochemical system as set forth in Claim 28 wherein the third input lead (420) is an inverting input lead and the fourth input lead (422) is a noninverting input lead.
34. The electrochemical system as set forth in Claim 33 wherein the fourth input terminal is at electrical ground.
35. The electrochemical system as set forth in Claim 34 wherein the sixth reference voltage (430) is approximately 1.2 volts.
36. The electrochemical system as set forth in Claim 21 wherein the optocoupler comprises a first optical device (902) for generating an optical signal;
a second optical device (904) responsive to the optical signal connected to the transmitter (700).
37. The electrochemical system as set forth in Claim 13 wherein the transmitter (700) comprises a radio frequency transmitter for transmitting a serial data signal.
38. The electrochemical system as set forth in Claim 14 wherein the at least one receiver (800) comprises a radio frequency receiver for receiving a serial data signal.
39. The electrochemical system as set forth in Claim 14 wherein the computer system (1000) comprises a computer network for processing the serial data signal.
40. The electrochemical system as set forth in Claim 3 wherein the at least one electrode (202, 204, 206) of the electrochemical sensor comprises a platinum electrode.
41. The electrochemical system as set forth in Claim 3 wherein the at least one electrode (202, 204, 206) of the electrochemical sensor is a silver/silver chloride electrode.
43. A telemetry unit for implantation into a body connectable to an electrochemical sensor having at least one electrode therein for detecting analyte concentrations, the telemetry unit comprising:
an electric circuit (400) convertable between a potentiostat circuit and a galvanostat circuit connected to the electrochemical sensor for providing an excitation voltage to a first electrode of the at least one electrode of the electrochemical sensor and generating thereby a first signal indicative of analyte concentrations;
at least one signal converter (610, 620) connected to the convertable electric circuit (400);
a microprocessor (600) connected to the convertible electric circuit (400) and the at least one signal converter (510, 620); and a power supply (680) for energizing the convertible electric circuit (400).
44. The telemetry unit as set forth in Claim 43 wherein the convertable electric circuit comprises:
a first operational amplifier (402) having a first output terminal (404) connected to a fast electrode (202) of the at least one electrode, a first switch (414) having at least one position connected to the at least one signal converter, a second switch (416) having at least one position connected to the at least one signal converter, a first input terminal (406) connected to the first switch, a second input terminal (408), a first feedback circuit (410) having at least one electric device therein connected to a second electrode (204) of the at least one electrode, the second input terminal (408) and the second switch (416); and a second operational amplifier (418) having a third input terminal (420) connected to a third electrode (206) of the at least one electrode, a fourth input terminal (422) connected to the at least one signal converter, a second output terminal (424); and a second feedback circuit (426) having at least one electric device therein connected to the second output terminal (424), the third input terminal (420) and the microprocessor (600), the convertable electric circuit (400) connected to the electrochemical sensor for providing an excitation voltage to a first electrode of the at least one electrode (202) of the electrochemical. sensor and generating thereby a first signal indicative of analyte concentrations;
at least one signal converter (610, 620} connected to the convertable electric circuit (400);
a microprocessor (600) connected to the convertable electric circuit (400) and the at least one signal converter (610, 620); and a power supply (680) for energizing the electric; circuit.
44. The telemetry unit as set forth in Claim 44 wherein the first feedback circuit (410) is a negative feedback circuit including a direct connection from the first output terminal (404) to the second input terminal (408).
-21a-45. The telemetry unit as set forth in Claim 44 wherein the first feedback circuit (410) is a negative feedback circuit including a just resistor (412) connected to the second input (408) terminal and the second switch (416).
46. The telemetry unit as set forth in Claim 44 wherein the second feedback circuit is a negative feedback circuit including a second resistor (426) connected to the second output terminal (424) and the third input terminal (420).
47. The telemetry unit as set forth in Claim. 47 wherein the second resistor (426) is controlled by the microprocessor (600).
48. The telemetry unit as set forth in Claim 44 wherein the second electrode (204) of the at least one electrode is an auxiliary electrode.
49. The telemetry unit as set forth in Claim 44 wherein the second electrode (204) of the at least one electrode is a reference electrode.
50. The telemetry unit as set forth in Claim 44 wherein the second electrode (204) of the at least one electrode is a working electrode and the third input terminal (420) is disconnected from the third electrode (206).
52. The telemetry unit as set forth in claim 44 wherein the electric circuit further comprises a filter circuit (500) connected to the convertable electric circuit (400) and an analog to digital converter (640).
53. The telemetry unit as set forth in claim 44 wherein the electric circuit further comprises a transmitter (700) connected to the microprocessor (600) for transmitting a signal indicative of analyte concentration.
an electrochemical sensor (200) for implantation into the body including at least one electrode (202, 204, 206);
a telemetry unit (300) for implantation into the body including an electric circuit (400) convertable between a potentiostat circuit and a galvanostat circuit connected to the electrochemical sensor for providing an excitation voltage to a first electrode of the at least one electrode of the electrochemical sensor and generating thereby a first signal indicative of glucose concentrations;
at least one signal converter (610, 620) connected to the potentiostat circuit;
a microprocessor (600) connected to the potentiostat circuit and the at least one signal converter;
at least one receiver (800) for receiving the signal from the telemetry unit;
and a power supply (680) for energizing the electric circuit.
4. The electrochemical system as set forth in Claim 3 wherein the convertable electric circuit comprises a first operational amplifier (402) having a first output terminal (404) connected to a first electrode (202) of the at least one electrode, a first switch (414) having at least one position connected to the at least one signal converter, a second switch (416) having at least one position connected to the at least one signal converter, a first input terminal (406) connected to the first switch, a second input terminal (408), a first feedback circuit (410) having at least one electric device therein connected to a second electrode (204) of the at least one electrode, the second input terminal (408) and the second switch (416); and a second operational amplifier (418) having a third input terminal (420) connected to a third electrode (206) of the at least one electrode, a fourth input terminal (422) connected to the at least one signal converter, a second output terminal (424) and a second feedback circuit (426) having at least one electric device therein connected to the second output terminal (424), the third input terminal (420) and the microprocessor (600).
5. The electrochemical system as set forth is Claim 4 wherein the first feedback circuit (410) is a negative feedback circuit including a direct connection from the first output terminal (404) to the second input terminal (408).
6. The electrochemical system as set forth in Claim 4 wherein the first feedback circuit (410) is a negative feedback circuit including a first resistor (412) connected to the second input terminal (408) and the second switch (416).
7. The electrochemical system as set forth in Claim 4 wherein the second feedback circuit is a negative feedback circuit including a second resistor (426) connected to the second output terminal (424) and the third input terminal (420).
8. The electrochemical system as set forth in Claim 7 wherein the second resistor (426) is controlled by the microprocessor (600).
9. The electrochemical system as set forth in Claim 4 wherein the second electrode (204) of the at least one electrode is an auxiliary electrode.
10. The electrochemical system as set forth in Claim 4 wherein the second electrode (204) of the at least one electrode is a reference electrode.
11. The electrochemical system as set forth in Claim 4 wherein the second electrode (204) of the at least one electrode is a working electrode and the third input terminal (420) is disconnected from the third electrode (206).
12. The electrochemical system as set forth in claim 3 wherein the electric circuit further comprises a filter circuit (500) connected to the convertable electric circuit (400) and an analog to digital converter (640).
13. The electrochemical system as set forth in claim 3 wherein the electric circuit (400) further comprises a transmitter (700) connected to the microprocessor {600) for transmitting a signal indicative of glucose concentrations.
14. The electrochemical system as set forth in claim 13 further comprising a computer system (1000) coupled to the at least one receiver (800) for processing the signal indicative of glucose concentrations.
15. The electrochemical system as set forth in. Claim 12 wherein the filter circuit (500) is a low pass filter circuit.
16. The electrochemical system as set forth in Claim 15 wherein the filter circuit comprises:
a third operational (502) amplifier having a third output terminal (504) connected to the analog to digital converter (640);
a fifth input terminal (506);
a sixth input terminal (508);
a third feedback circuit (510) having at least one electrical device therein connected to the third output terminal (504) and the fifth input terminal (506);
a fourth feedback circuit (510a) having at least one electrical device (518) therein connected to the third output terminal (504) and the sixth input terminal (508).
17. The electrochemical system as set forth in Claim 16 wherein the third feedback circuit (510) is a negative feedback circuit.
18. The electrochemical system as set forth inn Claim 16 wherein the third feedback circuit (510) comprises a direct connection.
19. The electrochemical system as set forth in Claim 16 wherein the fourth feedback circuit (510a) is a positive feedback circuit.
20. The electrochemical system as set forth in Claim 16 wherein the fourth feedback circuit comprises:
a first capacitor (516) connected to the sixth input terminal (508) and a third reference voltage (520);
a fourth resistor (514) connected to the sixth input terminal (508);
a second capacitor (518) connected to the third output terminal (504) and the fourth resistor (514);
a third resistor (512) connected to the first resistor, the second capacitor (518).
21. The electrochemical system as set forth in Claim 3 wherein the convertable electric circuit comprises:
a power supply (650) for energizing the electric circuit;
a first operational amplifier (402) connected to the power supply (650) and the electrochemical sensor (200) for maintaining the first electrode (202) of the electrochemical sensor at a substantially constant excitation voltage;
a second operational amplifier (418) connected to the power supply (650) and the electrochemical sensor (200) for converting the sensor current into an output voltage; and an optocoupler (900) connected to the second operational amplifier (418) and a transmitter for converting the output voltage into a changing resistance.
22. The electrochemical system as set forth in Claim 21 wherein the power supply comprises:
a third switch (602) having an open and closed position;
a battery (604) connected to the third switch (602) and a first reference voltage (606); and a voltage converter (608) connected to a first and second reference voltage (602a, 652).
23. The electrochemical system as set forth in Claim 21 wherein the first operational amplifier comprises a first input lead (408);
a second input lead (406);
a first output lead (404) connected to a first electrode (202) of the electrochemical sensor;
a first feedback circuit (410) connected to the first input lead (408) and the first output lead (404); and a first potentiometer (438) connected to a fourth reference voltage (442), the second input lead (406) and a fifth reference voltage (440).
24. The electrochemical system as set forth in Claim 22 wherein the first feedback circuit (410) comprises a direct connection.
25. The electrochemical system as set fore in Claim 23 wherein the first potentiometer (438) comprises a voltage divider (436) connected to the fourth reference voltage (442), the second input lead (406) and the fifth reference voltage (440).
26. The electrochemical system as set forth in Claim 23 wherein the fourth reference voltage (442) is approximately 1.2 volts and the fifth reference voltage (440) is electrical ground.
27. The electrochemical system as set forth in Claim 23 wherein the first input lead (408) is an inverting input lead and the second input lead (406) is a noninverting lead.
28. The electrochemical system as set forth in Claim 22 wherein the second operational amplifier (418) comprises a third input lead (420);
a fourth input lead (422) connected to a fourth reference voltage (444);
a second output lead (424);
a third switch (446) connected to the third input lead (420) and a second electrode (206) of the electrochemical sensor (200);
the third switch (446) having an open and closed position;
a fifth switch (434) connected to the second output lead (424) and the optocoupler (900);
the fifth switch (434) having an open and closed position;
a second feedback circuit (426) connected to the second output lead (424) and the third input lead (420);
an offset voltage compensation circuit (428) connected to the third input lead (420); and a sixth reference voltage (430).
29. The electrochemical system as set forth in Claim 28 wherein the second feedback circuit (426) comprises a first electrical device (426a) in parallel with a second electrical device (426b).
30. The electrochemical system as set forth in Claim 29 wherein the first electrical device is a capacitor (426a).
31. The electrochemical system as set forth in Claim 29 wherein the second electrical device is a resistor (426b).
32. The electrochemical system as set forth in Claim 28 wherein the offset voltage compensation (428) circuit comprises:
a fourth switch (432) connected to the third input lead (420); and a variable resistor (428a) connected to the fourth switch (432) and the sixth reference voltage (430).
33. The electrochemical system as set forth in Claim 28 wherein the third input lead (420) is an inverting input lead and the fourth input lead (422) is a noninverting input lead.
34. The electrochemical system as set forth in Claim 33 wherein the fourth input terminal is at electrical ground.
35. The electrochemical system as set forth in Claim 34 wherein the sixth reference voltage (430) is approximately 1.2 volts.
36. The electrochemical system as set forth in Claim 21 wherein the optocoupler comprises a first optical device (902) for generating an optical signal;
a second optical device (904) responsive to the optical signal connected to the transmitter (700).
37. The electrochemical system as set forth in Claim 13 wherein the transmitter (700) comprises a radio frequency transmitter for transmitting a serial data signal.
38. The electrochemical system as set forth in Claim 14 wherein the at least one receiver (800) comprises a radio frequency receiver for receiving a serial data signal.
39. The electrochemical system as set forth in Claim 14 wherein the computer system (1000) comprises a computer network for processing the serial data signal.
40. The electrochemical system as set forth in Claim 3 wherein the at least one electrode (202, 204, 206) of the electrochemical sensor comprises a platinum electrode.
41. The electrochemical system as set forth in Claim 3 wherein the at least one electrode (202, 204, 206) of the electrochemical sensor is a silver/silver chloride electrode.
43. A telemetry unit for implantation into a body connectable to an electrochemical sensor having at least one electrode therein for detecting analyte concentrations, the telemetry unit comprising:
an electric circuit (400) convertable between a potentiostat circuit and a galvanostat circuit connected to the electrochemical sensor for providing an excitation voltage to a first electrode of the at least one electrode of the electrochemical sensor and generating thereby a first signal indicative of analyte concentrations;
at least one signal converter (610, 620) connected to the convertable electric circuit (400);
a microprocessor (600) connected to the convertible electric circuit (400) and the at least one signal converter (510, 620); and a power supply (680) for energizing the convertible electric circuit (400).
44. The telemetry unit as set forth in Claim 43 wherein the convertable electric circuit comprises:
a first operational amplifier (402) having a first output terminal (404) connected to a fast electrode (202) of the at least one electrode, a first switch (414) having at least one position connected to the at least one signal converter, a second switch (416) having at least one position connected to the at least one signal converter, a first input terminal (406) connected to the first switch, a second input terminal (408), a first feedback circuit (410) having at least one electric device therein connected to a second electrode (204) of the at least one electrode, the second input terminal (408) and the second switch (416); and a second operational amplifier (418) having a third input terminal (420) connected to a third electrode (206) of the at least one electrode, a fourth input terminal (422) connected to the at least one signal converter, a second output terminal (424); and a second feedback circuit (426) having at least one electric device therein connected to the second output terminal (424), the third input terminal (420) and the microprocessor (600), the convertable electric circuit (400) connected to the electrochemical sensor for providing an excitation voltage to a first electrode of the at least one electrode (202) of the electrochemical. sensor and generating thereby a first signal indicative of analyte concentrations;
at least one signal converter (610, 620} connected to the convertable electric circuit (400);
a microprocessor (600) connected to the convertable electric circuit (400) and the at least one signal converter (610, 620); and a power supply (680) for energizing the electric; circuit.
44. The telemetry unit as set forth in Claim 44 wherein the first feedback circuit (410) is a negative feedback circuit including a direct connection from the first output terminal (404) to the second input terminal (408).
-21a-45. The telemetry unit as set forth in Claim 44 wherein the first feedback circuit (410) is a negative feedback circuit including a just resistor (412) connected to the second input (408) terminal and the second switch (416).
46. The telemetry unit as set forth in Claim 44 wherein the second feedback circuit is a negative feedback circuit including a second resistor (426) connected to the second output terminal (424) and the third input terminal (420).
47. The telemetry unit as set forth in Claim. 47 wherein the second resistor (426) is controlled by the microprocessor (600).
48. The telemetry unit as set forth in Claim 44 wherein the second electrode (204) of the at least one electrode is an auxiliary electrode.
49. The telemetry unit as set forth in Claim 44 wherein the second electrode (204) of the at least one electrode is a reference electrode.
50. The telemetry unit as set forth in Claim 44 wherein the second electrode (204) of the at least one electrode is a working electrode and the third input terminal (420) is disconnected from the third electrode (206).
52. The telemetry unit as set forth in claim 44 wherein the electric circuit further comprises a filter circuit (500) connected to the convertable electric circuit (400) and an analog to digital converter (640).
53. The telemetry unit as set forth in claim 44 wherein the electric circuit further comprises a transmitter (700) connected to the microprocessor (600) for transmitting a signal indicative of analyte concentration.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US10928998P | 1998-11-20 | 1998-11-20 | |
| US60/109,289 | 1998-11-20 | ||
| PCT/US1999/027543 WO2000030532A1 (en) | 1998-11-20 | 1999-11-19 | Generic integrated implantable potentiostat telemetry unit for electrochemical sensors |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2351734A1 true CA2351734A1 (en) | 2000-06-02 |
Family
ID=22326873
Family Applications (2)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA2354060A Expired - Fee Related CA2354060C (en) | 1998-11-20 | 1999-11-19 | Apparatus and method for control of tissue/implant interactions |
| CA002351734A Abandoned CA2351734A1 (en) | 1998-11-20 | 1999-11-19 | Generic integrated implantable potentiostat telemetry unit for electrochemical sensors |
Family Applications Before (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA2354060A Expired - Fee Related CA2354060C (en) | 1998-11-20 | 1999-11-19 | Apparatus and method for control of tissue/implant interactions |
Country Status (6)
| Country | Link |
|---|---|
| US (2) | US6497729B1 (en) |
| EP (2) | EP1130996B1 (en) |
| AT (2) | ATE269114T1 (en) |
| CA (2) | CA2354060C (en) |
| DE (2) | DE69924749T2 (en) |
| WO (2) | WO2000030532A1 (en) |
Families Citing this family (513)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5593852A (en) * | 1993-12-02 | 1997-01-14 | Heller; Adam | Subcutaneous glucose electrode |
| CA2050057A1 (en) | 1991-03-04 | 1992-09-05 | Adam Heller | Interferant eliminating biosensors |
| JP3348528B2 (en) * | 1994-07-20 | 2002-11-20 | 富士通株式会社 | Method for manufacturing semiconductor device, method for manufacturing semiconductor device and electronic circuit device, and electronic circuit device |
| US5869079A (en) * | 1995-06-02 | 1999-02-09 | Oculex Pharmaceuticals, Inc. | Formulation for controlled release of drugs by combining hydrophilic and hydrophobic agents |
| US6933331B2 (en) * | 1998-05-22 | 2005-08-23 | Nanoproducts Corporation | Nanotechnology for drug delivery, contrast agents and biomedical implants |
| US6001067A (en) | 1997-03-04 | 1999-12-14 | Shults; Mark C. | 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 |
| US9155496B2 (en) | 1997-03-04 | 2015-10-13 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
| US20050033132A1 (en) * | 1997-03-04 | 2005-02-10 | Shults Mark C. | Analyte measuring device |
| US6862465B2 (en) | 1997-03-04 | 2005-03-01 | Dexcom, Inc. | Device and method for determining analyte levels |
| US7657297B2 (en) * | 2004-05-03 | 2010-02-02 | Dexcom, Inc. | Implantable analyte sensor |
| US8527026B2 (en) | 1997-03-04 | 2013-09-03 | Dexcom, Inc. | Device and method for determining analyte levels |
| US7722671B1 (en) * | 1998-01-27 | 2010-05-25 | St. Jude Medical, Inc. | Medical devices with associated growth factors |
| US6134461A (en) | 1998-03-04 | 2000-10-17 | E. Heller & Company | Electrochemical analyte |
| US6175752B1 (en) | 1998-04-30 | 2001-01-16 | Therasense, 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 |
| US8465425B2 (en) | 1998-04-30 | 2013-06-18 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
| US6949816B2 (en) | 2003-04-21 | 2005-09-27 | Motorola, Inc. | Semiconductor component having first surface area for electrically coupling to a semiconductor chip and second surface area for electrically coupling to a substrate, and method of manufacturing same |
| US8974386B2 (en) | 1998-04-30 | 2015-03-10 | 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 |
| US8688188B2 (en) | 1998-04-30 | 2014-04-01 | 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 |
| WO2000043539A2 (en) * | 1999-01-25 | 2000-07-27 | Biochip Technologies Gmbh | Immobilization of molecules on surfaces via polymer brushes |
| SE0000285D0 (en) * | 1999-12-07 | 2000-01-31 | Mika Lahtinen | Medical implant |
| DE10015816A1 (en) * | 2000-03-30 | 2001-10-18 | Infineon Technologies Ag | Biosensor chip |
| US6726918B1 (en) | 2000-07-05 | 2004-04-27 | Oculex Pharmaceuticals, Inc. | Methods for treating inflammation-mediated conditions of the eye |
| US9008786B2 (en) * | 2000-08-21 | 2015-04-14 | Cochlear Limited | Determining stimulation signals for neural stimulation |
| AUPQ952800A0 (en) | 2000-08-21 | 2000-09-14 | Cochlear Limited | Power efficient electrical stimulation |
| US8285382B2 (en) * | 2000-08-21 | 2012-10-09 | Cochlear Limited | Determining stimulation signals for neural stimulation |
| DE60114229T2 (en) | 2000-11-29 | 2006-07-06 | Allergan, Inc., Irvine | PREVENTING TRANSPLANT DISCHARGE IN THE EYE |
| US6560471B1 (en) * | 2001-01-02 | 2003-05-06 | Therasense, Inc. | Analyte monitoring device and methods of use |
| GB0100761D0 (en) | 2001-01-11 | 2001-02-21 | Biocompatibles Ltd | Drug delivery from stents |
| US20030089030A1 (en) * | 2001-03-22 | 2003-05-15 | Jordan Frederick L. | Method and composition for using organic, plant-derived, oil-extracted materials in resid fuels for reduced emissions |
| EP1397068A2 (en) | 2001-04-02 | 2004-03-17 | Therasense, Inc. | Blood glucose tracking apparatus and methods |
| US7259448B2 (en) * | 2001-05-07 | 2007-08-21 | Broadcom Corporation | Die-up ball grid array package with a heat spreader and method for making the same |
| US6656506B1 (en) | 2001-05-09 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Microparticle coated medical device |
| AUPR604801A0 (en) * | 2001-06-29 | 2001-07-26 | Cochlear Limited | Multi-electrode cochlear implant system with distributed electronics |
| US6444318B1 (en) * | 2001-07-17 | 2002-09-03 | Surmodics, Inc. | Self assembling monolayer compositions |
| US7858679B2 (en) | 2001-07-20 | 2010-12-28 | Northwestern University | Polymeric compositions and related methods of use |
| US8815793B2 (en) | 2001-07-20 | 2014-08-26 | Northwestern University | Polymeric compositions and related methods of use |
| US7618937B2 (en) | 2001-07-20 | 2009-11-17 | Northwestern University | Peptidomimetic polymers for antifouling surfaces |
| 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 |
| US6670179B1 (en) * | 2001-08-01 | 2003-12-30 | University Of Kentucky Research Foundation | Molecular functionalization of carbon nanotubes and use as substrates for neuronal growth |
| US6913626B2 (en) * | 2001-08-14 | 2005-07-05 | Mcghan Jim J. | Medical implant having bioabsorbable textured surface |
| US7563457B2 (en) * | 2001-10-02 | 2009-07-21 | The Regents Of The University Of California | Nanoparticle assembled hollow spheres |
| JP2005518827A (en) * | 2001-10-05 | 2005-06-30 | サーモディクス，インコーポレイテッド | Particle fixing coating and use thereof |
| EP1434607A1 (en) * | 2001-10-11 | 2004-07-07 | Straumann Holding AG | Osteophilic implants |
| NL1019316C2 (en) * | 2001-11-06 | 2003-05-07 | Tno | A vascular prosthesis. |
| US6948079B2 (en) * | 2001-12-26 | 2005-09-20 | Intel Corporation | Method and apparatus for providing supply voltages for a processor |
| US20080255438A1 (en) * | 2001-12-27 | 2008-10-16 | Medtronic Minimed, Inc. | System for monitoring physiological characteristics |
| US7399277B2 (en) * | 2001-12-27 | 2008-07-15 | Medtronic Minimed, Inc. | System for monitoring physiological characteristics |
| US20050239155A1 (en) * | 2002-01-04 | 2005-10-27 | Javier Alarcon | Entrapped binding protein as biosensors |
| US20030153026A1 (en) * | 2002-01-04 | 2003-08-14 | Javier Alarcon | Entrapped binding protein as biosensors |
| WO2003061840A1 (en) * | 2002-01-22 | 2003-07-31 | Talton James D Ph D | Method of pulsed laser assisted surface modification |
| US8271202B1 (en) | 2002-02-11 | 2012-09-18 | Fernandez Dennis S | Modified host bio-data management |
| US8010174B2 (en) | 2003-08-22 | 2011-08-30 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
| US7613491B2 (en) | 2002-05-22 | 2009-11-03 | Dexcom, Inc. | Silicone based membranes for use in implantable glucose sensors |
| US9247901B2 (en) | 2003-08-22 | 2016-02-02 | 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 |
| US8364229B2 (en) | 2003-07-25 | 2013-01-29 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
| US8260393B2 (en) | 2003-07-25 | 2012-09-04 | Dexcom, Inc. | Systems and methods for replacing signal data artifacts in a glucose sensor data stream |
| US7396537B1 (en) * | 2002-02-28 | 2008-07-08 | The Trustees Of The University Of Pennsylvania | Cell delivery patch for myocardial tissue engineering |
| AU2003234176A1 (en) * | 2002-04-22 | 2003-11-03 | The Children's Hospital Of Philadelphia | Low profile combination device for gastrostomy or jejunostomy applications having anti-granuloma formation characteristics |
| US20070227907A1 (en) * | 2006-04-04 | 2007-10-04 | Rajiv Shah | Methods and materials for controlling the electrochemistry of analyte sensors |
| US7813780B2 (en) * | 2005-12-13 | 2010-10-12 | Medtronic Minimed, Inc. | Biosensors and methods for making and using them |
| US9492111B2 (en) * | 2002-04-22 | 2016-11-15 | Medtronic Minimed, Inc. | Methods and materials for stabilizing analyte sensors |
| ATE515277T1 (en) | 2002-05-24 | 2011-07-15 | Angiotech Int Ag | COMPOSITIONS AND METHODS FOR COATING MEDICAL IMPLANTS |
| US8313760B2 (en) | 2002-05-24 | 2012-11-20 | Angiotech International Ag | Compositions and methods for coating medical implants |
| US8911831B2 (en) | 2002-07-19 | 2014-12-16 | Northwestern University | Surface independent, surface-modifying, multifunctional coatings and applications thereof |
| US20060034807A1 (en) * | 2002-08-09 | 2006-02-16 | Ottawa Health Research Institute | Innervated artificial tissues and uses thereof |
| US7482427B2 (en) | 2002-08-20 | 2009-01-27 | Biosurface Engineering Technologies, Inc. | Positive modulator of bone morphogenic protein-2 |
| US7981862B2 (en) | 2003-08-19 | 2011-07-19 | Biosurface Engineering Technologies, Inc. | Composition comprising BMP-2 amplifier/co-activator for enhancement of osteogenesis |
| US7598224B2 (en) * | 2002-08-20 | 2009-10-06 | Biosurface Engineering Technologies, Inc. | Dual chain synthetic heparin-binding growth factor analogs |
| US8227411B2 (en) | 2002-08-20 | 2012-07-24 | BioSurface Engineering Technologies, Incle | FGF growth factor analogs |
| US7862831B2 (en) * | 2002-10-09 | 2011-01-04 | Synthasome, Inc. | Method and material for enhanced tissue-biomaterial integration |
| US9237865B2 (en) * | 2002-10-18 | 2016-01-19 | Medtronic Minimed, Inc. | Analyte sensors and methods for making and using them |
| US20050272989A1 (en) * | 2004-06-04 | 2005-12-08 | Medtronic Minimed, Inc. | Analyte sensors and methods for making and using them |
| US8105652B2 (en) * | 2002-10-24 | 2012-01-31 | Massachusetts Institute Of Technology | Methods of making decomposable thin films of polyelectrolytes and uses thereof |
| US7381184B2 (en) | 2002-11-05 | 2008-06-03 | Abbott Diabetes Care Inc. | Sensor inserter assembly |
| US7708974B2 (en) | 2002-12-10 | 2010-05-04 | Ppg Industries Ohio, Inc. | Tungsten comprising nanomaterials and related nanotechnology |
| US7468210B1 (en) * | 2002-12-10 | 2008-12-23 | Biosurface Engineering Technologies, Inc. | Cross-linked heparin coatings and methods |
| US7578912B2 (en) * | 2002-12-30 | 2009-08-25 | California Institute Of Technology | Electro-active sensor, method for constructing the same; apparatus and circuitry for detection of electro-active species |
| AU2003303597A1 (en) | 2002-12-31 | 2004-07-29 | Therasense, Inc. | Continuous glucose monitoring system and methods of use |
| 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 |
| US20050048099A1 (en) | 2003-01-09 | 2005-03-03 | Allergan, Inc. | Ocular implant made by a double extrusion process |
| US20040185013A1 (en) * | 2003-01-30 | 2004-09-23 | Burgio Paul A. | Dental whitening compositions and methods |
| US20040151691A1 (en) * | 2003-01-30 | 2004-08-05 | Oxman Joel D. | Hardenable thermally responsive compositions |
| US7223826B2 (en) * | 2003-01-30 | 2007-05-29 | 3M Innovative Properties Company | Amide-functional polymers, compositions, and methods |
| DE10305810A1 (en) * | 2003-02-12 | 2004-08-26 | Ethicon Gmbh | Osteo-inductive bone filling material, comprises matrix containing anabolic steroid to accelerate bone growth and healing |
| US7134999B2 (en) | 2003-04-04 | 2006-11-14 | Dexcom, Inc. | Optimized sensor geometry for an implantable glucose sensor |
| DE10322182A1 (en) * | 2003-05-16 | 2004-12-02 | Blue Membranes Gmbh | Process for the production of porous, carbon-based material |
| DE202004009060U1 (en) * | 2003-05-16 | 2004-08-12 | Blue Membranes Gmbh | Biocompatible coated medical implants |
| DE202004009059U1 (en) * | 2003-05-16 | 2004-09-16 | Blue Membranes Gmbh | Substrates coated with carbon-based material |
| US7875293B2 (en) | 2003-05-21 | 2011-01-25 | Dexcom, Inc. | Biointerface membranes incorporating bioactive agents |
| EA009836B1 (en) * | 2003-05-28 | 2008-04-28 | Синвеншн Аг | Implants comprising functionalized carbon surfaces |
| US8066639B2 (en) | 2003-06-10 | 2011-11-29 | Abbott Diabetes Care Inc. | Glucose measuring device for use in personal area network |
| US7695239B2 (en) * | 2003-07-14 | 2010-04-13 | Fortrend Engineering Corporation | End effector gripper arms having corner grippers which reorient reticle during transfer |
| US7074307B2 (en) | 2003-07-25 | 2006-07-11 | Dexcom, Inc. | Electrode systems for electrochemical sensors |
| US8423113B2 (en) | 2003-07-25 | 2013-04-16 | Dexcom, Inc. | Systems and methods for processing sensor data |
| US8282549B2 (en) * | 2003-12-09 | 2012-10-09 | Dexcom, Inc. | Signal processing for continuous analyte sensor |
| US9763609B2 (en) | 2003-07-25 | 2017-09-19 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
| US7778680B2 (en) | 2003-08-01 | 2010-08-17 | Dexcom, Inc. | System and methods for processing analyte sensor data |
| US8676287B2 (en) | 2003-08-01 | 2014-03-18 | Dexcom, Inc. | System and methods for processing analyte sensor data |
| US7494465B2 (en) | 2004-07-13 | 2009-02-24 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US9135402B2 (en) | 2007-12-17 | 2015-09-15 | Dexcom, Inc. | Systems and methods for processing sensor data |
| US8275437B2 (en) | 2003-08-01 | 2012-09-25 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US7774145B2 (en) | 2003-08-01 | 2010-08-10 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US8369919B2 (en) | 2003-08-01 | 2013-02-05 | Dexcom, Inc. | Systems and methods for processing sensor data |
| US20070208245A1 (en) * | 2003-08-01 | 2007-09-06 | Brauker James H | Transcutaneous analyte sensor |
| US20190357827A1 (en) | 2003-08-01 | 2019-11-28 | Dexcom, Inc. | Analyte sensor |
| US8160669B2 (en) * | 2003-08-01 | 2012-04-17 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US8845536B2 (en) | 2003-08-01 | 2014-09-30 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US8285354B2 (en) | 2003-08-01 | 2012-10-09 | Dexcom, Inc. | System and methods for processing analyte sensor data |
| US8761856B2 (en) | 2003-08-01 | 2014-06-24 | Dexcom, Inc. | System and methods for processing analyte sensor data |
| US20080119703A1 (en) | 2006-10-04 | 2008-05-22 | Mark Brister | Analyte sensor |
| US7591801B2 (en) * | 2004-02-26 | 2009-09-22 | Dexcom, Inc. | Integrated delivery device for continuous glucose sensor |
| US8233959B2 (en) | 2003-08-22 | 2012-07-31 | Dexcom, Inc. | 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 |
| US7920906B2 (en) | 2005-03-10 | 2011-04-05 | Dexcom, Inc. | System and methods for processing analyte sensor data for sensor calibration |
| US20050124896A1 (en) * | 2003-08-25 | 2005-06-09 | Jacob Richter | Method for protecting implantable sensors and protected implantable sensors |
| US20050090607A1 (en) * | 2003-10-28 | 2005-04-28 | Dexcom, Inc. | Silicone composition for biocompatible membrane |
| EP1682161A4 (en) * | 2003-10-29 | 2011-12-07 | Gentis Inc | Polymerizable emulsions for tissue engineering |
| 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 |
| USD914881S1 (en) | 2003-11-05 | 2021-03-30 | Abbott Diabetes Care Inc. | Analyte sensor electronic mount |
| EP1689321B1 (en) * | 2003-11-07 | 2017-01-04 | The University of Connecticut | Artificial tissue systems and uses thereof |
| US20070224278A1 (en) | 2003-11-12 | 2007-09-27 | Lyons Robert T | Low immunogenicity corticosteroid compositions |
| US20050101582A1 (en) | 2003-11-12 | 2005-05-12 | Allergan, Inc. | Compositions and methods for treating a posterior segment of an eye |
| US9247900B2 (en) | 2004-07-13 | 2016-02-02 | Dexcom, Inc. | Analyte sensor |
| WO2005051170A2 (en) | 2003-11-19 | 2005-06-09 | Dexcom, Inc. | Integrated receiver for continuous analyte sensor |
| EP2256493B1 (en) | 2003-12-05 | 2014-02-26 | DexCom, Inc. | Calibration techniques for a continuous analyte sensor |
| US8423114B2 (en) | 2006-10-04 | 2013-04-16 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
| US8364231B2 (en) | 2006-10-04 | 2013-01-29 | Dexcom, Inc. | Analyte sensor |
| US11633133B2 (en) | 2003-12-05 | 2023-04-25 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
| US8287453B2 (en) | 2003-12-05 | 2012-10-16 | Dexcom, Inc. | Analyte sensor |
| US8084513B2 (en) * | 2003-12-30 | 2011-12-27 | Beisang Arthur A | Implant filling material and method |
| US7988986B2 (en) * | 2003-12-30 | 2011-08-02 | Beisang Arthur A | Implant filling material and method |
| JP2007518804A (en) | 2004-01-20 | 2007-07-12 | アラーガン、インコーポレイテッド | Composition for topical ophthalmic treatment preferably containing triamcinolone acetonide and hyaluronic acid |
| 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 |
| US20080227696A1 (en) | 2005-02-22 | 2008-09-18 | Biosurface Engineering Technologies, Inc. | Single branch heparin-binding growth factor analogs |
| WO2009048462A1 (en) | 2007-10-09 | 2009-04-16 | Dexcom, Inc. | Integrated insulin delivery system with continuous glucose sensor |
| US8808228B2 (en) | 2004-02-26 | 2014-08-19 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
| US20050208093A1 (en) | 2004-03-22 | 2005-09-22 | Thierry Glauser | Phosphoryl choline coating compositions |
| US20050224370A1 (en) * | 2004-04-07 | 2005-10-13 | Jun Liu | Electrochemical deposition analysis system including high-stability electrode |
| US8048437B2 (en) * | 2004-04-21 | 2011-11-01 | Richard Nagler | Medical device with surface coating comprising bioactive compound |
| US6984299B2 (en) * | 2004-04-27 | 2006-01-10 | Advanced Technology Material, Inc. | Methods for determining organic component concentrations in an electrolytic solution |
| US20050244458A1 (en) * | 2004-04-30 | 2005-11-03 | Allergan, Inc. | Sustained release intraocular implants and methods for treating ocular neuropathies |
| US20050244463A1 (en) | 2004-04-30 | 2005-11-03 | Allergan, Inc. | Sustained release intraocular implants and methods for treating ocular vasculopathies |
| US8591885B2 (en) | 2004-04-30 | 2013-11-26 | Allergan, Inc. | Carbonic anhydrase inhibitor sustained release intraocular drug delivery systems |
| US8673341B2 (en) | 2004-04-30 | 2014-03-18 | Allergan, Inc. | Intraocular pressure reduction with intracameral bimatoprost implants |
| US7771742B2 (en) | 2004-04-30 | 2010-08-10 | Allergan, Inc. | Sustained release intraocular implants containing tyrosine kinase inhibitors and related methods |
| US7435320B2 (en) | 2004-04-30 | 2008-10-14 | Advanced Technology Materials, Inc. | Methods and apparatuses for monitoring organic additives in electrochemical deposition solutions |
| US8425929B2 (en) | 2004-04-30 | 2013-04-23 | Allergan, Inc. | Sustained release intraocular implants and methods for preventing retinal dysfunction |
| US7799336B2 (en) | 2004-04-30 | 2010-09-21 | Allergan, Inc. | Hypotensive lipid-containing biodegradable intraocular implants and related methods |
| US20050244469A1 (en) | 2004-04-30 | 2005-11-03 | Allergan, Inc. | Extended therapeutic effect ocular implant treatments |
| US8147865B2 (en) | 2004-04-30 | 2012-04-03 | Allergan, Inc. | Steroid-containing sustained release intraocular implants and related methods |
| US7993634B2 (en) | 2004-04-30 | 2011-08-09 | Allergan, Inc. | Oil-in-oil emulsified polymeric implants containing a hypotensive lipid and related methods |
| US8722097B2 (en) | 2004-04-30 | 2014-05-13 | Allergan, Inc. | Oil-in-water method for making polymeric implants containing a hypotensive lipid |
| US8512738B2 (en) | 2004-04-30 | 2013-08-20 | Allergan, Inc. | Biodegradable intravitreal tyrosine kinase implants |
| US8119154B2 (en) | 2004-04-30 | 2012-02-21 | Allergan, Inc. | Sustained release intraocular implants and related methods |
| US9498457B2 (en) | 2004-04-30 | 2016-11-22 | Allergan, Inc. | Hypotensive prostamide-containing biodegradable intraocular implants and related implants |
| US20050245799A1 (en) * | 2004-05-03 | 2005-11-03 | Dexcom, Inc. | Implantable analyte sensor |
| US8792955B2 (en) | 2004-05-03 | 2014-07-29 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US7427346B2 (en) * | 2004-05-04 | 2008-09-23 | Advanced Technology Materials, Inc. | Electrochemical drive circuitry and method |
| US8241655B2 (en) * | 2004-05-12 | 2012-08-14 | Surmodics, Inc. | Coatings for medical articles including natural biodegradable polysaccharides |
| US7125382B2 (en) * | 2004-05-20 | 2006-10-24 | Digital Angel Corporation | Embedded bio-sensor system |
| US9561309B2 (en) | 2004-05-27 | 2017-02-07 | Advanced Cardiovascular Systems, Inc. | Antifouling heparin coatings |
| CA2569375A1 (en) * | 2004-06-01 | 2006-08-17 | Microchips, Inc. | Devices and methods for measuring and enhancing drug or analyte transport to/from medical implant |
| WO2005119524A2 (en) | 2004-06-04 | 2005-12-15 | Therasense, Inc. | Diabetes care host-client architecture and data management system |
| EP1754059B1 (en) * | 2004-06-09 | 2010-08-04 | Becton, Dickinson and Company | Multianalyte sensor |
| US7519435B2 (en) * | 2004-06-23 | 2009-04-14 | Cochlear Limited | Methods for maintaining low impedance of electrodes |
| US8170803B2 (en) | 2004-07-13 | 2012-05-01 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US8452368B2 (en) | 2004-07-13 | 2013-05-28 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US8886272B2 (en) | 2004-07-13 | 2014-11-11 | Dexcom, Inc. | Analyte sensor |
| US20080242961A1 (en) * | 2004-07-13 | 2008-10-02 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US8565848B2 (en) | 2004-07-13 | 2013-10-22 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US20070045902A1 (en) | 2004-07-13 | 2007-03-01 | Brauker James H | Analyte sensor |
| US7537590B2 (en) * | 2004-07-30 | 2009-05-26 | Microchips, Inc. | Multi-reservoir device for transdermal drug delivery and sensing |
| CN100488635C (en) | 2004-09-01 | 2009-05-20 | 微芯片公司 | Multi-cap reservoir devices for controlled release or exposure of reservoir contents |
| US7205701B2 (en) * | 2004-09-03 | 2007-04-17 | Honeywell International Inc. | Passive wireless acoustic wave chemical sensor |
| WO2006038866A1 (en) * | 2004-10-01 | 2006-04-13 | Bio Polymer Products Of Sweden Ab | Improved coating comprising a bioadhesive polyphenolic protein derived from a byssus-forming mussel |
| US9259175B2 (en) | 2006-10-23 | 2016-02-16 | Abbott Diabetes Care, Inc. | Flexible patch for fluid delivery and monitoring body analytes |
| US10226207B2 (en) | 2004-12-29 | 2019-03-12 | Abbott Diabetes Care Inc. | Sensor inserter having introducer |
| US8029441B2 (en) | 2006-02-28 | 2011-10-04 | Abbott Diabetes Care Inc. | Analyte sensor transmitter unit configuration for a data monitoring and management 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 |
| 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 |
| US7697967B2 (en) | 2005-12-28 | 2010-04-13 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor insertion |
| US20090082693A1 (en) * | 2004-12-29 | 2009-03-26 | Therasense, Inc. | Method and apparatus for providing temperature sensor module in a data communication system |
| US20090105569A1 (en) | 2006-04-28 | 2009-04-23 | Abbott Diabetes Care, Inc. | Introducer Assembly and Methods of Use |
| US9351669B2 (en) | 2009-09-30 | 2016-05-31 | Abbott Diabetes Care Inc. | Interconnect for on-body analyte monitoring device |
| 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 |
| US7731657B2 (en) | 2005-08-30 | 2010-06-08 | Abbott Diabetes Care Inc. | Analyte sensor introducer and methods of use |
| 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 |
| US8512243B2 (en) | 2005-09-30 | 2013-08-20 | Abbott Diabetes Care Inc. | Integrated introducer and transmitter assembly 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 |
| US8545403B2 (en) | 2005-12-28 | 2013-10-01 | Abbott Diabetes Care Inc. | Medical device insertion |
| US9788771B2 (en) | 2006-10-23 | 2017-10-17 | Abbott Diabetes Care Inc. | Variable speed sensor insertion devices and methods of use |
| MX2007008425A (en) | 2005-01-13 | 2007-12-10 | Cinv Ag | Composite materials containing carbon nanoparticles. |
| AU2006208131A1 (en) * | 2005-01-25 | 2006-08-03 | Microchips, Inc. | Control of drug release by transient modification of local microenvironments |
| MX2007009430A (en) * | 2005-02-03 | 2007-08-17 | Cinv Ag | Drug delivery materials made by sol/gel technology. |
| US7545272B2 (en) | 2005-02-08 | 2009-06-09 | Therasense, Inc. | RF tag on test strips, test strip vials and boxes |
| BRPI0608186A2 (en) * | 2005-02-18 | 2011-01-04 | Synthasome Inc | synthetic structure for soft tissue repair |
| US8133178B2 (en) | 2006-02-22 | 2012-03-13 | Dexcom, Inc. | Analyte sensor |
| US20060229715A1 (en) * | 2005-03-29 | 2006-10-12 | Sdgi Holdings, Inc. | Implants incorporating nanotubes and methods for producing the same |
| US8744546B2 (en) | 2005-05-05 | 2014-06-03 | Dexcom, Inc. | 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 |
| US8060174B2 (en) | 2005-04-15 | 2011-11-15 | Dexcom, Inc. | Analyte sensing biointerface |
| US7182783B2 (en) * | 2005-04-25 | 2007-02-27 | Sdgi Holdings, Inc. | Selectively expandable composite structures for spinal arthroplasty |
| 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 |
| US7715911B2 (en) * | 2005-05-31 | 2010-05-11 | Medtronic, Inc. | Apparatus for tissue stimulation |
| AU2006270221B2 (en) | 2005-07-15 | 2012-01-19 | Micell Technologies, Inc. | Polymer coatings containing drug powder of controlled morphology |
| WO2007011708A2 (en) | 2005-07-15 | 2007-01-25 | Micell Technologies, Inc. | Stent with polymer coating containing amorphous rapamycin |
| JP2009507224A (en) | 2005-08-31 | 2009-02-19 | ユニヴァーシティー オブ ヴァージニア パテント ファンデーション | Improving the accuracy of continuous glucose sensors |
| US9521968B2 (en) | 2005-09-30 | 2016-12-20 | Abbott Diabetes Care Inc. | Analyte sensor retention mechanism and methods of use |
| US8880138B2 (en) | 2005-09-30 | 2014-11-04 | Abbott Diabetes Care Inc. | Device for channeling fluid and methods of use |
| KR100720052B1 (en) | 2005-10-07 | 2007-05-18 | (주) 차바이오텍 | Microsphere or microbead coated with nanoparticle containing growth factor for regenerating cartilaginous tissue |
| 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 |
| CA2633768A1 (en) * | 2005-11-10 | 2007-05-18 | Bayer Schering Pharma Aktiengesellschaft | Reduction of restenosis |
| US20070127745A1 (en) * | 2005-12-07 | 2007-06-07 | Cochlear Limited | Prevention of static bonding between medical device components |
| US11298058B2 (en) | 2005-12-28 | 2022-04-12 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor insertion |
| US9757061B2 (en) | 2006-01-17 | 2017-09-12 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
| US7736310B2 (en) | 2006-01-30 | 2010-06-15 | Abbott Diabetes Care Inc. | On-body medical device securement |
| US7732539B2 (en) * | 2006-02-16 | 2010-06-08 | National Science Foundation | Modified acrylic block copolymers for hydrogels and pressure sensitive wet adhesives |
| 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 |
| US7801582B2 (en) | 2006-03-31 | 2010-09-21 | Abbott Diabetes Care Inc. | Analyte monitoring and management system and methods therefor |
| US9675290B2 (en) | 2012-10-30 | 2017-06-13 | Abbott Diabetes Care Inc. | Sensitivity calibration of in vivo sensors used to measure analyte concentration |
| US8140312B2 (en) | 2007-05-14 | 2012-03-20 | Abbott Diabetes Care Inc. | Method and system for determining analyte levels |
| US8374668B1 (en) | 2007-10-23 | 2013-02-12 | Abbott Diabetes Care Inc. | Analyte sensor with lag compensation |
| US8226891B2 (en) | 2006-03-31 | 2012-07-24 | Abbott Diabetes Care Inc. | Analyte monitoring devices 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 |
| US9326709B2 (en) | 2010-03-10 | 2016-05-03 | Abbott Diabetes Care Inc. | Systems, devices and methods for managing glucose levels |
| US9392969B2 (en) | 2008-08-31 | 2016-07-19 | Abbott Diabetes Care Inc. | Closed loop control and signal attenuation detection |
| US8478557B2 (en) | 2009-07-31 | 2013-07-02 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte monitoring system calibration accuracy |
| US8224415B2 (en) | 2009-01-29 | 2012-07-17 | Abbott Diabetes Care Inc. | Method and device for providing offset model based calibration for analyte sensor |
| US7620438B2 (en) | 2006-03-31 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and system for powering an electronic device |
| US8219173B2 (en) | 2008-09-30 | 2012-07-10 | Abbott Diabetes Care Inc. | Optimizing analyte sensor calibration |
| US8346335B2 (en) | 2008-03-28 | 2013-01-01 | Abbott Diabetes Care Inc. | Analyte sensor calibration management |
| US8473022B2 (en) | 2008-01-31 | 2013-06-25 | Abbott Diabetes Care Inc. | Analyte sensor with time lag compensation |
| US7630748B2 (en) | 2006-10-25 | 2009-12-08 | Abbott Diabetes Care Inc. | Method and system for providing analyte monitoring |
| 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 |
| WO2007127363A2 (en) | 2006-04-26 | 2007-11-08 | Micell Technologies, Inc. | Coatings containing multiple drugs |
| TW200813181A (en) * | 2006-06-01 | 2008-03-16 | Akzo Nobel Coatings Int Bv | Adhesive system |
| US20070277928A1 (en) * | 2006-06-01 | 2007-12-06 | Akzo Nobel Coatings International B.V. | Adhesive system |
| US20070281145A1 (en) * | 2006-06-01 | 2007-12-06 | Akzo Nobel Coatings International B.V. | Adhesive system |
| US7820172B1 (en) | 2006-06-01 | 2010-10-26 | Biosurface Engineering Technologies, Inc. | Laminin-derived multi-domain peptides |
| US8703167B2 (en) * | 2006-06-05 | 2014-04-22 | Advanced Cardiovascular Systems, Inc. | Coatings for implantable medical devices for controlled release of a hydrophilic drug and a hydrophobic drug |
| US8323676B2 (en) | 2008-06-30 | 2012-12-04 | Abbott Cardiovascular Systems Inc. | Poly(ester-amide) and poly(amide) coatings for implantable medical devices for controlled release of a protein or peptide and a hydrophobic drug |
| US20090258028A1 (en) * | 2006-06-05 | 2009-10-15 | Abbott Cardiovascular Systems Inc. | Methods Of Forming Coatings For Implantable Medical Devices For Controlled Release Of A Peptide And A Hydrophobic Drug |
| US7920907B2 (en) | 2006-06-07 | 2011-04-05 | Abbott Diabetes Care Inc. | Analyte monitoring system and method |
| US8114150B2 (en) | 2006-06-14 | 2012-02-14 | Advanced Cardiovascular Systems, Inc. | RGD peptide attached to bioabsorbable stents |
| US8802128B2 (en) * | 2006-06-23 | 2014-08-12 | Allergan, Inc. | Steroid-containing sustained release intraocular implants and related methods |
| EP2037977A2 (en) * | 2006-06-28 | 2009-03-25 | SurModics, Inc. | Active agent eluting matrices with particulates |
| US7722665B2 (en) * | 2006-07-07 | 2010-05-25 | Graft Technologies, Inc. | System and method for providing a graft in a vascular environment |
| US8685430B1 (en) | 2006-07-14 | 2014-04-01 | Abbott Cardiovascular Systems Inc. | Tailored aliphatic polyesters for stent coatings |
| US8563117B2 (en) | 2006-08-04 | 2013-10-22 | Phillip B. Messersmith | Biomimetic modular adhesive complex: materials, methods and applications therefore |
| US7622533B2 (en) | 2006-08-04 | 2009-11-24 | Nerites Corporation | Biomimetic compounds and synthetic methods therefor |
| US8914090B2 (en) | 2006-09-27 | 2014-12-16 | The University Of Connecticut | Implantable biosensor and methods of use thereof |
| US8636767B2 (en) | 2006-10-02 | 2014-01-28 | Micell Technologies, Inc. | Surgical sutures having increased strength |
| US7943034B2 (en) * | 2006-10-19 | 2011-05-17 | Agamatrix, Inc. | Method and apparatus for providing a stable voltage to an analytical system |
| EP2081694B1 (en) | 2006-10-23 | 2020-05-13 | Micell Technologies, Inc. | Holder for electrically charging a substrate during coating |
| CN101636104B (en) | 2006-10-26 | 2012-07-18 | 雅培糖尿病护理公司 | Method, system for real-time detection of sensitivity decline in analyte sensors |
| CA2667890C (en) | 2006-10-31 | 2015-01-27 | Surmodics Pharmaceuticals, Inc. | Spheronized polymer particles |
| US7713541B1 (en) | 2006-11-21 | 2010-05-11 | Abbott Cardiovascular Systems Inc. | Zwitterionic terpolymers, method of making and use on medical devices |
| US8969415B2 (en) | 2006-12-01 | 2015-03-03 | Allergan, Inc. | Intraocular drug delivery systems |
| JP5603598B2 (en) | 2007-01-08 | 2014-10-08 | ミセル テクノロジーズ、インコーポレイテッド | Stent with biodegradable layer |
| US11426494B2 (en) | 2007-01-08 | 2022-08-30 | MT Acquisition Holdings LLC | Stents having biodegradable layers |
| DE102007005817A1 (en) | 2007-02-06 | 2008-08-14 | Laser Zentrum Hannover E.V. | Biologically active device and process for its preparation |
| 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 |
| US8383092B2 (en) * | 2007-02-16 | 2013-02-26 | Knc Ner Acquisition Sub, Inc. | Bioadhesive constructs |
| US8673286B2 (en) | 2007-04-09 | 2014-03-18 | Northwestern University | DOPA-functionalized, branched, poly(aklylene oxide) adhesives |
| US8732188B2 (en) | 2007-02-18 | 2014-05-20 | Abbott Diabetes Care Inc. | Method and system for providing contextual based medication dosage determination |
| US8930203B2 (en) | 2007-02-18 | 2015-01-06 | Abbott Diabetes Care Inc. | Multi-function analyte test device and methods therefor |
| US20100291180A1 (en) * | 2007-02-20 | 2010-11-18 | Uhrich Kathryn E | Nerve guidance tubes |
| US8123686B2 (en) | 2007-03-01 | 2012-02-28 | Abbott Diabetes Care Inc. | Method and apparatus for providing rolling data in communication systems |
| CA2680886A1 (en) * | 2007-03-15 | 2008-09-18 | Boston Scientific Limited | Methods to improve the stability of cellular adhesive proteins and peptides |
| US20080249385A1 (en) * | 2007-04-04 | 2008-10-09 | Luong Ngoc Phan | Isolated intravenous analyte monitoring system |
| US8093039B2 (en) * | 2007-04-10 | 2012-01-10 | The Trustees Of The Stevens Institute Of Technology | Surfaces differentially adhesive to eukaryotic cells and non-eukaryotic cells |
| EP2146623B1 (en) | 2007-04-14 | 2014-01-08 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
| CA2683962C (en) | 2007-04-14 | 2017-06-06 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
| ES2817503T3 (en) | 2007-04-14 | 2021-04-07 | Abbott Diabetes Care Inc | Procedure and apparatus for providing data processing and control in a 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 |
| EP2146624B1 (en) | 2007-04-14 | 2020-03-25 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
| EP2146622B1 (en) | 2007-04-14 | 2016-05-11 | Abbott Diabetes Care Inc. | Method and apparatus for providing dynamic multi-stage signal amplification in a medical device |
| US7777631B2 (en) * | 2007-04-29 | 2010-08-17 | James Neil Rodgers | Body chip |
| US8461985B2 (en) | 2007-05-08 | 2013-06-11 | 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 |
| US8456301B2 (en) | 2007-05-08 | 2013-06-04 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
| US7928850B2 (en) | 2007-05-08 | 2011-04-19 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
| 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 |
| 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 |
| 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 |
| 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 |
| 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 |
| 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 |
| 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 |
| 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 |
| US20200037875A1 (en) | 2007-05-18 | 2020-02-06 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
| EP2170418B1 (en) | 2007-05-25 | 2016-03-16 | Micell Technologies, Inc. | Polymer films for medical device coating |
| WO2008150917A1 (en) * | 2007-05-31 | 2008-12-11 | Abbott Diabetes Care, Inc. | Insertion devices and methods |
| US8649840B2 (en) * | 2007-06-07 | 2014-02-11 | Microchips, Inc. | Electrochemical biosensors and arrays |
| AU2008262018A1 (en) | 2007-06-08 | 2008-12-18 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
| US20080311177A1 (en) | 2007-06-14 | 2008-12-18 | Massachusetts Institute Of Technology | Self Assembled Films for Protein and Drug Delivery Applications |
| AU2008265541B2 (en) | 2007-06-21 | 2014-07-17 | Abbott Diabetes Care, Inc. | Health management devices and methods |
| WO2008157821A1 (en) | 2007-06-21 | 2008-12-24 | Abbott Diabetes Care, Inc. | Health monitor |
| 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 |
| US20110130822A1 (en) * | 2007-07-20 | 2011-06-02 | Orbusneich Medical, Inc. | Bioabsorbable Polymeric Compositions and Medical Devices |
| 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 |
| 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 |
| US8834366B2 (en) | 2007-07-31 | 2014-09-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor calibration |
| US20100098761A1 (en) * | 2007-08-03 | 2010-04-22 | University Of Massachusetts Medical School | Polymer Compositions For Biomedical And Material Applications |
| US8409093B2 (en) | 2007-10-23 | 2013-04-02 | Abbott Diabetes Care Inc. | Assessing measures of glycemic variability |
| 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 |
| US8377031B2 (en) | 2007-10-23 | 2013-02-19 | Abbott Diabetes Care Inc. | Closed loop control system with safety parameters and methods |
| US8417312B2 (en) | 2007-10-25 | 2013-04-09 | Dexcom, Inc. | Systems and methods for processing sensor data |
| WO2009059203A1 (en) * | 2007-11-02 | 2009-05-07 | Edwards Lifesciences Corporation | Analyte monitoring system having back-up power source for use in either transport of the system or primary power loss |
| US8290559B2 (en) | 2007-12-17 | 2012-10-16 | 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 |
| JP5530934B2 (en) * | 2008-01-24 | 2014-06-25 | ユニバーシティ オブ ユタ リサーチ ファンデーション | Adhesive composite coacervate and methods of making and using the same |
| US8283384B2 (en) | 2008-01-24 | 2012-10-09 | University Of Utah Research Foundation | Adhesive complex coacervates and methods of making and using thereof |
| EP2252196A4 (en) | 2008-02-21 | 2013-05-15 | Dexcom Inc | Systems and methods for processing, transmitting and displaying sensor data |
| 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 |
| US11730407B2 (en) | 2008-03-28 | 2023-08-22 | Dexcom, Inc. | Polymer membranes for continuous analyte sensors |
| US8583204B2 (en) | 2008-03-28 | 2013-11-12 | Dexcom, Inc. | Polymer membranes for continuous analyte sensors |
| US8252229B2 (en) | 2008-04-10 | 2012-08-28 | Abbott Diabetes Care Inc. | Method and system for sterilizing an analyte sensor |
| SG192523A1 (en) | 2008-04-17 | 2013-08-30 | Micell Technologies Inc | Stents having bioabsorbable layers |
| EP2265293B1 (en) * | 2008-04-18 | 2015-11-04 | SurModics, Inc. | Coating systems for the controlled delivery of hydrophilic bioactive agents |
| US8591410B2 (en) | 2008-05-30 | 2013-11-26 | 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 |
| US8924159B2 (en) | 2008-05-30 | 2014-12-30 | Abbott Diabetes Care Inc. | Method and apparatus for providing glycemic control |
| US8765162B2 (en) * | 2008-06-30 | 2014-07-01 | Abbott Cardiovascular Systems Inc. | Poly(amide) and poly(ester-amide) polymers and drug delivery particles and coatings containing same |
| US8876755B2 (en) | 2008-07-14 | 2014-11-04 | Abbott Diabetes Care Inc. | Closed loop control system interface and methods |
| CN102159257B (en) | 2008-07-17 | 2015-11-25 | 米歇尔技术公司 | Drug delivery medical device |
| WO2010021973A2 (en) | 2008-08-17 | 2010-02-25 | Massachusetts Institute Of Technology | Controlled delivery of bioactive agents from decomposable films |
| 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 |
| US20110257702A1 (en) * | 2008-09-04 | 2011-10-20 | Sule Kara | Self-assembled monolayer coating on electrically conductive regions of a medical implant |
| US20100066378A1 (en) * | 2008-09-18 | 2010-03-18 | Uti Limited Partnership | Current Mirror Potentiostat |
| US8986208B2 (en) | 2008-09-30 | 2015-03-24 | Abbott Diabetes Care Inc. | Analyte sensor sensitivity attenuation mitigation |
| US9326707B2 (en) | 2008-11-10 | 2016-05-03 | Abbott Diabetes Care Inc. | Alarm characterization for analyte monitoring devices and systems |
| US8834913B2 (en) | 2008-12-26 | 2014-09-16 | Battelle Memorial Institute | Medical implants and methods of making medical implants |
| US20100179646A1 (en) * | 2009-01-09 | 2010-07-15 | Rainbow Medical Ltd. | Glucose oxidase techniques |
| US8103456B2 (en) | 2009-01-29 | 2012-01-24 | Abbott Diabetes Care Inc. | Method and device for early signal attenuation detection using blood glucose measurements |
| FI20095084A0 (en) | 2009-01-30 | 2009-01-30 | Pekka Vallittu | Composite and its use |
| US9402544B2 (en) | 2009-02-03 | 2016-08-02 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
| US20100239635A1 (en) | 2009-03-23 | 2010-09-23 | Micell Technologies, Inc. | Drug delivery medical device |
| US9446194B2 (en) * | 2009-03-27 | 2016-09-20 | Dexcom, Inc. | Methods and systems for promoting glucose management |
| CA2757276C (en) | 2009-04-01 | 2017-06-06 | Micell Technologies, Inc. | Coated stents |
| US8497777B2 (en) | 2009-04-15 | 2013-07-30 | Abbott Diabetes Care Inc. | Analyte monitoring system having an alert |
| EP2419015A4 (en) | 2009-04-16 | 2014-08-20 | Abbott Diabetes Care Inc | Analyte sensor calibration management |
| CA2759015C (en) | 2009-04-17 | 2017-06-20 | James B. Mcclain | Stents having controlled elution |
| WO2010127050A1 (en) | 2009-04-28 | 2010-11-04 | Abbott Diabetes Care Inc. | Error detection in critical repeating data in a wireless sensor system |
| US8368556B2 (en) | 2009-04-29 | 2013-02-05 | Abbott Diabetes Care Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
| WO2010127051A1 (en) | 2009-04-29 | 2010-11-04 | Abbott Diabetes Care Inc. | Method and system for providing real time analyte sensor calibration with retrospective backfill |
| US9572693B2 (en) * | 2009-05-14 | 2017-02-21 | Orbusneich Medical, Inc. | Self-expanding stent with polygon transition zone |
| US9184490B2 (en) | 2009-05-29 | 2015-11-10 | Abbott Diabetes Care Inc. | Medical device antenna systems having external antenna configurations |
| US9517023B2 (en) | 2009-06-01 | 2016-12-13 | Profusa, Inc. | Method and system for directing a localized biological response to an implant |
| US8613892B2 (en) | 2009-06-30 | 2013-12-24 | Abbott Diabetes Care Inc. | Analyte meter with a moveable head and methods of using the same |
| EP2453834A4 (en) | 2009-07-16 | 2014-04-16 | Micell Technologies Inc | Drug delivery medical device |
| EP4276652A3 (en) | 2009-07-23 | 2024-01-31 | Abbott Diabetes Care, Inc. | Real time management of data relating to physiological control of glucose levels |
| US9795326B2 (en) | 2009-07-23 | 2017-10-24 | Abbott Diabetes Care Inc. | Continuous analyte measurement systems and systems and methods for implanting them |
| US9597430B2 (en) * | 2009-07-31 | 2017-03-21 | Synthasome, Inc. | Synthetic structure for soft tissue repair |
| EP4070729A1 (en) | 2009-08-31 | 2022-10-12 | Abbott Diabetes Care, Inc. | Displays for a medical device |
| EP2473963A4 (en) | 2009-08-31 | 2014-01-08 | Abbott Diabetes Care Inc | Medical devices and methods |
| EP2473099A4 (en) | 2009-08-31 | 2015-01-14 | Abbott Diabetes Care Inc | Analyte monitoring system and methods for managing power and noise |
| WO2011026147A1 (en) | 2009-08-31 | 2011-03-03 | 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 |
| US8185181B2 (en) | 2009-10-30 | 2012-05-22 | Abbott Diabetes Care Inc. | Method and apparatus for detecting false hypoglycemic conditions |
| NZ716349A (en) | 2009-11-09 | 2017-07-28 | Allergan Inc | Compositions and methods for stimulating hair growth |
| US8660628B2 (en) * | 2009-12-21 | 2014-02-25 | Medtronic Minimed, Inc. | Analyte sensors comprising blended membrane compositions and methods for making and using them |
| USD924406S1 (en) | 2010-02-01 | 2021-07-06 | Abbott Diabetes Care Inc. | Analyte sensor inserter |
| EP2531140B1 (en) | 2010-02-02 | 2017-11-01 | Micell Technologies, Inc. | Stent and stent delivery system with improved deliverability |
| EP2549918B2 (en) | 2010-03-24 | 2023-01-25 | Abbott Diabetes Care, Inc. | Medical device inserters and processes of inserting and using medical devices |
| US8795762B2 (en) | 2010-03-26 | 2014-08-05 | Battelle Memorial Institute | System and method for enhanced electrostatic deposition and surface coatings |
| CA2797110C (en) | 2010-04-22 | 2020-07-21 | Micell Technologies, Inc. | Stents and other devices having extracellular matrix coating |
| EP2575906B1 (en) | 2010-05-24 | 2014-12-10 | University of Utah Research Foundation | Reinforced adhesive complex coacervates and methods of making and using thereof |
| US10010272B2 (en) | 2010-05-27 | 2018-07-03 | Profusa, Inc. | Tissue-integrating electronic apparatus |
| US8635046B2 (en) | 2010-06-23 | 2014-01-21 | Abbott Diabetes Care Inc. | Method and system for evaluating analyte sensor response characteristics |
| US10092229B2 (en) | 2010-06-29 | 2018-10-09 | Abbott Diabetes Care Inc. | Calibration of analyte measurement system |
| CA2802229C (en) | 2010-06-29 | 2019-01-29 | Surmodics, Inc. | Fluorinated polymers and lubricious coatings |
| 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 |
| WO2012009684A2 (en) | 2010-07-16 | 2012-01-19 | Micell Technologies, Inc. | Drug delivery medical device |
| CN105147300B (en) | 2010-10-06 | 2019-09-03 | 普罗弗萨股份有限公司 | Tissue integration sensor |
| WO2012048168A2 (en) | 2010-10-07 | 2012-04-12 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods |
| EP2637707A4 (en) | 2010-11-09 | 2014-10-01 | Kensey Nash Corp | Adhesive compounds and methods use for hernia repair |
| CA2812599A1 (en) * | 2010-11-12 | 2012-05-18 | University Of Utah Research Foundation | Simple adhesive coacervates and methods of making and using thereof |
| US20120142648A1 (en) * | 2010-12-03 | 2012-06-07 | Warsaw Orthopedic, Inc. | Methods for delivering clonidine compositions in biodegradable polymer carrier and local steriods to a target tissue site |
| CA2823355C (en) | 2010-12-30 | 2017-08-22 | Micell Technologies, Inc. | Nanoparticle and surface-modified particulate coatings, coated balloons, and methods therefore |
| US8981025B2 (en) | 2011-02-10 | 2015-03-17 | Corning Incorporated | Polymerizable catonic peptide monomers and polymers |
| US8515540B2 (en) | 2011-02-24 | 2013-08-20 | Cochlear Limited | Feedthrough having a non-linear conductor |
| CA2827196A1 (en) | 2011-02-28 | 2012-11-15 | Jai Karan | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the 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 |
| AU2012234345A1 (en) * | 2011-03-28 | 2013-09-05 | F. Hoffmann-La Roche Ag | Improved diffusion layer for an enzymatic in-vivo sensor |
| US20120323311A1 (en) | 2011-04-13 | 2012-12-20 | Micell Technologies, Inc. | Stents having controlled elution |
| DK3575796T3 (en) | 2011-04-15 | 2021-01-18 | Dexcom Inc | ADVANCED ANALYZE SENSOR CALIBRATION AND ERROR DETECTION |
| US10464100B2 (en) | 2011-05-31 | 2019-11-05 | Micell Technologies, Inc. | System and process for formation of a time-released, drug-eluting transferable coating |
| CA2841360A1 (en) | 2011-07-15 | 2013-01-24 | Micell Technologies, Inc. | Drug delivery medical device |
| WO2013023051A1 (en) * | 2011-08-09 | 2013-02-14 | University Of Utah Research Foundation | Methods and compositions for improving the biocompatability of biomedical implants |
| US10188772B2 (en) | 2011-10-18 | 2019-01-29 | Micell Technologies, Inc. | Drug delivery medical device |
| WO2013066849A1 (en) | 2011-10-31 | 2013-05-10 | Abbott Diabetes Care Inc. | Model based variable risk false glucose threshold alarm prevention mechanism |
| US9069536B2 (en) | 2011-10-31 | 2015-06-30 | Abbott Diabetes Care Inc. | Electronic devices having integrated reset systems and methods thereof |
| AU2012335830B2 (en) | 2011-11-07 | 2017-05-04 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods |
| 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 |
| 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 |
| EP4056105B1 (en) | 2011-12-11 | 2023-10-11 | Abbott Diabetes Care, Inc. | Analyte sensor devices |
| US8927529B2 (en) | 2012-01-30 | 2015-01-06 | SpineThera | Treatment of back pain by injection of microparticles of dexamethasone acetate and a polymer |
| US9120095B2 (en) | 2012-03-29 | 2015-09-01 | Biomet Biologics, Llc | Apparatus and method for separating and concentrating a component of a fluid |
| WO2013163234A1 (en) | 2012-04-23 | 2013-10-31 | Massachusetts Institute Of Technology | Stable layer-by-layer coated particles |
| US8798332B2 (en) | 2012-05-15 | 2014-08-05 | Google Inc. | Contact lenses |
| US8857981B2 (en) | 2012-07-26 | 2014-10-14 | Google Inc. | Facilitation of contact lenses with capacitive sensors |
| US9523865B2 (en) | 2012-07-26 | 2016-12-20 | Verily Life Sciences Llc | Contact lenses with hybrid power sources |
| US9158133B1 (en) | 2012-07-26 | 2015-10-13 | Google Inc. | Contact lens employing optical signals for power and/or communication |
| US9298020B1 (en) | 2012-07-26 | 2016-03-29 | Verily Life Sciences Llc | Input system |
| US8919953B1 (en) | 2012-08-02 | 2014-12-30 | Google Inc. | Actuatable contact lenses |
| US9696564B1 (en) | 2012-08-21 | 2017-07-04 | Verily Life Sciences Llc | Contact lens with metal portion and polymer layer having indentations |
| US9111473B1 (en) | 2012-08-24 | 2015-08-18 | Google Inc. | Input system |
| EP2890297B1 (en) | 2012-08-30 | 2018-04-11 | Abbott Diabetes Care, Inc. | Dropout detection in continuous analyte monitoring data during data excursions |
| US8820934B1 (en) | 2012-09-05 | 2014-09-02 | Google Inc. | Passive surface acoustic wave communication |
| US20140192315A1 (en) | 2012-09-07 | 2014-07-10 | Google Inc. | In-situ tear sample collection and testing using a contact lens |
| US9398868B1 (en) | 2012-09-11 | 2016-07-26 | Verily Life Sciences Llc | Cancellation of a baseline current signal via current subtraction within a linear relaxation oscillator-based current-to-frequency converter circuit |
| US10010270B2 (en) | 2012-09-17 | 2018-07-03 | Verily Life Sciences Llc | Sensing system |
| 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 |
| US9326710B1 (en) | 2012-09-20 | 2016-05-03 | Verily Life Sciences Llc | Contact lenses having sensors with adjustable sensitivity |
| US8870370B1 (en) | 2012-09-24 | 2014-10-28 | Google Inc. | Contact lens that facilitates antenna communication via sensor impedance modulation |
| US8960898B1 (en) | 2012-09-24 | 2015-02-24 | Google Inc. | Contact lens that restricts incoming light to the eye |
| US20140088372A1 (en) | 2012-09-25 | 2014-03-27 | Google Inc. | Information processing method |
| US8989834B2 (en) | 2012-09-25 | 2015-03-24 | Google Inc. | Wearable device |
| US8979271B2 (en) | 2012-09-25 | 2015-03-17 | Google Inc. | Facilitation of temperature compensation for contact lens sensors and temperature sensing |
| US9884180B1 (en) | 2012-09-26 | 2018-02-06 | Verily Life Sciences Llc | Power transducer for a retinal implant using a contact lens |
| US8960899B2 (en) | 2012-09-26 | 2015-02-24 | Google Inc. | Assembling thin silicon chips on a contact lens |
| WO2014052136A1 (en) | 2012-09-26 | 2014-04-03 | 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 |
| US8985763B1 (en) | 2012-09-26 | 2015-03-24 | Google Inc. | Contact lens having an uneven embedded substrate and method of manufacture |
| US8821811B2 (en) | 2012-09-26 | 2014-09-02 | Google Inc. | In-vitro contact lens testing |
| US9063351B1 (en) | 2012-09-28 | 2015-06-23 | Google Inc. | Input detection system |
| US8965478B2 (en) | 2012-10-12 | 2015-02-24 | Google Inc. | Microelectrodes in an ophthalmic electrochemical sensor |
| US9176332B1 (en) | 2012-10-24 | 2015-11-03 | Google Inc. | Contact lens and method of manufacture to improve sensor sensitivity |
| KR20140052393A (en) | 2012-10-24 | 2014-05-07 | 삼성전자주식회사 | Method and apparatus for controlling amount of light in a visible light communication system |
| US9757056B1 (en) | 2012-10-26 | 2017-09-12 | Verily Life Sciences Llc | Over-molding of sensor apparatus in eye-mountable device |
| US8874182B2 (en) | 2013-01-15 | 2014-10-28 | Google Inc. | Encapsulated electronics |
| US9289954B2 (en) | 2013-01-17 | 2016-03-22 | Verily Life Sciences Llc | Method of ring-shaped structure placement in an eye-mountable device |
| US9636016B1 (en) | 2013-01-25 | 2017-05-02 | Verily Life Sciences Llc | Eye-mountable devices and methods for accurately placing a flexible ring containing electronics in eye-mountable devices |
| US20140209481A1 (en) * | 2013-01-25 | 2014-07-31 | Google Inc. | Standby Biasing Of Electrochemical Sensor To Reduce Sensor Stabilization Time During Measurement |
| WO2014123665A1 (en) | 2013-02-06 | 2014-08-14 | Kci Licensing, Inc. | Polymers, preparation and use thereof |
| AU2014216112B2 (en) | 2013-02-15 | 2019-02-21 | Allergan, Inc. | Sustained drug delivery implant |
| WO2014134029A1 (en) | 2013-02-26 | 2014-09-04 | Massachusetts Institute Of Technology | Nucleic acid particles, methods and use thereof |
| WO2014165264A1 (en) | 2013-03-12 | 2014-10-09 | Micell Technologies, Inc. | Bioabsorbable biomedical implants |
| US10130288B2 (en) | 2013-03-14 | 2018-11-20 | Cell and Molecular Tissue Engineering, LLC | Coated sensors, and corresponding systems and methods |
| US10405961B2 (en) | 2013-03-14 | 2019-09-10 | Cell and Molecular Tissue Engineering, LLC | Coated surgical mesh, and corresponding systems and methods |
| CN108013881B (en) | 2013-03-14 | 2021-06-15 | 普罗菲尤萨股份有限公司 | Method and apparatus for correcting optical signals |
| US10433773B1 (en) | 2013-03-15 | 2019-10-08 | Abbott Diabetes Care Inc. | Noise rejection methods and apparatus for sparsely sampled analyte sensor data |
| US9474475B1 (en) | 2013-03-15 | 2016-10-25 | Abbott Diabetes Care Inc. | Multi-rate analyte sensor data collection with sample rate configurable signal processing |
| US10076285B2 (en) | 2013-03-15 | 2018-09-18 | Abbott Diabetes Care Inc. | Sensor fault detection using analyte sensor data pattern comparison |
| WO2014150074A1 (en) | 2013-03-15 | 2014-09-25 | Massachusetts Institute Of Technology | Compositions and methods for nucleic acid delivery |
| US9161712B2 (en) | 2013-03-26 | 2015-10-20 | Google Inc. | Systems and methods for encapsulating electronics in a mountable device |
| US9113829B2 (en) | 2013-03-27 | 2015-08-25 | Google Inc. | Systems and methods for encapsulating electronics in a mountable device |
| EP2996629B1 (en) | 2013-05-15 | 2021-09-22 | Micell Technologies, Inc. | Bioabsorbable biomedical implants |
| EP3777656A1 (en) | 2013-06-06 | 2021-02-17 | Profusa, Inc. | Apparatus for detecting optical signals from implanted sensors |
| US20140371560A1 (en) | 2013-06-14 | 2014-12-18 | Google Inc. | Body-Mountable Devices and Methods for Embedding a Structure in a Body-Mountable Device |
| US9084561B2 (en) | 2013-06-17 | 2015-07-21 | Google Inc. | Symmetrically arranged sensor electrodes in an ophthalmic electrochemical sensor |
| US9948895B1 (en) | 2013-06-18 | 2018-04-17 | Verily Life Sciences Llc | Fully integrated pinhole camera for eye-mountable imaging system |
| US9685689B1 (en) | 2013-06-27 | 2017-06-20 | Verily Life Sciences Llc | Fabrication methods for bio-compatible devices |
| US9028772B2 (en) | 2013-06-28 | 2015-05-12 | Google Inc. | Methods for forming a channel through a polymer layer using one or more photoresist layers |
| US9814387B2 (en) | 2013-06-28 | 2017-11-14 | Verily Life Sciences, LLC | Device identification |
| US9307901B1 (en) | 2013-06-28 | 2016-04-12 | Verily Life Sciences Llc | Methods for leaving a channel in a polymer layer using a cross-linked polymer plug |
| US9492118B1 (en) | 2013-06-28 | 2016-11-15 | Life Sciences Llc | Pre-treatment process for electrochemical amperometric sensor |
| US9654674B1 (en) | 2013-12-20 | 2017-05-16 | Verily Life Sciences Llc | Image sensor with a plurality of light channels |
| US9572522B2 (en) | 2013-12-20 | 2017-02-21 | Verily Life Sciences Llc | Tear fluid conductivity sensor |
| CN105899132B (en) | 2013-12-31 | 2020-02-18 | 雅培糖尿病护理公司 | Self-powered analyte sensor and devices using same |
| US9366570B1 (en) | 2014-03-10 | 2016-06-14 | Verily Life Sciences Llc | Photodiode operable in photoconductive mode and photovoltaic mode |
| US9184698B1 (en) | 2014-03-11 | 2015-11-10 | Google Inc. | Reference frequency from ambient light signal |
| US9789655B1 (en) | 2014-03-14 | 2017-10-17 | Verily Life Sciences Llc | Methods for mold release of body-mountable devices including microelectronics |
| EP3865063A1 (en) | 2014-03-30 | 2021-08-18 | Abbott Diabetes Care, Inc. | Method and apparatus for determining meal start and peak events in analyte monitoring systems |
| US9913927B2 (en) | 2014-07-14 | 2018-03-13 | University Of Utah Research Foundation | In situ solidifying complex coacervates and methods of making and using thereof |
| US9764122B2 (en) | 2014-07-25 | 2017-09-19 | Warsaw Orthopedic, Inc. | Drug delivery device and methods having an occluding member |
| US9775978B2 (en) | 2014-07-25 | 2017-10-03 | Warsaw Orthopedic, Inc. | Drug delivery device and methods having a retaining member |
| US10101265B1 (en) | 2014-11-07 | 2018-10-16 | Board Of Regents For The University Of Nebraska | Birefringence imaging chromatography based on highly ordered 3D nanostructures |
| WO2016123197A1 (en) * | 2015-01-27 | 2016-08-04 | The Texas A&M University System | Self-cleaning membrane for medical devices |
| GB2536410A (en) * | 2015-03-06 | 2016-09-21 | The Queen's Univ Of Belfast | Coating composition and uses thereof |
| US10213139B2 (en) | 2015-05-14 | 2019-02-26 | Abbott Diabetes Care Inc. | Systems, devices, and methods for assembling an applicator and sensor control device |
| JP6986007B2 (en) | 2015-07-10 | 2021-12-22 | アボット ダイアベティス ケア インコーポレイテッドAbbott Diabetes Care Inc. | Systems, devices and methods of dynamic glucose profile response to physiological parameters |
| US10076650B2 (en) | 2015-11-23 | 2018-09-18 | Warsaw Orthopedic, Inc. | Enhanced stylet for drug depot injector |
| US10792477B2 (en) | 2016-02-08 | 2020-10-06 | Orbusneich Medical Pte. Ltd. | Drug eluting balloon |
| US20210196932A1 (en) | 2016-02-08 | 2021-07-01 | Orbusneich Medical, Inc. | Drug Eluting Balloon |
| ES2959428T3 (en) | 2016-04-22 | 2024-02-26 | Lilly Co Eli | Infusion device with components comprising a polymeric sorbent to reduce the concentration of m-cresol in insulin |
| USD802755S1 (en) | 2016-06-23 | 2017-11-14 | Warsaw Orthopedic, Inc. | Drug pellet cartridge |
| US20180085498A1 (en) | 2016-09-23 | 2018-03-29 | Micell Technologies, Inc. | Prolonged drug-eluting products |
| CN110099677A (en) | 2016-10-28 | 2019-08-06 | 斯皮内特赫拉公司 | Medical composition and its use |
| US10434261B2 (en) | 2016-11-08 | 2019-10-08 | Warsaw Orthopedic, Inc. | Drug pellet delivery system and method |
| WO2018119400A1 (en) | 2016-12-22 | 2018-06-28 | Profusa, Inc. | System and single-channel luminescent sensor for and method of determining analyte value |
| EP3600014A4 (en) | 2017-03-21 | 2020-10-21 | Abbott Diabetes Care Inc. | Methods, devices and system for providing diabetic condition diagnosis and therapy |
| US11331022B2 (en) | 2017-10-24 | 2022-05-17 | Dexcom, Inc. | Pre-connected analyte sensors |
| CN209606445U (en) | 2017-10-24 | 2019-11-08 | 德克斯康公司 | Pre-connection analyte sensor |
| WO2019089567A1 (en) | 2017-10-30 | 2019-05-09 | Massachusetts Institute Of Technology | Layer-by-layer nanoparticles for cytokine therapy in cancer treatment |
| CN111742019B (en) * | 2018-01-22 | 2022-08-05 | W.L.戈尔有限公司 | Composition for forming antistatic coating and article coated with the same |
| US11896234B2 (en) | 2018-01-26 | 2024-02-13 | Fluidx Medical Technology, Llc | Apparatus and method of using in situ solidifying complex coacervates for vascular occlusion |
| USD1002852S1 (en) | 2019-06-06 | 2023-10-24 | Abbott Diabetes Care Inc. | Analyte sensor device |
| WO2020261281A1 (en) * | 2019-06-27 | 2020-12-30 | Ramot At Tel-Aviv University Ltd. | Semaphorin 3a antibodies and uses thereof |
| US20210106718A1 (en) * | 2019-10-14 | 2021-04-15 | Board Of Regents, The University Of Texas System | Mussel inspired nancomposite adhesives for biomedical applications |
| EP3862032A1 (en) | 2020-02-07 | 2021-08-11 | Micell Technologies, Inc. | Stents having biodegradable layers |
| CN111759552A (en) | 2020-07-06 | 2020-10-13 | 苏州莱诺医疗器械有限公司 | Absorbable stent system |
| USD999913S1 (en) | 2020-12-21 | 2023-09-26 | Abbott Diabetes Care Inc | Analyte sensor inserter |
| US11846600B2 (en) * | 2021-09-01 | 2023-12-19 | Cirrus Logic Inc. | Circuitry for analyte measurement |
| GB2620979A (en) * | 2022-07-28 | 2024-01-31 | Imperial College Innovations Ltd | Implantable device for monitoring of human wellbeing and different health conditions |
Family Cites Families (37)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3773919A (en) | 1969-10-23 | 1973-11-20 | Du Pont | Polylactide-drug mixtures |
| US3921636A (en) * | 1973-01-15 | 1975-11-25 | Alza Corp | Novel drug delivery device |
| US4070347A (en) | 1976-08-16 | 1978-01-24 | Alza Corporation | Poly(orthoester) co- and homopolymers and poly(orthocarbonate) co- and homopolymers having carbonyloxy functionality |
| US4122605A (en) | 1976-09-22 | 1978-10-31 | Kyoto Ceramic Kabushiki Kaisha | Somatic element of single crystalline sapphire ceramics |
| US4186189A (en) | 1977-09-28 | 1980-01-29 | Ethicon, Inc. | Absorbable pharmaceutical compositions based on poly(alkylene oxalates) |
| US4130639A (en) | 1977-09-28 | 1978-12-19 | Ethicon, Inc. | Absorbable pharmaceutical compositions based on isomorphic copolyoxalates |
| US4304591A (en) | 1978-01-25 | 1981-12-08 | Ciba-Geigy Corporation | Water-insoluble hydrophilic copolymers used as carriers for medicaments and pesticides |
| US4498039A (en) * | 1979-06-18 | 1985-02-05 | International Business Machines Corporation | Instrument for use with an electrochemical cell |
| US4379138A (en) | 1981-12-28 | 1983-04-05 | Research Triangle Institute | Biodegradable polymers of lactones |
| IT1170375B (en) | 1983-04-19 | 1987-06-03 | Giuseppe Bombardieri | Implantable device for measuring body fluid parameters |
| US4648880A (en) | 1984-08-30 | 1987-03-10 | Daniel Brauman | Implantable prosthetic devices |
| US4900556A (en) | 1985-04-26 | 1990-02-13 | Massachusetts Institute Of Technology | System for delayed and pulsed release of biologically active substances |
| 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 |
| US5342622A (en) | 1986-05-16 | 1994-08-30 | The State Of Victoria | Subdermal biocompatible implants |
| US4994081A (en) | 1986-10-16 | 1991-02-19 | Cbs Lens | Method for locating on a cornea an artificial lens fabricated from a collagen-hydrogel for promoting epithelial cell growth |
| US4983181A (en) | 1986-10-16 | 1991-01-08 | Cbs Lens, | Collagen hydrogel for promoting epithelial cell growth and artificial lens using the same |
| US5282856A (en) | 1987-12-22 | 1994-02-01 | Ledergerber Walter J | Implantable prosthetic device |
| US5510418A (en) * | 1988-11-21 | 1996-04-23 | Collagen Corporation | Glycosaminoglycan-synthetic polymer conjugates |
| US5101814A (en) * | 1989-08-11 | 1992-04-07 | Palti Yoram Prof | System for monitoring and controlling blood glucose |
| US5271961A (en) * | 1989-11-06 | 1993-12-21 | Alkermes Controlled Therapeutics, Inc. | Method for producing protein microspheres |
| US5529914A (en) | 1990-10-15 | 1996-06-25 | The Board Of Regents The Univeristy Of Texas System | Gels for encapsulation of biological materials |
| NZ286242A (en) | 1991-03-26 | 1997-11-24 | Csl Ltd | Use of veterinary implant as a single dose vaccination system: rupturable polymer film coating around core of active agent and water soluble excipient |
| US5705178A (en) | 1991-05-31 | 1998-01-06 | Gliatech, Inc. | Methods and compositions based on inhibition of cell invasion and fibrosis by anionic polymers |
| IL103284A0 (en) | 1991-10-31 | 1993-02-21 | Transtech Medical Inc | Transplant protective coating |
| AU3469893A (en) * | 1992-01-15 | 1993-08-03 | Allergan, Inc. | Hydrogel compositions and structures made from same |
| NL9200207A (en) | 1992-02-05 | 1993-09-01 | Nedap Nv | IMPLANTABLE BIOMEDICAL SENSOR DEVICE, IN PARTICULAR FOR MEASUREMENT OF THE GLUCOSE CONCENTRATION. |
| US5656297A (en) * | 1992-03-12 | 1997-08-12 | Alkermes Controlled Therapeutics, Incorporated | Modulated release from biocompatible polymers |
| US5306294A (en) * | 1992-08-05 | 1994-04-26 | Ultrasonic Sensing And Monitoring Systems, Inc. | Stent construction of rolled configuration |
| JPH08507715A (en) | 1993-03-18 | 1996-08-20 | シーダーズ サイナイ メディカル センター | Drug-inducing and releasable polymeric coatings for bioartificial components |
| DE19501159B4 (en) * | 1995-01-06 | 2004-05-13 | Ehwald, Rudolf, Prof. Dr.sc.nat. | Microsensor for determining the concentration of glucose and other analytes in liquids on the basis of affinity viscometry |
| MX9707593A (en) * | 1995-04-04 | 1997-12-31 | Novartis Ag | Polymerizable perfluoroalkylether macromer. |
| US5711861A (en) | 1995-11-22 | 1998-01-27 | Ward; W. Kenneth | Device for monitoring changes in analyte concentration |
| AU705101B2 (en) | 1996-02-15 | 1999-05-13 | Interface Biologics Inc. | Bioresponsive pharmacologically-active polymers and articles made therefrom |
| US5916585A (en) * | 1996-06-03 | 1999-06-29 | Gore Enterprise Holdings, Inc. | Materials and method for the immobilization of bioactive species onto biodegradable polymers |
| US5932539A (en) * | 1996-10-15 | 1999-08-03 | The Board Of Trustees Of The University Of Illinois | Biodegradable polymer matrix for tissue repair |
| US5914026A (en) | 1997-01-06 | 1999-06-22 | Implanted Biosystems Inc. | Implantable sensor employing an auxiliary electrode |
| US6175752B1 (en) * | 1998-04-30 | 2001-01-16 | Therasense, Inc. | Analyte monitoring device and methods of use |
-
1999
- 1999-11-19 AT AT99959054T patent/ATE269114T1/en not_active IP Right Cessation
- 1999-11-19 AT AT99959055T patent/ATE292931T1/en not_active IP Right Cessation
- 1999-11-19 US US09/443,857 patent/US6497729B1/en not_active Expired - Lifetime
- 1999-11-19 CA CA2354060A patent/CA2354060C/en not_active Expired - Fee Related
- 1999-11-19 US US09/443,764 patent/US6366794B1/en not_active Expired - Fee Related
- 1999-11-19 EP EP99959055A patent/EP1130996B1/en not_active Expired - Lifetime
- 1999-11-19 WO PCT/US1999/027543 patent/WO2000030532A1/en active IP Right Grant
- 1999-11-19 DE DE69924749T patent/DE69924749T2/en not_active Expired - Fee Related
- 1999-11-19 CA CA002351734A patent/CA2351734A1/en not_active Abandoned
- 1999-11-19 EP EP99959054A patent/EP1131114B1/en not_active Expired - Lifetime
- 1999-11-19 DE DE69918159T patent/DE69918159T2/en not_active Expired - Lifetime
- 1999-11-19 WO PCT/US1999/027542 patent/WO2000030698A1/en active IP Right Grant
Also Published As
| Publication number | Publication date |
|---|---|
| WO2000030698A1 (en) | 2000-06-02 |
| EP1131114B1 (en) | 2004-06-16 |
| DE69924749D1 (en) | 2005-05-19 |
| EP1130996A1 (en) | 2001-09-12 |
| EP1130996B1 (en) | 2005-04-13 |
| US6366794B1 (en) | 2002-04-02 |
| ATE292931T1 (en) | 2005-04-15 |
| US6497729B1 (en) | 2002-12-24 |
| DE69918159T2 (en) | 2005-03-17 |
| WO2000030532A1 (en) | 2000-06-02 |
| EP1131114A1 (en) | 2001-09-12 |
| ATE269114T1 (en) | 2004-07-15 |
| DE69918159D1 (en) | 2004-07-22 |
| CA2354060A1 (en) | 2000-06-02 |
| DE69924749T2 (en) | 2006-04-27 |
| CA2354060C (en) | 2014-01-28 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| EP1130996B1 (en) | Generic integrated implantable potentiostat telemetry unit for electrochemical sensors | |
| US6618603B2 (en) | Apparatus for measurement and control of the content of glucose, lactate or other metabolites in biological fluids | |
| CA2330553C (en) | Implantable blood glucose sensor system | |
| US7778679B2 (en) | Implantable sensor and integrity tests therefor | |
| US6514689B2 (en) | Hydrogel biosensor | |
| JP4644425B2 (en) | Implantable sensor electrode and electronic circuit configuration | |
| US4703756A (en) | Complete glucose monitoring system with an implantable, telemetered sensor module | |
| US7125382B2 (en) | Embedded bio-sensor system | |
| EP2108948B1 (en) | Biological sample measuring device | |
| RU2683203C2 (en) | Self-powered analyte sensor and devices using the same | |
| KR20030031895A (en) | Hydrogel biosensor and biosensor-based health alarm system | |
| EP2079358A1 (en) | Implantable biosensor and methods of use thereof | |
| RU2694473C1 (en) | Measuring device | |
| WO2021168229A1 (en) | A deep tissue ultrasonic implantable luminescence oxygen sensor | |
| US11020019B2 (en) | Dynamic amplifier change | |
| GB2335496A (en) | Implanted blood glucose sensing and transmitting devices | |
| CN114746016A (en) | Method and system for reducing differences between calculated and measured analyte levels | |
| JP2009147484A (en) | Wireless communications system and wireless communications system for measuring information of living body |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| FZDE | Discontinued |