CA2153877C - Biosensing meter with fail/safe procedures to prevent erroneous indications - Google Patents
Biosensing meter with fail/safe procedures to prevent erroneous indicationsInfo
- Publication number
- CA2153877C CA2153877C CA002153877A CA2153877A CA2153877C CA 2153877 C CA2153877 C CA 2153877C CA 002153877 A CA002153877 A CA 002153877A CA 2153877 A CA2153877 A CA 2153877A CA 2153877 C CA2153877 C CA 2153877C
- Authority
- CA
- Canada
- Prior art keywords
- excitation
- sample
- current
- threshold value
- biosensing meter
- 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.)
- Expired - Lifetime
Links
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
- G01N27/28—Electrolytic cell components
- G01N27/30—Electrodes, e.g. test electrodes; Half-cells
- G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
- G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
- G01N27/3273—Devices therefor, e.g. test element readers, circuitry
Abstract
A biosensing meter (22) receives a sample strip (10) that includes electrically isolated sense and excitation electrodes (12, 14) bridged by a reaction zone. When a drop of biological sample fluid is placed in the reaction zone, a plurality of fail/safe tests are performed. A drop size test is performed by a circuit that detects the size of the drop placed in the reaction zone. The circuit both detects that a drop has been placed in the reaction zone and further measures a test current level, after a delay, to determine that the drop size is sufficient to enable hydration of reactants in the reaction zone.
Description
Q~
1 0 ( I
W094l29706 PCTIUS9~/0 BIOSFNSIIIG METER WITII FAIL/SAFE PROCEDURES
TO PREVENT ERRONEOUS INDICATIONS
FIELD oF TIIE INVENTION
This invention relates to biosensing meters that employ disposable sample strips, and more particularly, to fail/safe systems and procedures for preventing such meters from issuing erroneous results.
~ACKGROUND OF TI~E INVENTION
Biosensing in~LLI ants that employ disposable sample strips enjoy wide r?nq-lr~r acceptance. Such inaLL, Ls are employed for the detection of various analyte levels in blood samples, e.g., glucose and cholesterol. In general, such instruments provide accurate readings if the user is careful to follow the in~LL~ L's directions. Often however, the user is careless in the use of either the sample strip or the inaLL~ -nt and an erroneous reading results. Accordingly, significant efforts have been taken by instrument manufacturers to reduce the potential for errors during the use of such instruments.
Even if a biosensing instrument and sample strips are employed properly, the presence of a manufacturing defect in either will cause erroneous readings. Thus, while great care is taken in the production of such in~LL, -nts and sample strips, there is a need to incorporate analytical procedures in the instrument that enable instrument malfunctions, sample strip irregularities and user errors to be detected so as to prevent erroneous analyte readings.
The prior art includes a number of disclosures of biosensing instruments that employ disposable sample strips. In U.S. Patent 5,108,564 to Szuminsky et al., a biosensing instrument is disclosed that measures glucose concentrations in blood. The in~LL~ -nt depends upon a reaction wherein glucose, in the presence of an enzyme, CA 021~3877 1998-08-21 catalyzes a reaction of potassium ferricyanide to potassium ferrocyanide. After the reaction has completed, a voltage is applied across a reaction zone and causes a reversal of the reaction with an accompanying generation of a small but measurable current. That current is termed the Cottrell current and, in dependence upon the concentration of glucose in the reaction zone, follows a predetermined curve during the reverse reaction. A reading of the Cottrell current is converted into an indication of glucose concentration. The instrument also senses an impedance across the reaction zone and determines when a blood sample has been emplaced therein by detecting a sudden change in current flow. At such time, an incubation period is commenced, followed by application of a potential across the reaction zone and measurement of the Cottrell current.
European Patent Application 0 471 986 A2 of Tsutsumi et al.
discloses a blood glucose measurement system that employs disposable sample strips. The Tsutsumi et al. system detects the presence of a blood sample by sensing a resistance across a pair of electrodes. It further employs a plurality of sample-like strips, each having a specific resistance value which distinguishes it from other strips.
Each of those strips has a particular application, i.e., for use during an adjustment mode of the instrument, during an error compensation mode, during a calibration mode, etc.
U.S. Patent 4,999,582 to Parks et al., assigned to the same Assignee as this application, describes a biosensor electrode excitation circuit for determining if a sample strip has been properly inserted into a meter and if at least one electrode on the sample strip exhibits a proper level of contact resistance.
Canadian Patent Application Serial No. 2071484, filed December 14, 1990 to White, entitled "Biosensing Instrument and Method" and assigned to the same assignee as this application, teaches a biosensing instrument which employs , ~3~77 ~r W094/29706 PCT~S94/OS323 . . .
~ -3 the "Cottrell" curve relationship to determine glucose concentrations. In that instrument, current flow is proportional to the concentration of an analyte in the test cell; however, when something is amiss in the test cell, the current that results may bear no relationship whatever to analyte concentration. White found that a relationship exists that enables a determination to be made whether current flow through a reaction zone is, in fact, following the Cottrell relationship. More specifically, the ratio of the square roots of s~rceP~;ng sample times, for all analyte concentration curves, has been found to inversely approximate the ratio of the measured Cottrell currents at those same sample times. If over surr~ing time periods, the ratios are equal (within limits), the measurement system is properly following the Cottrell relatinnch;r. If the ratios found are not equal, the mea~u~ is disregarded.
U.S. Patent 4,940,945 to Littlejohn et al. describes an interface circuit for use in a biochemical sensing instrument. A disposable cartridge is employed that includes a pair of electrodes across which resistance measurements are taken. Circuitry is disclosed for sensing the presence of a fluid sample by an initial resistance measurement, and also the level of fluid in the cartridge.
U.S. Patent 4,420,564 to Tsuji et al. describes a blood sugar analyzer that employs a reaction cell having a fixed enzyme membrane sensor and a measuring electrode. The Tsuji et al: system includes several fail/safe procedures, one to determine that the reaction is taking place within specifically defined temperature limits and a second to determine that the reaction current remains within a prede~rm; n~d range.
. .
The above noted prior art indicates that biosensing meters have had the ability to determine when a biological sample is placed in a reaction zone. Xowever, the prior art has not addressed the problem of the presence of an insufficient amount of the sample to fully wet enzymatic reactants present in a reaction zone.
Furthermore, while a test is available to determine that a reaction is following the Cottrell relationship (as described in the aforesaid patent application to White), additional confirming, tests are desirable to assure that the reaction is in fact, following the Cottrell relationship.
~ Accordingly, it is an object of an aspect of this invention to provide a biosensing meter with means for~ 15 performing a plurality of fail/safe tests during the course of an analysis of a biological sample.
It is an object of an aspect of this invention to provide a biosensing meter with means for determining that ade~uate amount of a sample has been placed in a sample strip's reaction zone.
It is an object of an aspect of this invention to provide means for determining that a biological sample is reacting in a-ccordance with the Cottrell r~l~t;~nchlp during the course of the reaction and, if not, causing resulting readings to be ignored.
SUMMARY QF THE INVENTION
A biosensing meter receives a sample strip that includes electrically isolated sense and excitation electrodes bridged by a reaction zone. When a drop of biological sample fluid is placed in the reaction zone, a plurality of fail/safe tests are performed. A drop size test is performed by a circuit that detects the size of the drop ~ 5 2 1 53877 placed in the reaction zone. The circuit both detects that a drop has been placed in the reaction zone and further measures a test current level, after a delay, to determine that the drop size is sufficient to enable hydration of reactants in the reaction zone.
Subsequently, during the reaction, a "delta~ current change is measured at succeeding sample time. This test measures the difference between succeeding current samples during a measurement time. If each succeeding sample is not less than preceding sample by a delta value, a determination is made that the current is not monotonically decreasing and the test is aborted. At the termination of the measurement time, a current sum test is performed wherein a processor calculates a linear sum of all sample test currents and calculates a ratio between that sum and the last current sample. If that ratio matches a pre-calculated constant for the Cottrell relationship, then it is known that the measurement values exhibit the Cottrell relationship.
Another aspect of this invention is as follows:
A biosensing meter for receiving a sample strip that includes electrically isolated excitation and sense electrodes and a sample well bridging thereacross, with an analyte reactant resident therein, said biosensing meter comprising:
excitation supply means for applying an excitation potential to said excitation electrode;
sense amplifier means connected to said sense electrode for producing an output signal when a volume of a biological fluid is placed in said sample well and creates a current path between said excitation and sense electrode;
processor means coupled to said sense amplifier means for first, testing if said output signal exceeds a first threshold value and second, testing if said output B
5a 2 1 53877 signal thereafter exceeds a second, larger threshold value, an output signal that exceeds said first threshold value recognized as an indication of said volume in said sample cell, an output signal that exceeds said second larger threshold recognized as an indication that said volume is sufficient to enable a subsequent determination to be made for an analyte in said biological fluid, said processor means only enabling said subsequent determination after said second, larger threshold has been exceeded by said output signal.
DESCRIPTION OF THE DRAWINGS
Fig. 1 is a plan view of a sample strip.
Fig. 2 is a circuit/block diagram of a biosensing meter that embodies the invention hereof.
Fig. 3 is a wave form diagram illustrating both the excitation voltage applied to the excitation electrode on the sample strip of Fig. 1 and the resulting sense current from the sense electrode on the sample strip.
Fig. 4 is an ~r~n~Pd view of the sense current waveform 2s that occurs when a drop of analyte is initially detected.
Fig. 5 is an ~X~n~ view of a plurality of measured currents detected during the mea~u.~- nt period, which currents follow an expected Cottrell relationship.
~ 094/29706 2 1 ~ ~ 8 7 7 PCT~S94/05323 ~
Figs. 6 and 7 are high level flow diagrams illustrating the sample size, delta and current sum fail/safe tests performed by the circuit of the Fig. 2.
DETAILED DEscRlpTIoN OF THE TNVENTION
Referring to Fig. 1, a sample strip 10 comprises two electrodes, i_e., sense electrode 12 and excitation electrode 14.: Those electrodes are supported on a o polymeric sheet 16 and a cover sheet 18 is provided thereover and has openings 20 and Z1 which expose portions of electrodes 12 and 14. Opening ZO creates a sample well and defines a reaction zone between sense electrode 12 and excitation electrode 14. A layer (not shown) of enzymatic reactants overlays electrodes 12 and 14 in opening 20 and provides a substrate on which an analyte-containing fluid sample ~l~ced. In this example, it will be assumed that the analyte-containing sample is a drop of blood that is being subjected to a glucose determination. Opening 21 exposes electrodes 12 and 14 so that when sample strip 10 is inserted into a biosensing meter, electrical connection can be made thereto.
In Fig. 2, a schematically illustrated biosensing meter 22 includes a window (not shown) for accepting sample strip 10 and for enabling electrical connection to be made between excitation electrode 14 and a pair of contacts A and B and between sense electrode 12 and a pair of contacts C and D.
Excitation electrode 14, if it is continuous and properly inserted, electrically connects contacts A and B together.
similarly, sense electrode 12 electrically shorts contacts C and D if sample strip lo is properly inserted. Contacts A, B and C, D are spaced apart within biosensing meter 24 and enable a ~PtPnminAtion to be made that a sample strip 10 has been=properly inserted into meter 22 and that its electrodes reflect proper i -~nce states. Once such determinations indicate a properly inserted sample strip (with appropriate excitation and sense electrodes), sample ,. . .
CA 021~3877 1998-08-21 strip 10 may be dosed by application of a drop of blood to well 20 and subsequent measurements made.
An excitation supply 23 has its excitation voltage Ve applied via operational amplifier 24 and contact A to excitation electrode 14. A second input to operational amplifier 24 is fed from contact B via line 26. That same input is applied to analog to digital (A/D) converter 28 which, in turn, applies its digitized output onto bus 30. On the sense side of biosensing meter 22, contact C is connected to one input of operational amplifier 32. Another input to operational amplifier 32 is connected to a reference potential. The output from operational amplifier 32 is applied via A/D
converter 34 to bus 30.
Contact D is connected via conductor 36 and a multiplex switch 38 to A/D converter 40 whose output is, in turn, applied to bus 30. A supply voltage V is connected via a resistor to an input to A/D converter 40. Switch 38 is closed when meter 22 is initially powered so as to enable a determination to be made of the proper insertion of sense electrode 12. Once that determination is made, switch 38 is opened, thereby disabling the input to A/D converter 40.
A microprocessor 42 and an allied display 44 is connected to bus 30 and controls the overall operation of biosensing meter 22. Microprocessor 42, also, via line 46, controls the excitation voltage that is applied from supply 23 through operational amplifier 24 to contact A. An insertable read only memory (ROM) key 48 is interconnectable with bus 30 and enables the insertion of constants and other test parameters for use with a group of sample strips.
The operation of biosensing meter 22 in the sensing of proper insertion of sample strip 10 and the continuity of excitation and sense electrodes 14 and 12, respectively, is described in copending Canadian Patent Application Serial No. 2,153,883 to White et al., entitled "Biosensing Meter CA 021~3877 1998-08-21 which Detects Proper Electrode Engagement and Distinguishes Sample and Check Strips", filed on May 13, 1994.
Once microprocessor 42 determines that a sample strip is properly inserted and that sense and excitation electrodes 12 and 14 exhibit proper electrode continuities, excitation supply 23 is caused to apply an excitation voltage Ve to operational amplifier 24 and, in turn, to contact A. The waveform of excitation voltage Veis indicated in Fig.3 by trace 60. Initially, a high level voltage 62 is applied to excitation electrode 14 and a measurement is made of leakage current between excitation electrode 14 and sense electrode 12. If the leakage current is found to be within an acceptable range, microprocessor 42 indicates (on display 44~ that the user may apply a drop of blood to well 20. Upon application of the drop of blood, an immediate drop in resistance (i.e. an increase in current) is sensed between electrodes 12 and 14. The resulting output from operational amplifier 32 is indicated as pulse 64 of signal trace 66.
An expanded view of pulse 64 is shown in Fig. 4.
As pulse 64 passes through a first threshold 68, microprocessor 42 determines that a drop of blood has been detected, The level of threshold 68 is set at a low level so as to rapidly detect when a strip 10 is dosed with a blood sample and to thereby clearly indicate the commencement of an incubation period. Upon pulse 64 passing through threshold 68, a time delay d is commenced in microprocessor 42, at the termination of which a second delay d is employed to enable the drop of blood to wet the entire area within well 20. If the current sensed at time 70 is below a sample size threshold 72, the test is aborted as the volume of the blood drop is determined to be ~ W094/29706 21~ ~ 7 7 PCT~S94/05323 insufficient to assure complete hydration of the enzymatic reactants within well 20. By contrast, if the voltage (current) sensed at time 70 exceeds sample size threshold 72, the reaction is permitted to continue.
Shortly thereafter, microprocessor 42 causes the excitation voltage Ve from supply 22 to be removed from contact A
(trace 74 ln Fig. 3). Trace 74 is the "incubation" time and extends for a sufficient period of time to enable an lo enzymatic reaction to oocur between the blood drop and the enzymes in well 20.
Referring back to Fig. 3, at the termination of the incubation time an excitation voltage V, (trace 76) is again applied to contact A causing a reverse reaction in well 20. The resulting current (trace 78) is sensed at sense electrode 12. Fig. 5 is an enlarged showing of trace 78 and illustrates the classic Cottrell relationship exhibited by current flow during the above noted reverse reaction. In Fig. 5, sense current is plotted against elapsed time and, as known in the art, trace 78 is either displaced upwardly or downwardly in the plot of Fig. 5, p~n~ing upon glucose concentration. During the period of trace 78, microprocessor 42 records a plurality of current measurement values, each value taken a time interval with k being the interval count. Those measurements both enable a glucose determination to be made, and are used to assure that trace 78 is, in fact, following the Cottrell relationship.
A~5llming a glucose concentration determination is to be made, well 20 includes the following reactants: an enzyme, an electrolyte, a mediator, film formers, and a buffer.
For instance, the enzyme may be glucose oxidase (or glucose dehydrogenase); the buffer may be organic or inorganic; the electrolyte may be potassium chloride or sodium chloride;
the mediator is preferably potassium ferricyanide and the film formers comprise gelatin and propiofin. If the test W094~9706 PCT/US9410~ -21~3877 cell is to be employed for a cholesterol concentration determination, the enzyme would preferably be cholesterol oxidase with or without a cholesterol esterase additive.
The buffer is preferably inorganic and includes an electrolyte such as potassium chloride or sodium chloride.
In this case, two mediators are used, i.e. ferricyanide and quinones, and are placed in a gelatin film, as indicated above.
As the chemistries employed by this system are known in the art, they will not be described in further detail. Suffice to say that glucose concentration is det~rm;n~d by initially emplacing in well 20, a sample of blood. The glucose within the sample causes a forward reaction of potassium ferricyanide to potassium ferrocyanide. When the forward reaction has proceeded to completion during the incubation period, a subsequent application of a voltage (trace 76) to excitation electrode 14 will see the creation of a small current at sense electrode 12 that results from a reverse reaction of potassium ferrocyanide back to potassium ferricyanide. The flow of electrons during the reverse reaction (trace 78) is sensed and measured.
Turning to Figs. 6 and 7, the operation of the meter of Fig. 2 will be described. Initially (Fig. 6), miuLu~luc~ssor 42 detects an insertion of a sample strip 10 by sensing the electrical shorting of contacts A and B and contacts C and D ~decision box 100). Until microprocessor 42 detects the presence of sample strip 10, the procedures recycles. Upon sensing the presence of sample strip 10 and det~rmining that the contact resistances between contacts A, B and C, D, respectively, are within proper limits, microprocessor 42 causes excitation supply 23 to apply excitation voltage level 62 (Fig. 3) to excitation electrode 14. This application occurs prior to qny dosage of sample strip 10 and enables the leakage current (if any) between electrodes 12 and 14 to be measured.
Simultaneously, microprocessor 42 obtains a leakage current ~ 2153877 W094/29706 PCT~S9410~323 threshold value (i~x) from ROM key 48 and compares its value with a measured leakage current i fed from A/D
converter 34 (boxes 102 and 104). If the leakage current i is less than the threshold leakage current value (i~x) the procedure continues, as the leakage current is within limits. If not, the sample strip is rejected.
At this point, microprocessor 42 enters a "drop detect"
state wherein it is determined when a blood drop has been positioned in well 20 and whether the volume of the blood drop is sufficient to completely wet the enzymatic reactants positioned therein. Initially, microprocessor 42 loads a pair of constants from ROM key 48, i.e., a drop detect threshold value and a sample size threshold value (72). Microprocessor 42 then adds the measured leakage current value i to the drop detect threshold valuè to determine drop detect threshold 68 shown in Fig. 4 (box 106). Then, microprocessor 48 causes display 44 to indicate to the user that the sample strip is ready for dosing.
Microprocessor 42 now enters a wait state (with excitation voltage level 62 continuing to be applied to excitation electrode 14). When a blood drop is applied to well 20, a current increase is sensed (pulse 64 in Fig. 4), and when the measured current value exceeds threshold 68, a drop is indicated as having been detected (decision box 108). An incubation timing period now r~ which, for example, may be nine seconds. A sample size delay period d is also started, after which a second measurement is taken of pulse 64 (box 110). If the detected current exceeds sample size threshold 72, then it is known that sufficient blood is present in well 20 to hydrate the enzyme reactants positioned therein (decision box 112). If not, an error is indicated. If yes, the procedure continues, with microprocessor 42 causing the removal of excitation voltage V, from contact A (box 114).
W094l29706 PCT~S94105323 -After expiration of the incubation time period, microprocessor 42 causes excitation supply 23 to apply an excitation voltage (trace 76 in Fig. 3) to contact A (box 116). The application of Ve level 76 causes a reversal of the enzymatic reaction referred to above and results in a current flow (shown by trace 78 in Fig. 3) between excitation electrode 14 and sense electrode 12. At this point, a "measurement period" commences and, as shown in Fig. 5, a number of current measurements 82, 84, 86 etc, lo are taken (until measurement 88) and the results are stored (see Fig. 5 and box 118, Fig. 7). Each mea~uL~ ~ is taken after a time interval associated with count k. In Fig. 5, fourteen such time intervals are shown, with current measurements not being taken until the end of the second interval to prevent the resulting current reading from P~nee~;ng a maximum measurable current.
During the time when current values 82, 84, 86 etc. are being measured, a "delta" fail/safe calculation occurs after the second current measurement and then after each sunnp~ing current measurement (box 120). In essence, it is known that if trace 78 follows a Cottrell curve, it monotonically decreases and each su~c~P~ing current measurement is less than a preceding current measurement by at least a predetermined delta fail/safe threshold value.
That value is obtained ~rom R0~ key 48 and is ACcpcqpd by microprocessor 42.
As shown in decision box 120, microprocessor 42 detPrmln~c that each s~tncep~ing sense current ik is less than or equal to a preceding sampled current value (ik1) plus the delta fail/safe threshold value. If a sncceP~;ng sense current value does not meet that test, an abort message is sent to the user (via display 44) based on the ~etPrminAtion that the current waveform is not exhibiting an expected monotonic relationship. This test is repeated for each s~cc~P~ing current sample, including last current sample 88. ~ntil then, the procedure repeats as shown by decision ~ W094/29706 21 ~ 7 PCT~S94/05323 box 124.
Once current measurement 88 has been taken, the procedure moves to a "current sum" fail/safe determination. The current sum fail/safe procedure performs another check on the Cottrell response during the mea~ul~ L period. When the final current sample 88 is acquired, it is multiplied by two constants (i.e. values) that are accessed by microprocessor 42 from RO~ key 48. The results of the multiplication are then used as two limit values against which a sum of all of sensed currents 82, 84, 86 etc. is tested. If thq sum falls between the two limits, it is known that trace 78 follows the Cottrell relationship.
These actions are illustrated in boxes 122, 124, 126 and 128 in Fig. 7. Current sum IDUm is calculated as follows (box 122) m =~, ik k~l where ik is one of m current samples Then it is determined whether I~Um falls within upper and lower limits as follows (box 128) im KU > I5Um > im Kl ~5 where K~ is the lower limit constant, KU is the upper limit constant, and im is the final current sample.
If the test shown in decision box 128 is not met, an abort signal is issued. However, if the test is met, then a glucose calculation follows (box 130), with the result displayed to the user.
The basis of the current sum fail/safe test can be det~rmin~d from the following proof.
W094/29706 PCT~S94/OS323 ~
21~3877 Initially, consider the ratio r r = k-l ~A) of all sensed currents to the final sensed current.
It is to be proved, for any current trace with a Cottrell behavior, that the ratio has the same value rcOttrell in~p~n~nt of any factors (including glucose concentration).
The Cottrell response characteristic is given by equation (B) iCoctr~ll ( t) = nFA~D C (B) where: n is the number of electrons freed per glucose molecuIe F is Faraday's Constant A is the working electrode surface area t is elapsed time since application of excitation D is the diffusion coefficient C is the glucose concentration Of the above-listed parameters, n an F are constants, A is det~rmin~d by strip design, D and C while possibly varying from trace to trace, stay constant within the duration of a current trace for a given test. Thus, all parameters of equation B, except for time t are constant for a given current trace.
By replacement of current terms ik in equation (A) by their ~ W094/29706 21~ 3 8 7 7 PCT~S94/0~323 Cottrell representations from eguation (B), the following expression is obtained ~ nP~ c k~
rcotcrell nFA C (C) By removing the constant terms in the numerator and ,n, in~tor, expression (C) becomes:
rcottroll = k=l ~ (D) Considering expression (D), it can be concluded that if a trace has Cottrell behavior, then the ratio r shown in equation A calculated with this trace's currents must be equal to rCOttre~l. Inversely, if a trace has non-Cottrell behavior, then the corresponding ratio r from equation (A) is different from rcottre~l The Cottrell model (B), while very accurate, is still a model, therefore in practice there might be a small difference between r and rCOttrell for a trace with Cottrell behavior. In order to allow for this difference the calculated ratio r, instead of rh~ing on an exact equality to rcOttrell~ is compared with an upper limit rCottrell ~ -r ll and a lower limit rCottrell-~l~rcottrell~ where ~u and ~l are small numbers.
The following inrqn~lity rcottrell + CU rcottrel~ > r > rcottre~ I r tt 11 W094/29706 2 ~ ~ 3 8 ~ 7 PCT~S94/05323 -is equivalent to the following comparison:
m (rcoCCrol~+~urcocCrell) *il~>~ ik> (rCOCC~ell ~1 rcotcrell) *im (~) by denoting Ku (rcottrell + eu rcOttrell) * im Kl = (rcottrell - cl rcOttrell) * im ;~ql-~llty (E) becomes ineguality (F) m Ku > 2 i ~C > Kl ( F) k=l which is used as a failsafe test as shown in Fig. 7 (Box 128).
It should be understood that the foregoing description is only illustrative of the invention. Various alternatives and modifications can be devised by those skilled in the art without departing from the invention. Accordingly, the present invention is intended to embrace all such alternatives, mcdifications and variances which fall within the scope of the appended claims.
1 0 ( I
W094l29706 PCTIUS9~/0 BIOSFNSIIIG METER WITII FAIL/SAFE PROCEDURES
TO PREVENT ERRONEOUS INDICATIONS
FIELD oF TIIE INVENTION
This invention relates to biosensing meters that employ disposable sample strips, and more particularly, to fail/safe systems and procedures for preventing such meters from issuing erroneous results.
~ACKGROUND OF TI~E INVENTION
Biosensing in~LLI ants that employ disposable sample strips enjoy wide r?nq-lr~r acceptance. Such inaLL, Ls are employed for the detection of various analyte levels in blood samples, e.g., glucose and cholesterol. In general, such instruments provide accurate readings if the user is careful to follow the in~LL~ L's directions. Often however, the user is careless in the use of either the sample strip or the inaLL~ -nt and an erroneous reading results. Accordingly, significant efforts have been taken by instrument manufacturers to reduce the potential for errors during the use of such instruments.
Even if a biosensing instrument and sample strips are employed properly, the presence of a manufacturing defect in either will cause erroneous readings. Thus, while great care is taken in the production of such in~LL, -nts and sample strips, there is a need to incorporate analytical procedures in the instrument that enable instrument malfunctions, sample strip irregularities and user errors to be detected so as to prevent erroneous analyte readings.
The prior art includes a number of disclosures of biosensing instruments that employ disposable sample strips. In U.S. Patent 5,108,564 to Szuminsky et al., a biosensing instrument is disclosed that measures glucose concentrations in blood. The in~LL~ -nt depends upon a reaction wherein glucose, in the presence of an enzyme, CA 021~3877 1998-08-21 catalyzes a reaction of potassium ferricyanide to potassium ferrocyanide. After the reaction has completed, a voltage is applied across a reaction zone and causes a reversal of the reaction with an accompanying generation of a small but measurable current. That current is termed the Cottrell current and, in dependence upon the concentration of glucose in the reaction zone, follows a predetermined curve during the reverse reaction. A reading of the Cottrell current is converted into an indication of glucose concentration. The instrument also senses an impedance across the reaction zone and determines when a blood sample has been emplaced therein by detecting a sudden change in current flow. At such time, an incubation period is commenced, followed by application of a potential across the reaction zone and measurement of the Cottrell current.
European Patent Application 0 471 986 A2 of Tsutsumi et al.
discloses a blood glucose measurement system that employs disposable sample strips. The Tsutsumi et al. system detects the presence of a blood sample by sensing a resistance across a pair of electrodes. It further employs a plurality of sample-like strips, each having a specific resistance value which distinguishes it from other strips.
Each of those strips has a particular application, i.e., for use during an adjustment mode of the instrument, during an error compensation mode, during a calibration mode, etc.
U.S. Patent 4,999,582 to Parks et al., assigned to the same Assignee as this application, describes a biosensor electrode excitation circuit for determining if a sample strip has been properly inserted into a meter and if at least one electrode on the sample strip exhibits a proper level of contact resistance.
Canadian Patent Application Serial No. 2071484, filed December 14, 1990 to White, entitled "Biosensing Instrument and Method" and assigned to the same assignee as this application, teaches a biosensing instrument which employs , ~3~77 ~r W094/29706 PCT~S94/OS323 . . .
~ -3 the "Cottrell" curve relationship to determine glucose concentrations. In that instrument, current flow is proportional to the concentration of an analyte in the test cell; however, when something is amiss in the test cell, the current that results may bear no relationship whatever to analyte concentration. White found that a relationship exists that enables a determination to be made whether current flow through a reaction zone is, in fact, following the Cottrell relationship. More specifically, the ratio of the square roots of s~rceP~;ng sample times, for all analyte concentration curves, has been found to inversely approximate the ratio of the measured Cottrell currents at those same sample times. If over surr~ing time periods, the ratios are equal (within limits), the measurement system is properly following the Cottrell relatinnch;r. If the ratios found are not equal, the mea~u~ is disregarded.
U.S. Patent 4,940,945 to Littlejohn et al. describes an interface circuit for use in a biochemical sensing instrument. A disposable cartridge is employed that includes a pair of electrodes across which resistance measurements are taken. Circuitry is disclosed for sensing the presence of a fluid sample by an initial resistance measurement, and also the level of fluid in the cartridge.
U.S. Patent 4,420,564 to Tsuji et al. describes a blood sugar analyzer that employs a reaction cell having a fixed enzyme membrane sensor and a measuring electrode. The Tsuji et al: system includes several fail/safe procedures, one to determine that the reaction is taking place within specifically defined temperature limits and a second to determine that the reaction current remains within a prede~rm; n~d range.
. .
The above noted prior art indicates that biosensing meters have had the ability to determine when a biological sample is placed in a reaction zone. Xowever, the prior art has not addressed the problem of the presence of an insufficient amount of the sample to fully wet enzymatic reactants present in a reaction zone.
Furthermore, while a test is available to determine that a reaction is following the Cottrell relationship (as described in the aforesaid patent application to White), additional confirming, tests are desirable to assure that the reaction is in fact, following the Cottrell relationship.
~ Accordingly, it is an object of an aspect of this invention to provide a biosensing meter with means for~ 15 performing a plurality of fail/safe tests during the course of an analysis of a biological sample.
It is an object of an aspect of this invention to provide a biosensing meter with means for determining that ade~uate amount of a sample has been placed in a sample strip's reaction zone.
It is an object of an aspect of this invention to provide means for determining that a biological sample is reacting in a-ccordance with the Cottrell r~l~t;~nchlp during the course of the reaction and, if not, causing resulting readings to be ignored.
SUMMARY QF THE INVENTION
A biosensing meter receives a sample strip that includes electrically isolated sense and excitation electrodes bridged by a reaction zone. When a drop of biological sample fluid is placed in the reaction zone, a plurality of fail/safe tests are performed. A drop size test is performed by a circuit that detects the size of the drop ~ 5 2 1 53877 placed in the reaction zone. The circuit both detects that a drop has been placed in the reaction zone and further measures a test current level, after a delay, to determine that the drop size is sufficient to enable hydration of reactants in the reaction zone.
Subsequently, during the reaction, a "delta~ current change is measured at succeeding sample time. This test measures the difference between succeeding current samples during a measurement time. If each succeeding sample is not less than preceding sample by a delta value, a determination is made that the current is not monotonically decreasing and the test is aborted. At the termination of the measurement time, a current sum test is performed wherein a processor calculates a linear sum of all sample test currents and calculates a ratio between that sum and the last current sample. If that ratio matches a pre-calculated constant for the Cottrell relationship, then it is known that the measurement values exhibit the Cottrell relationship.
Another aspect of this invention is as follows:
A biosensing meter for receiving a sample strip that includes electrically isolated excitation and sense electrodes and a sample well bridging thereacross, with an analyte reactant resident therein, said biosensing meter comprising:
excitation supply means for applying an excitation potential to said excitation electrode;
sense amplifier means connected to said sense electrode for producing an output signal when a volume of a biological fluid is placed in said sample well and creates a current path between said excitation and sense electrode;
processor means coupled to said sense amplifier means for first, testing if said output signal exceeds a first threshold value and second, testing if said output B
5a 2 1 53877 signal thereafter exceeds a second, larger threshold value, an output signal that exceeds said first threshold value recognized as an indication of said volume in said sample cell, an output signal that exceeds said second larger threshold recognized as an indication that said volume is sufficient to enable a subsequent determination to be made for an analyte in said biological fluid, said processor means only enabling said subsequent determination after said second, larger threshold has been exceeded by said output signal.
DESCRIPTION OF THE DRAWINGS
Fig. 1 is a plan view of a sample strip.
Fig. 2 is a circuit/block diagram of a biosensing meter that embodies the invention hereof.
Fig. 3 is a wave form diagram illustrating both the excitation voltage applied to the excitation electrode on the sample strip of Fig. 1 and the resulting sense current from the sense electrode on the sample strip.
Fig. 4 is an ~r~n~Pd view of the sense current waveform 2s that occurs when a drop of analyte is initially detected.
Fig. 5 is an ~X~n~ view of a plurality of measured currents detected during the mea~u.~- nt period, which currents follow an expected Cottrell relationship.
~ 094/29706 2 1 ~ ~ 8 7 7 PCT~S94/05323 ~
Figs. 6 and 7 are high level flow diagrams illustrating the sample size, delta and current sum fail/safe tests performed by the circuit of the Fig. 2.
DETAILED DEscRlpTIoN OF THE TNVENTION
Referring to Fig. 1, a sample strip 10 comprises two electrodes, i_e., sense electrode 12 and excitation electrode 14.: Those electrodes are supported on a o polymeric sheet 16 and a cover sheet 18 is provided thereover and has openings 20 and Z1 which expose portions of electrodes 12 and 14. Opening ZO creates a sample well and defines a reaction zone between sense electrode 12 and excitation electrode 14. A layer (not shown) of enzymatic reactants overlays electrodes 12 and 14 in opening 20 and provides a substrate on which an analyte-containing fluid sample ~l~ced. In this example, it will be assumed that the analyte-containing sample is a drop of blood that is being subjected to a glucose determination. Opening 21 exposes electrodes 12 and 14 so that when sample strip 10 is inserted into a biosensing meter, electrical connection can be made thereto.
In Fig. 2, a schematically illustrated biosensing meter 22 includes a window (not shown) for accepting sample strip 10 and for enabling electrical connection to be made between excitation electrode 14 and a pair of contacts A and B and between sense electrode 12 and a pair of contacts C and D.
Excitation electrode 14, if it is continuous and properly inserted, electrically connects contacts A and B together.
similarly, sense electrode 12 electrically shorts contacts C and D if sample strip lo is properly inserted. Contacts A, B and C, D are spaced apart within biosensing meter 24 and enable a ~PtPnminAtion to be made that a sample strip 10 has been=properly inserted into meter 22 and that its electrodes reflect proper i -~nce states. Once such determinations indicate a properly inserted sample strip (with appropriate excitation and sense electrodes), sample ,. . .
CA 021~3877 1998-08-21 strip 10 may be dosed by application of a drop of blood to well 20 and subsequent measurements made.
An excitation supply 23 has its excitation voltage Ve applied via operational amplifier 24 and contact A to excitation electrode 14. A second input to operational amplifier 24 is fed from contact B via line 26. That same input is applied to analog to digital (A/D) converter 28 which, in turn, applies its digitized output onto bus 30. On the sense side of biosensing meter 22, contact C is connected to one input of operational amplifier 32. Another input to operational amplifier 32 is connected to a reference potential. The output from operational amplifier 32 is applied via A/D
converter 34 to bus 30.
Contact D is connected via conductor 36 and a multiplex switch 38 to A/D converter 40 whose output is, in turn, applied to bus 30. A supply voltage V is connected via a resistor to an input to A/D converter 40. Switch 38 is closed when meter 22 is initially powered so as to enable a determination to be made of the proper insertion of sense electrode 12. Once that determination is made, switch 38 is opened, thereby disabling the input to A/D converter 40.
A microprocessor 42 and an allied display 44 is connected to bus 30 and controls the overall operation of biosensing meter 22. Microprocessor 42, also, via line 46, controls the excitation voltage that is applied from supply 23 through operational amplifier 24 to contact A. An insertable read only memory (ROM) key 48 is interconnectable with bus 30 and enables the insertion of constants and other test parameters for use with a group of sample strips.
The operation of biosensing meter 22 in the sensing of proper insertion of sample strip 10 and the continuity of excitation and sense electrodes 14 and 12, respectively, is described in copending Canadian Patent Application Serial No. 2,153,883 to White et al., entitled "Biosensing Meter CA 021~3877 1998-08-21 which Detects Proper Electrode Engagement and Distinguishes Sample and Check Strips", filed on May 13, 1994.
Once microprocessor 42 determines that a sample strip is properly inserted and that sense and excitation electrodes 12 and 14 exhibit proper electrode continuities, excitation supply 23 is caused to apply an excitation voltage Ve to operational amplifier 24 and, in turn, to contact A. The waveform of excitation voltage Veis indicated in Fig.3 by trace 60. Initially, a high level voltage 62 is applied to excitation electrode 14 and a measurement is made of leakage current between excitation electrode 14 and sense electrode 12. If the leakage current is found to be within an acceptable range, microprocessor 42 indicates (on display 44~ that the user may apply a drop of blood to well 20. Upon application of the drop of blood, an immediate drop in resistance (i.e. an increase in current) is sensed between electrodes 12 and 14. The resulting output from operational amplifier 32 is indicated as pulse 64 of signal trace 66.
An expanded view of pulse 64 is shown in Fig. 4.
As pulse 64 passes through a first threshold 68, microprocessor 42 determines that a drop of blood has been detected, The level of threshold 68 is set at a low level so as to rapidly detect when a strip 10 is dosed with a blood sample and to thereby clearly indicate the commencement of an incubation period. Upon pulse 64 passing through threshold 68, a time delay d is commenced in microprocessor 42, at the termination of which a second delay d is employed to enable the drop of blood to wet the entire area within well 20. If the current sensed at time 70 is below a sample size threshold 72, the test is aborted as the volume of the blood drop is determined to be ~ W094/29706 21~ ~ 7 7 PCT~S94/05323 insufficient to assure complete hydration of the enzymatic reactants within well 20. By contrast, if the voltage (current) sensed at time 70 exceeds sample size threshold 72, the reaction is permitted to continue.
Shortly thereafter, microprocessor 42 causes the excitation voltage Ve from supply 22 to be removed from contact A
(trace 74 ln Fig. 3). Trace 74 is the "incubation" time and extends for a sufficient period of time to enable an lo enzymatic reaction to oocur between the blood drop and the enzymes in well 20.
Referring back to Fig. 3, at the termination of the incubation time an excitation voltage V, (trace 76) is again applied to contact A causing a reverse reaction in well 20. The resulting current (trace 78) is sensed at sense electrode 12. Fig. 5 is an enlarged showing of trace 78 and illustrates the classic Cottrell relationship exhibited by current flow during the above noted reverse reaction. In Fig. 5, sense current is plotted against elapsed time and, as known in the art, trace 78 is either displaced upwardly or downwardly in the plot of Fig. 5, p~n~ing upon glucose concentration. During the period of trace 78, microprocessor 42 records a plurality of current measurement values, each value taken a time interval with k being the interval count. Those measurements both enable a glucose determination to be made, and are used to assure that trace 78 is, in fact, following the Cottrell relationship.
A~5llming a glucose concentration determination is to be made, well 20 includes the following reactants: an enzyme, an electrolyte, a mediator, film formers, and a buffer.
For instance, the enzyme may be glucose oxidase (or glucose dehydrogenase); the buffer may be organic or inorganic; the electrolyte may be potassium chloride or sodium chloride;
the mediator is preferably potassium ferricyanide and the film formers comprise gelatin and propiofin. If the test W094~9706 PCT/US9410~ -21~3877 cell is to be employed for a cholesterol concentration determination, the enzyme would preferably be cholesterol oxidase with or without a cholesterol esterase additive.
The buffer is preferably inorganic and includes an electrolyte such as potassium chloride or sodium chloride.
In this case, two mediators are used, i.e. ferricyanide and quinones, and are placed in a gelatin film, as indicated above.
As the chemistries employed by this system are known in the art, they will not be described in further detail. Suffice to say that glucose concentration is det~rm;n~d by initially emplacing in well 20, a sample of blood. The glucose within the sample causes a forward reaction of potassium ferricyanide to potassium ferrocyanide. When the forward reaction has proceeded to completion during the incubation period, a subsequent application of a voltage (trace 76) to excitation electrode 14 will see the creation of a small current at sense electrode 12 that results from a reverse reaction of potassium ferrocyanide back to potassium ferricyanide. The flow of electrons during the reverse reaction (trace 78) is sensed and measured.
Turning to Figs. 6 and 7, the operation of the meter of Fig. 2 will be described. Initially (Fig. 6), miuLu~luc~ssor 42 detects an insertion of a sample strip 10 by sensing the electrical shorting of contacts A and B and contacts C and D ~decision box 100). Until microprocessor 42 detects the presence of sample strip 10, the procedures recycles. Upon sensing the presence of sample strip 10 and det~rmining that the contact resistances between contacts A, B and C, D, respectively, are within proper limits, microprocessor 42 causes excitation supply 23 to apply excitation voltage level 62 (Fig. 3) to excitation electrode 14. This application occurs prior to qny dosage of sample strip 10 and enables the leakage current (if any) between electrodes 12 and 14 to be measured.
Simultaneously, microprocessor 42 obtains a leakage current ~ 2153877 W094/29706 PCT~S9410~323 threshold value (i~x) from ROM key 48 and compares its value with a measured leakage current i fed from A/D
converter 34 (boxes 102 and 104). If the leakage current i is less than the threshold leakage current value (i~x) the procedure continues, as the leakage current is within limits. If not, the sample strip is rejected.
At this point, microprocessor 42 enters a "drop detect"
state wherein it is determined when a blood drop has been positioned in well 20 and whether the volume of the blood drop is sufficient to completely wet the enzymatic reactants positioned therein. Initially, microprocessor 42 loads a pair of constants from ROM key 48, i.e., a drop detect threshold value and a sample size threshold value (72). Microprocessor 42 then adds the measured leakage current value i to the drop detect threshold valuè to determine drop detect threshold 68 shown in Fig. 4 (box 106). Then, microprocessor 48 causes display 44 to indicate to the user that the sample strip is ready for dosing.
Microprocessor 42 now enters a wait state (with excitation voltage level 62 continuing to be applied to excitation electrode 14). When a blood drop is applied to well 20, a current increase is sensed (pulse 64 in Fig. 4), and when the measured current value exceeds threshold 68, a drop is indicated as having been detected (decision box 108). An incubation timing period now r~ which, for example, may be nine seconds. A sample size delay period d is also started, after which a second measurement is taken of pulse 64 (box 110). If the detected current exceeds sample size threshold 72, then it is known that sufficient blood is present in well 20 to hydrate the enzyme reactants positioned therein (decision box 112). If not, an error is indicated. If yes, the procedure continues, with microprocessor 42 causing the removal of excitation voltage V, from contact A (box 114).
W094l29706 PCT~S94105323 -After expiration of the incubation time period, microprocessor 42 causes excitation supply 23 to apply an excitation voltage (trace 76 in Fig. 3) to contact A (box 116). The application of Ve level 76 causes a reversal of the enzymatic reaction referred to above and results in a current flow (shown by trace 78 in Fig. 3) between excitation electrode 14 and sense electrode 12. At this point, a "measurement period" commences and, as shown in Fig. 5, a number of current measurements 82, 84, 86 etc, lo are taken (until measurement 88) and the results are stored (see Fig. 5 and box 118, Fig. 7). Each mea~uL~ ~ is taken after a time interval associated with count k. In Fig. 5, fourteen such time intervals are shown, with current measurements not being taken until the end of the second interval to prevent the resulting current reading from P~nee~;ng a maximum measurable current.
During the time when current values 82, 84, 86 etc. are being measured, a "delta" fail/safe calculation occurs after the second current measurement and then after each sunnp~ing current measurement (box 120). In essence, it is known that if trace 78 follows a Cottrell curve, it monotonically decreases and each su~c~P~ing current measurement is less than a preceding current measurement by at least a predetermined delta fail/safe threshold value.
That value is obtained ~rom R0~ key 48 and is ACcpcqpd by microprocessor 42.
As shown in decision box 120, microprocessor 42 detPrmln~c that each s~tncep~ing sense current ik is less than or equal to a preceding sampled current value (ik1) plus the delta fail/safe threshold value. If a sncceP~;ng sense current value does not meet that test, an abort message is sent to the user (via display 44) based on the ~etPrminAtion that the current waveform is not exhibiting an expected monotonic relationship. This test is repeated for each s~cc~P~ing current sample, including last current sample 88. ~ntil then, the procedure repeats as shown by decision ~ W094/29706 21 ~ 7 PCT~S94/05323 box 124.
Once current measurement 88 has been taken, the procedure moves to a "current sum" fail/safe determination. The current sum fail/safe procedure performs another check on the Cottrell response during the mea~ul~ L period. When the final current sample 88 is acquired, it is multiplied by two constants (i.e. values) that are accessed by microprocessor 42 from RO~ key 48. The results of the multiplication are then used as two limit values against which a sum of all of sensed currents 82, 84, 86 etc. is tested. If thq sum falls between the two limits, it is known that trace 78 follows the Cottrell relationship.
These actions are illustrated in boxes 122, 124, 126 and 128 in Fig. 7. Current sum IDUm is calculated as follows (box 122) m =~, ik k~l where ik is one of m current samples Then it is determined whether I~Um falls within upper and lower limits as follows (box 128) im KU > I5Um > im Kl ~5 where K~ is the lower limit constant, KU is the upper limit constant, and im is the final current sample.
If the test shown in decision box 128 is not met, an abort signal is issued. However, if the test is met, then a glucose calculation follows (box 130), with the result displayed to the user.
The basis of the current sum fail/safe test can be det~rmin~d from the following proof.
W094/29706 PCT~S94/OS323 ~
21~3877 Initially, consider the ratio r r = k-l ~A) of all sensed currents to the final sensed current.
It is to be proved, for any current trace with a Cottrell behavior, that the ratio has the same value rcOttrell in~p~n~nt of any factors (including glucose concentration).
The Cottrell response characteristic is given by equation (B) iCoctr~ll ( t) = nFA~D C (B) where: n is the number of electrons freed per glucose molecuIe F is Faraday's Constant A is the working electrode surface area t is elapsed time since application of excitation D is the diffusion coefficient C is the glucose concentration Of the above-listed parameters, n an F are constants, A is det~rmin~d by strip design, D and C while possibly varying from trace to trace, stay constant within the duration of a current trace for a given test. Thus, all parameters of equation B, except for time t are constant for a given current trace.
By replacement of current terms ik in equation (A) by their ~ W094/29706 21~ 3 8 7 7 PCT~S94/0~323 Cottrell representations from eguation (B), the following expression is obtained ~ nP~ c k~
rcotcrell nFA C (C) By removing the constant terms in the numerator and ,n, in~tor, expression (C) becomes:
rcottroll = k=l ~ (D) Considering expression (D), it can be concluded that if a trace has Cottrell behavior, then the ratio r shown in equation A calculated with this trace's currents must be equal to rCOttre~l. Inversely, if a trace has non-Cottrell behavior, then the corresponding ratio r from equation (A) is different from rcottre~l The Cottrell model (B), while very accurate, is still a model, therefore in practice there might be a small difference between r and rCOttrell for a trace with Cottrell behavior. In order to allow for this difference the calculated ratio r, instead of rh~ing on an exact equality to rcOttrell~ is compared with an upper limit rCottrell ~ -r ll and a lower limit rCottrell-~l~rcottrell~ where ~u and ~l are small numbers.
The following inrqn~lity rcottrell + CU rcottrel~ > r > rcottre~ I r tt 11 W094/29706 2 ~ ~ 3 8 ~ 7 PCT~S94/05323 -is equivalent to the following comparison:
m (rcoCCrol~+~urcocCrell) *il~>~ ik> (rCOCC~ell ~1 rcotcrell) *im (~) by denoting Ku (rcottrell + eu rcOttrell) * im Kl = (rcottrell - cl rcOttrell) * im ;~ql-~llty (E) becomes ineguality (F) m Ku > 2 i ~C > Kl ( F) k=l which is used as a failsafe test as shown in Fig. 7 (Box 128).
It should be understood that the foregoing description is only illustrative of the invention. Various alternatives and modifications can be devised by those skilled in the art without departing from the invention. Accordingly, the present invention is intended to embrace all such alternatives, mcdifications and variances which fall within the scope of the appended claims.
Claims (4)
1. A biosensing meter for receiving a sample strip that includes electrically isolated excitation and sense electrodes and a sample well bridging thereacross, with an analyte reactant resident therein, said biosensing meter comprising:
excitation supply means for applying an excitation potential to said excitation electrode;
sense amplifier means connected to said sense electrode for producing an output signal when a volume of a biological fluid is placed in said sample well and creates a current path between said excitation and sense electrode;
processor means coupled to said sense amplifier means for first, testing if said output signal exceeds a first threshold value and second, testing if said output signal thereafter exceeds a second, larger threshold value, an output signal that exceeds said first threshold value recognized as an indication of said volume in said sample cell, an output signal that exceeds said second larger threshold recognized as an indication that said volume is sufficient to enable a subsequent determination to be made for an analyte in said biological fluid, said processor means only enabling said subsequent determination after said second, larger threshold has been exceeded by said output signal.
excitation supply means for applying an excitation potential to said excitation electrode;
sense amplifier means connected to said sense electrode for producing an output signal when a volume of a biological fluid is placed in said sample well and creates a current path between said excitation and sense electrode;
processor means coupled to said sense amplifier means for first, testing if said output signal exceeds a first threshold value and second, testing if said output signal thereafter exceeds a second, larger threshold value, an output signal that exceeds said first threshold value recognized as an indication of said volume in said sample cell, an output signal that exceeds said second larger threshold recognized as an indication that said volume is sufficient to enable a subsequent determination to be made for an analyte in said biological fluid, said processor means only enabling said subsequent determination after said second, larger threshold has been exceeded by said output signal.
2. The biosensing meter as recited in Claim 1 wherein said processor performs said second test only after a preset delay, said delay sufficient to enable said volume of biological fluid to substantially wet said analyte reactant.
3. The biosensing meter as recited in Claim 1, wherein said amplifier means produces a leakage signal value prior to placement of said volume of biological fluid in said sample well, said leakage signal value indicative of a leakage current between said excitation and sense electrodes, said biosensing meter further comprising:
key means containing a memory with stored values, said stored values including a leakage current threshold value, a drop detect threshold value, and a said second threshold value;
whereby said processor means determines if said leakage current value exceeds said leakage current threshold value and, if not, adds said leakage current value to said drop detect threshold value to derive said first threshold.
key means containing a memory with stored values, said stored values including a leakage current threshold value, a drop detect threshold value, and a said second threshold value;
whereby said processor means determines if said leakage current value exceeds said leakage current threshold value and, if not, adds said leakage current value to said drop detect threshold value to derive said first threshold.
4. The biosensing meter as recited in Claim 3 wherein said processor means employs said second threshold values from said key means upon a determination that said volume is sufficient to enable said subsequent determination.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CA002175501A CA2175501C (en) | 1993-06-08 | 1994-05-13 | Biosensing meter with fail/safe procedures to prevent erroneous indications |
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US08/073,180 US5352351A (en) | 1993-06-08 | 1993-06-08 | Biosensing meter with fail/safe procedures to prevent erroneous indications |
| US08/073,180 | 1993-06-08 | ||
| PCT/US1994/005323 WO1994029706A1 (en) | 1993-06-08 | 1994-05-13 | Biosensing meter with fail/safe procedures to prevent erroneous indications |
Related Child Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002175501A Division CA2175501C (en) | 1993-06-08 | 1994-05-13 | Biosensing meter with fail/safe procedures to prevent erroneous indications |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2153877A1 CA2153877A1 (en) | 1994-12-22 |
| CA2153877C true CA2153877C (en) | 1999-06-15 |
Family
ID=22112218
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002153877A Expired - Lifetime CA2153877C (en) | 1993-06-08 | 1994-05-13 | Biosensing meter with fail/safe procedures to prevent erroneous indications |
Country Status (8)
| Country | Link |
|---|---|
| US (1) | US5352351A (en) |
| EP (2) | EP1582864B1 (en) |
| JP (1) | JP2800981B2 (en) |
| AU (1) | AU6832594A (en) |
| CA (1) | CA2153877C (en) |
| DE (3) | DE69434438T2 (en) |
| ES (2) | ES2270401T3 (en) |
| WO (1) | WO1994029706A1 (en) |
Families Citing this family (296)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH07128338A (en) * | 1993-11-02 | 1995-05-19 | Kyoto Daiichi Kagaku:Kk | Convenient blood sugar meter and data managing method therefor |
| US5781455A (en) * | 1993-11-02 | 1998-07-14 | Kyoto Daiichi Kagaku Co., Ltd. | Article of manufacture comprising computer usable medium for a portable blood sugar value measuring apparatus |
| JP3061351B2 (en) * | 1994-04-25 | 2000-07-10 | 松下電器産業株式会社 | Method and apparatus for quantifying specific compounds |
| US6027459A (en) * | 1996-12-06 | 2000-02-22 | Abbott Laboratories | Method and apparatus for obtaining blood for diagnostic tests |
| SE9700384D0 (en) * | 1997-02-04 | 1997-02-04 | Biacore Ab | Analytical method and apparatus |
| JP3394262B2 (en) | 1997-02-06 | 2003-04-07 | セラセンス、インク． | Small volume in vitro analyte sensor |
| US7657297B2 (en) | 2004-05-03 | 2010-02-02 | Dexcom, Inc. | Implantable analyte sensor |
| US7899511B2 (en) | 2004-07-13 | 2011-03-01 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
| US6862465B2 (en) | 1997-03-04 | 2005-03-01 | Dexcom, Inc. | Device and method for determining analyte levels |
| US6001067A (en) | 1997-03-04 | 1999-12-14 | Shults; Mark C. | Device and method for determining analyte levels |
| US8527026B2 (en) | 1997-03-04 | 2013-09-03 | Dexcom, Inc. | Device and method for determining analyte levels |
| US9155496B2 (en) | 1997-03-04 | 2015-10-13 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
| US6071391A (en) | 1997-09-12 | 2000-06-06 | Nok Corporation | Enzyme electrode structure |
| US6036924A (en) | 1997-12-04 | 2000-03-14 | Hewlett-Packard Company | Cassette of lancet cartridges for sampling blood |
| US5997817A (en) | 1997-12-05 | 1999-12-07 | Roche Diagnostics Corporation | Electrochemical biosensor test strip |
| US6645368B1 (en) * | 1997-12-22 | 2003-11-11 | Roche Diagnostics Corporation | Meter and method of using the meter for determining the concentration of a component of a fluid |
| US8071384B2 (en) | 1997-12-22 | 2011-12-06 | Roche Diagnostics Operations, Inc. | Control and calibration solutions and methods for their use |
| US7494816B2 (en) * | 1997-12-22 | 2009-02-24 | Roche Diagnostic Operations, Inc. | System and method for determining a temperature during analyte measurement |
| US6103033A (en) | 1998-03-04 | 2000-08-15 | Therasense, Inc. | Process for producing an electrochemical biosensor |
| US6391005B1 (en) | 1998-03-30 | 2002-05-21 | Agilent Technologies, Inc. | Apparatus and method for penetration with shaft having a sensor for sensing penetration depth |
| US8974386B2 (en) | 1998-04-30 | 2015-03-10 | 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 |
| US8688188B2 (en) | 1998-04-30 | 2014-04-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
| US8346337B2 (en) | 1998-04-30 | 2013-01-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
| US8465425B2 (en) | 1998-04-30 | 2013-06-18 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
| US6175752B1 (en) | 1998-04-30 | 2001-01-16 | Therasense, 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 |
| US8480580B2 (en) | 1998-04-30 | 2013-07-09 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
| AU4215999A (en) | 1998-06-01 | 1999-12-20 | Roche Diagnostics Corporation | Redox reversible imidazole-osmium complex conjugates |
| US6338790B1 (en) | 1998-10-08 | 2002-01-15 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
| US6150124A (en) * | 1999-05-20 | 2000-11-21 | Umm Electronics, Inc. | Method for passively determining the application of a sample fluid on an analyte strip |
| US6193873B1 (en) * | 1999-06-15 | 2001-02-27 | Lifescan, Inc. | Sample detection to initiate timing of an electrochemical assay |
| US6514460B1 (en) | 1999-07-28 | 2003-02-04 | Abbott Laboratories | Luminous glucose monitoring device |
| US6841052B2 (en) | 1999-08-02 | 2005-01-11 | Bayer Corporation | Electrochemical-sensor design |
| CA2305922C (en) * | 1999-08-02 | 2005-09-20 | Bayer Corporation | Improved electrochemical sensor design |
| DE19936693A1 (en) * | 1999-08-04 | 2001-02-08 | Lre Technology Partner Gmbh | Instrument for the measurement of blood sugar concentrations has a test field with electrodes for the test strip and a circuit for measurement/evaluation of the current strength for display |
| US7045054B1 (en) * | 1999-09-20 | 2006-05-16 | Roche Diagnostics Corporation | Small volume biosensor for continuous analyte monitoring |
| US6767440B1 (en) * | 2001-04-24 | 2004-07-27 | Roche Diagnostics Corporation | Biosensor |
| US7276146B2 (en) * | 2001-11-16 | 2007-10-02 | Roche Diagnostics Operations, Inc. | Electrodes, methods, apparatuses comprising micro-electrode arrays |
| US6645359B1 (en) | 2000-10-06 | 2003-11-11 | Roche Diagnostics Corporation | Biosensor |
| US20060091006A1 (en) * | 1999-11-04 | 2006-05-04 | Yi Wang | Analyte sensor with insertion monitor, and methods |
| US6616819B1 (en) | 1999-11-04 | 2003-09-09 | Therasense, Inc. | Small volume in vitro analyte sensor and methods |
| CN100347537C (en) * | 1999-11-15 | 2007-11-07 | 松下电器产业株式会社 | Biosensor, method of forming thin-film electrode, and method and apparatus for quantitative determination |
| US6413395B1 (en) | 1999-12-16 | 2002-07-02 | Roche Diagnostics Corporation | Biosensor apparatus |
| KR100340173B1 (en) * | 2000-03-22 | 2002-06-12 | 이동준 | Electrochemical Biosensor Readout Meter |
| US6858433B1 (en) * | 2000-04-03 | 2005-02-22 | Roche Diagnostics Operations, Inc. | Biosensor electromagnetic noise cancellation |
| US6413213B1 (en) | 2000-04-18 | 2002-07-02 | Roche Diagnostics Corporation | Subscription based monitoring system and method |
| US6428664B1 (en) | 2000-06-19 | 2002-08-06 | Roche Diagnostics Corporation | Biosensor |
| US6488828B1 (en) | 2000-07-20 | 2002-12-03 | Roche Diagnostics Corporation | Recloseable biosensor |
| US6540890B1 (en) | 2000-11-01 | 2003-04-01 | Roche Diagnostics Corporation | Biosensor |
| US6814843B1 (en) | 2000-11-01 | 2004-11-09 | Roche Diagnostics Corporation | Biosensor |
| DE10057832C1 (en) | 2000-11-21 | 2002-02-21 | Hartmann Paul Ag | Blood analysis device has syringe mounted in casing, annular mounting carrying needles mounted behind test strip and being swiveled so that needle can be pushed through strip and aperture in casing to take blood sample |
| US8641644B2 (en) | 2000-11-21 | 2014-02-04 | Sanofi-Aventis Deutschland Gmbh | Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means |
| EP2096437B1 (en) | 2000-11-30 | 2014-11-19 | Panasonic Healthcare Co., Ltd. | Biosensor for quantifying substrate |
| JP4639465B2 (en) * | 2000-11-30 | 2011-02-23 | パナソニック株式会社 | Biosensor |
| US6447657B1 (en) | 2000-12-04 | 2002-09-10 | Roche Diagnostics Corporation | Biosensor |
| US6560471B1 (en) | 2001-01-02 | 2003-05-06 | Therasense, Inc. | Analyte monitoring device and methods of use |
| CN102012389B (en) * | 2001-01-17 | 2013-04-10 | 爱科来株式会社 | Quantitative analyzing method and quantitative analyzer using sensor |
| WO2002078512A2 (en) | 2001-04-02 | 2002-10-10 | Therasense, Inc. | Blood glucose tracking apparatus and methods |
| US7473398B2 (en) | 2001-05-25 | 2009-01-06 | Roche Diagnostics Operations, Inc. | Biosensor |
| US7699791B2 (en) | 2001-06-12 | 2010-04-20 | Pelikan Technologies, Inc. | Method and apparatus for improving success rate of blood yield from a fingerstick |
| US7025774B2 (en) | 2001-06-12 | 2006-04-11 | Pelikan Technologies, Inc. | Tissue penetration device |
| US7981056B2 (en) | 2002-04-19 | 2011-07-19 | Pelikan Technologies, Inc. | Methods and apparatus for lancet actuation |
| US9427532B2 (en) | 2001-06-12 | 2016-08-30 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| US9795747B2 (en) | 2010-06-02 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Methods and apparatus for lancet actuation |
| US9226699B2 (en) | 2002-04-19 | 2016-01-05 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling module with a continuous compression tissue interface surface |
| EP1404232B1 (en) | 2001-06-12 | 2009-12-02 | Pelikan Technologies Inc. | Blood sampling apparatus and method |
| US8337419B2 (en) | 2002-04-19 | 2012-12-25 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| US7316700B2 (en) | 2001-06-12 | 2008-01-08 | Pelikan Technologies, Inc. | Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties |
| US7749174B2 (en) | 2001-06-12 | 2010-07-06 | Pelikan Technologies, Inc. | Method and apparatus for lancet launching device intergrated onto a blood-sampling cartridge |
| DE60238119D1 (en) | 2001-06-12 | 2010-12-09 | Pelikan Technologies Inc | ELECTRIC ACTUATOR ELEMENT FOR A LANZETTE |
| US20030032874A1 (en) | 2001-07-27 | 2003-02-13 | Dexcom, Inc. | Sensor head for use with implantable devices |
| US6814844B2 (en) | 2001-08-29 | 2004-11-09 | Roche Diagnostics Corporation | Biosensor with code pattern |
| US6755949B1 (en) | 2001-10-09 | 2004-06-29 | Roche Diagnostics Corporation | Biosensor |
| US6797150B2 (en) * | 2001-10-10 | 2004-09-28 | Lifescan, Inc. | Determination of sample volume adequacy in biosensor devices |
| DE60219060T2 (en) * | 2001-10-26 | 2007-12-06 | Arkray, Inc. | CONCENTRATION METHOD AND CONCENTRATION METHOD FOR SPECIFIC COMPONENTS |
| US7018843B2 (en) | 2001-11-07 | 2006-03-28 | Roche Diagnostics Operations, Inc. | Instrument |
| US20030116447A1 (en) | 2001-11-16 | 2003-06-26 | Surridge Nigel A. | Electrodes, methods, apparatuses comprising micro-electrode arrays |
| WO2003044514A1 (en) * | 2001-11-20 | 2003-05-30 | Arkray, Inc. | Fail judging method for analysis and analyzer |
| WO2003044513A1 (en) | 2001-11-20 | 2003-05-30 | Arkray, Inc. | Fail judging method and analyzer |
| US8010174B2 (en) | 2003-08-22 | 2011-08-30 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
| US8260393B2 (en) | 2003-07-25 | 2012-09-04 | Dexcom, Inc. | Systems and methods for replacing signal data artifacts in a glucose sensor data stream |
| US7229458B2 (en) | 2002-04-19 | 2007-06-12 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7909778B2 (en) | 2002-04-19 | 2011-03-22 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7717863B2 (en) | 2002-04-19 | 2010-05-18 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7648468B2 (en) | 2002-04-19 | 2010-01-19 | Pelikon Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7901362B2 (en) | 2002-04-19 | 2011-03-08 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7481776B2 (en) | 2002-04-19 | 2009-01-27 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7976476B2 (en) | 2002-04-19 | 2011-07-12 | Pelikan Technologies, Inc. | Device and method for variable speed lancet |
| US7892183B2 (en) | 2002-04-19 | 2011-02-22 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
| US8702624B2 (en) | 2006-09-29 | 2014-04-22 | Sanofi-Aventis Deutschland Gmbh | Analyte measurement device with a single shot actuator |
| US7291117B2 (en) | 2002-04-19 | 2007-11-06 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7713214B2 (en) | 2002-04-19 | 2010-05-11 | Pelikan Technologies, Inc. | Method and apparatus for a multi-use body fluid sampling device with optical analyte sensing |
| US8784335B2 (en) | 2002-04-19 | 2014-07-22 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling device with a capacitive sensor |
| US8221334B2 (en) | 2002-04-19 | 2012-07-17 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US8267870B2 (en) | 2002-04-19 | 2012-09-18 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for body fluid sampling with hybrid actuation |
| US7331931B2 (en) | 2002-04-19 | 2008-02-19 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US9314194B2 (en) | 2002-04-19 | 2016-04-19 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| US8579831B2 (en) | 2002-04-19 | 2013-11-12 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US7371247B2 (en) | 2002-04-19 | 2008-05-13 | Pelikan Technologies, Inc | Method and apparatus for penetrating tissue |
| US7297122B2 (en) | 2002-04-19 | 2007-11-20 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7547287B2 (en) | 2002-04-19 | 2009-06-16 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7674232B2 (en) | 2002-04-19 | 2010-03-09 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7491178B2 (en) | 2002-04-19 | 2009-02-17 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US9795334B2 (en) | 2002-04-19 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US7175642B2 (en) | 2002-04-19 | 2007-02-13 | Pelikan Technologies, Inc. | Methods and apparatus for lancet actuation |
| US9248267B2 (en) | 2002-04-19 | 2016-02-02 | Sanofi-Aventis Deustchland Gmbh | Tissue penetration device |
| US7232451B2 (en) | 2002-04-19 | 2007-06-19 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US6964871B2 (en) * | 2002-04-25 | 2005-11-15 | Home Diagnostics, Inc. | Systems and methods for blood glucose sensing |
| US6946299B2 (en) * | 2002-04-25 | 2005-09-20 | Home Diagnostics, Inc. | Systems and methods for blood glucose sensing |
| US20080112852A1 (en) * | 2002-04-25 | 2008-05-15 | Neel Gary T | Test Strips and System for Measuring Analyte Levels in a Fluid Sample |
| US6743635B2 (en) * | 2002-04-25 | 2004-06-01 | Home Diagnostics, Inc. | System and methods for blood glucose sensing |
| DE20321781U1 (en) | 2002-07-02 | 2009-12-31 | Panasonic Corp., Kadoma | Biosensor, biosensor chip and biosensor device |
| AU2003248095A1 (en) * | 2002-07-25 | 2004-02-16 | Arkray, Inc. | Sample analyzing method and sample analyzing device |
| AU2003234944A1 (en) * | 2002-08-27 | 2004-03-18 | Bayer Healthcare, Llc | Methods of Determining Glucose Concentration in Whole Blood Samples |
| US9017544B2 (en) | 2002-10-04 | 2015-04-28 | Roche Diagnostics Operations, Inc. | Determining blood glucose in a small volume sample receiving cavity and in a short time period |
| US7572237B2 (en) | 2002-11-06 | 2009-08-11 | Abbott Diabetes Care Inc. | Automatic biological analyte testing meter with integrated lancing device and methods of use |
| US8574895B2 (en) | 2002-12-30 | 2013-11-05 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus using optical techniques to measure analyte levels |
| US7641784B2 (en) * | 2003-01-30 | 2010-01-05 | Tanita Corporation | Method for measuring by means of chemical sensor, and chemical sensor type measuring apparatus |
| US7134999B2 (en) | 2003-04-04 | 2006-11-14 | Dexcom, Inc. | Optimized sensor geometry for an implantable glucose sensor |
| US7850621B2 (en) | 2003-06-06 | 2010-12-14 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
| WO2006001797A1 (en) | 2004-06-14 | 2006-01-05 | Pelikan Technologies, Inc. | Low pain penetrating |
| US7488601B2 (en) | 2003-06-20 | 2009-02-10 | Roche Diagnostic Operations, Inc. | System and method for determining an abused sensor during analyte measurement |
| US7452457B2 (en) * | 2003-06-20 | 2008-11-18 | Roche Diagnostics Operations, Inc. | System and method for analyte measurement using dose sufficiency electrodes |
| US8206565B2 (en) | 2003-06-20 | 2012-06-26 | Roche Diagnostics Operation, Inc. | System and method for coding information on a biosensor test strip |
| US7718439B2 (en) | 2003-06-20 | 2010-05-18 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
| US20070264721A1 (en) * | 2003-10-17 | 2007-11-15 | Buck Harvey B | System and method for analyte measurement using a nonlinear sample response |
| US7645373B2 (en) | 2003-06-20 | 2010-01-12 | Roche Diagnostic Operations, Inc. | System and method for coding information on a biosensor test strip |
| US7645421B2 (en) | 2003-06-20 | 2010-01-12 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
| US8058077B2 (en) | 2003-06-20 | 2011-11-15 | Roche Diagnostics Operations, Inc. | Method for coding information on a biosensor test strip |
| US7597793B2 (en) * | 2003-06-20 | 2009-10-06 | Roche Operations Ltd. | System and method for analyte measurement employing maximum dosing time delay |
| US8148164B2 (en) | 2003-06-20 | 2012-04-03 | Roche Diagnostics Operations, Inc. | System and method for determining the concentration of an analyte in a sample fluid |
| CA2530211C (en) | 2003-07-01 | 2011-10-04 | Eric R. Diebold | Electrochemical affinity biosensor system and methods |
| US7761130B2 (en) | 2003-07-25 | 2010-07-20 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
| US7074307B2 (en) | 2003-07-25 | 2006-07-11 | Dexcom, Inc. | Electrode systems for electrochemical sensors |
| US20100168542A1 (en) | 2003-08-01 | 2010-07-01 | Dexcom, Inc. | System and methods for processing analyte sensor data |
| US8275437B2 (en) | 2003-08-01 | 2012-09-25 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US8160669B2 (en) | 2003-08-01 | 2012-04-17 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US7774145B2 (en) | 2003-08-01 | 2010-08-10 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US6931327B2 (en) | 2003-08-01 | 2005-08-16 | Dexcom, Inc. | System and methods for processing analyte sensor data |
| US7494465B2 (en) | 2004-07-13 | 2009-02-24 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US8845536B2 (en) | 2003-08-01 | 2014-09-30 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US20080119703A1 (en) | 2006-10-04 | 2008-05-22 | Mark Brister | Analyte sensor |
| US20190357827A1 (en) | 2003-08-01 | 2019-11-28 | Dexcom, Inc. | Analyte sensor |
| US7591801B2 (en) | 2004-02-26 | 2009-09-22 | Dexcom, Inc. | Integrated delivery device for continuous glucose sensor |
| US9135402B2 (en) | 2007-12-17 | 2015-09-15 | Dexcom, Inc. | Systems and methods for processing sensor data |
| US7519408B2 (en) | 2003-11-19 | 2009-04-14 | Dexcom, Inc. | Integrated receiver for continuous analyte sensor |
| GB2404739B (en) * | 2003-08-05 | 2006-04-12 | E2V Tech Uk Ltd | Sensor |
| US7920906B2 (en) | 2005-03-10 | 2011-04-05 | Dexcom, Inc. | System and methods for processing analyte sensor data for sensor calibration |
| US20140121989A1 (en) | 2003-08-22 | 2014-05-01 | Dexcom, Inc. | Systems and methods for processing analyte sensor data |
| WO2005033659A2 (en) | 2003-09-29 | 2005-04-14 | Pelikan Technologies, Inc. | Method and apparatus for an improved sample capture device |
| EP1680014A4 (en) | 2003-10-14 | 2009-01-21 | Pelikan Technologies Inc | Method and apparatus for a variable user interface |
| WO2005040784A1 (en) * | 2003-10-29 | 2005-05-06 | Arkray, Inc. | Specimen analysis method and specimen analysis device |
| US9247900B2 (en) | 2004-07-13 | 2016-02-02 | Dexcom, Inc. | Analyte sensor |
| US11633133B2 (en) | 2003-12-05 | 2023-04-25 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
| US8423114B2 (en) | 2006-10-04 | 2013-04-16 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
| US8287453B2 (en) | 2003-12-05 | 2012-10-16 | Dexcom, Inc. | Analyte sensor |
| US8364231B2 (en) | 2006-10-04 | 2013-01-29 | Dexcom, Inc. | Analyte sensor |
| US20100185071A1 (en) * | 2003-12-05 | 2010-07-22 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
| WO2005057168A2 (en) | 2003-12-05 | 2005-06-23 | Dexcom, Inc. | Calibration techniques for a continuous analyte sensor |
| EP1711802B1 (en) * | 2003-12-08 | 2010-07-14 | DexCom, Inc. | Systems and methods for improving electrochemical analyte sensors |
| WO2005057175A2 (en) | 2003-12-09 | 2005-06-23 | Dexcom, Inc. | Signal processing for continuous analyte sensor |
| US8668656B2 (en) | 2003-12-31 | 2014-03-11 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for improving fluidic flow and sample capture |
| US7822454B1 (en) | 2005-01-03 | 2010-10-26 | Pelikan Technologies, Inc. | Fluid sampling device with improved analyte detecting member configuration |
| US7637868B2 (en) * | 2004-01-12 | 2009-12-29 | Dexcom, Inc. | Composite material for implantable device |
| CN1918471B (en) | 2004-02-06 | 2010-12-29 | 拜尔健康护理有限责任公司 | Electrochemical biosensor |
| CA2553632A1 (en) | 2004-02-06 | 2005-08-25 | Bayer Healthcare Llc | Oxidizable species as an internal reference for biosensors and method of use |
| US8808228B2 (en) | 2004-02-26 | 2014-08-19 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
| US8792955B2 (en) | 2004-05-03 | 2014-07-29 | Dexcom, Inc. | Transcutaneous analyte sensor |
| WO2006011062A2 (en) | 2004-05-20 | 2006-02-02 | Albatros Technologies Gmbh & Co. Kg | Printable hydrogel for biosensors |
| EP1765194A4 (en) | 2004-06-03 | 2010-09-29 | Pelikan Technologies Inc | Method and apparatus for a fluid sampling device |
| US7945394B2 (en) * | 2004-06-17 | 2011-05-17 | Bayer Healthcare Llc | Detecting incomplete fill of biosensors |
| US7569126B2 (en) | 2004-06-18 | 2009-08-04 | Roche Diagnostics Operations, Inc. | System and method for quality assurance of a biosensor test strip |
| CA3098002C (en) * | 2004-06-18 | 2022-07-26 | F. Hoffmann-La Roche Ag | System and method for quality assurance of a biosensor test strip |
| US20060015020A1 (en) * | 2004-07-06 | 2006-01-19 | Dexcom, Inc. | Systems and methods for manufacture of an analyte-measuring device including a membrane system |
| US7783333B2 (en) | 2004-07-13 | 2010-08-24 | Dexcom, Inc. | Transcutaneous medical device with variable stiffness |
| 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 |
| US20060020192A1 (en) | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US20060270922A1 (en) | 2004-07-13 | 2006-11-30 | Brauker James H | Analyte sensor |
| US8565848B2 (en) | 2004-07-13 | 2013-10-22 | Dexcom, Inc. | Transcutaneous analyte sensor |
| US8652831B2 (en) | 2004-12-30 | 2014-02-18 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for analyte measurement test time |
| US8133178B2 (en) | 2006-02-22 | 2012-03-13 | Dexcom, Inc. | Analyte sensor |
| US20090076360A1 (en) | 2007-09-13 | 2009-03-19 | Dexcom, Inc. | Transcutaneous analyte sensor |
| DE102005017364B4 (en) * | 2005-04-14 | 2007-02-01 | Roche Diagnostics Gmbh | Analyzer with replaceable test field carrier |
| US7645374B2 (en) * | 2005-04-15 | 2010-01-12 | Agamatrix, Inc. | Method for determination of analyte concentrations and related apparatus |
| US7517439B2 (en) * | 2005-04-15 | 2009-04-14 | Agamatrix, Inc. | Error detection in analyte measurements based on measurement of system resistance |
| US7713392B2 (en) * | 2005-04-15 | 2010-05-11 | Agamatrix, Inc. | Test strip coding and quality measurement |
| US7964089B2 (en) | 2005-04-15 | 2011-06-21 | Agamatrix, Inc. | Analyte determination method and analyte meter |
| US7547382B2 (en) * | 2005-04-15 | 2009-06-16 | Agamatrix, Inc. | Determination of partial fill in electrochemical strips |
| US7344626B2 (en) * | 2005-04-15 | 2008-03-18 | Agamatrix, Inc. | Method and apparatus for detection of abnormal traces during electrochemical analyte detection |
| GB0509919D0 (en) * | 2005-05-16 | 2005-06-22 | Ralph Ellerker 1795 Ltd | Improvements to door closure system |
| US7695600B2 (en) * | 2005-06-03 | 2010-04-13 | Hypoguard Limited | Test system |
| GB0511270D0 (en) * | 2005-06-03 | 2005-07-13 | Hypoguard Ltd | Test system |
| US20070017824A1 (en) * | 2005-07-19 | 2007-01-25 | Rippeth John J | Biosensor and method of manufacture |
| GB0514728D0 (en) * | 2005-07-19 | 2005-08-24 | Hypoguard Ltd | Biosensor and method of manufacture |
| BRPI0613592A2 (en) | 2005-07-20 | 2011-01-18 | Bayer Healthcare Llc | port-connected amperometry |
| ES2558873T3 (en) | 2005-07-26 | 2016-02-09 | Bayer Healthcare Llc | Procedure and verification system of an electromechanical biosensor |
| CN101365374B (en) | 2005-08-31 | 2011-11-16 | 弗吉尼亚大学专利基金委员会 | Improving accuracy of continuous glucose sensors |
| US8298389B2 (en) * | 2005-09-12 | 2012-10-30 | Abbott Diabetes Care Inc. | In vitro analyte sensor, and methods |
| CA2619703A1 (en) * | 2005-09-14 | 2007-03-22 | Sumitomo Electric Industries, Ltd. | Biosensor measurment machine, biosensor measurement system, and biosens or measurement method |
| EP3483598A1 (en) | 2005-09-30 | 2019-05-15 | Ascensia Diabetes Care Holdings AG | Gated voltammetry |
| US7429865B2 (en) | 2005-10-05 | 2008-09-30 | Roche Diagnostics Operations, Inc. | Method and system for error checking an electrochemical sensor |
| US7468125B2 (en) * | 2005-10-17 | 2008-12-23 | Lifescan, Inc. | System and method of processing a current sample for calculating a glucose concentration |
| US8066866B2 (en) * | 2005-10-17 | 2011-11-29 | Lifescan, Inc. | Methods for measuring physiological fluids |
| EP1776925A1 (en) * | 2005-10-20 | 2007-04-25 | Roche Diagnostics GmbH | Analyzing means with lancet and test element |
| US9757061B2 (en) | 2006-01-17 | 2017-09-12 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
| EP1813937A1 (en) * | 2006-01-25 | 2007-08-01 | Roche Diagnostics GmbH | Electrochemical biosensor analysis system |
| EP2988127B1 (en) * | 2006-02-27 | 2017-07-05 | Sumitomo Electric Industries, Ltd. | Measuring instrument for biosensor chip |
| 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 |
| US8219173B2 (en) | 2008-09-30 | 2012-07-10 | Abbott Diabetes Care Inc. | Optimizing analyte sensor calibration |
| US8529751B2 (en) | 2006-03-31 | 2013-09-10 | Lifescan, Inc. | Systems and methods for discriminating control solution from a physiological sample |
| US8038859B2 (en) * | 2006-04-28 | 2011-10-18 | Hmd Biomedical Inc. | Electrochemical sensor and method for analyzing liquid sample |
| US7966859B2 (en) * | 2006-05-03 | 2011-06-28 | Bayer Healthcare Llc | Underfill detection system for a biosensor |
| BRPI0711278A2 (en) * | 2006-05-03 | 2012-10-09 | Bayer Healthcare Llc | underfeed detection system for an electrochemical biosensor |
| US20080071158A1 (en) | 2006-06-07 | 2008-03-20 | Abbott Diabetes Care, Inc. | Analyte monitoring system and method |
| US8057659B2 (en) * | 2006-06-27 | 2011-11-15 | Agamatrix, Inc. | Detection of analytes in a dual-mediator electrochemical test strip |
| WO2008013225A1 (en) * | 2006-07-26 | 2008-01-31 | Panasonic Corporation | Biosensor measurement system and abnormal waveform detection method in biosensor |
| US8945369B2 (en) * | 2006-07-26 | 2015-02-03 | Panasonic Healthcare Co., Ltd. | Biosensor measurement system and measurement method |
| JP4582076B2 (en) * | 2006-10-03 | 2010-11-17 | パナソニック株式会社 | Substrate quantification method |
| WO2008049074A2 (en) * | 2006-10-18 | 2008-04-24 | Agamatrix, Inc. | Error detection in analyte measurements based on measurement of system resistance |
| WO2008049075A2 (en) * | 2006-10-18 | 2008-04-24 | Agamatrix, Inc. | Electrochemical determination of analytes |
| MX347099B (en) * | 2006-10-24 | 2017-04-12 | Ascensia Diabetes Care Holdings Ag | Transient decay amperometry. |
| EP1985996A1 (en) * | 2007-04-27 | 2008-10-29 | Roche Diagnostics GmbH | Analytic system for photometric determination of an analyte in a body fluid using an analytic device and a test panel to be fitted to the analytic device |
| US20080306444A1 (en) | 2007-06-08 | 2008-12-11 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
| GB0711780D0 (en) * | 2007-06-18 | 2007-07-25 | Oxford Biosensors Ltd | Electrochemical data rejection methodology |
| US8101062B2 (en) | 2007-07-26 | 2012-01-24 | Nipro Diagnostics, Inc. | System and methods for determination of analyte concentration using time resolved amperometry |
| BRPI0814202B1 (en) * | 2007-07-26 | 2019-10-29 | Home Diagnostics Inc | methods and systems for determining the concentration of analytical fluid sample |
| US8778168B2 (en) | 2007-09-28 | 2014-07-15 | Lifescan, Inc. | Systems and methods of discriminating control solution from a physiological sample |
| EP2227132B1 (en) | 2007-10-09 | 2023-03-08 | DexCom, Inc. | Integrated insulin delivery system with continuous glucose sensor |
| US8417312B2 (en) | 2007-10-25 | 2013-04-09 | Dexcom, Inc. | Systems and methods for processing sensor data |
| JP2009121996A (en) * | 2007-11-15 | 2009-06-04 | Sumitomo Electric Ind Ltd | Biosensor system and measuring instrument therefor |
| JP4985340B2 (en) * | 2007-11-15 | 2012-07-25 | 住友電気工業株式会社 | Biosensor system and measuring instrument |
| WO2009076302A1 (en) | 2007-12-10 | 2009-06-18 | Bayer Healthcare Llc | Control markers for auto-detection of control solution and methods of use |
| JP4992693B2 (en) * | 2007-12-12 | 2012-08-08 | 住友電気工業株式会社 | Biological information measuring device |
| US8290559B2 (en) | 2007-12-17 | 2012-10-16 | Dexcom, Inc. | Systems and methods for processing sensor data |
| US8603768B2 (en) | 2008-01-17 | 2013-12-10 | Lifescan, Inc. | System and method for measuring an analyte in a sample |
| CA2715628A1 (en) | 2008-02-21 | 2009-08-27 | Dexcom, Inc. | Systems and methods for processing, transmitting and displaying sensor data |
| US8396528B2 (en) | 2008-03-25 | 2013-03-12 | Dexcom, Inc. | Analyte sensor |
| EP2265324B1 (en) | 2008-04-11 | 2015-01-28 | Sanofi-Aventis Deutschland GmbH | Integrated analyte measurement system |
| US8551320B2 (en) | 2008-06-09 | 2013-10-08 | Lifescan, Inc. | System and method for measuring an analyte in a sample |
| WO2010005908A2 (en) | 2008-07-07 | 2010-01-14 | Agamatrix, Inc. | Integrated blood glucose measurement device |
| US8560039B2 (en) | 2008-09-19 | 2013-10-15 | Dexcom, Inc. | Particle-containing membrane and particulate electrode for analyte sensors |
| US20100198107A1 (en) | 2009-01-30 | 2010-08-05 | Roche Diagnostics Operations, Inc. | Integrated blood glucose meter and lancing device |
| US9375169B2 (en) | 2009-01-30 | 2016-06-28 | Sanofi-Aventis Deutschland Gmbh | Cam drive for managing disposable penetrating member actions with a single motor and motor and control system |
| US20100249965A1 (en) * | 2009-03-31 | 2010-09-30 | Agamatrix, Inc. | Integrated Blood Glucose Measurement Device |
| TWI388823B (en) * | 2009-04-09 | 2013-03-11 | Bionime Corp | A method for estimating the distribution of a sample |
| CN106053585A (en) * | 2009-05-12 | 2016-10-26 | 华广生技股份有限公司 | Detection method for judging sample distribution status |
| US20100331652A1 (en) | 2009-06-29 | 2010-12-30 | Roche Diagnostics Operations, Inc. | Modular diabetes management systems |
| US9218453B2 (en) * | 2009-06-29 | 2015-12-22 | Roche Diabetes Care, Inc. | Blood glucose management and interface systems and methods |
| WO2011003035A2 (en) | 2009-07-02 | 2011-01-06 | Dexcom, Inc. | Analyte sensor |
| US8622231B2 (en) | 2009-09-09 | 2014-01-07 | Roche Diagnostics Operations, Inc. | Storage containers for test elements |
| CA2776332C (en) * | 2009-11-10 | 2018-05-01 | Bayer Healthcare Llc | Underfill recognition system for a biosensor |
| US20110151571A1 (en) | 2009-12-23 | 2011-06-23 | Roche Diagnostics Operations, Inc. | Memory apparatus for multiuse analyte test element systems, and kits, systems, combinations and methods relating to same |
| US8101065B2 (en) * | 2009-12-30 | 2012-01-24 | Lifescan, Inc. | Systems, devices, and methods for improving accuracy of biosensors using fill time |
| US20110168575A1 (en) | 2010-01-08 | 2011-07-14 | Roche Diaagnostics Operations, Inc. | Sample characterization based on ac measurement methods |
| US20110186428A1 (en) | 2010-01-29 | 2011-08-04 | Roche Diagnostics Operations, Inc. | Electrode arrangements for biosensors |
| MX2012010860A (en) * | 2010-03-22 | 2013-03-05 | Bayer Healthcare Llc | Residual compensation for a biosensor. |
| US8965476B2 (en) | 2010-04-16 | 2015-02-24 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| RU2566382C2 (en) | 2010-06-07 | 2015-10-27 | БАЙЕР ХЕЛТКЭА ЭлЭлСи | Control system of insufficient filling for biosensor |
| KR101772596B1 (en) | 2010-07-07 | 2017-08-29 | 아가매트릭스, 인코포레이티드 | Analyte test strip and analyte meter device |
| US9176091B2 (en) | 2010-09-17 | 2015-11-03 | Agamatrix, Inc. | Method and apparatus for encoding test strips |
| US8603323B2 (en) * | 2010-09-20 | 2013-12-10 | Lifescan, Inc. | Apparatus and process for improved measurements of a monitoring device |
| WO2012042211A2 (en) * | 2010-09-28 | 2012-04-05 | Lifescan Scotland Limited | Analyte measurement method and system with error trapping |
| US9482636B2 (en) * | 2010-10-28 | 2016-11-01 | Panasonic Healthcare Holdings Co., Ltd. | Vital information measurement device and vital information measurement method employing same |
| US20120143085A1 (en) | 2010-12-02 | 2012-06-07 | Matthew Carlyle Sauers | Test element ejection mechanism for a meter |
| DK3575796T3 (en) | 2011-04-15 | 2021-01-18 | Dexcom Inc | ADVANCED ANALYZE SENSOR CALIBRATION AND ERROR DETECTION |
| CN103392127B (en) * | 2011-05-10 | 2016-05-04 | 松下健康医疗控股株式会社 | Organism sample determinator and the organism sample assay method that uses it |
| TWI427291B (en) | 2011-07-06 | 2014-02-21 | Bionime Corp | Method for operating a measurement of a sample on an electrochemical test strip |
| EP2737078B1 (en) | 2011-07-27 | 2017-11-01 | Agamatrix, Inc. | Reagents for electrochemical test strips |
| ES2663097T3 (en) | 2011-09-21 | 2018-04-11 | Ascensia Diabetes Care Holdings Ag | Biosensor with error compensation |
| US9914126B2 (en) | 2011-11-28 | 2018-03-13 | Roche Diabetes Care, Inc. | Storage container for biosensor test elements |
| EP2901153A4 (en) | 2012-09-26 | 2016-04-27 | 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 |
| JP6397822B2 (en) | 2012-10-17 | 2018-09-26 | ユニバーシティ オブ メリーランド， オフィス オブ テクノロジー コマーシャライゼーション | Device and method of using the device for detection of aminoacidopathy |
| US9310288B2 (en) * | 2013-01-28 | 2016-04-12 | Fisher-Rosemount Systems, Inc. | Systems and methods to monitor operating processes |
| EP2972268B1 (en) | 2013-03-15 | 2017-05-24 | Roche Diabetes Care GmbH | Methods of failsafing electrochemical measurements of an analyte as well as devices, apparatuses and systems incorporating the same |
| WO2014140164A1 (en) | 2013-03-15 | 2014-09-18 | Roche Diagnostics Gmbh | Methods of using information from recovery pulses in electrochemical analyte measurements as well as devices, apparatuses and systems incorporating the same |
| CN105164523B (en) | 2013-03-15 | 2017-09-12 | 豪夫迈·罗氏有限公司 | Scale the method for the data for constructing biology sensor algorithm and merge the unit and system of methods described |
| US10168313B2 (en) | 2013-03-15 | 2019-01-01 | Agamatrix, Inc. | Analyte detection meter and associated method of use |
| WO2014140177A2 (en) | 2013-03-15 | 2014-09-18 | Roche Diagnostics Gmbh | Methods of detecting high antioxidant levels during electrochemical measurements and failsafing an analyte concentration therefrom as well as devices, apparatuses and systems incorporting the same |
| US9459231B2 (en) * | 2013-08-29 | 2016-10-04 | Lifescan Scotland Limited | Method and system to determine erroneous measurement signals during a test measurement sequence |
| US9243276B2 (en) * | 2013-08-29 | 2016-01-26 | Lifescan Scotland Limited | Method and system to determine hematocrit-insensitive glucose values in a fluid sample |
| DK3540429T3 (en) | 2013-08-30 | 2021-02-15 | Univ Maryland | FACILITIES AND METHODS FOR USING HYPERAMMONYEM DETECTION FACILITIES |
| US9459232B2 (en) * | 2013-09-05 | 2016-10-04 | Lifescan Scotland Limited | Method and system to determine erroneous measurement signals during a test measurement sequence |
| US9828621B2 (en) * | 2013-09-10 | 2017-11-28 | Lifescan Scotland Limited | Anomalous signal error trap for an analyte measurement determined from a specified sampling time derived from a sensed physical characteristic of the sample containing the analyte |
| US20170198329A1 (en) | 2014-04-17 | 2017-07-13 | University Of Maryland, College Park | Device and methods of using device for detection of aminoacidopathies |
| WO2016073395A1 (en) | 2014-11-03 | 2016-05-12 | Roche Diabetes Care, Inc. | Electrode arrangements for electrochemical test elements and methods of use thereof |
| US9423374B2 (en) * | 2015-01-26 | 2016-08-23 | Lifescan Scotland Limited | Reference electrode error trap determined from a specified sampling time and a pre-determined sampling time |
| US10591495B2 (en) | 2015-04-27 | 2020-03-17 | University Of Maryland, College Park | Device and methods of using device for detection of hyperammonemia |
| CN109804240A (en) * | 2016-10-05 | 2019-05-24 | 豪夫迈·罗氏有限公司 | Detection reagent and electrode arrangement and its application method for multiple analyte diagnostic test element |
| US11331022B2 (en) | 2017-10-24 | 2022-05-17 | Dexcom, Inc. | Pre-connected analyte sensors |
| AU2018354120A1 (en) | 2017-10-24 | 2020-04-23 | Dexcom, Inc. | Pre-connected analyte sensors |
| WO2019103165A1 (en) * | 2017-11-21 | 2019-05-31 | 주식회사 비비비 | Biosensor |
| JP6749721B1 (en) * | 2020-05-27 | 2020-09-02 | 株式会社ファーストスクリーニング | Electrochemical sensor unit |
| CN111812175B (en) * | 2020-06-30 | 2022-06-14 | 江苏鱼跃医疗设备股份有限公司 | Blood detection method for reducing interference of hematocrit and biosensor |
| TWI799926B (en) * | 2021-07-28 | 2023-04-21 | 五鼎生物技術股份有限公司 | Electrochemical detection system, measuring instrument and electrochemical detection method |
Family Cites Families (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4420564A (en) * | 1980-11-21 | 1983-12-13 | Fuji Electric Company, Ltd. | Blood sugar analyzer having fixed enzyme membrane sensor |
| US4940945A (en) * | 1987-11-02 | 1990-07-10 | Biologix Inc. | Interface circuit for use in a portable blood chemistry measuring apparatus |
| US5108564A (en) * | 1988-03-15 | 1992-04-28 | Tall Oak Ventures | Method and apparatus for amperometric diagnostic analysis |
| KR910008421B1 (en) * | 1988-05-24 | 1991-10-15 | 주식회사 금성사 | A method for detecting barcode of barcode reader using hologram scanner and its scanning optical system |
| US5053199A (en) * | 1989-02-21 | 1991-10-01 | Boehringer Mannheim Corporation | Electronically readable information carrier |
| US4999582A (en) * | 1989-12-15 | 1991-03-12 | Boehringer Mannheim Corp. | Biosensor electrode excitation circuit |
| JPH0820412B2 (en) * | 1990-07-20 | 1996-03-04 | 松下電器産業株式会社 | Quantitative analysis method and device using disposable sensor |
-
1993
- 1993-06-08 US US08/073,180 patent/US5352351A/en not_active Expired - Lifetime
-
1994
- 1994-05-13 ES ES05013179T patent/ES2270401T3/en not_active Expired - Lifetime
- 1994-05-13 CA CA002153877A patent/CA2153877C/en not_active Expired - Lifetime
- 1994-05-13 AU AU68325/94A patent/AU6832594A/en not_active Abandoned
- 1994-05-13 EP EP05013179A patent/EP1582864B1/en not_active Expired - Lifetime
- 1994-05-13 WO PCT/US1994/005323 patent/WO1994029706A1/en active IP Right Grant
- 1994-05-13 DE DE69434438T patent/DE69434438T2/en not_active Expired - Lifetime
- 1994-05-13 DE DE0702788T patent/DE702788T1/en active Pending
- 1994-05-13 DE DE69434836T patent/DE69434836T2/en not_active Expired - Lifetime
- 1994-05-13 ES ES94916758T patent/ES2153334T3/en not_active Expired - Lifetime
- 1994-05-13 JP JP6521421A patent/JP2800981B2/en not_active Expired - Lifetime
- 1994-05-13 EP EP94916758A patent/EP0702788B1/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| DE702788T1 (en) | 2000-11-02 |
| DE69434438D1 (en) | 2005-09-01 |
| ES2270401T3 (en) | 2007-04-01 |
| DE69434836D1 (en) | 2006-10-05 |
| EP1582864A1 (en) | 2005-10-05 |
| ES2153334T1 (en) | 2001-03-01 |
| EP1582864B1 (en) | 2006-08-23 |
| DE69434438T2 (en) | 2006-01-12 |
| CA2153877A1 (en) | 1994-12-22 |
| WO1994029706A1 (en) | 1994-12-22 |
| AU6832594A (en) | 1995-01-03 |
| EP0702788B1 (en) | 2005-07-27 |
| ES2153334T3 (en) | 2006-03-01 |
| JP2800981B2 (en) | 1998-09-21 |
| DE69434836T2 (en) | 2007-10-18 |
| EP0702788A1 (en) | 1996-03-27 |
| US5352351A (en) | 1994-10-04 |
| JPH08502589A (en) | 1996-03-19 |
| EP0702788A4 (en) | 1997-05-28 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2153877C (en) | Biosensing meter with fail/safe procedures to prevent erroneous indications | |
| JP2702286B2 (en) | Biosensing meter with pluggable memory key | |
| US5243516A (en) | Biosensing instrument and method | |
| EP0702789B1 (en) | Biosensing meter which detects proper electrode engagement and distinguishes sample and check strips | |
| CA2068214C (en) | Biosensor electrode excitation circuit | |
| US7846321B2 (en) | Error detection in analyte measurements based on measurement of system resistance | |
| EP0702787B1 (en) | Biosensing meter with ambient temperature estimation method and system | |
| EP1883810B1 (en) | Error detection in analyte measurements based on measurement of system resistance | |
| US7771583B2 (en) | Electrochemical determination of analytes | |
| KR101256133B1 (en) | Method and apparatus for detection of abnormal traces during electrochemical analyte detection | |
| CA2175501C (en) | Biosensing meter with fail/safe procedures to prevent erroneous indications |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKEX | Expiry |
Effective date: 20140513 |