USRE42567E1 - Electrochemical cell - Google Patents

Electrochemical cell Download PDF

Info

Publication number
USRE42567E1
USRE42567E1 US12/899,342 US89934210A USRE42567E US RE42567 E1 USRE42567 E1 US RE42567E1 US 89934210 A US89934210 A US 89934210A US RE42567 E USRE42567 E US RE42567E
Authority
US
United States
Prior art keywords
cell
aperture
liquid sample
electrically
socket region
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
Application number
US12/899,342
Inventor
Alastair M. Hodges
Thomas W. Beck
Oddvar Johansen
Ian Andrew Maxwell
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Cilag GmbH International
Lifescan IP Holdings LLC
Original Assignee
LifeScan Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US09/314,251 external-priority patent/US6174420B1/en
Priority claimed from US09/709,968 external-priority patent/US6521110B1/en
Priority claimed from US09/840,624 external-priority patent/US6863801B2/en
Priority to US12/899,342 priority Critical patent/USRE42567E1/en
Application filed by LifeScan Inc filed Critical LifeScan Inc
Publication of USRE42567E1 publication Critical patent/USRE42567E1/en
Application granted granted Critical
Anticipated expiration legal-status Critical
Assigned to BANK OF AMERICA, N.A., AS COLLATERAL AGENT reassignment BANK OF AMERICA, N.A., AS COLLATERAL AGENT SECURITY AGREEMENT Assignors: LIFESCAN IP HOLDINGS, LLC
Assigned to BANK OF AMERICA, N.A., AS COLLATERAL AGENT reassignment BANK OF AMERICA, N.A., AS COLLATERAL AGENT SECURITY AGREEMENT Assignors: LIFESCAN IP HOLDINGS, LLC
Assigned to LIFESCAN IP HOLDINGS, LLC reassignment LIFESCAN IP HOLDINGS, LLC ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: CILAG GMBH INTERNATIONAL
Assigned to CILAG GMBH INTERNATIONAL reassignment CILAG GMBH INTERNATIONAL ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: LIFESCAN INC.
Assigned to JOHNSON & JOHNSON CONSUMER INC., JANSSEN BIOTECH, INC., LIFESCAN IP HOLDINGS, LLC reassignment JOHNSON & JOHNSON CONSUMER INC. RELEASE OF SECOND LIEN PATENT SECURITY AGREEMENT RECORDED OCT. 3, 2018, REEL/FRAME 047186/0836 Assignors: BANK OF AMERICA, N.A.
Assigned to CILAG GMBH INTERNATIONAL reassignment CILAG GMBH INTERNATIONAL CORRECTIVE ASSIGNMENT TO CORRECT THE PROPERTY LIST BY ADDING PATENTS 6990849;7169116; 7351770;7462265;7468125; 7572356;8093903; 8486245;8066866;AND DELETE 10881560. PREVIOUSLY RECORDED ON REEL 050836 FRAME 0737. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT. Assignors: LIFESCAN INC.
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • GPHYSICS
    • G01MEASURING; TESTING
    • G01NINVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/403Cells and electrode assemblies
    • CCHEMISTRY; METALLURGY
    • C12BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12QMEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
    • C12Q1/00Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/001Enzyme electrodes
    • C12Q1/005Enzyme electrodes involving specific analytes or enzymes
    • C12Q1/006Enzyme electrodes involving specific analytes or enzymes for glucose
    • CCHEMISTRY; METALLURGY
    • C12BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12QMEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
    • C12Q1/00Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/001Enzyme electrodes
    • C12Q1/004Enzyme electrodes mediator-assisted
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01NINVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/28Electrolytic cell components
    • G01N27/30Electrodes, e.g. test electrodes; Half-cells
    • G01N27/327Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
    • G01N27/3271Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
    • G01N27/3272Test elements therefor, i.e. disposable laminated substrates with electrodes, reagent and channels

Definitions

  • This invention relates to an electrochemical cell for determining the concentration of an analyte in a carrier.
  • the invention will herein be described with particular reference to a biosensor adapted to measure the concentration of glucose in blood, but it will be understood not to be limited to that particular use and is applicable to other analytic determinations.
  • a novel method for determining the concentration of the reduced (or oxidised) form of a redox species in an electrochemical cell of the kind comprising a working electrode and a counter (or counter/reference) electrode spaced from the working electrode by a predetermined distance.
  • the method involves applying an electric potential difference between the electrodes and selecting the potential of the working electrode such that the rate of electro-oxidation of the reduced form of the species (or of electro-reduction of the oxidised form) is diffusion controlled.
  • the spacing between the working electrode and the counter electrode is selected so that reaction products from the counter electrode arrive at the working electrode.
  • the method previously described allows the diffusion coefficient and/or the concentration of the reduced (or oxidised) form of the species to be estimated.
  • thin layer electrochemical cell refers to a cell having closely spaced electrodes such that reaction product from the counter electrode arrives at the working electrode.
  • the separation of electrodes in such a cell for measuring glucose in blood will be less than 500 microns, and preferably less than 200 microns.
  • the chemistry used in the exemplified electrochemical cell is as follows:
  • GOD is the enzyme glucose oxidase
  • GOD* is the ‘activated’ enzyme.
  • Ferricyanide ([Fe(CN) 6 ] 3 ⁇ ) is the ‘mediator’ which returns the GOD* to its catalytic state. GOD, an enzyme catalyst, is not consumed during the reaction so long as excess mediator is present.
  • Ferrocyanide ([Fe(CN) 6 ] 4 ⁇ ) is the product of the total reaction. Ideally there is initially no ferrocyanide, although in practice there is often a small quantity. After reaction is complete the concentration of ferrocyanide (measured electrochemically) indicates the initial concentration of glucose. The total reaction is the sum of reactions 1 and 2:
  • Glucose refers specifically to ⁇ -D-glucose.
  • sample size required is greater than desirable. It would be generally preferable to be able to make measurements on samples of reduced volume since this in turn enables use of less invasive methods to obtain samples.
  • the cells are disposable after use, it is desirable that they be capable of mass production at relatively low cost.
  • a biosensor for use in determining a concentration of a component in an aqueous liquid sample
  • the biosensor including: (a) an electrochemical cell, the electrochemical cell including a first electrically resistive substrate having a first thin layer of a first electrically conductive material on a first face, a second electrically resistive substrate having a second thin layer of a second electrically conductive material on a second face, the substrates being disposed with the first electrically conductive material facing the second electrically conductive material and being separated by a sheet including an aperture, the wall of which aperture cooperates with the electrically conductive materials to define a cell wall, and wherein the aperture defines a working electrode area in the cell, the cell further including a sample introduction aperture whereby the aqueous liquid sample may be introduced into the cell; and (b) a measuring circuit.
  • the electrochemical cell further includes a socket region having a first contact area in electrical communication with the first thin layer of the first electrically conductive material and a second contact area in electrical communication with the second thin layer of the second electrically conductive material, whereby the electrochemical cell may be electrically connected with the measuring circuit.
  • the measuring circuit includes a tongue plug.
  • At least one of the first electrically conductive material and the second electrically conductive material includes a metal.
  • the metal may further include a sputter coated metal.
  • the aqueous liquid sample includes blood, and the component includes glucose.
  • the measuring circuit includes an automated instrument for detecting an electrical signal from the electrochemical cell and relating the electrical signal to the concentration of the component in the aqueous liquid sample.
  • the electrochemical cell includes a substantially flat strip having a thickness, the strip having at least two lateral edges, and wherein the sample introduction aperture includes a notch through the entire thickness of the strip in at least one of the lateral edges thereof.
  • a biosensor for use in determining a concentration of a component in an aqueous liquid sample including: (a) a thin layer electrochemical cell, the cell including: (i) an electrically resistive sheet including an aperture wherein the aperture defines a working electrode area in the cell; (ii) a first electrode layer covering the aperture on a first side of the sheet; (iii) a second electrode layer covering the aperture on a second side of the sheet; and (iv) a passage for admission into the aperture of the aqueous liquid sample; and (b) a measuring circuit.
  • the electrochemical cell further includes a socket region having a first contact area in electrical communication with the first electrode layer and a second contact area in electrical communication with the second electrode layer, whereby the electrochemical cell may be electrically connected with the measuring circuit.
  • the measuring circuit includes a tongue plug.
  • the aqueous liquid sample includes blood, and the component includes glucose.
  • the measuring circuit includes an automated instrument for detecting an electrical signal from the electrochemical cell and relating the electrical signal to the concentration of the component in the aqueous liquid sample.
  • the cell includes a substantially flat strip having a thickness, the strip having at least two lateral edges, and wherein the passage for admission into the aperture includes a notch through the entire thickness of the strip in at least one of the lateral edges thereof.
  • an apparatus for determining a concentration of a reduced form or an oxidized form of a redox species in a liquid sample including: (a) a hollow electrochemical cell having a working electrode and a counter or counter/reference electrode wherein the working electrode is spaced from the counter or counter/reference electrode by less than 500 ⁇ m; (b) means for applying an electric potential difference between the electrodes; and (c) means for electrochemically determining the concentration of the reduced form or the oxidized form of the redox species in the liquid sample.
  • means for electrochemically determining the concentration of the reduced form or the oxidized form of the redox species includes: (i) means for determining a change in current with time after application of the electric potential difference and prior to achievement of a steady state current; (ii) means for estimating a magnitude of the steady state current; and (iii) means for obtaining from the change in current with time and the magnitude of the steady state current, a value indicative of the concentration of the reduced form or the oxidized form of the redox species.
  • the cell further includes a socket region having a first contact area in electrical communication with the working electrode and a second contact area in electrical communication with the counter or counter/reference electrode, whereby the cell may be electrically connected with at least one of the means for applying an electric potential difference between the electrodes and the means for electrochemically-determining the concentration of the reduced form or the oxidized form of the redox species in the liquid sample.
  • At least one of the means for applying an electric potential difference between the electrodes and the means for electrochemically determining the concentration of the reduced form or the oxidized form of the redox species in the liquid sample includes a tongue plug.
  • At least one of the means for applying an electric potential difference between the electrodes and the means for electrochemically determining the concentration of the reduced form or the oxidized form of the redox species in the liquid sample includes an automated instrument for detecting an electrical signal from the electrochemical cell and relating the electrical signal to the concentration of the reduced form or the oxidized form of the redox species in the liquid sample.
  • the cell includes a substantially flat strip having a thickness, the strip having at least two lateral edges, and wherein a notch extends through a wall of the electrochemical cell and through the entire thickness of the strip in at least one of the lateral edges thereof, whereby the liquid sample may be introduced into the cell.
  • the liquid sample includes blood, and the redox species includes glucose.
  • a method for determining a concentration of a reduced form or an oxidized form of a redox species in a liquid sample including: (a) providing a hollow electrochemical cell having a working electrode and a counter or counter/reference electrode wherein the working electrode is spaced from the counter or counter/reference electrode by less than 500 ⁇ m; (b) applying an electric potential difference between the electrodes; and (c) electrochemically determining the concentration of the reduced form or the oxidized form of the redox species in the liquid sample.
  • step (c) includes: (i) determining a change in current with time after application of the electric potential difference and prior to achievement of a steady state current; (ii) estimating a magnitude of the steady state current; and (iii) obtaining from the change in current with time and the magnitude of the steady state current, a value indicative of the concentration of the reduced form or the oxidized form of the redox species.
  • the cell further includes a socket region having a first contact area in electrical communication with the working electrode and a second contact area in electrical communication with the counter or counter/reference electrode.
  • step (b) further includes the step of: providing an automated instrument for applying an electric potential difference between the electrodes.
  • step (c) includes the steps of: (i) providing an automated instrument for detecting an electrical signal from the electrochemical cell; and (ii) relating the electrical signal to the concentration of the reduced form or the oxidized form of the redox species in the liquid sample.
  • the cell includes a substantially flat strip having a thickness, the strip having at least two lateral edges, and wherein a notch extends through a wall of the electrochemical cell and through the entire thickness of the strip in at least one of the lateral edges thereof, whereby the liquid sample may be introduced into the cell.
  • the liquid sample includes blood and the redox species includes glucose.
  • FIG. 1 shows the product of manufacturing step 2 in plan.
  • FIG. 2 shows the product of FIG. 1 in side elevation.
  • FIG. 3 shows the product of FIG. 1 in end elevation.
  • FIG. 4 shows the product of manufacturing step 3 in plan.
  • FIG. 5 shows the product of FIG. 4 in cross-section on line 5 - 5 of FIG. 4 .
  • FIG. 6 shows the product of manufacturing step 5 in plan.
  • FIG. 7 shows the product of FIG. 6 in side elevation.
  • FIG. 8 shows the product of FIG. 6 in end elevation.
  • FIG. 9 shows the product of manufacturing step 7 in plan.
  • FIG. 10 is a cross-section of FIG. 9 on line 10 - 10 .
  • FIG. 11 shows the product of FIG. 9 in end elevation.
  • FIG. 12 shows a cell according to the invention in plan.
  • FIG. 13 shows the call of FIG. 12 in side elevation.
  • FIG. 14 shows the cell of FIG. 12 in end elevation.
  • FIG. 15 shows a scrap portion of a second embodiment of the invention in enlarged section.
  • Step 1 A sheet 1 of Melinex® (a chemically inert, and electrically resistive Polyethylene Terephthalate [“PET”]) approximately 13 cm ⁇ 30 cm and 100 micron thick was laid flat on a sheet of release paper 2 and coated using a Number 2 MYAR bar to a thickness of 12 microns wet (approximately 2-5 microns dry) with a water-based heat activated adhesive 3 (ICI Novacoat system using catalyst:adhesive). The water was then evaporated by means of a hot air dryer leaving a contact adhesive surface. The sheet was then turned over on a release paper and the reverse side was similarly coated with the same adhesive 4 , dried, and a protective release paper 5 applied to the exposed adhesive surface. The edges were trimmed to obtain a sheet uniformly coated on both sides with tacky contact adhesive protected by release paper.
  • Melinex® a chemically inert, and electrically resistive Polyethylene Terephthalate [“PET”]
  • Step 2 The sheet with protective release papers was cut into strips 7 , each about 18 mm ⁇ 210 mm ( FIGS. 1-3 ).
  • Step 3 A strip 7 of adhesive-coated PET from step 2 with release paper 2 , 5 on respective sides, was placed in a die assembly (not shown) and clamped.
  • the die assembly was adapted to punch the strip with a locating hole 10 at each end and with for example 37 circular holes 11 each of 3.4 mm diameter at 5 mm centres equi-spaced along a line between locating holes 10 .
  • the area of each hole 11 is approximately 9 square mm.
  • Step 4 A sheet 12 of Mylar® PET approximately 21 cm square and 135 microns thick was placed in a sputter coating chamber for palladium coating 13 .
  • the sputter coating took place under a vacuum of between 4 and 6 millibars and in an atmosphere of argon gas.
  • Palladium was coated on the PET to a thickness of 100-1000 angstroms. There is thus formed a sheet 14 having a palladium sputter coating 13 .
  • Step 5 The palladium coated PET sheet 14 from Step 4 was then cut into strips 14 and 15 and a die was used to punch two location holes 16 in each strip, at one end ( FIGS. 6 , 7 and 8 ). Strips 14 and 15 differ only in dimension strips 14 being 25 mm ⁇ 210 mm and strips 15 being 23 mm ⁇ 210 mm.
  • Step 6 A spacer strip 7 prepared as in step 3 was then placed in a jig (not shown) having two locating pins (one corresponding to each locating hole 10 of strip 7 ) and the upper release paper 2 was removed.
  • a strip 14 of palladium coated PET prepared as in step 5 was then laid over the adhesive layer, palladium surface downwards, using the jig pins to align the locating holes 16 with the underlying PET strip 7 .
  • This combination was then passed through a laminator comprising a set of pinch rollers, one of which was adapted to heat the side bearing a palladium coated PET strip 14 . The roller on the opposite side of the strip 7 was cooled. By this means, only the adhesive between the palladium of strip 14 and PET strip 7 was activated.
  • Step 7 PET strip 7 was then turned over and located in the jig with the release coating uppermost.
  • the release coating was peeled off and second palladium coated strip 15 was placed palladium side down on the exposed adhesive surface using the locating pins to align the strips.
  • this assembly was now passed again through the laminator of step 6, this time with the hot roll adjacent the palladium coated Mylar® added in step 7 so as to activate the intervening adhesive ( FIGS. 9 , 10 and 11 ).
  • Step 8 The assembly from step 7 was returned to the die assembly and notches 17 punched in locations so as to extend between the circular holes 11 previously punched in the Melinex® PET and the strip edge 17 . Notches 16 extend so as to intercept the circumference of each circular cell.
  • the strip was then guillotined to give 37 individual “sensor strips”, each strip being about 5 mm wide and each having one thin layer cavity cell ( FIGS. 12 , 13 and 14 ).
  • the cell comprises a first electrode consisting of PET layer 12 , a palladium layer 13 , an adhesive layer 3 , a PET sheet 1 , a second adhesive layer 4 , a second electrode comprising palladium layer 13 , and a PET layer 12 .
  • Sheet 1 defines a cylindrical cell 11 having a thickness in the cell axial direction corresponding to the thickness of the Melinex® PET sheet layer 1 together with the thickness of adhesive layers 3 and 4 .
  • the cell has circular palladium end walls. Access to the cell is provided at the side edge of the cell where notches 16 intersect cell 11 .
  • a sample to be analysed is introduced to the cell by capillary action.
  • the sample is placed on contact with notch 16 and is spontaneously drawn by capillary action into the cell, displaced air from the cell venting from the opposite notch 16 .
  • a surfactant may be included in the capillary space to assist in drawing in the sample.
  • connection means for example edge connectors whereby the sensors may be placed into a measuring circuit.
  • this is achieved by making spacer 1 shorter than palladium supporting sheets 14 , 15 and by making one sheet 15 of shorter length than the other 14 .
  • This forms a socket region 20 having contact areas 21 , 22 electrically connected with the working and counter electrodes respectively.
  • a simple tongue plug having corresponding engaging conduct surfaces can then be used for electrical connection.
  • Connectors of other form may be devised.
  • Chemicals for use in the cell may be supported on the cell electrodes or walls, may be supported on an independent support contained within the cell or may be self-supporting.
  • chemicals for use in the cell are printed onto the palladium surface of the electrode immediately after step 1 at which stage the freshly-deposited palladium is more hydrophilic.
  • a solution containing 0.2 molar potassium ferricyanide and 1% by weight of glucose oxidase dehydrogenase may be printed on to the palladium surface.
  • the chemicals are printed only in the areas which will form a wall of the cell and for preference the chemicals are printed on the surface by means of an ink jet printer. In this manner, the deposition of chemicals may be precisely controlled.
  • chemicals which are desirably separated until required for use may be printed respectively on the first and second electrodes.
  • a GOD/ferrocyanide composition can be printed on one electrode and a buffer on the other.
  • chemicals may also be introduced into the cell as a solution after step 6 or step 8 by pipette in the traditional manner and the solvent subsequently is removed by evaporation or drying.
  • Chemicals need not be printed on the cell wall or the electrodes and may instead be impregnated into a gauze, membrane, non-woven fabric or the like contained within, or filling, the cavity (eg inserted in cell 11 prior to steps 6 or 7).
  • the chemicals are formed into a porous mass which may be introduced into the cell as a pellet or granules.
  • the chemicals maybe introduced as a gel.
  • a laminate 21 is first made from a strip 14 as obtained in step 5 adhesively sandwiched between two strips 7 as obtained from step 3.
  • Laminate 20 is substituted for sheet 1 in step 5 and assembled with electrodes as in steps 6 and 7.
  • FIG. 15 which differs from that of FIGS. 9 to 11 in that the cell has an annular electrode disposed between the first and second electrode.
  • This electrode can for example be used as a reference electrode.
  • the parts may be assembled as a laminate on a continuous line.
  • a continuous sheet 1 of PET could be first punched and then adhesive could be applied continuously by printing on the remaining sheet.
  • Electrodes pre-printed with chemical solution and dried) could be fed directly as a laminate onto the adhesive coated side.
  • Adhesive could then be applied to the other side of the punched core sheet and then the electrode could be fed as a laminate onto the second side.
  • the adhesive could be applied as a hot melt interleaving film.
  • the core sheet could first be adhesive coated and then punched.
  • the cell has been described with reference to Mylar® and Melinex® PET, other chemically inert and electrically resistive materials may be utilised and other dimensions chosen.
  • the materials used for spacer sheet 1 and-for supporting the reference and counter electrodes may be the same or may differ one from the other.
  • palladium electrodes other metals such as platinum, silver, gold, copper or the like may be used and silver may be reacted with a chloride to form a silver/silver chloride electrode or with other halides.
  • the electrodes need not be of the same metal.
  • the dimensions of the sensor may readily be varied according to requirements.
  • the electrodes cover the cell end openings, in other embodiments (not illustrated) the electrodes do not entirely cover the cell end openings. In that case it is desirable that the electrodes be in substantial overlying registration.
  • Electrodes cover the apertures of cell 11 have the advantages that the electrode area is precisely defined simply by punching hole 11 . Furthermore the electrodes so provided are parallel, overlying, of substantially the same area, and are substantially or entirely devoid of “edge” effects.
  • each sensor has one cell cavity
  • sensors may be provided with two or more cavities.
  • a second cavity may be provided with a predetermined quantity of the analyte and may function as a reference cell.

Abstract

A biosensor for use in determining a concentration of a component in an aqueous liquid sample is provided including: an electrochemical cell having a first electrically resistive substrate having a thin layer of electrically conductive material, a second electrically resistive substrate having a thin layer of electrically conductive material, the substrates being disposed with the electrically conductive materials facing each other and being separated by a sheet including an aperture, the wall of which aperture defines a cell wall and a sample introduction aperture whereby the aqueous liquid sample may be introduced into the cell; and a measuring circuit.

Description

RELATED APPLICATIONS
This application is a continuation of U.S. patent application Ser. No. 09/840,624 filed on Apr. 23, 2001, which issued as U.S. Pat. No. 6,863,801 on Mar. 8, 2005, which is a continuation of U.S. application Ser. No. 09/709,968, filed Nov. 10, 2000, which issued as U.S. Pat. No. 6,521,110 on Feb. 18, 2003, which is a continuation of U.S. application Ser. No. 09/314,251, filed May 18, 1999, which issued as U.S. Pat. No. 6,174,420 on Jan. 16, 2001, which is a continuation-in-part of U.S. application Ser. No. 09/068,828, filed on Mar. 15, 1999, which issued as U.S. Pat. No. 6,179,979 on Jan. 30, 2001, and is also a continuation-in-part of U.S. application Ser. No. 08/852,804, filed on May 7, 1997, which issued as U.S. Pat. No. 5,942,102 on Aug. 24, 1999, the contents of which are incorporated herein by reference in their entirety.
FIELD OF THE INVENTION
This invention relates to an electrochemical cell for determining the concentration of an analyte in a carrier.
BACKGROUND OF THE INVENTION
The invention herein described is an improvement in or modification of the invention described in our co-pending U.S. application Ser. No. 08/981,385, entitled ELECTROCHEMICAL CELL, filed on Dec. 18, 1997, the contents of which are incorporated herein by reference in its entirety.
The invention will herein be described with particular reference to a biosensor adapted to measure the concentration of glucose in blood, but it will be understood not to be limited to that particular use and is applicable to other analytic determinations.
It is known to measure the concentration of a component to be analysed in an aqueous liquid sample by placing the sample into a reaction zone in an electrochemical cell comprising two electrodes having an impedance which renders them suitable for amperometric measurement. The component to be analysed is allowed to react directly or indirectly with a redox reagent whereby to form an oxidisable (or reducible) substance in an amount corresponding to the concentration of the component to be analysed. The quantity of the oxidisable (or reducible) substance present is then estimated electrochemically. Generally this method requires sufficient separation of the electrodes so that electrolysis products at one electrode cannot reach the other electrode and interfere with the processes at the other electrode during the period of measurement.
In our co-pending application we described a novel method for determining the concentration of the reduced (or oxidised) form of a redox species in an electrochemical cell of the kind comprising a working electrode and a counter (or counter/reference) electrode spaced from the working electrode by a predetermined distance. The method involves applying an electric potential difference between the electrodes and selecting the potential of the working electrode such that the rate of electro-oxidation of the reduced form of the species (or of electro-reduction of the oxidised form) is diffusion controlled. The spacing between the working electrode and the counter electrode is selected so that reaction products from the counter electrode arrive at the working electrode. By determining the current as a function of time after application of the potential and prior to achievement of a steady state current and then estimating the magnitude of the steady state current, the method previously described allows the diffusion coefficient and/or the concentration of the reduced (or oxidised) form of the species to be estimated.
Our co-pending application exemplifies this method with reference to use of a “thin layer electrochemical cell” employing a GOD/Ferrocyanide system. As herein used, the term “thin layer electrochemical cell” refers to a cell having closely spaced electrodes such that reaction product from the counter electrode arrives at the working electrode. In practice, the separation of electrodes in such a cell for measuring glucose in blood will be less than 500 microns, and preferably less than 200 microns.
The chemistry used in the exemplified electrochemical cell is as follows:
Figure USRE042567-20110726-C00001

where GOD is the enzyme glucose oxidase, and GOD* is the ‘activated’ enzyme. Ferricyanide ([Fe(CN)6]3−) is the ‘mediator’ which returns the GOD* to its catalytic state. GOD, an enzyme catalyst, is not consumed during the reaction so long as excess mediator is present. Ferrocyanide ([Fe(CN)6]4−) is the product of the total reaction. Ideally there is initially no ferrocyanide, although in practice there is often a small quantity. After reaction is complete the concentration of ferrocyanide (measured electrochemically) indicates the initial concentration of glucose. The total reaction is the sum of reactions 1 and 2:
Figure USRE042567-20110726-C00002

“Glucose” refers specifically to β-D-glucose.
The prior art suffers from a number of disadvantages. Firstly, sample size required is greater than desirable. It would be generally preferable to be able to make measurements on samples of reduced volume since this in turn enables use of less invasive methods to obtain samples.
Secondly, it would be generally desirable to improve the accuracy of measurement and to eliminate or reduce variations due, for example, to cell asymmetry or other factors introduced during mass production of microcells. Likewise, it would be desirable to reduce electrode “edge” effects.
Thirdly, since the cells are disposable after use, it is desirable that they be capable of mass production at relatively low cost.
SUMMARY OF THE INVENTION
In a first embodiment of the present invention, a biosensor for use in determining a concentration of a component in an aqueous liquid sample is provided, the biosensor including: (a) an electrochemical cell, the electrochemical cell including a first electrically resistive substrate having a first thin layer of a first electrically conductive material on a first face, a second electrically resistive substrate having a second thin layer of a second electrically conductive material on a second face, the substrates being disposed with the first electrically conductive material facing the second electrically conductive material and being separated by a sheet including an aperture, the wall of which aperture cooperates with the electrically conductive materials to define a cell wall, and wherein the aperture defines a working electrode area in the cell, the cell further including a sample introduction aperture whereby the aqueous liquid sample may be introduced into the cell; and (b) a measuring circuit.
In one aspect of the first embodiment, the electrochemical cell further includes a socket region having a first contact area in electrical communication with the first thin layer of the first electrically conductive material and a second contact area in electrical communication with the second thin layer of the second electrically conductive material, whereby the electrochemical cell may be electrically connected with the measuring circuit.
In another aspect of the first embodiment, the measuring circuit includes a tongue plug.
In a further aspect of the first embodiment, at least one of the first electrically conductive material and the second electrically conductive material includes a metal. The metal may further include a sputter coated metal.
In still other aspects of the first embodiment, the aqueous liquid sample includes blood, and the component includes glucose.
In yet another aspect of the first embodiment, the measuring circuit includes an automated instrument for detecting an electrical signal from the electrochemical cell and relating the electrical signal to the concentration of the component in the aqueous liquid sample.
In a further aspect of the first embodiment, the electrochemical cell includes a substantially flat strip having a thickness, the strip having at least two lateral edges, and wherein the sample introduction aperture includes a notch through the entire thickness of the strip in at least one of the lateral edges thereof.
In a second embodiment of the present invention, a biosensor for use in determining a concentration of a component in an aqueous liquid sample is provided, the biosensor including: (a) a thin layer electrochemical cell, the cell including: (i) an electrically resistive sheet including an aperture wherein the aperture defines a working electrode area in the cell; (ii) a first electrode layer covering the aperture on a first side of the sheet; (iii) a second electrode layer covering the aperture on a second side of the sheet; and (iv) a passage for admission into the aperture of the aqueous liquid sample; and (b) a measuring circuit.
In one aspect of the second embodiment, the electrochemical cell further includes a socket region having a first contact area in electrical communication with the first electrode layer and a second contact area in electrical communication with the second electrode layer, whereby the electrochemical cell may be electrically connected with the measuring circuit.
In another aspect of the second embodiment, the measuring circuit includes a tongue plug.
In still other aspects of the second embodiment, the aqueous liquid sample includes blood, and the component includes glucose.
In a further aspect of the second embodiment, the measuring circuit includes an automated instrument for detecting an electrical signal from the electrochemical cell and relating the electrical signal to the concentration of the component in the aqueous liquid sample.
In yet another aspect of the second embodiment, the cell includes a substantially flat strip having a thickness, the strip having at least two lateral edges, and wherein the passage for admission into the aperture includes a notch through the entire thickness of the strip in at least one of the lateral edges thereof.
In a third embodiment of the present invention, an apparatus for determining a concentration of a reduced form or an oxidized form of a redox species in a liquid sample is provided, the apparatus including: (a) a hollow electrochemical cell having a working electrode and a counter or counter/reference electrode wherein the working electrode is spaced from the counter or counter/reference electrode by less than 500 μm; (b) means for applying an electric potential difference between the electrodes; and (c) means for electrochemically determining the concentration of the reduced form or the oxidized form of the redox species in the liquid sample.
In one aspect of the third embodiment, means for electrochemically determining the concentration of the reduced form or the oxidized form of the redox species includes: (i) means for determining a change in current with time after application of the electric potential difference and prior to achievement of a steady state current; (ii) means for estimating a magnitude of the steady state current; and (iii) means for obtaining from the change in current with time and the magnitude of the steady state current, a value indicative of the concentration of the reduced form or the oxidized form of the redox species.
In another aspect of the third embodiment, the cell further includes a socket region having a first contact area in electrical communication with the working electrode and a second contact area in electrical communication with the counter or counter/reference electrode, whereby the cell may be electrically connected with at least one of the means for applying an electric potential difference between the electrodes and the means for electrochemically-determining the concentration of the reduced form or the oxidized form of the redox species in the liquid sample.
In a further aspect of the third embodiment, at least one of the means for applying an electric potential difference between the electrodes and the means for electrochemically determining the concentration of the reduced form or the oxidized form of the redox species in the liquid sample includes a tongue plug.
In yet another aspect of the third embodiment, at least one of the means for applying an electric potential difference between the electrodes and the means for electrochemically determining the concentration of the reduced form or the oxidized form of the redox species in the liquid sample includes an automated instrument for detecting an electrical signal from the electrochemical cell and relating the electrical signal to the concentration of the reduced form or the oxidized form of the redox species in the liquid sample.
In a further aspect of the third embodiment, the cell includes a substantially flat strip having a thickness, the strip having at least two lateral edges, and wherein a notch extends through a wall of the electrochemical cell and through the entire thickness of the strip in at least one of the lateral edges thereof, whereby the liquid sample may be introduced into the cell.
In still other aspects of the third embodiment, the liquid sample includes blood, and the redox species includes glucose.
In a fourth embodiment of the present invention, a method for determining a concentration of a reduced form or an oxidized form of a redox species in a liquid sample is provided, the method including: (a) providing a hollow electrochemical cell having a working electrode and a counter or counter/reference electrode wherein the working electrode is spaced from the counter or counter/reference electrode by less than 500 μm; (b) applying an electric potential difference between the electrodes; and (c) electrochemically determining the concentration of the reduced form or the oxidized form of the redox species in the liquid sample.
In one aspect of the fourth embodiment, step (c) includes: (i) determining a change in current with time after application of the electric potential difference and prior to achievement of a steady state current; (ii) estimating a magnitude of the steady state current; and (iii) obtaining from the change in current with time and the magnitude of the steady state current, a value indicative of the concentration of the reduced form or the oxidized form of the redox species.
In another aspect of the fourth embodiment, the cell further includes a socket region having a first contact area in electrical communication with the working electrode and a second contact area in electrical communication with the counter or counter/reference electrode.
In a further aspect of the fourth embodiment, step (b) further includes the step of: providing an automated instrument for applying an electric potential difference between the electrodes.
In yet another aspect of the fourth embodiment, step (c) includes the steps of: (i) providing an automated instrument for detecting an electrical signal from the electrochemical cell; and (ii) relating the electrical signal to the concentration of the reduced form or the oxidized form of the redox species in the liquid sample.
In a further aspect of the fourth embodiment, the cell includes a substantially flat strip having a thickness, the strip having at least two lateral edges, and wherein a notch extends through a wall of the electrochemical cell and through the entire thickness of the strip in at least one of the lateral edges thereof, whereby the liquid sample may be introduced into the cell.
In still other aspects of the fourth embodiment, the liquid sample includes blood and the redox species includes glucose.
BRIEF DESCRIPTION OF THE DRAWINGS
The invention will now be particularly described by way of example only with reference to the accompanying schematic drawings wherein:
FIG. 1 shows the product of manufacturing step 2 in plan.
FIG. 2 shows the product of FIG. 1 in side elevation.
FIG. 3 shows the product of FIG. 1 in end elevation.
FIG. 4 shows the product of manufacturing step 3 in plan.
FIG. 5 shows the product of FIG. 4 in cross-section on line 5-5 of FIG. 4.
FIG. 6 shows the product of manufacturing step 5 in plan.
FIG. 7 shows the product of FIG. 6 in side elevation.
FIG. 8 shows the product of FIG. 6 in end elevation.
FIG. 9 shows the product of manufacturing step 7 in plan.
FIG. 10 is a cross-section of FIG. 9 on line 10-10.
FIG. 11 shows the product of FIG. 9 in end elevation.
FIG. 12 shows a cell according to the invention in plan.
FIG. 13 shows the call of FIG. 12 in side elevation.
FIG. 14 shows the cell of FIG. 12 in end elevation.
FIG. 15 shows a scrap portion of a second embodiment of the invention in enlarged section.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT
The construction of a thin layer electrochemical cell will now be described by way of example of the improved method of manufacture.
Step 1: A sheet 1 of Melinex® (a chemically inert, and electrically resistive Polyethylene Terephthalate [“PET”]) approximately 13 cm×30 cm and 100 micron thick was laid flat on a sheet of release paper 2 and coated using a Number 2 MYAR bar to a thickness of 12 microns wet (approximately 2-5 microns dry) with a water-based heat activated adhesive 3 (ICI Novacoat system using catalyst:adhesive). The water was then evaporated by means of a hot air dryer leaving a contact adhesive surface. The sheet was then turned over on a release paper and the reverse side was similarly coated with the same adhesive 4, dried, and a protective release paper 5 applied to the exposed adhesive surface. The edges were trimmed to obtain a sheet uniformly coated on both sides with tacky contact adhesive protected by release paper.
Step 2: The sheet with protective release papers was cut into strips 7, each about 18 mm×210 mm (FIGS. 1-3).
Step 3: A strip 7 of adhesive-coated PET from step 2 with release paper 2, 5 on respective sides, was placed in a die assembly (not shown) and clamped. The die assembly was adapted to punch the strip with a locating hole 10 at each end and with for example 37 circular holes 11 each of 3.4 mm diameter at 5 mm centres equi-spaced along a line between locating holes 10. The area of each hole 11 is approximately 9 square mm.
Step 4: A sheet 12 of Mylar® PET approximately 21 cm square and 135 microns thick was placed in a sputter coating chamber for palladium coating 13. The sputter coating took place under a vacuum of between 4 and 6 millibars and in an atmosphere of argon gas. Palladium was coated on the PET to a thickness of 100-1000 angstroms. There is thus formed a sheet 14 having a palladium sputter coating 13.
Step 5: The palladium coated PET sheet 14 from Step 4 was then cut into strips 14 and 15 and a die was used to punch two location holes 16 in each strip, at one end (FIGS. 6, 7 and 8). Strips 14 and 15 differ only in dimension strips 14 being 25 mm×210 mm and strips 15 being 23 mm×210 mm.
Step 6: A spacer strip 7 prepared as in step 3 was then placed in a jig (not shown) having two locating pins (one corresponding to each locating hole 10 of strip 7) and the upper release paper 2 was removed. A strip 14 of palladium coated PET prepared as in step 5 was then laid over the adhesive layer, palladium surface downwards, using the jig pins to align the locating holes 16 with the underlying PET strip 7. This combination was then passed through a laminator comprising a set of pinch rollers, one of which was adapted to heat the side bearing a palladium coated PET strip 14. The roller on the opposite side of the strip 7 was cooled. By this means, only the adhesive between the palladium of strip 14 and PET strip 7 was activated.
Step 7: PET strip 7 was then turned over and located in the jig with the release coating uppermost. The release coating was peeled off and second palladium coated strip 15 was placed palladium side down on the exposed adhesive surface using the locating pins to align the strips. this assembly was now passed again through the laminator of step 6, this time with the hot roll adjacent the palladium coated Mylar® added in step 7 so as to activate the intervening adhesive (FIGS. 9, 10 and 11).
Step 8: The assembly from step 7 was returned to the die assembly and notches 17 punched in locations so as to extend between the circular holes 11 previously punched in the Melinex® PET and the strip edge 17. Notches 16 extend so as to intercept the circumference of each circular cell. The strip was then guillotined to give 37 individual “sensor strips”, each strip being about 5 mm wide and each having one thin layer cavity cell (FIGS. 12, 13 and 14).
There is thus produced a cell as shown in FIG. 12, 13 or 14. The cell comprises a first electrode consisting of PET layer 12, a palladium layer 13, an adhesive layer 3, a PET sheet 1, a second adhesive layer 4, a second electrode comprising palladium layer 13, and a PET layer 12. Sheet 1 defines a cylindrical cell 11 having a thickness in the cell axial direction corresponding to the thickness of the Melinex® PET sheet layer 1 together with the thickness of adhesive layers 3 and 4. The cell has circular palladium end walls. Access to the cell is provided at the side edge of the cell where notches 16 intersect cell 11.
In preferred embodiments of the invention, a sample to be analysed is introduced to the cell by capillary action. The sample is placed on contact with notch 16 and is spontaneously drawn by capillary action into the cell, displaced air from the cell venting from the opposite notch 16. A surfactant may be included in the capillary space to assist in drawing in the sample.
The sensors are provided with connection means for example edge connectors whereby the sensors may be placed into a measuring circuit. In a preferred embodiment this is achieved by making spacer 1 shorter than palladium supporting sheets 14, 15 and by making one sheet 15 of shorter length than the other 14. This forms a socket region 20 having contact areas 21, 22 electrically connected with the working and counter electrodes respectively. A simple tongue plug having corresponding engaging conduct surfaces can then be used for electrical connection. Connectors of other form may be devised.
Chemicals for use in the cell may be supported on the cell electrodes or walls, may be supported on an independent support contained within the cell or may be self-supporting.
In one embodiment, chemicals for use in the cell are printed onto the palladium surface of the electrode immediately after step 1 at which stage the freshly-deposited palladium is more hydrophilic. For example, a solution containing 0.2 molar potassium ferricyanide and 1% by weight of glucose oxidase dehydrogenase may be printed on to the palladium surface. Desirably, the chemicals are printed only in the areas which will form a wall of the cell and for preference the chemicals are printed on the surface by means of an ink jet printer. In this manner, the deposition of chemicals may be precisely controlled. If desired, chemicals which are desirably separated until required for use may be printed respectively on the first and second electrodes. For example, a GOD/ferrocyanide composition can be printed on one electrode and a buffer on the other. Although it is highly preferred to apply the chemicals to the electrodes prior to assembly into a cell, chemicals may also be introduced into the cell as a solution after step 6 or step 8 by pipette in the traditional manner and the solvent subsequently is removed by evaporation or drying. Chemicals need not be printed on the cell wall or the electrodes and may instead be impregnated into a gauze, membrane, non-woven fabric or the like contained within, or filling, the cavity (eg inserted in cell 11 prior to steps 6 or 7). In another embodiment the chemicals are formed into a porous mass which may be introduced into the cell as a pellet or granules. Alternatively, the chemicals maybe introduced as a gel.
In a second embodiment of the invention a laminate 21 is first made from a strip 14 as obtained in step 5 adhesively sandwiched between two strips 7 as obtained from step 3. Laminate 20 is substituted for sheet 1 in step 5 and assembled with electrodes as in steps 6 and 7.
There is thus obtained a cell as shown in FIG. 15 which differs from that of FIGS. 9 to 11 in that the cell has an annular electrode disposed between the first and second electrode. This electrode can for example be used as a reference electrode.
It will be understood that in mass production of the cell, the parts may be assembled as a laminate on a continuous line. For example, a continuous sheet 1 of PET could be first punched and then adhesive could be applied continuously by printing on the remaining sheet. Electrodes (pre-printed with chemical solution and dried) could be fed directly as a laminate onto the adhesive coated side. Adhesive could then be applied to the other side of the punched core sheet and then the electrode could be fed as a laminate onto the second side.
The adhesive could be applied as a hot melt interleaving film. Alternatively, the core sheet could first be adhesive coated and then punched.
By drying chemicals on each electrode prior to the gluing step the electrode surface is protected from contamination.
Although the cell has been described with reference to Mylar® and Melinex® PET, other chemically inert and electrically resistive materials may be utilised and other dimensions chosen. The materials used for spacer sheet 1 and-for supporting the reference and counter electrodes may be the same or may differ one from the other. Although the invention has been described with reference to palladium electrodes, other metals such as platinum, silver, gold, copper or the like may be used and silver may be reacted with a chloride to form a silver/silver chloride electrode or with other halides. The electrodes need not be of the same metal.
Although the use of heat activated adhesives has been described, the parts may be assembled by use of hot melt adhesives, fusible laminates and other methods.
The dimensions of the sensor may readily be varied according to requirements.
While it is greatly preferred that the electrodes cover the cell end openings, in other embodiments (not illustrated) the electrodes do not entirely cover the cell end openings. In that case it is desirable that the electrodes be in substantial overlying registration.
Preferred forms of the invention in which the electrodes cover the apertures of cell 11 have the advantages that the electrode area is precisely defined simply by punching hole 11. Furthermore the electrodes so provided are parallel, overlying, of substantially the same area, and are substantially or entirely devoid of “edge” effects.
Although in the embodiments described each sensor has one cell cavity, sensors may be provided with two or more cavities. For example, a second cavity may be provided with a predetermined quantity of the analyte and may function as a reference cell.
As will be apparent to those skilled in the art from the teaching herein contained, a feature of one embodiment herein described may be combined with features of other embodiments herein described or with other embodiments described in our co-pending application. Although the sensor has been described with reference to palladium electrodes and a GOD/ferrocyanide chemistry, it will be apparent to those skilled in the art that other chemistries, and other materials of construction may be employed without departing from the principles herein taught.

Claims (14)

1. A biosensor An apparatus for use in determining a concentration of a component in an aqueous liquid sample, the biosensor apparatus comprising:
(a) an electrochemical cell, the electrochemical cell comprising a first electrically resistive substrate having a first thin layer of a first electrically conductive material on a first face, a second electrically resistive substrate having a second thin layer of a second electrically conductive material on a second face, the substrates being disposed with the first electrically conductive material facing the second electrically conductive material and being separated by a sheet comprising an aperture, the wall of which aperture cooperates with the electrically conductive materials to define a cell wall, and wherein the aperture defines a working electrode area in the cell, the cell further comprising a sample introduction aperture whereby the aqueous liquid sample may be introduced into the cell,
(b) a socket region having a first contact area in electrical communication with the first thin layer of the first electrically conductive material on the first electrically resistive substrate and a second contact area in electrical communication with the second thin layer of the second electrically conductive material on the second electrically resistive substrate, wherein the socket region extends the full width of at least one of the first and second electrically resistive substrates, and the first and second electrically resistive substrates have lengths that are different from one another in the socket region; and
(c) a measuring circuit, the measuring circuit being electrically connectable with the electrochemical cell by engaging with the socket region.
2. The biosensor apparatus of claim 1, wherein the measuring circuit comprises a tongue plug having conductive surfaces that correspond to a shape of the first and second electrically resistive substrates in the socket region such that the tongue plug can be electrically connected to the socket region.
3. The biosensor apparatus of claim 1, wherein at least one of the first electrically conductive material and the second electrically conductive material comprises a metal.
4. The biosensor apparatus of claim 3, wherein the metal comprises a sputter coated metal.
5. The biosensor apparatus of claim 1, wherein the aqueous liquid sample comprises blood.
6. The biosensor apparatus of claim 1, wherein the component comprises glucose.
7. The biosensor apparatus of claim 1, wherein the measuring circuit comprises an automated instrument for detecting an electrical signal from the electrochemical cell and relating the electrical signal to the concentration of the component in the aqueous liquid sample.
8. A biosensor An apparatus for use in determining a concentration of a component in an aqueous liquid sample, the biosensor apparatus comprising:
(a) a thin layer electrochemical cell, the cell comprising:
(i) an electrically resistive sheet comprising an aperture wherein the aperture defines a working electrode area in the cell;
(ii) a first electrode layer covering the aperture on a first side of the sheet;
(iii) a second electrode layer covering the aperture on a second side of the sheet;
(iv) a passage for admission into the aperture of the aqueous liquid sample; and
(v) a socket region for receiving a tongue plug, the socket region having a first contact area in electrical communication with the first electrode layer and a second contact area in electrical communication with the second electrode layer, wherein the socket region extends the full width of at least one of the first and second electrode layers and the first and second electrode layers have lengths that are different from one another in the socket region; and
(b) a measuring circuit.
9. The biosensor apparatus of claim 8, wherein the electrochemical cell is adapted to electrically connect with the measuring circuit.
10. The biosensor apparatus of claim 8, wherein the measuring circuit comprises a tongue plug having conductive surfaces that correspond to a shape of the first and second electrode layers in the socket region such that the tongue plug can be electrically connected to the socket region.
11. The biosensor apparatus of claim 8, wherein the aqueous liquid sample comprises blood.
12. The biosensor apparatus of claim 8, wherein the component comprises glucose.
13. The biosensor apparatus of claim 8, wherein the measuring circuit comprises an automated instrument for detecting an electrical signal from the electrochemical cell and relating the electrical signal to the concentration of the component in the aqueous liquid sample.
14. The biosensor apparatus of claim 8, wherein the cell comprises a substantially flat strip having a thickness, the strip having at least two lateral edges, and wherein the passage for admission into the aperture comprises a notch through the entire thickness of the strip in at least one of the lateral edges thereof.
US12/899,342 1995-11-16 2010-10-06 Electrochemical cell Expired - Lifetime USRE42567E1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US12/899,342 USRE42567E1 (en) 1995-11-16 2010-10-06 Electrochemical cell

Applications Claiming Priority (11)

Application Number Priority Date Filing Date Title
AUPN6619 1995-11-16
AUPN6619A AUPN661995A0 (en) 1995-11-16 1995-11-16 Electrochemical cell 2
AUPCT/AU96/00724 1996-11-15
US09/068,828 US6179979B1 (en) 1995-11-16 1996-11-15 Electrochemical cell
PCT/AU1996/000724 WO1997018464A1 (en) 1995-11-16 1996-11-15 Electrochemical cell
US08/852,804 US5942102A (en) 1995-11-16 1997-05-07 Electrochemical method
US09/314,251 US6174420B1 (en) 1996-11-15 1999-05-18 Electrochemical cell
US09/709,968 US6521110B1 (en) 1995-11-16 2000-11-10 Electrochemical cell
US09/840,624 US6863801B2 (en) 1995-11-16 2001-04-23 Electrochemical cell
US10/843,956 US7431814B2 (en) 1995-11-16 2004-05-12 Electrochemical cell
US12/899,342 USRE42567E1 (en) 1995-11-16 2010-10-06 Electrochemical cell

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US10/843,956 Reissue US7431814B2 (en) 1995-11-16 2004-05-12 Electrochemical cell

Publications (1)

Publication Number Publication Date
USRE42567E1 true USRE42567E1 (en) 2011-07-26

Family

ID=3790943

Family Applications (3)

Application Number Title Priority Date Filing Date
US09/068,828 Expired - Lifetime US6179979B1 (en) 1995-11-16 1996-11-15 Electrochemical cell
US08/852,804 Expired - Lifetime US5942102A (en) 1995-11-16 1997-05-07 Electrochemical method
US12/899,342 Expired - Lifetime USRE42567E1 (en) 1995-11-16 2010-10-06 Electrochemical cell

Family Applications Before (2)

Application Number Title Priority Date Filing Date
US09/068,828 Expired - Lifetime US6179979B1 (en) 1995-11-16 1996-11-15 Electrochemical cell
US08/852,804 Expired - Lifetime US5942102A (en) 1995-11-16 1997-05-07 Electrochemical method

Country Status (16)

Country Link
US (3) US6179979B1 (en)
EP (5) EP0923722B1 (en)
JP (2) JP3863184B2 (en)
KR (5) KR100741181B1 (en)
CN (8) CN1105304C (en)
AT (4) ATE553212T1 (en)
AU (3) AUPN661995A0 (en)
BR (2) BR9611513B1 (en)
CA (3) CA2236848C (en)
DE (3) DE69628588T2 (en)
DK (4) DK0923722T3 (en)
ES (4) ES2365981T3 (en)
HK (6) HK1018096A1 (en)
IL (5) IL132089A (en)
RU (4) RU2174679C2 (en)
WO (2) WO1997018465A1 (en)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9518951B2 (en) 2013-12-06 2016-12-13 Changsha Sinocare Inc. Disposable test sensor with improved sampling entrance
US9523653B2 (en) 2013-05-09 2016-12-20 Changsha Sinocare Inc. Disposable test sensor with improved sampling entrance
US9897566B2 (en) 2014-01-13 2018-02-20 Changsha Sinocare Inc. Disposable test sensor
US9939401B2 (en) 2014-02-20 2018-04-10 Changsha Sinocare Inc. Test sensor with multiple sampling routes

Families Citing this family (299)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6413410B1 (en) * 1996-06-19 2002-07-02 Lifescan, Inc. Electrochemical cell
US6863801B2 (en) * 1995-11-16 2005-03-08 Lifescan, Inc. Electrochemical cell
AUPN661995A0 (en) 1995-11-16 1995-12-07 Memtec America Corporation Electrochemical cell 2
AUPP238898A0 (en) * 1998-03-12 1998-04-09 Usf Filtration And Separations Group Inc. Heated electrochemical cell
US6638415B1 (en) 1995-11-16 2003-10-28 Lifescan, Inc. Antioxidant sensor
US6632349B1 (en) * 1996-11-15 2003-10-14 Lifescan, Inc. Hemoglobin sensor
ATE227844T1 (en) * 1997-02-06 2002-11-15 Therasense Inc SMALL VOLUME SENSOR FOR IN-VITRO DETERMINATION
AUPO581397A0 (en) 1997-03-21 1997-04-17 Memtec America Corporation Sensor connection means
AUPO585797A0 (en) 1997-03-25 1997-04-24 Memtec America Corporation Improved electrochemical cell
AU781184B2 (en) * 1997-08-13 2005-05-12 Lifescan, Inc. Method and apparatus for automatic analysis
AUPO855897A0 (en) * 1997-08-13 1997-09-04 Usf Filtration And Separations Group Inc. Automatic analysing apparatus II
AU758963B2 (en) * 1997-08-13 2003-04-03 Lifescan, Inc. Method and apparatus for automatic analysis
US6036924A (en) 1997-12-04 2000-03-14 Hewlett-Packard Company Cassette of lancet cartridges for sampling blood
DE19753847A1 (en) 1997-12-04 1999-06-10 Roche Diagnostics Gmbh Analytical test element with capillary channel
DE19753850A1 (en) 1997-12-04 1999-06-10 Roche Diagnostics Gmbh Sampling device
US5997817A (en) * 1997-12-05 1999-12-07 Roche Diagnostics Corporation Electrochemical biosensor test strip
US7390667B2 (en) * 1997-12-22 2008-06-24 Roche Diagnostics Operations, Inc. System and method for analyte measurement using AC phase angle measurements
US7407811B2 (en) * 1997-12-22 2008-08-05 Roche Diagnostics Operations, Inc. System and method for analyte measurement using AC excitation
US8071384B2 (en) 1997-12-22 2011-12-06 Roche Diagnostics Operations, Inc. Control and calibration solutions and methods for their use
US6878251B2 (en) * 1998-03-12 2005-04-12 Lifescan, Inc. Heated electrochemical cell
AU743852B2 (en) * 1998-03-12 2002-02-07 Lifescan, Inc. Heated electrochemical cell
AU779350B2 (en) * 1998-03-12 2005-01-20 Lifescan, Inc. Heated electrochemical cell
US6475360B1 (en) 1998-03-12 2002-11-05 Lifescan, Inc. Heated electrochemical cell
US6652734B1 (en) 1999-03-16 2003-11-25 Lifescan, Inc. Sensor with improved shelf life
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
US6591125B1 (en) 2000-06-27 2003-07-08 Therasense, Inc. Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator
US6338790B1 (en) 1998-10-08 2002-01-15 Therasense, Inc. Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator
US6475372B1 (en) * 2000-02-02 2002-11-05 Lifescan, Inc. Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations
US6193873B1 (en) * 1999-06-15 2001-02-27 Lifescan, Inc. Sample detection to initiate timing of an electrochemical assay
AU5747100A (en) * 1999-06-18 2001-01-09 Therasense, Inc. Mass transport limited in vivo analyte sensor
US7276146B2 (en) 2001-11-16 2007-10-02 Roche Diagnostics Operations, Inc. Electrodes, methods, apparatuses comprising micro-electrode arrays
US20050103624A1 (en) * 1999-10-04 2005-05-19 Bhullar Raghbir S. Biosensor and method of making
KR100445489B1 (en) 1999-11-15 2004-08-21 마츠시타 덴끼 산교 가부시키가이샤 Biosensor, method of forming thin-film electrode, and method and apparatus for quantitative determination
US6676815B1 (en) 1999-12-30 2004-01-13 Roche Diagnostics Corporation Cell for electrochemical analysis of a sample
US6716577B1 (en) 2000-02-02 2004-04-06 Lifescan, Inc. Electrochemical test strip for use in analyte determination
US6612111B1 (en) * 2000-03-27 2003-09-02 Lifescan, Inc. Method and device for sampling and analyzing interstitial fluid and whole blood samples
US6571651B1 (en) * 2000-03-27 2003-06-03 Lifescan, Inc. Method of preventing short sampling of a capillary or wicking fill device
CA2644178C (en) * 2000-03-28 2011-03-01 Diabetes Diagnostics, Inc. Rapid response glucose sensor
US6908593B1 (en) 2000-03-31 2005-06-21 Lifescan, Inc. Capillary flow control in a fluidic diagnostic device
US6488827B1 (en) * 2000-03-31 2002-12-03 Lifescan, Inc. Capillary flow control in a medical diagnostic device
IL151914A0 (en) 2000-03-31 2003-04-10 Lifescan Inc Electrically-conductive patterns for monitoring the filling of medical devices
CA2407973C (en) 2000-05-03 2011-06-07 Jen-Jr Gau Biological identification system with integrated sensor chip
AU2006203606B2 (en) * 2000-07-14 2007-05-17 Lifescan, Inc. Electrochemical method for measuring chemical reaction rates
AU2007209797B2 (en) * 2000-07-14 2010-06-03 Lifescan, Inc. Electrochemical method for measuring chemical reaction rates
US6444115B1 (en) 2000-07-14 2002-09-03 Lifescan, Inc. Electrochemical method for measuring chemical reaction rates
CA2733852A1 (en) * 2000-07-14 2002-01-24 Lifescan, Inc. Electrochemical method for measuring chemical reaction rates
RU2278612C2 (en) 2000-07-14 2006-06-27 Лайфскен, Инк. Immune sensor
MXPA03000382A (en) * 2000-07-14 2004-09-13 Lifescan Inc Electrochemical method for measuring chemical reaction rates.
CN1234580C (en) * 2000-08-29 2006-01-04 雀巢制品公司 Flexible container having flat walls
US7182853B2 (en) * 2000-09-22 2007-02-27 University Of Dayton Redox control/monitoring platform for high throughput screening/drug discovery applications
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
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
EP3364187B1 (en) 2000-11-30 2019-09-18 PHC Holdings Corporation Method of quantifying substrate
US6620310B1 (en) * 2000-12-13 2003-09-16 Lifescan, Inc. Electrochemical coagulation assay and device
US7144495B2 (en) 2000-12-13 2006-12-05 Lifescan, Inc. Electrochemical test strip with an integrated micro-needle and associated methods
US6558528B1 (en) 2000-12-20 2003-05-06 Lifescan, Inc. Electrochemical test strip cards that include an integral dessicant
EP2202511A3 (en) * 2001-01-17 2010-09-29 ARKRAY, Inc. Quantitative analyzing method and quantitative analyzer using sensor
US6572745B2 (en) * 2001-03-23 2003-06-03 Virotek, L.L.C. Electrochemical sensor and method thereof
US6855243B2 (en) * 2001-04-27 2005-02-15 Lifescan, Inc. Electrochemical test strip having a plurality of reaction chambers and methods for using the same
US6896778B2 (en) 2001-06-04 2005-05-24 Epocal Inc. Electrode module
US6721586B2 (en) 2001-06-12 2004-04-13 Lifescan, Inc. Percutaneous biological fluid sampling and analyte measurement devices and methods
ES2357887T3 (en) 2001-06-12 2011-05-03 Pelikan Technologies Inc. APPARATUS FOR IMPROVING THE BLOOD OBTAINING SUCCESS RATE FROM A CAPILLARY PUNCTURE.
US8337419B2 (en) 2002-04-19 2012-12-25 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US7981056B2 (en) 2002-04-19 2011-07-19 Pelikan Technologies, Inc. Methods and apparatus for lancet actuation
US7041068B2 (en) 2001-06-12 2006-05-09 Pelikan Technologies, Inc. Sampling module device and method
US6875613B2 (en) 2001-06-12 2005-04-05 Lifescan, Inc. Biological fluid constituent sampling and measurement devices and methods
US7682318B2 (en) 2001-06-12 2010-03-23 Pelikan Technologies, Inc. Blood sampling apparatus and method
US6837988B2 (en) * 2001-06-12 2005-01-04 Lifescan, Inc. Biological fluid sampling and analyte measurement devices and methods
US9226699B2 (en) 2002-04-19 2016-01-05 Sanofi-Aventis Deutschland Gmbh Body fluid sampling module with a continuous compression tissue interface surface
US7344507B2 (en) 2002-04-19 2008-03-18 Pelikan Technologies, Inc. Method and apparatus for lancet actuation
CA2448902C (en) 2001-06-12 2010-09-07 Pelikan Technologies, Inc. Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties
US6793632B2 (en) 2001-06-12 2004-09-21 Lifescan, Inc. Percutaneous biological fluid constituent sampling and measurement devices and methods
WO2002100254A2 (en) 2001-06-12 2002-12-19 Pelikan Technologies, Inc. Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge
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
EP1395185B1 (en) 2001-06-12 2010-10-27 Pelikan Technologies Inc. Electric lancet actuator
US6501976B1 (en) 2001-06-12 2002-12-31 Lifescan, Inc. Percutaneous biological fluid sampling and analyte measurement devices and methods
EP1411352B1 (en) * 2001-07-13 2012-01-11 ARKRAY, Inc. Analysing instrument and lancet-integrated attachment for concentration measuring device
US20030036202A1 (en) * 2001-08-01 2003-02-20 Maria Teodorcyzk Methods and devices for use in analyte concentration determination assays
US6939310B2 (en) 2001-10-10 2005-09-06 Lifescan, Inc. Devices for physiological fluid sampling and methods of using the same
CN1232818C (en) 2001-10-10 2005-12-21 生命扫描有限公司 Electrochemical cell
US7018843B2 (en) * 2001-11-07 2006-03-28 Roche Diagnostics Operations, Inc. Instrument
EP1448489B1 (en) * 2001-11-16 2010-08-25 Stefan Ufer Flexible sensor and method of fabrication
US20030116447A1 (en) 2001-11-16 2003-06-26 Surridge Nigel A. Electrodes, methods, apparatuses comprising micro-electrode arrays
US6749887B1 (en) 2001-11-28 2004-06-15 Lifescan, Inc. Solution drying system
US6689411B2 (en) 2001-11-28 2004-02-10 Lifescan, Inc. Solution striping system
US6856125B2 (en) 2001-12-12 2005-02-15 Lifescan, Inc. Biosensor apparatus and method with sample type and volume detection
US6946067B2 (en) * 2002-01-04 2005-09-20 Lifescan, Inc. Method of forming an electrical connection between an electrochemical cell and a meter
US6872358B2 (en) 2002-01-16 2005-03-29 Lifescan, Inc. Test strip dispenser
US8260393B2 (en) 2003-07-25 2012-09-04 Dexcom, Inc. Systems and methods for replacing signal data artifacts in a glucose sensor data stream
US8010174B2 (en) 2003-08-22 2011-08-30 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US20060134713A1 (en) 2002-03-21 2006-06-22 Lifescan, Inc. Biosensor apparatus and methods of use
US20030180814A1 (en) * 2002-03-21 2003-09-25 Alastair Hodges Direct immunosensor assay
US20030186446A1 (en) 2002-04-02 2003-10-02 Jerry Pugh Test strip containers and methods of using the same
US7297122B2 (en) 2002-04-19 2007-11-20 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7232451B2 (en) 2002-04-19 2007-06-19 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8221334B2 (en) 2002-04-19 2012-07-17 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US6837976B2 (en) * 2002-04-19 2005-01-04 Nova Biomedical Corporation Disposable sensor with enhanced sample port inlet
US8579831B2 (en) 2002-04-19 2013-11-12 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7491178B2 (en) 2002-04-19 2009-02-17 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9314194B2 (en) 2002-04-19 2016-04-19 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US9795334B2 (en) 2002-04-19 2017-10-24 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US9248267B2 (en) 2002-04-19 2016-02-02 Sanofi-Aventis Deustchland Gmbh Tissue penetration device
US7331931B2 (en) 2002-04-19 2008-02-19 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
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
US7674232B2 (en) 2002-04-19 2010-03-09 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7892183B2 (en) 2002-04-19 2011-02-22 Pelikan Technologies, Inc. Method and apparatus for body fluid sampling and analyte sensing
US7198606B2 (en) 2002-04-19 2007-04-03 Pelikan Technologies, Inc. Method and apparatus for a multi-use body fluid sampling device with analyte sensing
US7976476B2 (en) 2002-04-19 2011-07-12 Pelikan Technologies, Inc. Device and method for variable speed lancet
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
US8702624B2 (en) 2006-09-29 2014-04-22 Sanofi-Aventis Deutschland Gmbh Analyte measurement device with a single shot actuator
US7371247B2 (en) 2002-04-19 2008-05-13 Pelikan Technologies, Inc Method and apparatus for penetrating tissue
US7291117B2 (en) 2002-04-19 2007-11-06 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US6942770B2 (en) * 2002-04-19 2005-09-13 Nova Biomedical Corporation Disposable sub-microliter volume biosensor with enhanced sample inlet
US8267870B2 (en) 2002-04-19 2012-09-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for body fluid sampling with hybrid actuation
US8784335B2 (en) 2002-04-19 2014-07-22 Sanofi-Aventis Deutschland Gmbh Body fluid sampling device with a capacitive sensor
US7547287B2 (en) 2002-04-19 2009-06-16 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7229458B2 (en) 2002-04-19 2007-06-12 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7343188B2 (en) * 2002-05-09 2008-03-11 Lifescan, Inc. Devices and methods for accessing and analyzing physiological fluid
GB0211449D0 (en) * 2002-05-17 2002-06-26 Oxford Biosensors Ltd Analyte measurement
US7291256B2 (en) * 2002-09-12 2007-11-06 Lifescan, Inc. Mediator stabilized reagent compositions and methods for their use in electrochemical analyte detection assays
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
US7118916B2 (en) * 2002-10-21 2006-10-10 Lifescan, Inc. Method of reducing analysis time of endpoint-type reaction profiles
US8574895B2 (en) 2002-12-30 2013-11-05 Sanofi-Aventis Deutschland Gmbh Method and apparatus using optical techniques to measure analyte levels
US7144485B2 (en) * 2003-01-13 2006-12-05 Hmd Biomedical Inc. Strips for analyzing samples
ES2490740T3 (en) 2003-06-06 2014-09-04 Sanofi-Aventis Deutschland Gmbh Apparatus for blood fluid sampling and analyte detection
WO2006001797A1 (en) 2004-06-14 2006-01-05 Pelikan Technologies, Inc. Low pain penetrating
US7645373B2 (en) * 2003-06-20 2010-01-12 Roche Diagnostic Operations, Inc. System and method for coding information on a biosensor test strip
US8071030B2 (en) 2003-06-20 2011-12-06 Roche Diagnostics Operations, Inc. Test strip with flared sample receiving chamber
US7488601B2 (en) 2003-06-20 2009-02-10 Roche Diagnostic Operations, Inc. System and method for determining an abused sensor during analyte measurement
US7645421B2 (en) 2003-06-20 2010-01-12 Roche Diagnostics Operations, 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
US8679853B2 (en) * 2003-06-20 2014-03-25 Roche Diagnostics Operations, Inc. Biosensor with laser-sealed capillary space and method of making
US7597793B2 (en) * 2003-06-20 2009-10-06 Roche Operations Ltd. System and method for analyte measurement employing maximum dosing time delay
US8206565B2 (en) 2003-06-20 2012-06-26 Roche Diagnostics Operation, Inc. System and method for coding information on a biosensor test strip
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
ES2683013T3 (en) * 2003-06-20 2018-09-24 F. Hoffmann-La Roche Ag Reagent band for test strip
US8058077B2 (en) * 2003-06-20 2011-11-15 Roche Diagnostics Operations, Inc. Method for coding information on a biosensor test strip
EP1642125B1 (en) * 2003-06-20 2017-09-27 Roche Diabetes Care GmbH Biosensor with multiple electrical functionalities
US7452457B2 (en) * 2003-06-20 2008-11-18 Roche Diagnostics Operations, Inc. System and method for analyte measurement using dose sufficiency electrodes
US7220034B2 (en) * 2003-07-11 2007-05-22 Rudolph Technologies, Inc. Fiber optic darkfield ring light
US20190357827A1 (en) 2003-08-01 2019-11-28 Dexcom, Inc. Analyte sensor
BRPI0413213A (en) 2003-08-21 2006-10-03 Agamatrix Inc method and apparatus for determining the presence of a selected analyte in a sample arranged in an electrochemical cell, method for determining the effective separation distance between a first electrode and a second electrode in an electrochemical cell, and method for determining an effective electrode transport property. a species in a liquid sample disposed between a first electrode and a second electrode in an electrochemical cell
US20140121989A1 (en) 2003-08-22 2014-05-01 Dexcom, Inc. Systems and methods for processing analyte sensor data
EP1671096A4 (en) 2003-09-29 2009-09-16 Pelikan Technologies Inc Method and apparatus for an improved sample capture device
JP4458802B2 (en) * 2003-10-02 2010-04-28 パナソニック株式会社 Method for measuring glucose in blood and sensor used therefor
EP1680014A4 (en) 2003-10-14 2009-01-21 Pelikan Technologies Inc Method and apparatus for a variable user interface
US8532730B2 (en) 2006-10-04 2013-09-10 Dexcom, Inc. Analyte sensor
US8364231B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
WO2005057175A2 (en) 2003-12-09 2005-06-23 Dexcom, Inc. Signal processing for continuous analyte sensor
US7822454B1 (en) 2005-01-03 2010-10-26 Pelikan Technologies, Inc. Fluid sampling device with improved analyte detecting member configuration
WO2005065414A2 (en) 2003-12-31 2005-07-21 Pelikan Technologies, Inc. Method and apparatus for improving fluidic flow and sample capture
BRPI0507376A (en) 2004-02-06 2007-07-10 Bayer Healthcare Llc oxidizable species as an internal reference for biosensors and method of use
CN100370249C (en) * 2004-03-04 2008-02-20 五鼎生物技术股份有限公司 Method for reducing measurement deviation of current type biosensors
US9101302B2 (en) * 2004-05-03 2015-08-11 Abbott Diabetes Care Inc. Analyte test device
JP4773428B2 (en) 2004-05-14 2011-09-14 バイエル・ヘルスケア・エルエルシー Voltammetric system for analyzing biological analytes
US8828203B2 (en) 2004-05-20 2014-09-09 Sanofi-Aventis Deutschland Gmbh Printable hydrogels for biosensors
JP5215661B2 (en) * 2004-05-21 2013-06-19 アガマトリックス インコーポレーテッド Electrochemical cell and method for making an electrochemical cell
WO2005120365A1 (en) 2004-06-03 2005-12-22 Pelikan Technologies, Inc. Method and apparatus for a fluid sampling device
US9775553B2 (en) 2004-06-03 2017-10-03 Sanofi-Aventis Deutschland Gmbh Method and apparatus for a fluid sampling device
US7556723B2 (en) * 2004-06-18 2009-07-07 Roche Diagnostics Operations, Inc. Electrode design for biosensor
US7569126B2 (en) 2004-06-18 2009-08-04 Roche Diagnostics Operations, Inc. System and method for quality assurance of a biosensor test strip
US8343074B2 (en) 2004-06-30 2013-01-01 Lifescan Scotland Limited Fluid handling devices
US20060002817A1 (en) 2004-06-30 2006-01-05 Sebastian Bohm Flow modulation devices
US7512432B2 (en) * 2004-07-27 2009-03-31 Abbott Laboratories Sensor array
JP2006170974A (en) 2004-12-15 2006-06-29 F Hoffmann-La Roche Ag Analysis system for analyzing liquid sample on assay element
US8652831B2 (en) 2004-12-30 2014-02-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for analyte measurement test time
ES2293493T3 (en) * 2005-03-03 2008-03-16 Apex Biotechnology Corporation A METHOD TO REDUCE THE DEVIATION OF MEASUREMENT OF AMPERIMETRIC BIOSENSORS.
US7645374B2 (en) 2005-04-15 2010-01-12 Agamatrix, Inc. Method for determination of analyte concentrations and related apparatus
US7547382B2 (en) * 2005-04-15 2009-06-16 Agamatrix, Inc. Determination of partial fill in electrochemical strips
US7964089B2 (en) 2005-04-15 2011-06-21 Agamatrix, Inc. Analyte determination method and analyte meter
US7344626B2 (en) * 2005-04-15 2008-03-18 Agamatrix, Inc. Method and apparatus for detection of abnormal traces during electrochemical analyte detection
US7517439B2 (en) * 2005-04-15 2009-04-14 Agamatrix, Inc. Error detection in analyte measurements based on measurement of system resistance
GB0509919D0 (en) * 2005-05-16 2005-06-22 Ralph Ellerker 1795 Ltd Improvements to door closure system
US8323464B2 (en) 2005-05-25 2012-12-04 Universal Biosensors Pty Ltd Method and apparatus for electrochemical analysis
US8192599B2 (en) * 2005-05-25 2012-06-05 Universal Biosensors Pty Ltd Method and apparatus for electrochemical analysis
US8016154B2 (en) * 2005-05-25 2011-09-13 Lifescan, Inc. Sensor dispenser device and method of use
ES2717135T3 (en) 2005-07-20 2019-06-19 Ascensia Diabetes Care Holdings Ag Method to signal the user to add an additional sample to a test strip, method to measure the temperature of a sample and methods to determine the concentration of an analyte based on controlled amperometry
US8298389B2 (en) 2005-09-12 2012-10-30 Abbott Diabetes Care Inc. In vitro analyte sensor, and methods
US7846311B2 (en) 2005-09-27 2010-12-07 Abbott Diabetes Care Inc. In vitro analyte sensor and methods of use
KR101577176B1 (en) * 2005-09-30 2015-12-14 바이엘 헬스케어 엘엘씨 Gated voltammetry analyte determination
US7749371B2 (en) 2005-09-30 2010-07-06 Lifescan, Inc. Method and apparatus for rapid electrochemical analysis
US8163162B2 (en) * 2006-03-31 2012-04-24 Lifescan, Inc. Methods and apparatus for analyzing a sample in the presence of interferents
US8529751B2 (en) * 2006-03-31 2013-09-10 Lifescan, Inc. Systems and methods for discriminating control solution from a physiological sample
GB0607205D0 (en) * 2006-04-10 2006-05-17 Diagnoswiss Sa Miniaturised biosensor with optimized anperimetric detection
DE102006043718B4 (en) * 2006-09-18 2014-12-31 Alexander Adlassnig Determination of hydrogen peroxide concentrations
EP1909096A1 (en) * 2006-10-04 2008-04-09 Infopia Co., Ltd. Biosensor
ES2445742T3 (en) 2006-10-05 2014-03-05 Lifescan Scotland Ltd Procedures for determining the presence of a sufficient amount of fluid sample in a test strip
ES2375288T3 (en) * 2006-10-05 2012-02-28 Lifescan Scotland Limited PROCEDURE TO DETERMINE ANALYTE CONCENTRATIONS CORRECTED WITH HEMATOCRITE.
US9046480B2 (en) 2006-10-05 2015-06-02 Lifescan Scotland Limited Method for determining hematocrit corrected analyte concentrations
WO2008040997A1 (en) * 2006-10-05 2008-04-10 Lifescan Scotland Limited A test strip comprising patterned electrodes
EP2957908A1 (en) 2006-10-05 2015-12-23 Lifescan Scotland Limited Methods for determining an analyte concentration using signal processing algorithms
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
JP5244116B2 (en) 2006-10-24 2013-07-24 バイエル・ヘルスケア・エルエルシー Transient decay current measurement method
US7646166B2 (en) * 2006-12-06 2010-01-12 Gm Global Technology Operations, Inc. Method and apparatus for modeling diffusion in an electrochemical system
US8808515B2 (en) * 2007-01-31 2014-08-19 Abbott Diabetes Care Inc. Heterocyclic nitrogen containing polymers coated analyte monitoring device and methods of use
US7875461B2 (en) 2007-07-24 2011-01-25 Lifescan Scotland Limited Test strip and connector
US8101062B2 (en) 2007-07-26 2012-01-24 Nipro Diagnostics, Inc. System and methods for determination of analyte concentration using time resolved amperometry
JP5179583B2 (en) * 2007-07-26 2013-04-10 ニプロ ダイアグナスティックス,インコーポレーテッド Analyte concentration measurement system and method using time-resolved amperometry
CN101377473B (en) * 2007-08-31 2012-04-25 中国科学院过程工程研究所 Fast quantitative electroanalysis method
US7943022B2 (en) 2007-09-04 2011-05-17 Lifescan, Inc. Analyte test strip with improved reagent deposition
JP5523323B2 (en) * 2007-09-24 2014-06-18 バイエル・ヘルスケア・エルエルシー Analyte test sensor
US8778168B2 (en) * 2007-09-28 2014-07-15 Lifescan, Inc. Systems and methods of discriminating control solution from a physiological sample
TWI516601B (en) 2007-10-26 2016-01-11 環球生物醫療感測器私人有限公司 Apparatus and method for electrochemical detection
US8001825B2 (en) * 2007-11-30 2011-08-23 Lifescan, Inc. Auto-calibrating metering system and method of use
WO2009076302A1 (en) 2007-12-10 2009-06-18 Bayer Healthcare Llc Control markers for auto-detection of control solution and methods of use
EP2222867B1 (en) * 2007-12-10 2018-07-11 Ascensia Diabetes Care Holdings AG Rapid-read gated amperometry
US8097674B2 (en) * 2007-12-31 2012-01-17 Bridgestone Corporation Amino alkoxy-modified silsesquioxanes in silica-filled rubber with low volatile organic chemical evolution
US8603768B2 (en) 2008-01-17 2013-12-10 Lifescan, Inc. System and method for measuring an analyte in a sample
RU2500349C2 (en) * 2008-03-17 2013-12-10 Айсенс Корпорейшн Auxiliary unit of analyte sensor and methods and devices for introduction of analyte sensor, connected with auxiliary unit
WO2009126900A1 (en) 2008-04-11 2009-10-15 Pelikan Technologies, Inc. Method and apparatus for analyte detecting device
US8551320B2 (en) 2008-06-09 2013-10-08 Lifescan, Inc. System and method for measuring an analyte in a sample
CN102089650B (en) 2008-07-10 2014-01-29 拜尔健康护理有限责任公司 Systems and methods including amperometric and voltammetric duty cycles
PT2373805E (en) * 2008-12-08 2015-12-30 Bayer Healthcare Llc Low total salt reagent compositions and systems for biosensors
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
US20100213057A1 (en) 2009-02-26 2010-08-26 Benjamin Feldman Self-Powered Analyte Sensor
US20100219085A1 (en) * 2009-02-27 2010-09-02 Edwards Lifesciences Corporation Analyte Sensor Offset Normalization
RU2489089C2 (en) * 2009-03-16 2013-08-10 АРКРЭЙ, Инк. Method of continuous measurement of substrate concentration
TWI388823B (en) 2009-04-09 2013-03-11 Bionime Corp A method for estimating the distribution of a sample
EP2448469B1 (en) * 2009-06-30 2021-07-21 Lifescan, Inc. Analyte testing methods and device for calculating basal insulin therapy
EP2449493A2 (en) * 2009-06-30 2012-05-09 Lifescan Scotland Limited Systems for diabetes management and methods
BRPI1015922A2 (en) * 2009-06-30 2016-04-26 Lifescan Inc systems and methods for testing analytes
EP2459730B1 (en) 2009-07-27 2016-12-07 Suresensors LTD Improvements relating to sensor devices
KR101102525B1 (en) * 2009-09-03 2012-01-03 한국수력원자력 주식회사 The method for sensing of chemical environment in high temperature water using electrochemical water chemistry technique
WO2011041007A1 (en) * 2009-09-29 2011-04-07 Lifescan Scotland Limited Analyte testing method and device for diabetes management
US8221994B2 (en) 2009-09-30 2012-07-17 Cilag Gmbh International Adhesive composition for use in an immunosensor
US8101065B2 (en) 2009-12-30 2012-01-24 Lifescan, Inc. Systems, devices, and methods for improving accuracy of biosensors using fill time
US8877034B2 (en) 2009-12-30 2014-11-04 Lifescan, Inc. Systems, devices, and methods for measuring whole blood hematocrit based on initial fill velocity
CN102121914B (en) * 2010-01-11 2013-09-11 明志科技大学 Electrochemical power supply method and device
US8773106B2 (en) 2010-02-25 2014-07-08 Lifescan Scotland Limited Capacitance detection in electrochemical assay with improved sampling time offset
US8742773B2 (en) 2010-02-25 2014-06-03 Lifescan Scotland Limited Capacitance detection in electrochemical assay with improved response
US20110208435A1 (en) 2010-02-25 2011-08-25 Lifescan Scotland Ltd. Capacitance detection in electrochemical assays
BR112012021572A2 (en) 2010-02-25 2016-10-25 Lifescan Scotland Ltd analyte testing method and system with notification of high and low blood glucose trends.
RU2012140730A (en) 2010-02-25 2014-03-27 Лайфскэн Скотлэнд Лимитед DETERMINATION OF CAPACITY AT ANALYSIS BY ELECTROCHEMICAL METHOD
AU2010346624A1 (en) 2010-02-25 2012-09-06 Lifescan Scotland Limited Analyte testing method and system with safety warnings for insulin dosing
US8965476B2 (en) 2010-04-16 2015-02-24 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US9164076B2 (en) 2010-06-07 2015-10-20 Bayer Healthcare Llc Slope-based compensation including secondary output signals
ES2529118T3 (en) * 2010-06-30 2015-02-17 Lifescan Scotland Limited Methods to ensure statistical power for messages of mean pre and post-pandial glucose difference
KR101899307B1 (en) 2010-07-19 2018-09-18 시락 게엠베하 인터내셔날 System and method for measuring an analyte in a sample
RU2013109288A (en) 2010-08-02 2014-09-10 Цилаг Гмбх Интернэшнл SYSTEMS AND METHODS OF INCREASING ACCURACY AT TEMPERATURE CORRECTION OF THE RESULTS OF MEASURING THE GLUCOSE LEVEL IN THE CONTROL SOLUTION
US8468680B2 (en) 2010-08-24 2013-06-25 Roche Diagnostics Operations, Inc. Biosensor test member and method for making the same
AU2011301843B2 (en) 2010-09-17 2015-02-05 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
US8617370B2 (en) 2010-09-30 2013-12-31 Cilag Gmbh International Systems and methods of discriminating between a control sample and a test fluid using capacitance
US8932445B2 (en) 2010-09-30 2015-01-13 Cilag Gmbh International Systems and methods for improved stability of electrochemical sensors
US20120122197A1 (en) * 2010-11-12 2012-05-17 Abner David Jospeh Inkjet reagent deposition for biosensor manufacturing
US20130229288A1 (en) 2010-11-15 2013-09-05 Lifescan Scotland Limited Server-side initiated communication with analyte meter-side completed data transfer
AU2012212655B2 (en) 2011-01-06 2015-12-24 Pepex Biomedical, Inc. Sensor module with enhanced capillary flow
EP3575796B1 (en) 2011-04-15 2020-11-11 DexCom, Inc. Advanced analyte sensor calibration and error detection
EP2715330B1 (en) 2011-05-27 2018-05-23 Lifescan Scotland Limited Peak offset correction for analyte test strip
AU2012286927B2 (en) 2011-07-27 2015-09-24 Agamatrix, Inc. Reagents for electrochemical test strips
US9903830B2 (en) 2011-12-29 2018-02-27 Lifescan Scotland Limited Accurate analyte measurements for electrochemical test strip based on sensed physical characteristic(s) of the sample containing the analyte
CN104203097B (en) 2012-03-30 2017-10-24 生命扫描苏格兰有限公司 Battery status detection and storage method and system in medical monitoring
US9201038B2 (en) * 2012-07-24 2015-12-01 Lifescan Scotland Limited System and methods to account for interferents in a glucose biosensor
PL3403995T3 (en) 2012-08-15 2021-07-12 Lockheed Martin Energy, Llc High solubility iron hexacyanides
WO2014037688A1 (en) 2012-09-07 2014-03-13 Cilag Gmbh International Electrochemical sensors and a method for their manufacture
US9494555B2 (en) 2012-09-24 2016-11-15 Cilag Gmbh International System and method for measuring an analyte in a sample and calculating glucose results to account for physical characteristics of the sample
US9080196B2 (en) * 2012-09-28 2015-07-14 Cilag Gmbh International System and method for determining hematocrit insensitive glucose concentration
US9005426B2 (en) * 2012-09-28 2015-04-14 Cilag Gmbh International System and method for determining hematocrit insensitive glucose concentration
US8926369B2 (en) 2012-12-20 2015-01-06 Lifescan Scotland Limited Electrical connector for substrate having conductive tracks
EP2746759B1 (en) * 2012-12-23 2016-09-07 Tyson Bioresearch, Inc. Method of detecting concentration of an analyte in a sample with a test strip
US9261478B2 (en) 2013-02-12 2016-02-16 Cilag Gmbh International System and method for measuring an analyte in a sample and calculating hematocrit-insensitive glucose concentrations
US10168313B2 (en) 2013-03-15 2019-01-01 Agamatrix, Inc. Analyte detection meter and associated method of use
KR102131408B1 (en) 2013-06-13 2020-07-08 에스케이이노베이션 주식회사 Fabrication method for a stacked carbon electrode set including suspended carbon nanomeshes and a planar carbon electrode, and biosensors and electrochemical sensors using the same
US10545132B2 (en) 2013-06-25 2020-01-28 Lifescan Ip Holdings, Llc Physiological monitoring system communicating with at least a social network
US9482635B2 (en) 2013-06-25 2016-11-01 Animas Corporation Glucose-measurement systems and methods presenting icons
US9835578B2 (en) 2013-06-27 2017-12-05 Lifescan Scotland Limited Temperature compensation for an analyte measurement determined from a specified sampling time derived from a sensed physical characteristic of the sample containing the analyte
US9435764B2 (en) 2013-06-27 2016-09-06 Lifescan Scotland Limited Transient 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
US9529503B2 (en) 2013-06-27 2016-12-27 Lifescan Scotland Limited Analyte-measurement system recording user menu choices
US9435762B2 (en) 2013-06-27 2016-09-06 Lifescan Scotland Limited Fill error trap for an analyte measurement determined from a specified sampling time derived from a sensed physical characteristic of the sample containing the analyte
CN104345079A (en) * 2013-08-02 2015-02-11 达尔生技股份有限公司 Determination methods
CN105492902B (en) 2013-08-07 2020-07-24 爱科来株式会社 Substance measuring method and measuring device using electrochemical biosensor
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
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
KR102253905B1 (en) 2013-10-16 2021-05-18 록히드 마틴 에너지, 엘엘씨 Method and apparatus for measuring transient state-of-charge using inlet/outlet potentials
RU2558599C2 (en) * 2013-10-18 2015-08-10 Федеральное государственное бюджетное учреждение науки Институт механики Уральского отделения РАН Method of making photosensitive silver-palladium resistive film
CN105993091B (en) * 2013-11-01 2020-05-29 洛克希德马丁能量有限公司 Apparatus and method for determining state of charge in a redox flow battery via limiting current
US10388978B2 (en) 2013-11-15 2019-08-20 Lockheed Martin Energy, Llc Methods for determining state of charge and calibrating reference electrodes in a redox flow battery
US9291593B2 (en) 2013-11-22 2016-03-22 Cilag Gmbh International Dual-chamber analytical test strip
US20150176049A1 (en) 2013-12-23 2015-06-25 Cilag Gmbh International Determining usability of analytical test strip
US20160091450A1 (en) 2014-09-25 2016-03-31 Lifescan Scotland Limited Accurate analyte measurements for electrochemical test strip to determine analyte measurement time based on measured temperature, physical characteristic and estimated analyte value and their temperature compensated values
US20160091451A1 (en) 2014-09-25 2016-03-31 Lifescan Scotland Limited Accurate analyte measurements for electrochemical test strip to determine analyte measurement time based on measured temperature, physical characteristic and estimated analyte value
GB2531728A (en) 2014-10-27 2016-05-04 Cilag Gmbh Int Method for determining diffusion
EP3230724A4 (en) 2014-12-08 2018-07-11 Lockheed Martin Energy, LLC Electrochemical systems incorporationg in situ spectroscopic determination of state of charge and methods directed to the same
US10197522B2 (en) 2015-03-18 2019-02-05 Materion Corporation Multilayer constructs for metabolite strips providing inert surface and mechanical advantage
US10378098B2 (en) * 2015-03-18 2019-08-13 Materion Corporation Methods for optimized production of multilayer metal/transparent conducting oxide (TCO) constructs
SI3220137T1 (en) 2016-03-14 2019-05-31 F. Hoffmann-La Roche Ag Method for detecting an interferent contribution in a biosensor
JP6778058B2 (en) * 2016-08-31 2020-10-28 シスメックス株式会社 Sensor assembly, test substance monitoring system and test substance monitoring method
US10903511B2 (en) 2016-11-29 2021-01-26 Lockheed Martin Energy, Llc Flow batteries having adjustable circulation rate capabilities and methods associated therewith
US11147920B2 (en) 2017-04-18 2021-10-19 Lifescan Ip Holdings, Llc Diabetes management system with automatic basal and manual bolus insulin control
EP3457121A1 (en) * 2017-09-18 2019-03-20 Roche Diabetes Care GmbH Electrochemical sensor and sensor system for detecting at least one analyte
RU2743884C1 (en) * 2020-08-05 2021-03-01 Общество с ограниченной ответственностью «Техохрана» Method and device for detecting electrochemical deposition
CN111912697B (en) * 2020-08-14 2023-03-07 南京原码科技合伙企业(有限合伙) Rapid concentration device and method for pathogenic microorganisms
WO2023219648A1 (en) 2022-05-09 2023-11-16 Lockheed Martin Energy, Llc Flow battery with a dynamic fluidic network

Citations (189)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4053381A (en) 1976-05-19 1977-10-11 Eastman Kodak Company Device for determining ionic activity of components of liquid drops
US4076596A (en) 1976-10-07 1978-02-28 Leeds & Northrup Company Apparatus for electrolytically determining a species in a fluid and method of use
US4088448A (en) 1975-09-29 1978-05-09 Lilja Jan Evert Apparatus for sampling, mixing the sample with a reagent and making particularly optical analyses
JPS546595Y2 (en) 1972-05-04 1979-03-28
GB2020424A (en) 1978-05-05 1979-11-14 Baker Chem Co J T Determination of glucose
US4224125A (en) 1977-09-28 1980-09-23 Matsushita Electric Industrial Co., Ltd. Enzyme electrode
US4233029A (en) 1978-10-25 1980-11-11 Eastman Kodak Company Liquid transport device and method
US4254083A (en) 1979-07-23 1981-03-03 Eastman Kodak Company Structural configuration for transport of a liquid drop through an ingress aperture
US4254546A (en) 1978-09-11 1981-03-10 Ses, Incorporated Photovoltaic cell array
US4259165A (en) 1978-12-20 1981-03-31 Hokushin Electric Works, Ltd. Dissolved oxygen probe
US4301414A (en) 1979-10-29 1981-11-17 United States Surgical Corporation Disposable sample card and method of making same
US4301412A (en) 1979-10-29 1981-11-17 United States Surgical Corporation Liquid conductivity measuring system and sample cards therefor
US4303887A (en) 1979-10-29 1981-12-01 United States Surgical Corporation Electrical liquid conductivity measuring system
US4307188A (en) 1979-09-06 1981-12-22 Miles Laboratories, Inc. Precursor indicator compositions
US4319969A (en) 1979-08-31 1982-03-16 Asahi Glass Company, Ltd. Aqueous alkali metal chloride electrolytic cell
DE3103464A1 (en) 1981-02-02 1982-08-05 Gkss - Forschungszentrum Geesthacht Gmbh, 2054 Geesthacht Sealing frame for electrodialysis membrane stack
US4374013A (en) 1980-03-05 1983-02-15 Enfors Sven Olof Oxygen stabilized enzyme electrode
US4404066A (en) 1980-08-25 1983-09-13 The Yellow Springs Instrument Company Method for quantitatively determining a particular substrate catalyzed by a multisubstrate enzyme
US4404065A (en) 1980-01-14 1983-09-13 Enviromental Sciences Associates, Inc. Electrochemical detection system and method of analysis
JPS593345A (en) 1982-06-30 1984-01-10 Hitachi Ltd Dissolved oxygen meter equipped with electrode for removing interfering component
US4431507A (en) 1981-01-14 1984-02-14 Matsushita Electric Industrial Co., Ltd. Enzyme electrode
US4431004A (en) 1981-10-27 1984-02-14 Bessman Samuel P Implantable glucose sensor
EP0125137A2 (en) 1983-05-05 1984-11-14 MediSense, Inc. Measurement of enzyme-catalysed reactions
US4508613A (en) 1983-12-19 1985-04-02 Gould Inc. Miniaturized potassium ion sensor
US4511659A (en) 1983-03-04 1985-04-16 Esa, Inc. Liquid chromatograph with electrochemical detector and method
US4517287A (en) 1979-04-04 1985-05-14 Boehringer Mannheim Gmbh Method and reagent for the enzymatic determination of enzyme substrates
US4517291A (en) 1983-08-15 1985-05-14 E. I. Du Pont De Nemours And Company Biological detection process using polymer-coated electrodes
JPS6017344Y2 (en) 1980-11-14 1985-05-28 凸版印刷株式会社 decorative magnets
US4533440A (en) 1983-08-04 1985-08-06 General Electric Company Method for continuous measurement of the sulfite/sulfate ratio
GB2154735A (en) 1984-01-27 1985-09-11 Menarini Sas Reagent for determining blood glucose content
US4545382A (en) 1981-10-23 1985-10-08 Genetics International, Inc. Sensor for components of a liquid mixture
US4552840A (en) 1982-12-02 1985-11-12 California And Hawaiian Sugar Company Enzyme electrode and method for dextran analysis
US4554064A (en) 1984-03-28 1985-11-19 Imasco-Cdc Research Foundation Dual working-electrode electrochemical detector for high performance liquid chromatography
JPS60244853A (en) 1984-05-21 1985-12-04 Matsushita Electric Works Ltd Biosensor
JPS60250246A (en) 1984-05-25 1985-12-10 Matsushita Electric Works Ltd Measurement using biosensor
JPS612060Y2 (en) 1981-02-09 1986-01-23
EP0170375A2 (en) 1984-06-13 1986-02-05 Unilever Plc Devices for use in chemical test procedures
EP0171375A1 (en) 1984-07-09 1986-02-12 Institut Cerac S.A. High pressure water valve
US4591550A (en) 1984-03-01 1986-05-27 Molecular Devices Corporation Device having photoresponsive electrode for determining analytes including ligands and antibodies
US4629563A (en) 1980-03-14 1986-12-16 Brunswick Corporation Asymmetric membranes
US4654197A (en) 1983-10-18 1987-03-31 Aktiebolaget Leo Cuvette for sampling and analysis
US4664119A (en) 1985-12-04 1987-05-12 University Of Southern California Transcutaneous galvanic electrode oxygen sensor
JPS62228274A (en) 1986-03-28 1987-10-07 Mitsubishi Chem Ind Ltd Thin membrane of immobilized enzyme
SU1351627A2 (en) 1986-03-27 1987-11-15 Томский инженерно-строительный институт Filtering element
EP0251915A2 (en) 1986-06-27 1988-01-07 Terumo Kabushiki Kaisha Enzyme sensor
EP0255291A1 (en) 1986-07-23 1988-02-03 Unilever Plc Method and apparatus for electrochemical measurements
EP0266204A2 (en) 1986-10-31 1988-05-04 Kingston Technologies, Inc. Pressure dependent anisotropic transport membrane system
EP0278647A2 (en) 1987-02-09 1988-08-17 AT&T Corp. Electronchemical processes involving enzymes
GB2201248A (en) 1987-02-24 1988-08-24 Ici Plc Enzyme electrode sensors
JPS63139246U (en) 1987-03-03 1988-09-13
US4774039A (en) 1980-03-14 1988-09-27 Brunswick Corporation Dispersing casting of integral skinned highly asymmetric polymer membranes
US4782265A (en) 1981-03-20 1988-11-01 U.S. Philips Corporation Electrochemical luminescent cell
EP0290770A2 (en) 1987-05-14 1988-11-17 Ace Medical Company Pressure sensor
US4790925A (en) 1987-09-18 1988-12-13 Mine Safety Appliances Company Electrochemical gas sensor
JPS63317097A (en) 1987-06-19 1988-12-26 Matsushita Electric Ind Co Ltd Biosensor
EP0299779A2 (en) 1987-07-15 1989-01-18 Sri International Fast response time microsensors for gaseous and vaporous species
WO1989008713A1 (en) 1988-03-15 1989-09-21 Life-Chek Laboratories Method and apparatus for amperometric diagnostic analysis
GB2215846A (en) 1988-03-23 1989-09-27 Nat Res Dev Method and apparatus for measuring the type and concentration of ion species in liquids
JPH01253648A (en) 1988-03-31 1989-10-09 Matsushita Electric Ind Co Ltd Biosensor
JPH01294453A (en) 1988-05-12 1989-11-28 Youken:Kk Container id
EP0351891A2 (en) 1983-05-05 1990-01-24 MediSense, Inc. Printed electrodes
EP0351516A2 (en) 1988-07-18 1990-01-24 Martin J. Patko Precalibrated, disposable, electrochemical sensors
US4897173A (en) 1985-06-21 1990-01-30 Matsushita Electric Industrial Co., Ltd. Biosensor and method for making the same
US4900424A (en) 1986-11-28 1990-02-13 Unilever Patent Holdings B.V. Electrochemical measurement cell
US4911794A (en) 1986-06-20 1990-03-27 Molecular Devices Corporation Measuring with zero volume cell
EP0359831A1 (en) 1988-03-31 1990-03-28 Matsushita Electric Industrial Co., Ltd. Biosensor and process for its production
US4919770A (en) 1982-07-30 1990-04-24 Siemens Aktiengesellschaft Method for determining the concentration of electro-chemically convertible substances
EP0367432A1 (en) 1988-10-31 1990-05-09 Gec-Marconi Limited Biosensor device
GB2194112B (en) 1986-07-18 1990-05-30 Malvern Instr Ltd Improvements relating to laser doppler velocimetry
US4963815A (en) 1987-07-10 1990-10-16 Molecular Devices Corporation Photoresponsive electrode for determination of redox potential
EP0400918A1 (en) 1989-05-31 1990-12-05 Nakano Vinegar Co., Ltd. Enzyme sensor
US4988429A (en) 1989-06-30 1991-01-29 Dragerwerk Aktiengesellschaft Measuring cell for an electrochemical gas sensor
US4989452A (en) 1987-11-09 1991-02-05 Solinst Canada Ltd. Liquid-level detector
GB2235050A (en) 1989-08-14 1991-02-20 Sieger Ltd Electrochemical gas sensor
EP0418404A1 (en) 1989-09-15 1991-03-27 Hewlett-Packard GmbH Method of determining optimum operating conditions in an electrochemical detector and electrochemical detector using the method
WO1991009139A1 (en) 1989-12-15 1991-06-27 Boehringer Mannheim Corporation Redox mediator reagent and biosensor
JPH03167464A (en) 1989-11-27 1991-07-19 Yamatake Honeywell Co Ltd Humidity-sensitive element and its manufacture
EP0451981A2 (en) 1990-03-26 1991-10-16 Cascade Medical, Inc. Disposable reagent unit
US5059908A (en) 1990-05-31 1991-10-22 Capital Controls Company, Inc. Amperimetric measurement with cell electrode deplating
US5064516A (en) 1987-07-16 1991-11-12 Gas Research Institute Measuring gas levels
US5089112A (en) 1989-03-20 1992-02-18 Associated Universities, Inc. Electrochemical biosensor based on immobilized enzymes and redox polymers
US5089320A (en) 1989-01-09 1992-02-18 James River Ii, Inc. Resealable packaging material
US5095407A (en) 1987-02-27 1992-03-10 Hitachi, Ltd. Double-sided memory board
US5108564A (en) 1988-03-15 1992-04-28 Tall Oak Ventures Method and apparatus for amperometric diagnostic analysis
US5122244A (en) 1990-02-03 1992-06-16 Boehringer Mannheim Gmbh Method and sensor electrode system for the electrochemical determination of an analyte or an oxidoreductase as well as the use of suitable compounds therefor
US5126034A (en) 1988-07-21 1992-06-30 Medisense, Inc. Bioelectrochemical electrodes
US5141868A (en) 1984-06-13 1992-08-25 Internationale Octrooi Maatschappij "Octropa" Bv Device for use in chemical test procedures
WO1992015701A1 (en) 1991-02-27 1992-09-17 Boehringer Mannheim Corporation Improved method and reagent for determination of an analyte
US5151166A (en) 1989-10-02 1992-09-29 Normalair-Garrett (Holdings) Limited Oxygen monitoring method and apparatus
US5156972A (en) 1989-09-05 1992-10-20 The State Of Israel, Atomic Energy Commission, Soreq Nuclear Research Center Analyte specific chemical sensor with a ligand and an analogue bound on the sensing surface
JPH0466112B2 (en) 1985-02-27 1992-10-22 Stanley Electric Co Ltd
JPH04343065A (en) 1991-05-17 1992-11-30 Ngk Spark Plug Co Ltd Biosensor
US5171689A (en) 1984-11-08 1992-12-15 Matsushita Electric Industrial Co., Ltd. Solid state bio-sensor
JPH052007Y2 (en) 1985-04-22 1993-01-19
US5192415A (en) 1991-03-04 1993-03-09 Matsushita Electric Industrial Co., Ltd. Biosensor utilizing enzyme and a method for producing the same
US5194133A (en) 1990-05-04 1993-03-16 The General Electric Company, P.L.C. Sensor devices
AU3104293A (en) 1992-01-14 1993-07-15 Commonwealth Scientific And Industrial Research Organisation Viscometer
US5229282A (en) 1989-11-24 1993-07-20 Matsushita Electric Industrial Co., Ltd. Preparation of biosensor having a layer containing an enzyme, electron acceptor and hydrophilic polymer on an electrode system
US5243516A (en) 1989-12-15 1993-09-07 Boehringer Mannheim Corporation Biosensing instrument and method
US5243526A (en) 1990-05-18 1993-09-07 Mitsubishi Jidosha Kogyo Kabushiki Kaisha Output control apparatus for vehicle
EP0560336A1 (en) 1992-03-12 1993-09-15 Matsushita Electric Industrial Co., Ltd. A catalyst made from phosphate and a biosensor including the same
JPH0580018B2 (en) 1988-12-29 1993-11-05 Ibm
JPH05312761A (en) 1992-05-12 1993-11-22 Toto Ltd Biosensor and its manufacture
US5269903A (en) 1987-03-13 1993-12-14 Yoshito Ikariyama Microbioelectrode and method of fabricating the same
US5272087A (en) 1988-04-20 1993-12-21 Centre National De La Recherche Scientifique (C.N.R.S.) Enzymatic electrode and its preparation method
US5282950A (en) 1991-07-15 1994-02-01 Boehringer Mannheim Gmbh Electrochemical analysis system
WO1994002842A1 (en) 1992-07-28 1994-02-03 The Victoria University Of Manchester Analytical method for the detection and measurement of paracetamol
US5312590A (en) 1989-04-24 1994-05-17 National University Of Singapore Amperometric sensor for single and multicomponent analysis
US5314605A (en) 1989-06-30 1994-05-24 Dragerwerk Aktiengesellschaft Measuring cell for electrochemically detecting a gas
US5320732A (en) 1990-07-20 1994-06-14 Matsushita Electric Industrial Co., Ltd. Biosensor and measuring apparatus using the same
EP0609760A1 (en) 1993-02-04 1994-08-10 Asulab S.A. Electrochemical measurement system with snap-off sensor zones for the determination of glucose
US5354447A (en) 1991-12-12 1994-10-11 Kyoto Daiichi Kagaku Co., Ltd. Biosensor and method of quantitative analysis using the same
JPH06310746A (en) 1993-04-27 1994-11-04 Hitachi Ltd Electrochemical element
US5366609A (en) 1993-06-08 1994-11-22 Boehringer Mannheim Corporation Biosensing meter with pluggable memory key
WO1994029731A1 (en) 1993-06-03 1994-12-22 Boehringer Mannheim Corporation Biosensor for hematocrit determination
US5382346A (en) 1991-05-17 1995-01-17 Kyoto Daiichi Kagaku Co., Ltd. Biosensor and method of quantitative analysis using the same
US5384028A (en) 1992-08-28 1995-01-24 Nec Corporation Biosensor with a data memory
US5388163A (en) 1991-12-23 1995-02-07 At&T Corp. Electret transducer array and fabrication technique
US5393399A (en) 1992-09-07 1995-02-28 Gie Cylergie Amperometric measuring device having an electrochemical sensor
US5399256A (en) 1994-01-07 1995-03-21 Bioanalytical Systems, Inc. Electrochemical detector cell
US5405511A (en) 1993-06-08 1995-04-11 Boehringer Mannheim Corporation Biosensing meter with ambient temperature estimation method and system
US5413690A (en) 1993-07-23 1995-05-09 Boehringer Mannheim Corporation Potentiometric biosensor and the method of its use
WO1995016198A1 (en) 1993-12-08 1995-06-15 Unilever Plc Methods and apparatus for electrochemical measurements
US5437999A (en) 1994-02-22 1995-08-01 Boehringer Mannheim Corporation Electrochemical sensor
WO1995021934A1 (en) 1994-02-10 1995-08-17 Cranfield University Hexacyanoferrate modified electrodes
US5443710A (en) 1984-05-09 1995-08-22 Research Foundation, The City University Of New York Microelectrodes and their use in a cathodic electrochemical current arrangement with telemetric application
RU2046361C1 (en) 1992-01-27 1995-10-20 Веревкин Валерий Иванович Device for measuring specific electric conduction of liquids
WO1995028634A1 (en) 1994-04-14 1995-10-26 Memtec America Corporation Electrochemical cells
JPH0862179A (en) 1995-02-13 1996-03-08 Hitachi Ltd Electrolyte analyzer
US5508171A (en) 1989-12-15 1996-04-16 Boehringer Mannheim Corporation Assay method with enzyme electrode system
US5509410A (en) 1983-06-06 1996-04-23 Medisense, Inc. Strip electrode including screen printing of a single layer
US5512159A (en) 1992-01-21 1996-04-30 Matsushita Electric Industrial Co. Ltd. Biosensor
US5517313A (en) 1995-02-21 1996-05-14 Colvin, Jr.; Arthur E. Fluorescent optical sensor
US5518590A (en) 1994-06-21 1996-05-21 Pennzoil Products Company Electrochemical sensors for motor oils and other lubricants
US5520787A (en) 1994-02-09 1996-05-28 Abbott Laboratories Diagnostic flow cell device
US5527446A (en) 1995-04-13 1996-06-18 United States Of America As Represented By The Secretary Of The Air Force Gas sensor
EP0735303A1 (en) 1995-03-31 1996-10-02 Tracto-Technik Paul Schmidt Spezialmaschinen Process for laying underground pipes between control chambers
US5567302A (en) 1995-06-07 1996-10-22 Molecular Devices Corporation Electrochemical system for rapid detection of biochemical agents that catalyze a redox potential change
US5575895A (en) 1994-06-02 1996-11-19 Matsushita Electric Industrial Co., Ltd. Biosensor and method for producing the same
JPH08304340A (en) 1995-05-05 1996-11-22 Bayer Corp Method and device for measuring concentration of analysis object by utilizing amperometric sensor
WO1997000441A1 (en) 1995-06-19 1997-01-03 Memtec America Corporation Electrochemical cell
US5607565A (en) 1995-03-27 1997-03-04 Coulter Corporation Apparatus for measuring analytes in a fluid sample
US5611908A (en) 1994-12-22 1997-03-18 Dr agerwerk Aktiengesellschaft Method of operating and amperometric measuring cell
US5628890A (en) 1995-09-27 1997-05-13 Medisense, Inc. Electrochemical sensor
WO1997018464A1 (en) 1995-11-16 1997-05-22 Memtec America Corporation Electrochemical cell
US5651869A (en) 1995-02-28 1997-07-29 Matsushita Electric Industrial Co., Ltd. Biosensor
JPH09222408A (en) 1996-02-19 1997-08-26 Matsushita Electric Ind Co Ltd Ph sensor and ion water creating device
DE29709141U1 (en) 1997-05-24 1997-08-28 Kurt Schwabe Inst Fuer Mes Und Membrane covered electrochemical gas sensor
JPH09236570A (en) 1996-03-04 1997-09-09 Matsushita Electric Ind Co Ltd Ph sensor and ion water maker
JPH09243588A (en) 1996-03-08 1997-09-19 Matsushita Electric Ind Co Ltd Ph sensor and ionic water forming device
US5682884A (en) 1983-05-05 1997-11-04 Medisense, Inc. Strip electrode with screen printing
US5695947A (en) 1995-06-06 1997-12-09 Biomedix, Inc. Amperometric cholesterol biosensor
US5707502A (en) 1996-07-12 1998-01-13 Chiron Diagnostics Corporation Sensors for measuring analyte concentrations and methods of making same
US5726565A (en) 1992-10-28 1998-03-10 Nakano Vinegar Co., Ltd. Coulometric analysis method and a device therefor
WO1998011426A1 (en) 1996-09-13 1998-03-19 Usf Filtration And Separations Group Inc. Analytic cell
US5762770A (en) 1994-02-21 1998-06-09 Boehringer Mannheim Corporation Electrochemical biosensor test strip
WO1998043074A1 (en) 1997-03-25 1998-10-01 Usf Filtration And Separations Group Inc. Improved electrochemical cell
WO1998043073A1 (en) 1997-03-21 1998-10-01 Usf Filtration And Separations Group Inc. Sensor connection means
US5849174A (en) 1994-08-01 1998-12-15 Medisense, Inc. Electrodes and their use in analysis
US5858188A (en) 1990-02-28 1999-01-12 Aclara Biosciences, Inc. Acrylic microchannels and their use in electrophoretic applications
WO1999046585A1 (en) 1998-03-12 1999-09-16 Usf Filtration And Separations Group Inc. Heated electrochemical cell
US5997817A (en) 1997-12-05 1999-12-07 Roche Diagnostics Corporation Electrochemical biosensor test strip
EP0603954B1 (en) 1992-12-22 2000-03-08 Johnson & Johnson Clinical Diagnostics, Inc. Immunoassay using a 4-hydroxy or 4-alkoxyarylacetamide as stabilizer
WO2000020626A1 (en) 1998-10-08 2000-04-13 Therasense, Inc. Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator
US6071391A (en) 1997-09-12 2000-06-06 Nok Corporation Enzyme electrode structure
US6117289A (en) 1996-12-20 2000-09-12 Matsushita Electric Industrial Co., Ltd. Cholesterol sensor and method for producing the same
US6153069A (en) 1995-02-09 2000-11-28 Tall Oak Ventures Apparatus for amperometric Diagnostic analysis
US6174420B1 (en) 1996-11-15 2001-01-16 Usf Filtration And Separations Group, Inc. Electrochemical cell
US6193873B1 (en) 1999-06-15 2001-02-27 Lifescan, Inc. Sample detection to initiate timing of an electrochemical assay
US6214205B1 (en) 1996-01-26 2001-04-10 Yissum Research Development Company Of The Hebrew University Of Jerusalem Determination of an analyte in a liquid medium
US6218134B1 (en) 1991-07-29 2001-04-17 Mochida Pharmaceutical Co., Ltd. Process for specific binding assay for measuring the amount of analyte in a liquid test sample
JP3167464B2 (en) 1992-11-26 2001-05-21 富士電機株式会社 Inverter fault diagnosis device
US6251260B1 (en) 1998-08-24 2001-06-26 Therasense, Inc. Potentiometric sensors for analytic determination
JP2001281219A (en) 2000-03-29 2001-10-10 Kyocera Corp Air-fuel ratio sensor element
US6325973B1 (en) 1991-02-06 2001-12-04 Igen International, Inc. Methods and apparatus for improved luminescence assays
US20020012943A1 (en) 1997-02-06 2002-01-31 Dana M. Fowlkes Electrochemical probes for detection of molecular interactions and drug discovery
WO2002008763A3 (en) 2000-07-14 2002-06-13 Usf Filtration & Separations Immunosensor
US6413410B1 (en) 1996-06-19 2002-07-02 Lifescan, Inc. Electrochemical cell
US6413395B1 (en) 1999-12-16 2002-07-02 Roche Diagnostics Corporation Biosensor apparatus
US6521110B1 (en) 1995-11-16 2003-02-18 Lifescan, Inc. Electrochemical cell
US6521260B1 (en) 1995-01-31 2003-02-18 Vectura Limited Carrier particles for use in dry powder inhalers
US6544212B2 (en) 2001-07-31 2003-04-08 Roche Diagnostics Corporation Diabetes management system
WO1990005910A3 (en) 1988-11-14 2004-04-22 I Stat Corp Wholly microfabricated biosensors and process for the manufacture and use thereof
US6780756B1 (en) 2003-02-28 2004-08-24 Texas Instruments Incorporated Etch back of interconnect dielectrics
US6863801B2 (en) 1995-11-16 2005-03-08 Lifescan, Inc. Electrochemical cell
EP0585933B1 (en) 1992-09-04 2005-12-21 Matsushita Electric Industrial Co., Ltd. Planar electrode
EP0764469B1 (en) 1995-09-25 2007-03-07 Bayer Corporation Method and apparatus for marking predetermined events with a biosensor
JP4066112B2 (en) 1999-01-28 2008-03-26 株式会社スーパーシリコン研究所 Wire saw control method and wire saw
EP0964059B1 (en) 1998-06-11 2008-08-13 Matsushita Electric Industrial Co., Ltd. Biosensor comprising a working and a counter electrode, the counter electrode having a base plate with a curved portion

Family Cites Families (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US453340A (en) * 1891-06-02 Wagon-bed elevator
JPS612060A (en) * 1984-06-15 1986-01-08 Matsushita Electric Works Ltd Biosensor
JPH0466112A (en) 1990-07-03 1992-03-02 Ube Ind Ltd Determination of transportation condition in membrane transport

Patent Citations (230)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS546595Y2 (en) 1972-05-04 1979-03-28
US4088448A (en) 1975-09-29 1978-05-09 Lilja Jan Evert Apparatus for sampling, mixing the sample with a reagent and making particularly optical analyses
US4053381A (en) 1976-05-19 1977-10-11 Eastman Kodak Company Device for determining ionic activity of components of liquid drops
US4076596A (en) 1976-10-07 1978-02-28 Leeds & Northrup Company Apparatus for electrolytically determining a species in a fluid and method of use
US4224125A (en) 1977-09-28 1980-09-23 Matsushita Electric Industrial Co., Ltd. Enzyme electrode
GB2020424A (en) 1978-05-05 1979-11-14 Baker Chem Co J T Determination of glucose
US4254546A (en) 1978-09-11 1981-03-10 Ses, Incorporated Photovoltaic cell array
US4233029A (en) 1978-10-25 1980-11-11 Eastman Kodak Company Liquid transport device and method
US4259165A (en) 1978-12-20 1981-03-31 Hokushin Electric Works, Ltd. Dissolved oxygen probe
US4517287A (en) 1979-04-04 1985-05-14 Boehringer Mannheim Gmbh Method and reagent for the enzymatic determination of enzyme substrates
US4254083A (en) 1979-07-23 1981-03-03 Eastman Kodak Company Structural configuration for transport of a liquid drop through an ingress aperture
US4319969A (en) 1979-08-31 1982-03-16 Asahi Glass Company, Ltd. Aqueous alkali metal chloride electrolytic cell
US4307188A (en) 1979-09-06 1981-12-22 Miles Laboratories, Inc. Precursor indicator compositions
US4301414A (en) 1979-10-29 1981-11-17 United States Surgical Corporation Disposable sample card and method of making same
US4301412A (en) 1979-10-29 1981-11-17 United States Surgical Corporation Liquid conductivity measuring system and sample cards therefor
US4303887A (en) 1979-10-29 1981-12-01 United States Surgical Corporation Electrical liquid conductivity measuring system
US4404065A (en) 1980-01-14 1983-09-13 Enviromental Sciences Associates, Inc. Electrochemical detection system and method of analysis
US4374013A (en) 1980-03-05 1983-02-15 Enfors Sven Olof Oxygen stabilized enzyme electrode
US4629563A (en) 1980-03-14 1986-12-16 Brunswick Corporation Asymmetric membranes
US4774039A (en) 1980-03-14 1988-09-27 Brunswick Corporation Dispersing casting of integral skinned highly asymmetric polymer membranes
US4629563B1 (en) 1980-03-14 1997-06-03 Memtec North America Asymmetric membranes
US4404066A (en) 1980-08-25 1983-09-13 The Yellow Springs Instrument Company Method for quantitatively determining a particular substrate catalyzed by a multisubstrate enzyme
JPS6017344Y2 (en) 1980-11-14 1985-05-28 凸版印刷株式会社 decorative magnets
US4431507A (en) 1981-01-14 1984-02-14 Matsushita Electric Industrial Co., Ltd. Enzyme electrode
DE3103464C2 (en) 1981-02-02 1984-10-11 Gkss - Forschungszentrum Geesthacht Gmbh, 2054 Geesthacht Sealing frame for electrodialysis membrane stacks
DE3103464A1 (en) 1981-02-02 1982-08-05 Gkss - Forschungszentrum Geesthacht Gmbh, 2054 Geesthacht Sealing frame for electrodialysis membrane stack
JPS612060Y2 (en) 1981-02-09 1986-01-23
US4782265A (en) 1981-03-20 1988-11-01 U.S. Philips Corporation Electrochemical luminescent cell
US4545382A (en) 1981-10-23 1985-10-08 Genetics International, Inc. Sensor for components of a liquid mixture
US4431004A (en) 1981-10-27 1984-02-14 Bessman Samuel P Implantable glucose sensor
JPS593345A (en) 1982-06-30 1984-01-10 Hitachi Ltd Dissolved oxygen meter equipped with electrode for removing interfering component
US4919770A (en) 1982-07-30 1990-04-24 Siemens Aktiengesellschaft Method for determining the concentration of electro-chemically convertible substances
US4552840A (en) 1982-12-02 1985-11-12 California And Hawaiian Sugar Company Enzyme electrode and method for dextran analysis
US4511659A (en) 1983-03-04 1985-04-16 Esa, Inc. Liquid chromatograph with electrochemical detector and method
US5682884A (en) 1983-05-05 1997-11-04 Medisense, Inc. Strip electrode with screen printing
EP0125137A2 (en) 1983-05-05 1984-11-14 MediSense, Inc. Measurement of enzyme-catalysed reactions
EP0351891A2 (en) 1983-05-05 1990-01-24 MediSense, Inc. Printed electrodes
EP0351892A2 (en) 1983-05-05 1990-01-24 MediSense, Inc. Diagnostic aid and assemblies therefor
US5727548A (en) 1983-05-05 1998-03-17 Medisense, Inc. Strip electrode with screen printing
EP0125137B1 (en) 1983-05-05 1990-08-22 MediSense, Inc. Measurement of enzyme-catalysed reactions
US4711245A (en) 1983-05-05 1987-12-08 Genetics International, Inc. Sensor for components of a liquid mixture
US5509410A (en) 1983-06-06 1996-04-23 Medisense, Inc. Strip electrode including screen printing of a single layer
US4533440A (en) 1983-08-04 1985-08-06 General Electric Company Method for continuous measurement of the sulfite/sulfate ratio
US4517291A (en) 1983-08-15 1985-05-14 E. I. Du Pont De Nemours And Company Biological detection process using polymer-coated electrodes
US4654197A (en) 1983-10-18 1987-03-31 Aktiebolaget Leo Cuvette for sampling and analysis
US4508613A (en) 1983-12-19 1985-04-02 Gould Inc. Miniaturized potassium ion sensor
GB2154735A (en) 1984-01-27 1985-09-11 Menarini Sas Reagent for determining blood glucose content
US4591550A (en) 1984-03-01 1986-05-27 Molecular Devices Corporation Device having photoresponsive electrode for determining analytes including ligands and antibodies
US4554064A (en) 1984-03-28 1985-11-19 Imasco-Cdc Research Foundation Dual working-electrode electrochemical detector for high performance liquid chromatography
US5443710A (en) 1984-05-09 1995-08-22 Research Foundation, The City University Of New York Microelectrodes and their use in a cathodic electrochemical current arrangement with telemetric application
JPS60244853A (en) 1984-05-21 1985-12-04 Matsushita Electric Works Ltd Biosensor
JPS60250246A (en) 1984-05-25 1985-12-10 Matsushita Electric Works Ltd Measurement using biosensor
EP0170375B1 (en) 1984-06-13 1990-05-16 Unilever Plc Devices for use in chemical test procedures
EP0170375A2 (en) 1984-06-13 1986-02-05 Unilever Plc Devices for use in chemical test procedures
EP0422708B1 (en) 1984-06-13 1996-09-25 Applied Research Systems Ars Holding N.V. Devices for use in chemical test procedures
US5141868A (en) 1984-06-13 1992-08-25 Internationale Octrooi Maatschappij "Octropa" Bv Device for use in chemical test procedures
EP0171375A1 (en) 1984-07-09 1986-02-12 Institut Cerac S.A. High pressure water valve
US5171689A (en) 1984-11-08 1992-12-15 Matsushita Electric Industrial Co., Ltd. Solid state bio-sensor
JPH0466112B2 (en) 1985-02-27 1992-10-22 Stanley Electric Co Ltd
JPH052007Y2 (en) 1985-04-22 1993-01-19
US4897173A (en) 1985-06-21 1990-01-30 Matsushita Electric Industrial Co., Ltd. Biosensor and method for making the same
US4664119A (en) 1985-12-04 1987-05-12 University Of Southern California Transcutaneous galvanic electrode oxygen sensor
SU1351627A2 (en) 1986-03-27 1987-11-15 Томский инженерно-строительный институт Filtering element
JPS62228274A (en) 1986-03-28 1987-10-07 Mitsubishi Chem Ind Ltd Thin membrane of immobilized enzyme
US4911794A (en) 1986-06-20 1990-03-27 Molecular Devices Corporation Measuring with zero volume cell
EP0251915A2 (en) 1986-06-27 1988-01-07 Terumo Kabushiki Kaisha Enzyme sensor
GB2194112B (en) 1986-07-18 1990-05-30 Malvern Instr Ltd Improvements relating to laser doppler velocimetry
EP0255291A1 (en) 1986-07-23 1988-02-03 Unilever Plc Method and apparatus for electrochemical measurements
EP0266204A2 (en) 1986-10-31 1988-05-04 Kingston Technologies, Inc. Pressure dependent anisotropic transport membrane system
US4900424A (en) 1986-11-28 1990-02-13 Unilever Patent Holdings B.V. Electrochemical measurement cell
EP0278647A2 (en) 1987-02-09 1988-08-17 AT&T Corp. Electronchemical processes involving enzymes
GB2201248B (en) 1987-02-24 1991-04-17 Ici Plc Enzyme electrode sensors
GB2201248A (en) 1987-02-24 1988-08-24 Ici Plc Enzyme electrode sensors
US5095407A (en) 1987-02-27 1992-03-10 Hitachi, Ltd. Double-sided memory board
JPS63139246U (en) 1987-03-03 1988-09-13
US5269903A (en) 1987-03-13 1993-12-14 Yoshito Ikariyama Microbioelectrode and method of fabricating the same
EP0290770B1 (en) 1987-05-14 1993-09-22 Ace Medical Company Pressure sensor
EP0290770A2 (en) 1987-05-14 1988-11-17 Ace Medical Company Pressure sensor
JPS63317097A (en) 1987-06-19 1988-12-26 Matsushita Electric Ind Co Ltd Biosensor
US4963815A (en) 1987-07-10 1990-10-16 Molecular Devices Corporation Photoresponsive electrode for determination of redox potential
EP0299779A2 (en) 1987-07-15 1989-01-18 Sri International Fast response time microsensors for gaseous and vaporous species
US5064516A (en) 1987-07-16 1991-11-12 Gas Research Institute Measuring gas levels
US4790925A (en) 1987-09-18 1988-12-13 Mine Safety Appliances Company Electrochemical gas sensor
US4989452A (en) 1987-11-09 1991-02-05 Solinst Canada Ltd. Liquid-level detector
EP0406304A1 (en) 1988-03-15 1991-01-09 Life Chek Lab Method and apparatus for amperometric diagnostic analysis.
WO1989008713A1 (en) 1988-03-15 1989-09-21 Life-Chek Laboratories Method and apparatus for amperometric diagnostic analysis
EP0406304B1 (en) 1988-03-15 1997-08-20 Tall Oak Ventures Method and apparatus for amperometric diagnostic analysis
US5108564A (en) 1988-03-15 1992-04-28 Tall Oak Ventures Method and apparatus for amperometric diagnostic analysis
US5128015A (en) 1988-03-15 1992-07-07 Tall Oak Ventures Method and apparatus for amperometric diagnostic analysis
GB2215846A (en) 1988-03-23 1989-09-27 Nat Res Dev Method and apparatus for measuring the type and concentration of ion species in liquids
GB2215846B (en) 1988-03-23 1992-04-22 Nat Res Dev Method and apparatus for measuring the type and concentration of ion species in liquids
EP0359831A1 (en) 1988-03-31 1990-03-28 Matsushita Electric Industrial Co., Ltd. Biosensor and process for its production
US5120420B1 (en) 1988-03-31 1999-11-09 Matsushita Electric Ind Co Ltd Biosensor and a process for preparation thereof
US5120420A (en) 1988-03-31 1992-06-09 Matsushita Electric Industrial Co., Ltd. Biosensor and a process for preparation thereof
JPH01253648A (en) 1988-03-31 1989-10-09 Matsushita Electric Ind Co Ltd Biosensor
EP0359831B2 (en) 1988-03-31 2007-06-20 Matsushita Electric Industrial Co., Ltd. Biosensor and process for its production
US5272087A (en) 1988-04-20 1993-12-21 Centre National De La Recherche Scientifique (C.N.R.S.) Enzymatic electrode and its preparation method
JPH01294453A (en) 1988-05-12 1989-11-28 Youken:Kk Container id
EP0351516A2 (en) 1988-07-18 1990-01-24 Martin J. Patko Precalibrated, disposable, electrochemical sensors
US5126034A (en) 1988-07-21 1992-06-30 Medisense, Inc. Bioelectrochemical electrodes
EP0593096A2 (en) 1988-07-21 1994-04-20 MediSense, Inc. Bioelectrochemical electrodes
EP0593096A3 (en) 1988-07-21 1997-12-03 MediSense, Inc. Bioelectrochemical electrodes
EP0367432A1 (en) 1988-10-31 1990-05-09 Gec-Marconi Limited Biosensor device
WO1990005910A3 (en) 1988-11-14 2004-04-22 I Stat Corp Wholly microfabricated biosensors and process for the manufacture and use thereof
JPH0580018B2 (en) 1988-12-29 1993-11-05 Ibm
US5089320A (en) 1989-01-09 1992-02-18 James River Ii, Inc. Resealable packaging material
US5089112A (en) 1989-03-20 1992-02-18 Associated Universities, Inc. Electrochemical biosensor based on immobilized enzymes and redox polymers
US5312590A (en) 1989-04-24 1994-05-17 National University Of Singapore Amperometric sensor for single and multicomponent analysis
EP0400918A1 (en) 1989-05-31 1990-12-05 Nakano Vinegar Co., Ltd. Enzyme sensor
US5314605A (en) 1989-06-30 1994-05-24 Dragerwerk Aktiengesellschaft Measuring cell for electrochemically detecting a gas
US4988429A (en) 1989-06-30 1991-01-29 Dragerwerk Aktiengesellschaft Measuring cell for an electrochemical gas sensor
GB2235050A (en) 1989-08-14 1991-02-20 Sieger Ltd Electrochemical gas sensor
US5156972A (en) 1989-09-05 1992-10-20 The State Of Israel, Atomic Energy Commission, Soreq Nuclear Research Center Analyte specific chemical sensor with a ligand and an analogue bound on the sensing surface
EP0418404A1 (en) 1989-09-15 1991-03-27 Hewlett-Packard GmbH Method of determining optimum operating conditions in an electrochemical detector and electrochemical detector using the method
US5151166A (en) 1989-10-02 1992-09-29 Normalair-Garrett (Holdings) Limited Oxygen monitoring method and apparatus
US5229282A (en) 1989-11-24 1993-07-20 Matsushita Electric Industrial Co., Ltd. Preparation of biosensor having a layer containing an enzyme, electron acceptor and hydrophilic polymer on an electrode system
JPH03167464A (en) 1989-11-27 1991-07-19 Yamatake Honeywell Co Ltd Humidity-sensitive element and its manufacture
US5508171A (en) 1989-12-15 1996-04-16 Boehringer Mannheim Corporation Assay method with enzyme electrode system
US5243516A (en) 1989-12-15 1993-09-07 Boehringer Mannheim Corporation Biosensing instrument and method
WO1991009139A1 (en) 1989-12-15 1991-06-27 Boehringer Mannheim Corporation Redox mediator reagent and biosensor
US5288636A (en) 1989-12-15 1994-02-22 Boehringer Mannheim Corporation Enzyme electrode system
US5122244A (en) 1990-02-03 1992-06-16 Boehringer Mannheim Gmbh Method and sensor electrode system for the electrochemical determination of an analyte or an oxidoreductase as well as the use of suitable compounds therefor
US5858188A (en) 1990-02-28 1999-01-12 Aclara Biosciences, Inc. Acrylic microchannels and their use in electrophoretic applications
EP0451981A2 (en) 1990-03-26 1991-10-16 Cascade Medical, Inc. Disposable reagent unit
US5194133A (en) 1990-05-04 1993-03-16 The General Electric Company, P.L.C. Sensor devices
US5243526A (en) 1990-05-18 1993-09-07 Mitsubishi Jidosha Kogyo Kabushiki Kaisha Output control apparatus for vehicle
US5059908A (en) 1990-05-31 1991-10-22 Capital Controls Company, Inc. Amperimetric measurement with cell electrode deplating
US5320732A (en) 1990-07-20 1994-06-14 Matsushita Electric Industrial Co., Ltd. Biosensor and measuring apparatus using the same
US6325973B1 (en) 1991-02-06 2001-12-04 Igen International, Inc. Methods and apparatus for improved luminescence assays
WO1992015701A1 (en) 1991-02-27 1992-09-17 Boehringer Mannheim Corporation Improved method and reagent for determination of an analyte
US5192415A (en) 1991-03-04 1993-03-09 Matsushita Electric Industrial Co., Ltd. Biosensor utilizing enzyme and a method for producing the same
US5496453A (en) 1991-05-17 1996-03-05 Kyoto Daiichi Kagaku Co., Ltd. Biosensor and method of quantitative analysis using the same
JPH04343065A (en) 1991-05-17 1992-11-30 Ngk Spark Plug Co Ltd Biosensor
US5382346A (en) 1991-05-17 1995-01-17 Kyoto Daiichi Kagaku Co., Ltd. Biosensor and method of quantitative analysis using the same
US5282950A (en) 1991-07-15 1994-02-01 Boehringer Mannheim Gmbh Electrochemical analysis system
US6218134B1 (en) 1991-07-29 2001-04-17 Mochida Pharmaceutical Co., Ltd. Process for specific binding assay for measuring the amount of analyte in a liquid test sample
US5354447A (en) 1991-12-12 1994-10-11 Kyoto Daiichi Kagaku Co., Ltd. Biosensor and method of quantitative analysis using the same
US5388163A (en) 1991-12-23 1995-02-07 At&T Corp. Electret transducer array and fabrication technique
AU3104293A (en) 1992-01-14 1993-07-15 Commonwealth Scientific And Industrial Research Organisation Viscometer
US5512159A (en) 1992-01-21 1996-04-30 Matsushita Electric Industrial Co. Ltd. Biosensor
RU2046361C1 (en) 1992-01-27 1995-10-20 Веревкин Валерий Иванович Device for measuring specific electric conduction of liquids
EP0560336A1 (en) 1992-03-12 1993-09-15 Matsushita Electric Industrial Co., Ltd. A catalyst made from phosphate and a biosensor including the same
JPH05312761A (en) 1992-05-12 1993-11-22 Toto Ltd Biosensor and its manufacture
WO1994002842A1 (en) 1992-07-28 1994-02-03 The Victoria University Of Manchester Analytical method for the detection and measurement of paracetamol
US5384028A (en) 1992-08-28 1995-01-24 Nec Corporation Biosensor with a data memory
EP0585933B1 (en) 1992-09-04 2005-12-21 Matsushita Electric Industrial Co., Ltd. Planar electrode
US5393399A (en) 1992-09-07 1995-02-28 Gie Cylergie Amperometric measuring device having an electrochemical sensor
US5726565A (en) 1992-10-28 1998-03-10 Nakano Vinegar Co., Ltd. Coulometric analysis method and a device therefor
US5909114A (en) 1992-10-28 1999-06-01 Nakano Vinegar Co., Ltd. Coulometric analysis method and a device therefor
JP3167464B2 (en) 1992-11-26 2001-05-21 富士電機株式会社 Inverter fault diagnosis device
EP0603954B1 (en) 1992-12-22 2000-03-08 Johnson & Johnson Clinical Diagnostics, Inc. Immunoassay using a 4-hydroxy or 4-alkoxyarylacetamide as stabilizer
AU5487394A (en) 1993-02-04 1994-08-11 Asulab S.A. Electrochemical measuring system with multizone sensors
US5395504A (en) 1993-02-04 1995-03-07 Asulab S.A. Electrochemical measuring system with multizone sensors
EP0609760A1 (en) 1993-02-04 1994-08-10 Asulab S.A. Electrochemical measurement system with snap-off sensor zones for the determination of glucose
JPH06310746A (en) 1993-04-27 1994-11-04 Hitachi Ltd Electrochemical element
WO1994029731A1 (en) 1993-06-03 1994-12-22 Boehringer Mannheim Corporation Biosensor for hematocrit determination
US5385846A (en) 1993-06-03 1995-01-31 Boehringer Mannheim Corporation Biosensor and method for hematocrit determination
US5405511A (en) 1993-06-08 1995-04-11 Boehringer Mannheim Corporation Biosensing meter with ambient temperature estimation method and system
US5366609A (en) 1993-06-08 1994-11-22 Boehringer Mannheim Corporation Biosensing meter with pluggable memory key
US5413690A (en) 1993-07-23 1995-05-09 Boehringer Mannheim Corporation Potentiometric biosensor and the method of its use
WO1995016198A1 (en) 1993-12-08 1995-06-15 Unilever Plc Methods and apparatus for electrochemical measurements
US5645709A (en) 1993-12-08 1997-07-08 Van Den Bergh Foods Co., Division Of Conopco, Inc. Methods and apparatus for electrochemical measurements
US5399256A (en) 1994-01-07 1995-03-21 Bioanalytical Systems, Inc. Electrochemical detector cell
US5520787A (en) 1994-02-09 1996-05-28 Abbott Laboratories Diagnostic flow cell device
WO1995021934A1 (en) 1994-02-10 1995-08-17 Cranfield University Hexacyanoferrate modified electrodes
US5762770A (en) 1994-02-21 1998-06-09 Boehringer Mannheim Corporation Electrochemical biosensor test strip
US5437999A (en) 1994-02-22 1995-08-01 Boehringer Mannheim Corporation Electrochemical sensor
US5863400A (en) 1994-04-14 1999-01-26 Usf Filtration & Separations Group Inc. Electrochemical cells
WO1995028634A1 (en) 1994-04-14 1995-10-26 Memtec America Corporation Electrochemical cells
US5575895A (en) 1994-06-02 1996-11-19 Matsushita Electric Industrial Co., Ltd. Biosensor and method for producing the same
US5518590A (en) 1994-06-21 1996-05-21 Pennzoil Products Company Electrochemical sensors for motor oils and other lubricants
US5849174A (en) 1994-08-01 1998-12-15 Medisense, Inc. Electrodes and their use in analysis
US5611908A (en) 1994-12-22 1997-03-18 Dr agerwerk Aktiengesellschaft Method of operating and amperometric measuring cell
US6521260B1 (en) 1995-01-31 2003-02-18 Vectura Limited Carrier particles for use in dry powder inhalers
US6153069A (en) 1995-02-09 2000-11-28 Tall Oak Ventures Apparatus for amperometric Diagnostic analysis
JPH0862179A (en) 1995-02-13 1996-03-08 Hitachi Ltd Electrolyte analyzer
US5517313A (en) 1995-02-21 1996-05-14 Colvin, Jr.; Arthur E. Fluorescent optical sensor
US5651869A (en) 1995-02-28 1997-07-29 Matsushita Electric Industrial Co., Ltd. Biosensor
US5607565A (en) 1995-03-27 1997-03-04 Coulter Corporation Apparatus for measuring analytes in a fluid sample
EP0735303A1 (en) 1995-03-31 1996-10-02 Tracto-Technik Paul Schmidt Spezialmaschinen Process for laying underground pipes between control chambers
US5527446A (en) 1995-04-13 1996-06-18 United States Of America As Represented By The Secretary Of The Air Force Gas sensor
US5620579A (en) 1995-05-05 1997-04-15 Bayer Corporation Apparatus for reduction of bias in amperometric sensors
JPH08304340A (en) 1995-05-05 1996-11-22 Bayer Corp Method and device for measuring concentration of analysis object by utilizing amperometric sensor
EP0741186B1 (en) 1995-05-05 2001-10-17 Bayer Corporation Method and apparatus for reduction of bias in amperometric sensors
US5695947A (en) 1995-06-06 1997-12-09 Biomedix, Inc. Amperometric cholesterol biosensor
US5567302A (en) 1995-06-07 1996-10-22 Molecular Devices Corporation Electrochemical system for rapid detection of biochemical agents that catalyze a redox potential change
JP2007225619A (en) 1995-06-19 2007-09-06 Lifescan Inc Electrochemical cell
WO1997000441A1 (en) 1995-06-19 1997-01-03 Memtec America Corporation Electrochemical cell
US7608175B2 (en) 1995-06-19 2009-10-27 Lifescan, Inc. Electrochemical cell
US6284125B1 (en) 1995-06-19 2001-09-04 Usf Filtration And Separations Group, Inc. Electrochemical cell
US7604722B2 (en) 1995-06-19 2009-10-20 Lifescan, Inc. Electrochemical cell
CN1325908C (en) 1995-06-19 2007-07-11 利费斯坎公司 Electrochemical detector
EP0764469B1 (en) 1995-09-25 2007-03-07 Bayer Corporation Method and apparatus for marking predetermined events with a biosensor
US5628890A (en) 1995-09-27 1997-05-13 Medisense, Inc. Electrochemical sensor
WO1997018464A1 (en) 1995-11-16 1997-05-22 Memtec America Corporation Electrochemical cell
US6521110B1 (en) 1995-11-16 2003-02-18 Lifescan, Inc. Electrochemical cell
US6179979B1 (en) 1995-11-16 2001-01-30 Usf Filtration & Separations Group, Inc. Electrochemical cell
WO1997018465A1 (en) 1995-11-16 1997-05-22 Memtec America Corporation Electrochemical method
US6863801B2 (en) 1995-11-16 2005-03-08 Lifescan, Inc. Electrochemical cell
US7431814B2 (en) 1995-11-16 2008-10-07 Lifescan, Inc. Electrochemical cell
US5942102A (en) 1995-11-16 1999-08-24 Usf Filtration And Separations Group Inc. Electrochemical method
US6214205B1 (en) 1996-01-26 2001-04-10 Yissum Research Development Company Of The Hebrew University Of Jerusalem Determination of an analyte in a liquid medium
JPH09222408A (en) 1996-02-19 1997-08-26 Matsushita Electric Ind Co Ltd Ph sensor and ion water creating device
JPH09236570A (en) 1996-03-04 1997-09-09 Matsushita Electric Ind Co Ltd Ph sensor and ion water maker
JPH09243588A (en) 1996-03-08 1997-09-19 Matsushita Electric Ind Co Ltd Ph sensor and ionic water forming device
US6413410B1 (en) 1996-06-19 2002-07-02 Lifescan, Inc. Electrochemical cell
US5707502A (en) 1996-07-12 1998-01-13 Chiron Diagnostics Corporation Sensors for measuring analyte concentrations and methods of making same
WO1998011426A1 (en) 1996-09-13 1998-03-19 Usf Filtration And Separations Group Inc. Analytic cell
US6174420B1 (en) 1996-11-15 2001-01-16 Usf Filtration And Separations Group, Inc. Electrochemical cell
US6117289A (en) 1996-12-20 2000-09-12 Matsushita Electric Industrial Co., Ltd. Cholesterol sensor and method for producing the same
US20020012943A1 (en) 1997-02-06 2002-01-31 Dana M. Fowlkes Electrochemical probes for detection of molecular interactions and drug discovery
WO1998043073A1 (en) 1997-03-21 1998-10-01 Usf Filtration And Separations Group Inc. Sensor connection means
WO1998043074A1 (en) 1997-03-25 1998-10-01 Usf Filtration And Separations Group Inc. Improved electrochemical cell
DE29709141U1 (en) 1997-05-24 1997-08-28 Kurt Schwabe Inst Fuer Mes Und Membrane covered electrochemical gas sensor
US6071391A (en) 1997-09-12 2000-06-06 Nok Corporation Enzyme electrode structure
US6503381B1 (en) 1997-09-12 2003-01-07 Therasense, Inc. Biosensor
US6270637B1 (en) 1997-12-05 2001-08-07 Roche Diagnostics Corporation Electrochemical biosensor test strip
US5997817A (en) 1997-12-05 1999-12-07 Roche Diagnostics Corporation Electrochemical biosensor test strip
WO1999046585A1 (en) 1998-03-12 1999-09-16 Usf Filtration And Separations Group Inc. Heated electrochemical cell
EP0964059B1 (en) 1998-06-11 2008-08-13 Matsushita Electric Industrial Co., Ltd. Biosensor comprising a working and a counter electrode, the counter electrode having a base plate with a curved portion
US6251260B1 (en) 1998-08-24 2001-06-26 Therasense, Inc. Potentiometric sensors for analytic determination
US6461496B1 (en) 1998-10-08 2002-10-08 Therasense, Inc. Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator
WO2000020626A1 (en) 1998-10-08 2000-04-13 Therasense, Inc. Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator
JP4066112B2 (en) 1999-01-28 2008-03-26 株式会社スーパーシリコン研究所 Wire saw control method and wire saw
US6193873B1 (en) 1999-06-15 2001-02-27 Lifescan, Inc. Sample detection to initiate timing of an electrochemical assay
US6413395B1 (en) 1999-12-16 2002-07-02 Roche Diagnostics Corporation Biosensor apparatus
JP2001281219A (en) 2000-03-29 2001-10-10 Kyocera Corp Air-fuel ratio sensor element
WO2002008763A3 (en) 2000-07-14 2002-06-13 Usf Filtration & Separations Immunosensor
US6544212B2 (en) 2001-07-31 2003-04-08 Roche Diagnostics Corporation Diabetes management system
US6780756B1 (en) 2003-02-28 2004-08-24 Texas Instruments Incorporated Etch back of interconnect dielectrics

Non-Patent Citations (88)

* Cited by examiner, † Cited by third party
Title
(Abstract Only) Kobayashi Yoshiaki et al., Biosensor, JP 61002060, A; Jan. 3, 1986.
(Abstract Only) Miyawaki Akiyoshi et al, Measurement Using Biosensor, JP60250246, Dec. 10, 1985.
Abstract for JP 6310746 A; To: Miyahara et al.
Abstracts of Jpan; Title: "Electrolyte Analyzer"; Publication No. 08062179A; Mar. 8, 1996.
Anderson and Reilly; "Thin-Layer Electrochemistry: Search-State Methods of Studying Rate Processes"; J. Electroanal. Chem., vol. 10; 1965.
Anderson, et al., Diagnostic Criteria for the Study of Chemical and Physical Processes by Twin-Electrode Thin-Layer Electrochemistry, J. Electroanalytical Chemistry; vol. 12, 1966, pp. 477-494.
Anderson, et al., Thin-Layer Electrochemistry: Steady-State Methods of Studying Rate Processes,J. Electroanalytical Chemistry; vol. 10, 1965, pp. 295-305.
Anderson, McDuffie and Reilley; "Diagnostic Criteria for the Study of Chemical and Physical Processes by Twin-Electrode Thin-Layer Electrochemistry"; Electroanalytical Chemistry; vol. 12, 1966, pp. 477-494.
Cassidy, et al.; Novel Electrochemical Device for the Detection of Cholesterol or Glucose, Analyst, vol. 118; Apr. 1993; pp. 415-418.
Chidsey, et al., Micrometer-Spaced Platinum Interdigitated Array Electrode: Fabrication, Theory, and Initial Use, Analytical Chemistry, vol. 58, No. 3, Mar. 1986, pp. 801-807.
Chidsey, Feldman, Lundgren, and Murray; "Micrometer-Spaced Platinum Interdigitated Array Electrode: Fabrication, Theory, and Initial Use"; Analytical Chemistry; vol. 58, No. 3; Mar. 1986.
Chinese Office Action (Application No. CN200610100717.9) dated Dec. 5, 2008.
Christensen & Anson; "Chronpotentionmetry in Thin Layers of Solution"; Analytical Chemistry; vol. 35; No. 2, 1963.
Christensen, et al. Chronopotentiometry in Thin Layer of Solution, Analytical Chemistry, vol. 35, No. 2, 1963, pp. 205-209.
Daruhazi, et al., "Cyclic Voltammetry for Reversible Redox-Electrode Reaction in Thin Layer Cells with Closely Separated Working and Auxiliary Electrodes of the Same Size", in J. Electroanal. Chem. 264; 77-89 (1989).
Data Sheet for ARcae 7148 double-side adhesive coated polyester film, (Mar. 30, 1995) (2 pp.).
Denuault, et al., Direct Determination of Diffusion-Coefficients by Chronoamperometry at Microdisk Electrodes, Journal of Electroanalytical Chemistry, vol. 308, No. 1-2, 1991, pp. 27-38.
Denuault, G. et al., "Direct Determination of Diffusion-Coefficients by Chronoamperometry at Microdisk Electrodes", Journal of Electroanalytical Chemistry, vol. 308, No. 1-2, 1991, pp. 27-38.
Derwent Abstract Accession No. 93-140898/17, JP, A., 05080018 (Rikagaku Kenkyusho) Mar. 30, 1993.
Derwent Abstract Accession No. 95-026336/04, JP, A., 06310746 (Hitachi Ltd) Nov. 4, 1994.
Derwent Abstracts Accession No. 92 119462/15, Class S03, JP, A, 04-62463 (Tokyo Yogyo K.K.) Feb. 27, 1992. Patent Abstracts of Japan.
Diagnostic Criteria For The Study of Chemical And Physical Processes By Twin-Electrode Thin-Layer Electrochemistry; Anderson et al., J. Electroanal. Chem, 12(996)477-494.
Enthone-Imaging Technologies Update Jun. 2001/No. 3) Enplate DSR 3241.
Enthone-Imaging Technologies Update Jun. 2001/No. 3.
European Search Report for App. No. 03 00 7604 dated May 19, 2003.
European Search Report for App. No. 96 93 7919 apparently published Jan. 24, 2001.
European Search Report for App. No. 99 20 2305 apparently published May 23, 2001.
European Search Report No. EP 03007604 dated May 19, 2003.
European Search Report, Application No. 96937919.
European Search Report, Application No. EP 99202305.
Hall, E., Biosensors, Chapter 5: "Ampermetric Assay Techniques", 1990.
Hall, E., Biosensors, Chapter 5: "Amperometric Assay Techniques", 1990.
Hubbard & Anson; "New Electrodes for Chronopotentiometry in Thin Layers of Solutions"; Analytical Chemistry; vol. 36, No. 4, Apr. 1964.
Hubbard, et al., New Electrodes for Chronopotentiometry in Thin Layers of Solution, Analystical Chemistry, vol. 36, No. 4, Apr. 1964, pp. 723-728.
Hubbard, et al., The Theory and Practice of Electrochemicsty with Thin Layer Cells, in Electroanalytical Chemistry, (Bard, Ed.), Marcel Deletier, New York, 1970, vol. 4 (pp. 129-214).
Hubbard, et al., The Theory and Practice of Electrochemistry with Thin Layer Cells, Electroanalytical Chemistry, (Bard, Ed.), Marcel Deletier, New York, 1970, vol. 4., pp. 129-214.
Hubbard, Study of the Kinetics of Electrochemical Reactions by Thin-Layer Voltammetry, J. Electroanalytical Chemistry, vol. 22, 1969, pp. 165-174.
Hubbard: "Study of the Kinetics of Electrochemical Reactions by Thin-Layer Voltammetry"; Journal of Electroanalytical Chemistry; vol. 22; 1969.
International Search Report PCT/US02/31289 dated Jul. 18, 2003.
J. Salbeck, "Spectrochemical Thin-Layer Cell for Nanaqueous Solvent Systems," Anal. Chem., 1993, vol. 65, pp. 2165-2173.
Japanese Office Action (Application No. 102675/2007) dated Jan. 8, 2010.
Japanese Office Action (Application No. 2003-535271) dated Jul. 28, 2008, 7 pages.
Japanese Office Action for Japanese Application No. 2003-535271 dated Jun. 29, 2010 (3 pages).
John F. Cassidy et al., "Novel Electrochemical Device for the Detection of Cholesterol or Glucose" in Analyst Apr. 1993, vol. 118, p. 415-418.
JPO computer generated English language translation of Japanese Patent Application Publication 2001-281219, downloaded on Feb. 28, 2011. *
JPO Patent Abstract of JP-04-56112-A.
Jung, et al., Simultaneous Determination of Diffusion Coefficient and Concentration by Chronoamperometry at a Microdisk Electrode, Bull Korean Chem. Soc.; 1004, V. 15, No. 3, pp. 209-213 1994.
Laszlo Daruhazi et al., "Cyclic Voltammetry for Reversible Redox-Electrode Reaction in Thin Layer Cells with Closely Separated Working and Auxiliary Electrodes of the Same Size", in J. Electroanal. Chem. 264: 77-89 (1989).
McDuffie, Anderson, & Reilly; "Twin Electrode Thin-Layer Electrochemistry"; Analytical Chemistry; vol. 38, No. 7; pp. 883-890, Jun. 1966.
McDuffie, et al., Twin electrode thin-Layer Electrochemistry, Analytical Chemistry, vol. 38, No. 7, Jun. 1966; pp. 883-890.
Morris, et al., Electrochemistry at Pt Band Electrodes of Width Appraching Molecular Dimensions, Breakdown of Transport Equaltions at Very Small Electrodes, J. of Physical Chemistry, vol. 91, No. 13, 1987, pp. 3559-3564.
Morris, Franta and White; "Electrochemistry at Pt Band Electrodes of Width Approaching Molecular Dimensions. Breakdown of Transport Equestions at Very Small Electrodes"; The Journal of Physical Chemistry; vol. 91, No. 13; 1987.
Nicholson and Shain; "Theoty of Stationary Electrode Polarography"; Analytical Chemistry; vol. 36, No. 4, Apr. 1964.
Nicholson, et al., Theory of Stationary Electrode Polarography, Analytical Chemistry; vol. 36, No. 4, Apr. 1964, pp. 706-723.
Niwa, et al., Electrochemical Behavior of Reversibel Redox Species at Interdigitated Array Electrodes with Different Geometries: Consideration of Redox Cycling and Collection Efficiency, Analytical Chemistry; Mar. 1990, vol. 62, No. 5, pp. 447-452.
Niwa, et al., Highly Selective electrochemical Detection of Dopamine Using Interdigitated Array of Electrodes Modified with Nafion/Polyester Ionomer Layered Film, Electroanalysis, vol. 6, No. 3, Mar. 1994, pp. 237-243, XP000943528.
Niwa, O., et al., "Electrochemical Behavior of Reversible Redox Species at Interdigitated Array Electrodes with Different Geometries: Consideration of Redox Cycling and Collection"; Analytical Chemistry, Mar. 1990, vol. 62, No. 5.
O. Niwa, M. Morita, H. Tabei, "Highly Selective Electrochemical Detection of Dopamine Using Interdigital Array of Electrodes Modified with Nafion/Polyester Ionomer Layered Film", Electroanalysis, vol. 6, No. 3, Mar. 1994, pp. 237-243, XP000943528.
Oglesby et al. Anal. Chem. vol. 37, No. 11, Oct. 1965, pp. 1312-1316. *
Oglesby, et al., Thin Layer Electrochemical Studies Using Controlled Potential or Controlled Current, Analytical Chemistry, vol. 37, No. 11, Oct. 1965, pp. 1312-1316.
Paeschke, et al., Dynamic Redox Recycling of Cytochrome C, Journal of Electroanalytical Chemistry; vol. 393, No. 1/02, 1995, pp. 131-135.
Paeschke, et al., Properties of Interdigital Electrode Arrays With Different Geometries, Analytical Chimica Acta; vol. 305, No. 1/03, 1995, pp. 126-136.
Paeschke, M. et al., "Dynamic Redox Recycling of Cytochrome C", Journal of Electroanalytical Chemistry, vol. 393, No. 1/02, 1995, pp. 131-135.
Paeschkle, M. et al., "Properties of Interdigital Electrode Arrays With Different Geometries", Analytica Chimica Acta; vol. 305, No. 1/03, 1995, pp. 126-136.
Patent Abstract of Japan, Publication No. 60250246, published Dec. 10, 1985.
Patent Abstracts of Japan JP63-139246 A2 (Jun. 1988).
Patent Abstracts of Japan, JP A 04-62463.
Patent Abstracts of Japan, p.-269, p. 168, JP, A, 59-3345, (Hitachi Seisakusho K.K.) Jan. 10, 2994.
Patent family history and equivalent filings for WO 97/00441 A1 downloaded from Derwent on Mar. 4, 2011. *
Pickup Lutner, Leidner, and Murray; "Redox Conduction in Single and bilayer Films of Redox Polymer"; American Chemical Society; vol. 106; No. 7; 1984.
Pickup, et al., Redox Conduction in Single and Bilayer Films of Redox Polymer, J. Amer. Chem. Soc.; vol. 106; No. 7; 1984.
Reilley, Charles, Electrochemistry Using Thin-Layer Cells, Review of Pure and Appl. Chem, vol. 18, 1968, pp. 137-151.
Reilly, Charles: "Electrochemistry Using Thin-Layer Cells", Rev. Pure and Appl. Chem. vol. 18.
Salbeck, J., Spectrochemical Thin-Layer Cell for Nonaqueous Solvent Systems, Anal. Chem., 1993, vol. 65, pp. 2165-2173.
Seddon, B. J., et al., "Preparation and Amperometric Response of Carbon and Platimum Dual Cylinder Microelectrodes", Electrochinica Act, vol. 40, No. 4, Mar. 1, 1995, pp. 455-465.
Seddon, et al., Preparation and Ameprometric Response of Carbon and Platinum Dual Cylinder Microelectrodes, Electrochimica Acta, vol. 40, No. 4, Mar. 1, 1995, pp. 455-465.
Simultaneous Determination of Diffusion Coefficient and Concentration by Chronoaperometry at a Microdisk Electrode; Jung et al.; Bull. Korean Chem. Soc., 1994, vol. 15, No. 3, 209-213.
Specification sheet for Adhesives Research, Inc. ARClad® 8314 (May 2, 1997) (1 pg.).
Specification sheet for Adhesives Research, Inc., ARCare® 7148, double-sided adhesive coated polyester film (Mar. 30, 1995) (2 pages).
Specification sheet from Adhesives Research, Inc. Arclad® 8314 (May 2, 1997).
Trojanek et al., "Data processing in reaction rate measurements," Collect. Chezech. Chem commun., 38(9):2572-2580, 1973.
Trojanek, et al., Data processing in reaction rate measurements, Collect. Chzech. Chem commun., 38(9):2572-2580, 1973.
Uchiyama et al., Measurement Of Homogeneous Reaction Rate By Concentration-Step, Controlled Potential Electrolysis,: J. Electroanal. Chem Interfacial Electrochem., 91(3):301-308, 1978.
Uchiyama, et al., Measurement Of Homogeneous Reaction Rate By Concentration-Step, Controlled Potential Electrolysis, J. Electroanal. Chem Interfacial Electrochem., 91(3):301-308, 1978.
Vidal, et al., A chronoamperometric sensor for hydrogen peroxide based on electro transfer between immobilized horseradish peroxidase on a glossy carbon electrode and a diffusing ferrocene mediator, Sensors and Actuators, B, Ch, Elsevier Sequoia S.A., Lausanne, vol. 21, No. 2 (Aug. 1, 1994), pp. 135-141.
Vidal, J. C. et al., "A Chronoamperometric Sensor for Hydrogen Peroxide Based on Electron Transfer Between Immobilized Horseradish Peroxidase on a Glassy Carbon Electrode and a Diffusing Ferrocene Mediator", Sensors and Actuators B:Chemical, vol. 21, Issue 2, Aug. 1994, pp. 135-141.
Yaoita, et al., Pulse Chronoamperometric Technique of Enzyme Embodied Electrode Applied to Glucose Measurement in Whole Serum, Extended Abstracts, US, Electrochemical Society, Princeton, NJ; vol. 93/1, 1993, p. 2801.
Yaoita, M. et al., "Pulse Chronoamperometric Technique of Enzyme Embodied Electrode Applied to Glucose Measurement in Whole Serum", Extended Abstracts, US Electrochemical Society, Princeton, NJ; vol. 93/1, 1993, p. 2801.

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9523653B2 (en) 2013-05-09 2016-12-20 Changsha Sinocare Inc. Disposable test sensor with improved sampling entrance
US10247693B2 (en) 2013-05-09 2019-04-02 Changsha Sinocare Inc. Disposable test sensor with improved sampling entrance
US10571425B2 (en) 2013-05-09 2020-02-25 Changsha Sinocare Inc. Disposable test sensor with improved sampling entrance
US9518951B2 (en) 2013-12-06 2016-12-13 Changsha Sinocare Inc. Disposable test sensor with improved sampling entrance
US10088444B2 (en) 2013-12-06 2018-10-02 Changsha Sinocare Inc. Disposable test sensor with improved sampling entrance
US10527576B2 (en) 2013-12-06 2020-01-07 Changsha Sinocare Inc. Disposable test sensor with improved sampling entrance
US9897566B2 (en) 2014-01-13 2018-02-20 Changsha Sinocare Inc. Disposable test sensor
US9939401B2 (en) 2014-02-20 2018-04-10 Changsha Sinocare Inc. Test sensor with multiple sampling routes
US10386323B2 (en) 2014-02-20 2019-08-20 Sinocare Inc. Test sensor with multiple sampling routes

Also Published As

Publication number Publication date
DK1362922T3 (en) 2012-05-07
WO1997018465A1 (en) 1997-05-22
EP0923722B1 (en) 2011-05-04
AU7554996A (en) 1997-06-05
US5942102A (en) 1999-08-24
EP0923722A4 (en) 2001-01-24
IL132089A (en) 2004-05-12
CN1204399A (en) 1999-01-06
AUPN661995A0 (en) 1995-12-07
RU2243545C2 (en) 2004-12-27
ES2197572T3 (en) 2004-01-01
CN1763518A (en) 2006-04-26
EP0923722A1 (en) 1999-06-23
KR100741187B1 (en) 2007-07-19
CN1445541A (en) 2003-10-01
RU2305279C2 (en) 2007-08-27
HK1104604A1 (en) 2008-01-18
KR100628860B1 (en) 2006-09-27
AU7555096A (en) 1997-06-05
KR100468550B1 (en) 2005-05-24
BR9611513A (en) 1999-09-14
HK1018096A1 (en) 1999-12-10
CN1445540B (en) 2010-05-12
RU2174679C2 (en) 2001-10-10
HK1028914A1 (en) 2001-03-09
DK0967480T3 (en) 2003-10-27
CN1928541A (en) 2007-03-14
ATE508358T1 (en) 2011-05-15
WO1997018464A1 (en) 1997-05-22
CN1105304C (en) 2003-04-09
DK0923722T3 (en) 2011-06-14
EP0967480B1 (en) 2003-07-02
ES2195019T3 (en) 2003-12-01
HK1049513A1 (en) 2003-05-16
CN1160564C (en) 2004-08-04
BR9611513B1 (en) 2008-11-18
CA2236850C (en) 2004-06-01
KR19990067672A (en) 1999-08-25
IL124495A0 (en) 1999-01-26
KR20050042506A (en) 2005-05-09
EP0967480A3 (en) 2001-01-17
ATE244401T1 (en) 2003-07-15
EP1362922B1 (en) 2012-04-11
CN1932500B (en) 2011-07-27
CN1932500A (en) 2007-03-21
JP3863184B2 (en) 2006-12-27
DE69628588D1 (en) 2003-07-10
CA2236850A1 (en) 1997-05-22
JP2000500572A (en) 2000-01-18
CA2577229C (en) 2008-01-08
CA2577229A1 (en) 1997-05-22
EP1362922A1 (en) 2003-11-19
DE69628948T2 (en) 2003-12-24
KR20060097067A (en) 2006-09-13
IL172879A0 (en) 2006-06-11
CN1445540A (en) 2003-10-01
IL124494A (en) 2000-08-31
ATE242477T1 (en) 2003-06-15
CA2236848C (en) 2007-05-15
DE69638367D1 (en) 2011-06-16
KR20030096453A (en) 2003-12-31
IL124494A0 (en) 1999-01-26
AU705313B2 (en) 1999-05-20
CN1104645C (en) 2003-04-02
CN1204400A (en) 1999-01-06
ES2384166T3 (en) 2012-07-02
JP2000500571A (en) 2000-01-18
KR100655357B1 (en) 2007-12-04
AU705165B2 (en) 1999-05-20
EP0882226B1 (en) 2003-06-04
KR19990067673A (en) 1999-08-25
HK1060597A1 (en) 2004-08-13
BR9611514A (en) 1999-09-14
CN100409008C (en) 2008-08-06
IL124495A (en) 2003-06-24
DK0882226T3 (en) 2003-06-23
KR100741181B1 (en) 2007-07-19
IL133994A0 (en) 2002-03-10
DE69628948D1 (en) 2003-08-07
CA2236848A1 (en) 1997-05-22
ES2365981T3 (en) 2011-10-14
DE69628588T2 (en) 2003-12-24
US6179979B1 (en) 2001-01-30
CN1254840A (en) 2000-05-31
RU2202781C2 (en) 2003-04-20
HK1018097A1 (en) 1999-12-10
ATE553212T1 (en) 2012-04-15
EP0882226A4 (en) 2001-01-17
EP1236995A1 (en) 2002-09-04
EP0882226A1 (en) 1998-12-09
EP0967480A2 (en) 1999-12-29

Similar Documents

Publication Publication Date Title
USRE42567E1 (en) Electrochemical cell
US7431814B2 (en) Electrochemical cell
US6174420B1 (en) Electrochemical cell
US6521110B1 (en) Electrochemical cell
US8801907B2 (en) Electrochemical cell
US5916156A (en) Electrochemical sensors having improved selectivity and enhanced sensitivity
JP3821685B2 (en) Biosensor
AU738128B2 (en) Electrochemical cell
ZA200107967B (en) Electrochemical biosensor test strip, fabrication method thereof and electrochemical biosensor.

Legal Events

Date Code Title Description
FPAY Fee payment

Year of fee payment: 4

FPAY Fee payment

Year of fee payment: 8

AS Assignment

Owner name: BANK OF AMERICA, N.A., AS COLLATERAL AGENT, NORTH CAROLINA

Free format text: SECURITY AGREEMENT;ASSIGNOR:LIFESCAN IP HOLDINGS, LLC;REEL/FRAME:047179/0150

Effective date: 20181001

Owner name: BANK OF AMERICA, N.A., AS COLLATERAL AGENT, NORTH

Free format text: SECURITY AGREEMENT;ASSIGNOR:LIFESCAN IP HOLDINGS, LLC;REEL/FRAME:047179/0150

Effective date: 20181001

AS Assignment

Owner name: BANK OF AMERICA, N.A., AS COLLATERAL AGENT, NORTH CAROLINA

Free format text: SECURITY AGREEMENT;ASSIGNOR:LIFESCAN IP HOLDINGS, LLC;REEL/FRAME:047186/0836

Effective date: 20181001

Owner name: BANK OF AMERICA, N.A., AS COLLATERAL AGENT, NORTH

Free format text: SECURITY AGREEMENT;ASSIGNOR:LIFESCAN IP HOLDINGS, LLC;REEL/FRAME:047186/0836

Effective date: 20181001

AS Assignment

Owner name: CILAG GMBH INTERNATIONAL, SWITZERLAND

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:LIFESCAN INC.;REEL/FRAME:050836/0737

Effective date: 20181001

Owner name: LIFESCAN IP HOLDINGS, LLC, CALIFORNIA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:CILAG GMBH INTERNATIONAL;REEL/FRAME:050837/0001

Effective date: 20181001

MAFP Maintenance fee payment

Free format text: PAYMENT OF MAINTENANCE FEE, 12TH YEAR, LARGE ENTITY (ORIGINAL EVENT CODE: M1553); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY

Year of fee payment: 12

AS Assignment

Owner name: JOHNSON & JOHNSON CONSUMER INC., NEW JERSEY

Free format text: RELEASE OF SECOND LIEN PATENT SECURITY AGREEMENT RECORDED OCT. 3, 2018, REEL/FRAME 047186/0836;ASSIGNOR:BANK OF AMERICA, N.A.;REEL/FRAME:064206/0176

Effective date: 20230627

Owner name: JANSSEN BIOTECH, INC., PENNSYLVANIA

Free format text: RELEASE OF SECOND LIEN PATENT SECURITY AGREEMENT RECORDED OCT. 3, 2018, REEL/FRAME 047186/0836;ASSIGNOR:BANK OF AMERICA, N.A.;REEL/FRAME:064206/0176

Effective date: 20230627

Owner name: LIFESCAN IP HOLDINGS, LLC, CALIFORNIA

Free format text: RELEASE OF SECOND LIEN PATENT SECURITY AGREEMENT RECORDED OCT. 3, 2018, REEL/FRAME 047186/0836;ASSIGNOR:BANK OF AMERICA, N.A.;REEL/FRAME:064206/0176

Effective date: 20230627

AS Assignment

Owner name: CILAG GMBH INTERNATIONAL, SWITZERLAND

Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE PROPERTY LIST BY ADDING PATENTS 6990849;7169116; 7351770;7462265;7468125; 7572356;8093903; 8486245;8066866;AND DELETE 10881560. PREVIOUSLY RECORDED ON REEL 050836 FRAME 0737. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT;ASSIGNOR:LIFESCAN INC.;REEL/FRAME:064782/0443

Effective date: 20181001