US20050139469A1 - Electrochemical test strip for reducing the effect of direct and mediated interference current - Google Patents

Electrochemical test strip for reducing the effect of direct and mediated interference current Download PDF

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Publication number
US20050139469A1
US20050139469A1 US10/977,316 US97731604A US2005139469A1 US 20050139469 A1 US20050139469 A1 US 20050139469A1 US 97731604 A US97731604 A US 97731604A US 2005139469 A1 US2005139469 A1 US 2005139469A1
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working electrode
reagent layer
inactive
active
electrode
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US10/977,316
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Oliver Davies
Robert Marshall
Damian Baskeyfield
Lysney Whyte
Elaine Leiper
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LifeScan Scotland Ltd
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LifeScan Scotland Ltd
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Priority to US10/977,316 priority Critical patent/US20050139469A1/en
Assigned to LIFESCAN SCOTLAND LIMITED reassignment LIFESCAN SCOTLAND LIMITED ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: BASKEYFIELD, DAMIAN EDWARD HAYDON, DAVIES, OLIVER WILLIAM HARDWICK, LEIPER, ELAINE, MARSHALL, ROBERT, WHYTE, LYNSEY
Publication of US20050139469A1 publication Critical patent/US20050139469A1/en
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    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12Q—MEASURING 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
    • C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/001—Enzyme electrodes
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/416—Systems
    • G01N27/49—Systems involving the determination of the current at a single specific value, or small range of values, of applied voltage for producing selective measurement of one or more particular ionic species
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1486—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/15—Devices for taking samples of blood
    • A61B5/150007—Details
    • A61B5/150015—Source of blood
    • A61B5/150022—Source of blood for capillary blood or interstitial fluid
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/15—Devices for taking samples of blood
    • A61B5/150007—Details
    • A61B5/150206—Construction or design features not otherwise provided for; manufacturing or production; packages; sterilisation of piercing element, piercing device or sampling device
    • A61B5/150274—Manufacture or production processes or steps for blood sampling devices
    • A61B5/150282—Manufacture or production processes or steps for blood sampling devices for piercing elements, e.g. blade, lancet, canula, needle
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/15—Devices for taking samples of blood
    • A61B5/150007—Details
    • A61B5/150358—Strips for collecting blood, e.g. absorbent
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/15—Devices for taking samples of blood
    • A61B5/150007—Details
    • A61B5/150374—Details of piercing elements or protective means for preventing accidental injuries by such piercing elements
    • A61B5/150381—Design of piercing elements
    • A61B5/150412—Pointed piercing elements, e.g. needles, lancets for piercing the skin
    • A61B5/150435—Specific design of proximal end
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/15—Devices for taking samples of blood
    • A61B5/150007—Details
    • A61B5/150374—Details of piercing elements or protective means for preventing accidental injuries by such piercing elements
    • A61B5/150381—Design of piercing elements
    • A61B5/150503—Single-ended needles
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12Q—MEASURING 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
    • C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/001—Enzyme electrodes
    • C12Q1/005—Enzyme electrodes involving specific analytes or enzymes
    • C12Q1/006—Enzyme electrodes involving specific analytes or enzymes for glucose
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
    • G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
    • G01N27/3274—Corrective measures, e.g. error detection, compensation for temperature or hematocrit, calibration
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/416—Systems
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/483—Physical analysis of biological material
    • G01N33/487—Physical analysis of biological material of liquid biological material
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02A—TECHNOLOGIES FOR ADAPTATION TO CLIMATE CHANGE
    • Y02A90/00—Technologies having an indirect contribution to adaptation to climate change
    • Y02A90/10—Information and communication technologies [ICT] supporting adaptation to climate change, e.g. for weather forecasting or climate simulation

Definitions

  • the present invention is related, in general to electrochemical strips and systems which are designed to reduce the effect of interfering compounds on measurements taken by such analyte measurement systems and, more particularly, to an improved electrochemical strip for reducing the effects of direct interference currents and mediated interference currents in a glucose monitoring system wherein the electrochemical strip has electrodes with regions coated by active reagent and regions coated with inactive reagent.
  • an electrochemical glucose measuring system may have an elevated oxidation current due to the oxidation of interfering compounds commonly found in physiological fluids such as, for example, acetaminophen, ascorbic acid, bilirubin, dopamine, gentisic acid, glutathione, levodopa, methyldopa, tolazimide, tolbutamide, and uric acid.
  • the accuracy of glucose meters may, therefore, be improved by reducing or eliminating the portion of the oxidation current generated by interfering compounds.
  • there should be no oxidation current generated from any of the interfering compounds so that the entire oxidation current would depend only on the glucose concentration.
  • electrochemical sensors it is, therefore, desirable to improve the accuracy of electrochemical sensors in the presence of potentially interfering compounds such as, for example, ascorbate, urate, and, acetaminophen, commonly found in physiological fluids.
  • analytes for such electrochemical sensors may include glucose, lactate, and fructosamine.
  • glucose will be the main analyte discussed, it will be obvious to one skilled in the art that the invention set forth herein may also be used with other analytes.
  • Oxidation current may be generated in several ways.
  • desirable oxidation current results from the interaction of the mediator with the analyte of interest (e.g., glucose) while undesirable oxidation current is generally comprised of interfering compounds being oxidized at the electrode surface and by interaction with the mediator.
  • interfering compounds e.g., acetominophen
  • Other interfering compounds e.g., ascorbic acid
  • This oxidation of the interfering compound in a glucose measuring system causes the measured oxidation current to be dependent on the concentration of both the glucose and any interfering compound.
  • the measurement of the glucose concentration would be improved by reducing or eliminating the contribution of the interfering compounds to the total oxidation current.
  • a negatively charged membrane to cover the working electrode.
  • a sulfonated fluoropolymer such as NAFIONTM may be used to repel all negatively charged chemicals.
  • most interfering compounds such as ascorbate and urate have a negative charge, thus, the negatively charged membrane prevents the negatively charged interfering compounds from reaching the electrode surface and being oxidized at that surface.
  • this technique is not always successful since some interfering compounds such as acetaminophen do not have a net negative charge, and thus, can pass through a negatively charged membrane.
  • This technique reduce the oxidation current resulting from the interaction of interfering compounds with some mediators.
  • the use of a negatively charged membrane on the working electrode could also prevent some commonly used mediators, such as ferricyanide, from passing through the negatively charged membrane to exchange electrons with the electrode.
  • a size selective membrane on top of the working electrode.
  • a 100 Dalton exclusion membrane such as cellulose acetate may be used to cover the working electrode to exclude all chemicals with a molecular weight greater than 100 Daltons.
  • most interfering compounds have a molecular weight greater than 100 Daltons, and thus, are excluded from being oxidized at the electrode surface.
  • selective membranes typically make the test strip more complicated to manufacture and increase the test time because the oxidized glucose must diffuse through the selective membrane to get to the electrode.
  • mediators having a relatively low redox potential include osmium bipyridyl complexes, ferrocene derivatives, and quinone derivatives.
  • mediators having a relatively low potential are often difficult to synthesize, unstable and have a low water solubility.
  • Another known strategy that can be used to decrease the effects of interfering compounds is to use a dummy electrode which is coated with a mediator.
  • the dummy electrode may also be coated with an inert protein or deactivated redox enzyme.
  • the purpose of the dummy electrode is to oxidize the interfering compound at the electrode surface and/or to oxidize the mediator reduced by the interfering compound.
  • the current measured at the dummy electrode is subtracted from the total oxidizing current measured at the working electrode to remove the interference effect.
  • a disadvantage of this strategy is that it requires that the test strip include an additional electrode and electrical connection (i.e., the dummy electrode) which cannot be used to measure glucose.
  • the inclusion of dummy electrode is an inefficient use of an electrode in a glucose measuring system.
  • the present invention is directed to an electrochemical sensor or electrochemical strip which includes a substrate, a first working electrode disposed on the substrate, a second working electrode disposed on the substrate, a reference electrode, an active reagent layer disposed on the first working electrode, wherein the active reagent layer completely covers the first working electrode and an inactive reagent layer disposed on the second working electrode, wherein the inactive reagent completely covers the second working electrode.
  • the present invention further includes an electrochemical sensor wherein the first working electrode, the second working electrode and the reference electrode are positioned in a sample receiving chamber, the sample receiving chamber has a proximal and a distal end, the distal end including a first opening which is adapted to receive bodily fluids and the second working electrode being positioned adjacent the first opening.
  • the present invention further includes an electrochemical sensor wherein the first working electrode and the reference electrode are positioned proximal to the second working electrode.
  • the present invention is also directed to an electrochemical sensor an electrochemical sensor including a substrate, a first working electrode disposed on the substrate, a second working electrode disposed on the substrate, a reference electrode, an active reagent layer disposed on the first working electrode, wherein the active reagent layer completely covers the first working electrode, the second working electrode having an active region and an inactive region, the active reagent layer disposed on an active region of the second working electrode and an inactive reagent layer disposed on the inactive region of the second working electrode.
  • the present invention further includes an electrochemical sensor wherein the first working electrode, the second working electrode and the reference electrode are positioned in a sample receiving chamber, the sample receiving chamber having a proximal and a distal end, the distal end including a first opening which is adapted to receive bodily fluids and the inactive region of the second working electrode being positioned adjacent the first opening.
  • the present invention further includes an electrochemical sensor wherein the active region of the second working electrode and the first working electrode are positioned proximal to the inactive region of the second working electrode.
  • FIG. 1 is an exploded perspective view of a test strip according to an exemplary embodiment of the present invention
  • FIG. 2 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 1 including a conductive layer and an insulation layer;
  • FIG. 3 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 1 , wherein the position of an active and an inactive reagent layer do not touch each other and are illustrated with the insulation and conductive layer;
  • FIG. 4 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 1 , wherein the position of the active and the inactive reagent layer are immediately adjacent to each other and are illustrated with the insulation and conductive layer;
  • FIG. 5 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 1 , wherein the position of the active and the inactive reagent layer that overlap with each other and are illustrated with the insulation and conductive layer;
  • FIG. 6 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 1 , wherein the active and the inactive reagent layer do not touch each other and are illustrated with the conductive layer;
  • FIG. 7 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 1 , wherein the active and the inactive reagent layer are immediately adjacent to each other and are illustrated with the conductive layer;
  • FIG. 8 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 1 , wherein the active and the inactive reagent layer overlap with each other and are illustrated with the conductive layer;
  • FIG. 9 is a simplified schematic showing a meter interfacing with a test strip that has a first contact, second contact, and reference contact disposed on a substrate;
  • FIG. 10 is a simplified schematic showing a meter interfacing with a test strip that has a first contact and a second contact disposed on a substrate and a reference contact which is orientated in a facing orientation with the first contact and second contact;
  • FIG. 11 is a graph showing the effects of gamma radiation on precision for test strips tested at a 20 mg/dL glucose concentration
  • FIG. 12 is a graph showing the effects of gamma radiation on precision for test strips tested at a 50 mg/dL glucose concentration
  • FIG. 13 is a graph showing the effects of gamma radiation on precision for test strips tested at a 100 mg/dL glucose concentration
  • FIG. 14 is a graph showing the effects of gamma radiation on precision for test strips tested at a 300 mg/dL glucose concentration
  • FIG. 15 is a graph showing the effects of gamma radiation on precision for test strips tested at a 500 mg/dL glucose concentration
  • FIG. 16 is a graph showing the effects of gentisic acid on accuracy for test strips tested at a 70 mg/dL glucose concentration
  • FIG. 17 is a graph showing the effects of gentisic acid on accuracy for test strips tested at a 240 mg/dL glucose concentration
  • FIG. 18 is a graph showing the effects of uric acid on accuracy for test strips tested at a 70 mg/dL glucose concentration
  • FIG. 19 is a graph showing the effects of uric acid on accuracy for test strips tested at a 240 mg/dL glucose concentration
  • FIG. 20 a simplified plane view of a distal portion of a test showing a modified cutout that allows the area of a second working electrode to be increased;
  • FIG. 21 is an exploded perspective view of a test strip according to another exemplary embodiment of the present invention.
  • FIG. 22 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 21 , wherein the position of an active and an inactive reagent layer do not touch each other and are illustrated with the insulation and conductive layer;
  • FIG. 23 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 21 , wherein the position of the active and the inactive reagent layer are immediately adjacent to each other and are illustrated with the insulation and conductive layer;
  • FIG. 24 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 21 , wherein the position of the active and the inactive reagent layer that overlap with each other and are illustrated with the insulation and conductive layer;
  • FIG. 25 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 21 , wherein the active and the inactive reagent layer do not touch each other and are illustrated with the conductive layer;
  • FIG. 26 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 21 , wherein the active and the inactive reagent layer are immediately adjacent to each other and are illustrated with the conductive layer; and
  • FIG. 27 is a simplified plane view of a distal portion of a test strip according to the embodiment of the present invention illustrated in FIG. 21 , wherein the active and the inactive reagent layer overlap with each other and are illustrated with the conductive layer;
  • the invention described herein includes a test strip to improve the accuracy of a glucose measurement in the presence of interfering compounds.
  • a type of interfering compound may develop in the test strip itself before bodily fluid such as, for example, blood is added.
  • An example this type of interfering compound may be a reduced mediator (e.g. ferrocyanide) which develops from the conversion of an oxidized mediator (e.g. ferricyanide). This causes the background signal to increase which, in turn, decreases the accuracy of the test strip measurement.
  • the interfering compound develops in the test strip itself as opposed to being provided to the test strip in the form of a bodily fluid.
  • an oxidized mediator is disposed on a working electrode with the intent that the oxidized mediator will be stable and not transition over to the reduced redox state.
  • the generation of reduced mediator causes the background signal to increase for electrochemical sensors which use an oxidation current to correlate with the glucose concentration.
  • ferricyanide e.g. oxidized mediator
  • Ferricyanide tends to become reduced over time to the reduced redox state.
  • Ferricyanide generally transitions to the reduced redox state more rapidly when exposed to environmental conditions which include but are not limited to, basic pH, elevated temperature, elevated humidity, bright light conditions, electron beam radiation, and gamma radiation.
  • a lance and a test strip have been integrated into a single medical device. These integrated medical devices can be employed, along with an associated meter, to monitor various analytes, including glucose. Depending on the situation, test strips can be designed to monitor analytes in an episodic single-use format, semi-continuous format, or continuous format.
  • the integration of the lance and the test strip simplifies a monitoring procedure by eliminating the need for a user to coordinate the extraction of a bodily fluid from a sample site with the subsequent transfer of that bodily fluid to the test strip. In such a case, the lance and test strip must be sterilized together so as to mitigate the risk of infection.
  • Ionizing radiation may be used to sterilize test strips with a lance.
  • Possible sources of ionizing radiation are electron beam, gamma, and x-ray.
  • one of the challenges in sterilizing a test strip is to provide a sufficiently high intensity of radiation such that a sufficiently high proportion of microorganisms are neutralized for an entire package of test strips, while at the same time not adversely affecting the reagent layer.
  • a batch or package of test strips are exposed to an ionizing radiation dose ranging from about 10 KGy to about 50 KGy.
  • the energy of the incident e-beam source can range from about 3 MeV to about 12 MeV.
  • the impingent ionizing radiation may often have some non-uniformities in its intensity causing a particular portion of the package to receive more ionizing radiation than another portion of the package.
  • both gamma radiation and electron beam radiation cause the background signal of the electrochemical sensors to increase.
  • the relatively non-uniform nature of the radiation causes the background signal to increase in a non-uniform nature for a sterilized batch of test strips. This causes the precision to decrease when testing a particular batch of sterilized glucose test strips.
  • the decrease in precision is exacerbated at the low glucose concentration range (e.g. about 20 mg/dL to about 100 mg/dL) because the proportion of reduced mediator is relatively high with respect to the low glucose concentration range.
  • FIG. 1 shows an exploded perspective view of a test strip 800 that is designed to compensate for the variations in increased background potentially caused by the conversion of oxidized mediator to reduced mediator.
  • an electrochemical test strip 800 which may be used for measuring glucose concentration in bodily fluids such as blood or interstitial fluid, includes a first working electrode 808 , a second working electrode 806 , and a reference electrode 810 .
  • An active reagent layer 820 is disposed on first working electrode 808 and reference electrode 810 where active reagent layer 820 completely covers first working electrode 808 and at least partially covers reference electrode 810 .
  • An inactive reagent layer 818 is disposed on second working electrode 806 .
  • active reagent layer 820 may include, for example, glucose oxidase and a mediator such as, for example, ferricyanide.
  • Inactive reagent layer 818 may include a mediator, but no active enzymes which are specific for the analyte of interest. Because ferricyanide has a redox potential of approximately 400 mV (when measured with respect to a saturated calomel electrode) at a carbon electrode, the introduction of a bodily fluid e.g., blood may generate a significant and undesirable oxidation of interferents by the mediator and/or the working electrode.
  • the oxidation current measured at first working electrode 808 will be a superposition of oxidation current sources: a first, desirable, oxidation current generated by the oxidation of glucose; a second, undesirable, direct oxidation of interferents at the electrode (direct interference current); and a third, undesirable, indirect oxidation of interferents via a mediator (mediated interference current).
  • the oxidation current measured at second working electrode 806 will also be a superposition of oxidation current sources similar to first working electrode 808 , but the first, desirable, oxidation current should not occur because there is no enzyme present on second working electrode 806 .
  • the oxidation current measured at second working electrode 806 depends only on interferents, and the oxidation current measured at first working electrode 808 depends on glucose and interferents, it is possible to calculate a corrected glucose current which is independent to the effects of interfering compounds oxidized at first working electrode 808 and second working electrode 806 .
  • the interferent oxidation current density at second working electrode 806 may be slightly different than the interferent oxidation current density at first working electrode 808 because there is no enzyme on second working electrode 806 .
  • Test strip 800 includes a substrate 50 , a conductive layer 802 , an insulation layer 804 , inactive reagent layer 818 , active reagent layer 820 , an adhesive layer 830 , and a top layer 824 .
  • Test strip 800 may be manufactured by sequentially printing five layers which are conductive layer 802 , insulation layer 804 , inactive reagent layer 818 , active reagent layer 820 , and adhesive layer 830 onto substrate 50 .
  • Top layer 824 may be assembled by a lamination process.
  • Test strip 800 further includes a first side 54 , a second side 56 , a distal portion 58 , and a proximal portion 60 .
  • substrate 50 is an electrically insulating material such as plastic, glass, ceramic, and the like.
  • substrate 50 may be a plastic such as, for example, nylon, polycarbonate, polyimide, polyvinylchloride, polyethylene, polypropylene, PETG, or polyester. More particularly the polyester may be, for example Melinex® ST328 which is manufactured by DuPont Teijin Films.
  • Substrate 50 may also include an acrylic coating which is applied to one or both sides to improve ink adhesion.
  • the first layer deposited on substrate 50 is conductive layer 802 which includes first working electrode 808 , second working electrode 806 , reference electrode 810 , and strip detection bar 17 .
  • a screen mesh with an emulsion pattern may be used to deposit a material such as, for example, a conductive carbon ink in a defined geometry as illustrated in FIG. 1 .
  • Conductive layer 802 may be disposed on substrate 50 by using screen printing, rotogravure printing, sputtering, evaporation, electroless plating, ink jetting, sublimation, chemical vapor deposition, and the like.
  • Suitable materials which may be used for conductive layer 802 are Au, Pd, Ir, Pt, Rh, stainless steel, doped tin oxide, carbon, and the like.
  • the carbon ink layer may have a height between 1 and 100 microns, more particularly between 5 and 25 microns, and yet even more particularly at approximately 13 microns.
  • the height of conductive layer 802 can vary depending on the desired resistance and conductivity of the printed material.
  • a first contact 814 , a second contact 812 , and a reference contact 816 may be used to electrically interface with a meter. This allows the meter to electrically communicate to first working electrode 808 , second working electrode 806 , and reference electrode 810 via, respective, first contact 814 , second contact 812 , and reference contact 816 .
  • the second layer deposited on substrate 50 is insulation layer 804 .
  • Insulation layer 804 is disposed on at least a portion of conductive layer 802 as shown in FIGS. 1 and 2 .
  • FIG. 2 is a simplified plane view of distal portion 58 of test strip 800 which highlights the position of first working electrode 808 , second working electrode 806 , and reference electrode 810 with respect to insulation layer 804 .
  • Insulation layer 804 further includes a cutout 18 which may have a rectangular shaped structure as shown in FIG. 1 and 2 . Cutout 18 exposes a portions of first working electrode 808 , second working electrode 806 , and reference electrode 810 which can be wetted with liquid. Cutout 18 includes a cutout width W 20 and a cutout length L 26 .
  • Cutout width W 20 corresponds to a width of second working electrode 806 , reference electrode 810 , and first working electrode 808 as illustrated in FIG. 2 .
  • cutout width W 20 may range from about 0.7 mm to about 1.4 mm
  • cutout length L 26 may range from about 0.4 mm and about 3.4 mm.
  • second working electrode 806 and first working electrode 808 have a respective length of L 20 and L 21 which may be the same and range from about 0.1 mm to about 0.8 mm.
  • Reference electrode 810 may have a length L 24 which may range from about 0.2 mm to about 1.6 mm.
  • electrode spacing S 1 is a distance between second working electrode 806 and reference electrode 810 ; and between reference electrode 810 and first working electrode 808 which may range from about 0.2 mm to about 0.6 mm.
  • an area of first working electrode 808 may be different than an area of second working electrode 806 .
  • a ratio of first working electrode 808 area:second working electrode 806 area may range from about 1:1 to about 1:3. Under certain situations, the reduction in background can be improved by increasing the relative area of second working electrode 806 .
  • the area of second working electrode 806 may be increased by modifying the geometry of a cutout 6008 as shown in FIG. 20 .
  • FIG. 2 shows that strip 800 may be cut along incision line A-A′ after it is fully laminated as illustrated in FIG. 1 .
  • a sample inlet 52 is created in which a liquid sample can be applied for dosing test strip 800 .
  • FIGS. 3 to 5 are a simplified plane view of distal portion 58 of test strip 800 according to the embodiment of the present invention illustrated in FIG. 1 , which show various positions of active reagent layer 820 and inactive reagent layer 818 with respect to each other.
  • FIGS. 6 to 8 which correspond to FIGS. 3 to 5 respectively, do not show insulation layer 804 to help demonstrate more clearly the relationship between the conductive layer 802 , active reagent layer 820 , and inactive reagent layer 818 .
  • Test strip 800 may have inactive reagent layer 818 disposed on second working electrode 806 such that it completely covers second working electrode 806 as is illustrated in FIGS. 3 to 5 .
  • inactive reagent layer 818 completely covers second working electrode 806 , but does not touch reference electrode 810 as is illustrated in FIGS. 3 and 4 .
  • inactive reagent layer 818 completely covers second working electrode 806 and at least partially covers reference electrode 810 as is illustrated in FIG. 5 .
  • inactive reagent layer 818 includes at least an oxidized mediator, such as ferricyanide, and may optionally include an inert protein or inactivated enzyme.
  • Inactive reagent layer 818 may further include a citrate buffer at pH 6, a polyvinyl alcohol, a polyvinyl pyrrolidone-vinyl acetate, a Dow Corning DC1500 antifoam, a hydroxyethyl cellulose (Natrosol 250G, Hercules), and a surface modified silica (Cab-o-sil TS 610, Cabot) having both hydrophilic and hydrophobic domains.
  • oxidized mediators may be ferricyanide, ferricinium complexes, quinone complexes, and osmium complexes.
  • inert protein may be crotein or albumin (e.g. bovine or human).
  • inactivated enzyme may be the apo form of PQQ-glucose dehydrogenase (where PQQ is an acronym for pyrrolo-quinoline-quinone) or apo glucose oxidase (e.g. enzyme with no active site). Enzyme may also be deactivated or sufficiently attenuated by heat treatment or by treatment with denaturing agents such as urea. Because inactive reagent layer 818 does not include an active enzyme, the oxidation current measured at second working electrode 806 is not proportional to the glucose concentration. For this reason, one skilled in the art may refer to second working electrode 806 as a dummy electrode.
  • the inert protein or deactivated enzyme in inactive reagent layer 818 may act as a stabilizer for the mediator.
  • the inert protein or deactivated enzyme may shield the mediator during the drying process at elevated temperature.
  • the inert protein or deactivated enzyme may act as a desiccant which helps protect the mediator from moisture that may potentially destabilize the mediator.
  • Test strip 800 has active reagent layer 820 disposed on first working electrode 808 as illustrated in FIGS. 3 to 5 .
  • active reagent layer 820 completely covers first working electrode 808 , but does not touch reference electrode 810 .
  • active reagent layer 820 completely covers first working electrode 808 and at least partially covers reference electrode 810 as illustrated in FIGS. 3 to 5 .
  • active reagent layer 820 includes at least an oxidized mediator, and an enzyme.
  • Active reagent layer 820 may further include a citrate buffer at pH 6, a polyvinyl alcohol, a polyvinyl pyrrolidone-vinyl acetate, a Dow Corning DC1500 antifoam, a hydroxyethyl cellulose (Natrosol 250G, Hercules), and a surface modified silica (Cab-o-sil TS 610, Cabot) having both hydrophilic and hydrophobic domains.
  • oxidized mediators may be ferricyanide, ferricinium complexes quinone complexes, and osmium complexes.
  • Examples of the enzyme may be glucose oxidase, glucose dehydrogenase using a PQQ co-factor, and glucose dehydrogenase using a nicotinamide adenine dinucleotide co-factor. Because active reagent layer 820 does include the enzyme, the oxidation current measured at first working electrode 808 is proportional to the glucose concentration.
  • FIG. 3 shows an embodiment of this invention which has inactive reagent layer 818 disposed on second working electrode 806 , and active reagent layer 820 disposed on first working electrode 808 and reference electrode 810 .
  • inactive reagent layer 818 does not touch or overlap with active reagent layer 820 .
  • second working electrode 806 , first working electrode 808 and reference electrode 810 is relatively small, it can be difficult to sequentially align and coat inactive reagent layer 818 and active reagent layer 820 , respectively, with the desired yield. It should also be noted that relatively small electrode areas (e.g. about 0.6 mm 2 ) are preferred because this allows the volume of liquid sample required for a test strip to be small.
  • inactive reagent layer 818 is printed first and then dried at an elevated temperature. Active reagent layer 820 is then subsequently printed followed by another drying step at an elevated temperature as described in International Application serial number PCT/GB/03004708 which is hereby incorporated by reference herein. Because active reagent layer 820 is deposited second, it is exposed to only one drying step as opposed to the two drying steps for inactive reagent layer 818 . This helps stabilize both mediator and enzyme within active reagent layer 820 because under certain conditions enzymes can degrade with continued exposure to elevated temperatures.
  • FIG. 4 shows inactive reagent layer 818 disposed on second working electrode 806 , and active reagent layer 820 disposed on first working electrode 808 and reference electrode 810 .
  • inactive reagent layer 818 and active reagent layer 820 are immediately adjacent to each other.
  • the inactive reagent layer 818 and active reagent layer 820 would touch, but typically not overlap with each other to any significant extent.
  • the printing process targets the alignment such that inactive reagent layer 818 and active reagent layer 820 are immediately adjacent to each other, normal manufacturing variation will cause some overlap to occur with a certain frequency between inactive reagent layer 818 and active reagent layer 820 .
  • inactive reagent layer 818 will also cause inactive reagent layer 818 to sometimes not touch active reagent layer 820 . Because inactive reagent layer 818 was allowed to touch or not touch active reagent layer 820 and the operation of the method of the invention still works to reduce the variation in the background in either circumstance, the yield of acceptable test strips was improved.
  • inactive reagent layer 818 does not affect the glucose measurement as long as the enzyme from active reagent layer 820 cannot diffuse, to any significant extent in the time allowed for the measurement (i.e. about 5 seconds or less), to second working electrode 806 . If enzyme were to diffuse to second working electrode 806 , then first working electrode 808 would measure a glucose current in addition to the non-enzyme specific currents. This would prevent test strip 800 from effectively reducing the background signal.
  • inactive reagent layer 818 with active reagent layer 820 were to occur on reference electrode 810 that this would not affect the glucose measurement. In such a case, the amount of enzyme and/or oxidized mediator on reference electrode 810 will increase, but should not affect the glucose measurement or the background correction algorithm.
  • inactive reagent layer 818 may be coated such that it completely covers second working electrode 806 and a portion of reference electrode 810 .
  • active reagent layer 820 may be coated such that it completely covers first working electrode 808 and at least a portion of reference electrode 810 .
  • the printing process can target the alignment such that inactive reagent layer 818 and active reagent layer 820 substantially overlap with each other on reference electrode 810 at an overlap zone 822 . In such a case, inactive reagent layer 818 and active reagent layer 820 may mix with each other at overlap zone 822 .
  • second working electrode 806 (e.g. dummy electrode) is located on distal portion 58 of test strip 800 as illustrated in FIGS. 1 to 5 .
  • This causes the physiological fluid to sequentially wet in the following order—second working electrode 806 , reference electrode 810 , and then first working electrode 808 .
  • Test strip 800 was purposefully designed to have inactive reagent layer 818 (which contains no enzyme) upstream of active reagent layer 820 (which does contain enzyme). This reduces the possibility of enzyme being present at both second working electrode 806 and first working electrode 808 .
  • active reagent layer 820 which contains enzyme, was coated over second working electrode 806 , and no enzyme were present over first working electrode 808 then it would be possible that some enzyme could be swept to first working electrode 808 from second working electrode 806 . The presence of a significant amount of enzyme on first working electrode 808 would prevent the background signal from being reduced through the use of the dummy electrode format.
  • top layer 824 may be in the form of an integrated lance 826 as shown in FIG. 1 .
  • top layer 824 may include a lance 826 which is located at distal portion 58 .
  • Lance 826 which may also be referred to as a penetration member, may be adapted to pierce a user's skin and draw blood into test strip 800 such that second working electrode 806 , first working electrode 808 , and reference electrode 810 are wetted.
  • Top layer 824 is adhered to test strip 800 by adhesive layer 830 .
  • This adhesive layer 830 can be a heat seal or a pressure sensitive adhesive.
  • Lance 826 includes a lancet base 832 that terminates at distal portion 58 of assembled test strip 800 .
  • Lance 826 may be made with either an insulating material such as plastic, glass, and silicon, or a conducting material such as stainless steel and gold.
  • top layer 824 may also be used as a reference electrode 810 which is orientated with a facing relationship to second working electrode 806 and first working electrode 808 .
  • Further descriptions of integrated medical devices that use an integrated lance can be found in International Application No. PCT/GB01/05634 and U.S. patent application Ser. No. 10/143,399 which are hereby fully incorporated by reference herein.
  • lance 826 can be fabricated, for example, by a progressive die-stamping technique, as disclosed in the aforementioned International Application No. PCT/GB01/05634 and U.S. patent application Ser. No. 10/143,399 which are hereby fully incorporated by reference herein.
  • adhesive layer 830 has a height of about 70 to 110 microns.
  • Adhesive layer 830 may include a double sided pressure sensitive adhesive, a UV cured adhesive, heat activated adhesive, thermosetting plastic, or other adhesive known to those skilled in the art.
  • adhesive layer 830 may be formed by screen printing a pressure sensitive adhesive such as, for example, a water based acrylic copolymer pressure sensitive adhesive which is commercially available from Tape Specialties LTD in Tring, Herts, United Kingdom (part#A6435).
  • the background variations are reduced by subtracting a first current from first working electrode 808 from a second current from second working electrode 806 .
  • a sample is applied to sample inlet 52 which allows a current to be measured at second working electrode 806 and first working electrode 808 .
  • second working electrode 806 does not have a glucose oxidizing enzyme disposed thereon, a magnitude of an oxidation current at second working electrode 806 is proportional to an amount of interfering compounds present on test strip 800 and also an amount of interfering compounds originating from the sample. This allows a corrected current value to be calculated using a difference between first working electrode 808 and second working electrode 806 to reduce the effects of interfering compounds present in the sample and also for interfering compounds that may be present on test strip 800 .
  • FIG. 9 is a simplified schematic showing a meter 900 interfacing with test strip 800 .
  • Meter 900 has at least three electrical contacts that form an electrical connection to second working electrode 806 , first working electrode 808 , and reference electrode 810 .
  • second contact 812 and reference contact 816 connect to first voltage source 910 ;
  • first contact 814 and reference contact 816 connect to second voltage source 920 .
  • first voltage source 910 applies a first potential E 1 between second working electrode 806 and reference electrode 810 ; and second voltage source 920 applies a second potential E 2 between first working electrode 808 and reference electrode 810 .
  • first potential E 1 and second potential E 2 may be the same such as for example about +0.4 V. In another embodiment of this invention, first potential E 1 and second potential E 2 may be different.
  • a sample of blood is applied such that second working electrode 806 , first working electrode 808 , and reference electrode 810 are covered with blood. This allows second working electrode 806 and first working electrode 808 to measure a current which is proportional to glucose and/or non-enzyme specific sources.
  • meter 900 measures an oxidation current for both second working electrode 806 and first working electrode 808 .
  • FIG. 10 is a simplified schematic showing a meter 900 interfacing with test strip 800 .
  • top layer 824 is conductive and used as a reference electrode instead of reference electrode 810 which is disposed on substrate 50 . More particularly, FIG. 10 shows that top layer 824 , in the form of a reference electrode, has a facing relationship with first working electrode 808 and second working electrode 806 . In this case, meter 900 forms an electrical contact to top layer 824 instead of at reference contact 816 as is shown in FIG. 1 .
  • FIG. 21 is an exploded perspective view of a test strip 1000 according to another embodiment of the present invention.
  • the oxidation current measured at a first working electrode 100 will be a superposition of oxidation current sources: a first, desirable, oxidation current generated by the oxidation of glucose and a second, undesirable, oxidation current generated by the interferents.
  • the oxidation of interferents may occur directly at first working electrode 100 and indirectly through a mediated mechanism via a mediator.
  • Second working electrode 102 has a geometric trace that has an active portion 102 a which is coated with active reagent 820 and an inactive portion 102 i which is coated with inactive reagent 818 as illustrated in FIGS. 22 to 27 .
  • the oxidation current sources measured at active portion 102 a will be similar to first working electrode 100 .
  • Inactive portion 102 i of second working electrode 102 will oxidize interferents and not oxidize glucose because there is no enzyme present. Further, inactive portion 102 i will oxidize interferents directly at second working electrode 102 and indirectly through a mediated mechanism via a mediator.
  • the oxidation current measured at inactive portion 102 i does not depend on glucose and the area of inactive portion 102 i is known, it is possible to calculate its contribution to the interferent oxidation current measured at second working electrode 102 . In turn, using the interferent oxidation current calculated for inactive portion 102 i and knowing the area of first working electrode 100 and the area of active portion 102 a, it is possible to calculate a corrected glucose current which accounts for the effects of interfering compounds oxidized at the electrode. It should be noted that in the present invention, inactive portion 102 i helps correct the glucose current for direct and mediated interference oxidation. It should also be noted that inactive portion 102 i and active portion 102 a may sometimes by referred to as an inactive region and an active region, respectively.
  • An algorithm may, therefore be used to calculate a corrected glucose current that is independent of interferences.
  • a constant potential is applied to first working electrode 100 and second working electrode 102 and a current is measured for both electrodes.
  • WE 2 G+I 2a +I 2i (Eq 2) where WE 2 is a current density at the second working electrode, I 2a is a current density due to interferences at the active portion 102 a, and I 2i is a current density due to interferences at inactive portion 102 i.
  • Inactive portion 102 i can oxidize interferents, but not glucose because it is not coated with enzyme. Active portion 102 a can oxidize glucose and interferents. Because it was experimentally found that inactive portion 102 i oxidizes interferents in a manner proportional to the area of active portion 102 a, it is possible to predict the proportion of interferent current measured overall at second working electrode 102 . This allows the overall current measured at second working electrode 102 (i.e. WE 2 ) to be corrected by subtracting the contribution of the interferent current. In an embodiment of the present invention the ratio of A 2i :A 2a may be between about 0.5:1 to 5:1, and is preferably about 3:1. More details describing this mathematical algorithm for current correction will be described in the subsequent sections.
  • Equation 1, 2, and 3a may be manipulated to derive an equation that outputs a corrected glucose current density independent of interferences.
  • the three equations (Equation 1, 2, and 3a) collectively have 4 unknowns which are G, I 2i , I 2a , and I 1a .
  • I 1a and I 2a can be conservatively assumed to be equal because they are measured at the same conductive material and coated with the same active reagent layer 820 .
  • Equation 1 can be rearranged to the following form.
  • I 2a from Equation 3a can be substituted into Equation 4 to yield Equation 5.
  • Equation 1 and Equation 2 can be combined to yield Equation 6.
  • I 2i WE 2 ⁇ WE 1 (Eq 6)
  • I 2i from Equation 6 can be substituted into Equation 5 to yield Equation 7a.
  • G WE 1 - ⁇ ( A 2 ⁇ a A 2 ⁇ i ) ⁇ X ⁇ ( WE 2 - WE 1 ) ⁇ ( Eq ⁇ ⁇ 7 ⁇ a )
  • Equation 7a outputs a corrected glucose current density G which removes the effects of interferences requiring only the measured current density from first working electrode 100 and second working electrode 102 (i.e. WE 1 and WE 2 ), and a proportion of an area of the second working electrode covered with active reagent to an area of the second working electrode covered with inactive reagent ( i . e ⁇ ⁇ A 2 ⁇ a A 2 ⁇ i ) .
  • the proportion ⁇ A 2 ⁇ a A 2 ⁇ i may be programmed into a glucose meter, in, for example, a read only memory.
  • the proportion ⁇ A 2 ⁇ a A 2 ⁇ i may be transferred to the meter via a calibration code chip which would may account for manufacturing variations in A 2a or A 2i .
  • Equation 1 Equation 1 + Equation 7b
  • the corrected glucose current Equation 7a or 7b may be used by the meter only when a certain threshold is exceeded. For example, if WE 2 is about 10% or greater than WE 1 , then the meter would use Equation 7a or 7b to correct for the current output. However, if WE 2 is about 10% or less than WE 1 , the meter would simple take an average current value between WE 1 and WE 2 to improve the accuracy and precision of the measurement. The strategy of using Equation 7a or 7b only under certain situations where it is likely that a significant level of interferences are in the sample mitigates the risk of overcorrecting the measured glucose current. It should be noted that when WE 2 is sufficiently greater than WE 1 (e.g.
  • this is an indicator of having a sufficiently high concentration of interferents.
  • FIG. 21 shows an exploded perspective view of a test strip embodiment that is designed to compensate for variations in increased background caused by the conversion of oxidized mediator to reduced mediator.
  • Test strip 1000 includes a substrate 50 , a conductive layer 164 , an insulation layer 106 , an inactive reagent layer 818 , an active reagent layer 820 , an adhesive layer 830 , and a top layer 824 .
  • Test strip 1000 further includes a distal end 58 and a proximal end 60 . It should be noted that test strip 1000 is a modification of test strip 800 so that an active reagent coating 820 covers a portion of both a first working electrode 100 and a second working electrode 102 .
  • Test strip 1000 would employ either Equation 7a or 7b for reducing the effect of interfering compounds or increased background.
  • test strip 1000 has a modification to conductive layer 164 and insulation layer 106 .
  • Substrate 50 , inactive reagent layer 818 , active reagent layer 820 , adhesive layer 830 and top layer 824 are similar in both shape and material for both test strip 1000 and test strip 800 .
  • FIGS. 22 to 24 are a simplified plane view of distal portion 58 of test strip 1000 , according to the embodiment of the present invention illustrated in FIG. 21 , which show various positions of active reagent layer 820 and inactive reagent layer 818 with respect to each other.
  • FIGS. 25 to 27 which correspond to FIGS. 22 to 24 respectively, do not show insulation layer 804 to help demonstrate more clearly the relationship between the conductive layer 164 , active reagent layer 820 , and inactive reagent layer 818 .
  • Conductive layer 164 is disposed on substrate 50 .
  • Conductive layer 164 includes a first working electrode 100 , a second working electrode 102 , a reference electrode 104 , a first contact 101 , a second contact 103 , a reference contact 105 , a strip detection bar 17 , as shown in FIG. 21 .
  • second working electrode 806 and first working electrode 102 has a C-shape.
  • FIG. 22 is a simplified plane view of first working electrode 100 , second working electrode 102 , and reference electrode 104 , insulation layer 106 , inactive reagent layer 818 , and active reagent layer 820 .
  • Insulation layer 106 includes a cutout 108 which defines the area of second working electrode 102 to have an inactive portion 102 i and an active portion 102 a.
  • inactive reagent layer 818 was disposed on inactive portion 102 i and active reagent layer 820 was disposed on active portion 102 a, first working electrode 100 , and reference electrode 104 .
  • FIG. 22 shows that inactive reagent layer 818 does not touch or overlap with active reagent layer 820 .
  • Test strip 1000 differs from test strip 800 in that both inactive reagent layer 818 and active reagent layer 820 both coat a portion of second working electrode 102 . This allows two glucose measurements to be performed while at the same time reduce the effects of background and/or interferences.
  • One of the challenges with making test strip 1000 as shown in FIG. 22 is that it can be difficult to sequentially align and coat the respective inactive reagent layer 818 and active reagent layer 820 so that they do not touch each other with the desired yield because the area of first working electrode 100 , second working electrode 102 and reference electrode 104 is relatively small.
  • FIG. 23 shows inactive reagent layer 818 disposed on inactive portion 102 i, and active reagent layer 820 disposed on active portion 102 a, first working electrode 100 , and reference electrode 104 .
  • inactive reagent layer 818 and active reagent layer 820 are immediately adjacent to each other.
  • the inactive reagent layer 818 and active reagent layer 820 would touch, but not substantially overlap with each other.
  • the printing process targets the alignment such that inactive reagent layer 818 and active reagent layer 820 are immediately adjacent to each other, normal manufacturing variation will cause some overlap to occur with a certain frequency between inactive reagent layer 818 and active reagent layer 820 .
  • inactive reagent layer 818 will also cause inactive reagent layer 818 to not touch active reagent layer 820 at a certain frequency. Because inactive reagent layer 818 was allowed to touch or not touch active reagent layer 820 , the yield of acceptable test strips was improved.
  • FIG. 24 Yet another embodiment of this invention which improves upon the method of coating inactive reagent layer 818 and active reagent layer 820 is shown in FIG. 24 .
  • Inactive reagent layer 818 may be coated such that it completely covers inactive portion 102 i and a portion of reference electrode 104 .
  • active reagent layer 820 may be coated such that it completely covers active portion 102 a, first working electrode 100 and at least a portion of reference electrode 104 .
  • the printing process can target the alignment such that inactive reagent layer 818 and active reagent layer 820 substantially overlap with each other on reference electrode 810 at an overlap zone 822 .
  • inactive reagent layer 818 and active reagent layer 820 may mix with each other at overlap zone 822 . Because the length of both inactive reagent layer 818 and active reagent layer 820 was further increased compared to the embodiment described in FIG. 23 , the alignment and coating of active reagent layer 820 and inactive reagent layer 818 was yet further improved in terms of manufacturing yield.
  • Test strips 800 were prepared as illustrated in FIGS. 1 to 3 a. Test strips 800 were tested in blood which were exposed to varying levels of sterilizing radiation. To test strips 800 , they were electrically connected to a potentiostat which has the means to apply a constant potential of +0.4 volts between first working electrode 808 and reference electrode 810 ; and second working electrode 806 and the reference electrode 810 . A sample of blood is applied to sample inlet 52 allowing the blood to wick into the sample receiving chamber and to wet first working electrode 808 , reference electrode 810 , and second working electrode 806 . Active layer 820 becomes hydrated with blood and then generates ferrocyanide which may be proportional to the amount of glucose and/or interferent concentration present in the sample.
  • inactive layer 818 becomes hydrated with blood and does not generate additional ferrocyanide that was not present within inactive layer 818 before hydration.
  • an oxidation of ferrocyanide and/or interferences are measured as a current for both first working electrode 808 and second working electrode 806 .
  • test strips Two batches of test strips were prepared to show that the use of inactive reagent layer 818 and active reagent layer 820 improved the overall precision for test strips sterilized by gamma radiation. Both batches of test strips were tested in a similar manner as described in Example 1.
  • the first test strip batch is test strip 800 and is referred to as Batch 1 .
  • the second test strip batch which is referred to as Batch 2 , is also similar to test strip 800 , but does not include inactive reagent layer 818 and also has a modified active reagent layer which covers both first working electrode 808 , second working electrode 806 , and reference electrode 810 .
  • test cases which are Batch 1 —0 kGy, Batch 1 —25 kGy, Batch 2 —0 kGy, and Batch 2 —25 kGy, were evaluated for precision by testing 24 test strips with blood for each test case at 5 glucose concentrations which was 20, 50, 100, 300, and 500 mg/dL.
  • FIGS. 11 to 15 show that Batch 1 test strips did not suffer from a degradation in precision after being sterilized with 25 kGy of gamma radiation. For all five glucose concentrations, the precision was substantially similar or better after sterilization for Batch 1 test strips. This shows that the use of active reagent layer 820 and inactive reagent layer 818 helps compensate for background levels of ferrocyanide produced during the sterilization process.
  • FIGS. 11 to 13 show that Batch 2 test strips did suffer from a degradation in precision after being sterilized with 25 kGy of gamma radiation.
  • This control experiment verifies that there is a degradation in precision when not using the background reduction method of the present invention.
  • Batch 2 test strip did not have inactive reagent layer 818 , the background reduction method could not be implemented.
  • Batch 2 test strips did not suffer from a degradation in precision after being sterilized because relatively high glucose concentrations were tested (300 and 500 mg/dL) in which the effect of sterilization on precision is not as significant. In this case, the amount of ferrocyanide generated by glucose oxidase is significantly higher than ferrocyanide generated (e.g. by sterilization processes) before hydrating the test strip.
  • Batch 3 Another batch of test strips, which is referred to as Batch 3 , was prepared in a manner similar to test strip 800 except that second working electrode 806 was not coated with either active reagent layer 820 or inactive reagent layer 818 .
  • Batches 1 to 3 were tested to evaluate the overall accuracy in the presence of interfering compounds such as uric acid and gentisic acid.
  • Batch 1 , Batch 2 , and Batch 3 test strips were tested in blood at three concentrations of gentisic acid which were 0, 25, and 50 mg/dL. For each gentisic acid concentration, two glucose concentrations were tested which were 70 and 240 mg/dL.
  • FIGS. 16 and 17 show that Batch 1 and Batch 3 test strips had an insignificant change ( ⁇ 10 mg/dL or 10%) in bias when testing them at 25 and 50 mg/dL gentisic acid concentration.
  • Batch 2 test strips had a significant change (>10 mg/dL or 10%) in bias when testing them at a 25 and a 50 mg/dL gentisic acid concentration. This shows that the use of second working electrode 806 not coated with enzyme allows for an effective correction of the glucose signal in the presence of high concentrations of gentisic acid.
  • Batch 1 , Batch 2 , and Batch 3 test strips were tested in blood at three concentrations of uric acid which were 0, 10, and 20 mg/dL. For each uric acid concentration, two glucose concentrations were tested which were 70 and 240 mg/dL.
  • FIGS. 18 and 19 show that Batch 1 and Batch 3 test strips had an insignificant change ( ⁇ 10 mg/dL or 10%) in bias when testing them at 10 and 20 mg/dL uric acid concentration.
  • Batch 2 test strips had a significant change (>10 mg/dL or 10%) in bias when testing them at a 10 and a 20 mg/dL uric acid concentration. This shows that the use of second working electrode 806 not coated with enzyme allows for an effective correction of the glucose signal in the presence of high concentrations of uric acid.

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Cited By (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050109618A1 (en) * 2003-10-31 2005-05-26 Davies Oliver W.H. Meter for use in an improved method of reducing interferences in an electrochemical sensor using two different applied potentials
US20050183965A1 (en) * 2003-10-31 2005-08-25 Davies Oliver William H. Method of reducing interferences in an electrochemical sensor using two different applied potentials
US20070111196A1 (en) * 2005-08-19 2007-05-17 Javier Alarcon Sterilization of Biosensors
WO2008050145A1 (en) * 2006-10-27 2008-05-02 Suresensors Ltd Measurement device
USD611151S1 (en) 2008-06-10 2010-03-02 Lifescan Scotland, Ltd. Test meter
USD611372S1 (en) 2008-09-19 2010-03-09 Lifescan Scotland Limited Analyte test meter
USD612274S1 (en) 2008-01-18 2010-03-23 Lifescan Scotland, Ltd. User interface in an analyte meter
US20100327886A1 (en) * 2008-03-27 2010-12-30 Toshifumi Nakamura Measurement device, measurement system, and concentration measurement method
US20110144915A1 (en) * 2009-12-11 2011-06-16 Lifescan Scotland Ltd. Fill sufficiency method and system
US20110192721A1 (en) * 2006-05-04 2011-08-11 Nipro Diagnostics, Inc. System and methods for automatically recognizing a control solution
US20120048746A1 (en) * 2010-08-30 2012-03-01 Cilag Gmbh International Analyte test strip with electrically distinguishable divided electrode
US20130112573A1 (en) * 2010-05-07 2013-05-09 Exacsys Limited Devices and methods for testing analytes
US8917184B2 (en) 2008-03-21 2014-12-23 Lifescan Scotland Limited Analyte testing method and system
US9034250B2 (en) 2005-03-02 2015-05-19 Roche Diagnostics Operations, Inc. Dynamic integrated lancing test strip with sterility cover
CN109270145A (zh) * 2018-11-20 2019-01-25 三诺生物传感股份有限公司 一种双电极的电化学试条的测试方法
AU2020210301B2 (en) * 2019-08-02 2021-12-16 Bionime Corporation Micro Biosensor and Method for Reducing Measurement Interference Using the Same
DE102022107214B4 (de) 2022-03-28 2024-07-18 Senslab - Gesellschaft Zur Entwicklung Und Herstellung Bioelektrochemischer Sensoren Mbh Verfahren und Sensor zur Bestimmung einer plasmabezogenen Analytkonzentration in Vollblut

Families Citing this family (230)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP3394262B2 (ja) 1997-02-06 2003-04-07 セラセンス、インク． 小体積インビトロ被検体センサー
US6862465B2 (en) 1997-03-04 2005-03-01 Dexcom, Inc. Device and method for determining analyte levels
US7899511B2 (en) 2004-07-13 2011-03-01 Dexcom, Inc. Low oxygen in vivo analyte sensor
US8527026B2 (en) 1997-03-04 2013-09-03 Dexcom, Inc. Device and method for determining analyte levels
US6001067A (en) 1997-03-04 1999-12-14 Shults; Mark C. Device and method for determining analyte levels
US9155496B2 (en) 1997-03-04 2015-10-13 Dexcom, Inc. Low oxygen in vivo analyte sensor
US6036924A (en) 1997-12-04 2000-03-14 Hewlett-Packard Company Cassette of lancet cartridges for sampling blood
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
US8465425B2 (en) 1998-04-30 2013-06-18 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8346337B2 (en) 1998-04-30 2013-01-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8688188B2 (en) 1998-04-30 2014-04-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8480580B2 (en) 1998-04-30 2013-07-09 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US6175752B1 (en) 1998-04-30 2001-01-16 Therasense, Inc. Analyte monitoring device and methods of use
US9066695B2 (en) 1998-04-30 2015-06-30 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8974386B2 (en) 1998-04-30 2015-03-10 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US6949816B2 (en) 2003-04-21 2005-09-27 Motorola, Inc. Semiconductor component having first surface area for electrically coupling to a semiconductor chip and second surface area for electrically coupling to a substrate, and method of manufacturing same
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
US6560471B1 (en) 2001-01-02 2003-05-06 Therasense, Inc. Analyte monitoring device and methods of use
US7310543B2 (en) * 2001-03-26 2007-12-18 Kumetrix, Inc. Silicon microprobe with integrated biosensor
JP4209767B2 (ja) 2001-06-12 2009-01-14 ペリカン テクノロジーズ インコーポレイテッド 皮膚の性状の一時的変化に対する適応手段を備えた自動最適化形切開器具
AU2002344825A1 (en) 2001-06-12 2002-12-23 Pelikan Technologies, Inc. Method and apparatus for improving success rate of blood yield from a fingerstick
AU2002348683A1 (en) 2001-06-12 2002-12-23 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
US9226699B2 (en) 2002-04-19 2016-01-05 Sanofi-Aventis Deutschland Gmbh Body fluid sampling module with a continuous compression tissue interface surface
US7981056B2 (en) 2002-04-19 2011-07-19 Pelikan Technologies, Inc. Methods and apparatus for lancet actuation
DE60234597D1 (de) 2001-06-12 2010-01-14 Pelikan Technologies Inc Gerät und verfahren zur entnahme von blutproben
DE60238119D1 (de) 2001-06-12 2010-12-09 Pelikan Technologies Inc Elektrisches betätigungselement für eine lanzette
US7041068B2 (en) 2001-06-12 2006-05-09 Pelikan Technologies, Inc. Sampling module device and method
US8337419B2 (en) 2002-04-19 2012-12-25 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
DE10134650B4 (de) * 2001-07-20 2009-12-03 Roche Diagnostics Gmbh System zur Entnahme kleiner Körperflüssigkeitsmengen
US20030032874A1 (en) 2001-07-27 2003-02-13 Dexcom, Inc. Sensor head for use with implantable devices
US8010174B2 (en) 2003-08-22 2011-08-30 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US10022078B2 (en) 2004-07-13 2018-07-17 Dexcom, Inc. Analyte sensor
US7828728B2 (en) 2003-07-25 2010-11-09 Dexcom, Inc. Analyte sensor
US7497827B2 (en) 2004-07-13 2009-03-03 Dexcom, Inc. Transcutaneous analyte sensor
US7613491B2 (en) 2002-05-22 2009-11-03 Dexcom, Inc. Silicone based membranes for use in implantable glucose sensors
US9247901B2 (en) 2003-08-22 2016-02-02 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US9282925B2 (en) 2002-02-12 2016-03-15 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US8260393B2 (en) 2003-07-25 2012-09-04 Dexcom, Inc. Systems and methods for replacing signal data artifacts in a glucose sensor data stream
US7674232B2 (en) 2002-04-19 2010-03-09 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7331931B2 (en) 2002-04-19 2008-02-19 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8784335B2 (en) 2002-04-19 2014-07-22 Sanofi-Aventis Deutschland Gmbh Body fluid sampling device with a capacitive sensor
US7491178B2 (en) 2002-04-19 2009-02-17 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8579831B2 (en) 2002-04-19 2013-11-12 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7175642B2 (en) 2002-04-19 2007-02-13 Pelikan Technologies, Inc. Methods and apparatus for lancet actuation
US7901362B2 (en) 2002-04-19 2011-03-08 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
US9795334B2 (en) 2002-04-19 2017-10-24 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7976476B2 (en) 2002-04-19 2011-07-12 Pelikan Technologies, Inc. Device and method for variable speed lancet
US7229458B2 (en) 2002-04-19 2007-06-12 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8360992B2 (en) 2002-04-19 2013-01-29 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7892183B2 (en) 2002-04-19 2011-02-22 Pelikan Technologies, Inc. Method and apparatus for body fluid sampling and analyte sensing
US7547287B2 (en) 2002-04-19 2009-06-16 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
US7909778B2 (en) 2002-04-19 2011-03-22 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7371247B2 (en) 2002-04-19 2008-05-13 Pelikan Technologies, Inc Method and apparatus for penetrating tissue
US7297122B2 (en) 2002-04-19 2007-11-20 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7648468B2 (en) 2002-04-19 2010-01-19 Pelikon Technologies, Inc. Method and apparatus for penetrating tissue
US8267870B2 (en) 2002-04-19 2012-09-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for body fluid sampling with hybrid actuation
US8372016B2 (en) 2002-04-19 2013-02-12 Sanofi-Aventis Deutschland Gmbh Method and apparatus for body fluid sampling and analyte sensing
US7717863B2 (en) 2002-04-19 2010-05-18 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8221334B2 (en) 2002-04-19 2012-07-17 Sanofi-Aventis Deutschland Gmbh 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
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
US9314194B2 (en) 2002-04-19 2016-04-19 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US9248267B2 (en) 2002-04-19 2016-02-02 Sanofi-Aventis Deustchland Gmbh Tissue penetration device
US7767068B2 (en) * 2002-12-02 2010-08-03 Epocal Inc. Heterogeneous membrane electrodes
US7842234B2 (en) * 2002-12-02 2010-11-30 Epocal Inc. Diagnostic devices incorporating fluidics and methods of manufacture
US8052926B2 (en) * 2002-12-27 2011-11-08 Roche Diagnostics Operations, Inc. Method for manufacturing a sterilized lancet integrated biosensor
US8574895B2 (en) 2002-12-30 2013-11-05 Sanofi-Aventis Deutschland Gmbh Method and apparatus using optical techniques to measure analyte levels
US7134999B2 (en) 2003-04-04 2006-11-14 Dexcom, Inc. Optimized sensor geometry for an implantable glucose sensor
WO2004107975A2 (en) 2003-05-30 2004-12-16 Pelikan Technologies, Inc. Method and apparatus for fluid injection
WO2004107964A2 (en) 2003-06-06 2004-12-16 Pelikan Technologies, Inc. Blood harvesting device with electronic control
WO2006001797A1 (en) 2004-06-14 2006-01-05 Pelikan Technologies, Inc. Low pain penetrating
US7761130B2 (en) 2003-07-25 2010-07-20 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US7424318B2 (en) * 2003-12-05 2008-09-09 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US7460898B2 (en) * 2003-12-05 2008-12-02 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
EP1648298A4 (de) 2003-07-25 2010-01-13 Dexcom Inc Sauerstoffverbessernde membransysteme für implantierbare vorrichtungen
US7366556B2 (en) * 2003-12-05 2008-04-29 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8423113B2 (en) 2003-07-25 2013-04-16 Dexcom, Inc. Systems and methods for processing sensor data
US7467003B2 (en) * 2003-12-05 2008-12-16 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8160669B2 (en) 2003-08-01 2012-04-17 Dexcom, Inc. Transcutaneous analyte sensor
US20100168542A1 (en) 2003-08-01 2010-07-01 Dexcom, Inc. System and methods for processing analyte sensor data
US9135402B2 (en) * 2007-12-17 2015-09-15 Dexcom, Inc. Systems and methods for processing sensor data
US8761856B2 (en) 2003-08-01 2014-06-24 Dexcom, Inc. System and methods for processing analyte sensor data
US20190357827A1 (en) 2003-08-01 2019-11-28 Dexcom, Inc. Analyte sensor
US7778680B2 (en) 2003-08-01 2010-08-17 Dexcom, Inc. System and methods for processing analyte sensor data
US7519408B2 (en) 2003-11-19 2009-04-14 Dexcom, Inc. Integrated receiver for continuous analyte sensor
US8845536B2 (en) 2003-08-01 2014-09-30 Dexcom, Inc. Transcutaneous analyte sensor
US8369919B2 (en) 2003-08-01 2013-02-05 Dexcom, Inc. Systems and methods for processing sensor data
US7925321B2 (en) 2003-08-01 2011-04-12 Dexcom, Inc. System and methods for processing analyte sensor data
US8886273B2 (en) 2003-08-01 2014-11-11 Dexcom, Inc. Analyte sensor
US7591801B2 (en) 2004-02-26 2009-09-22 Dexcom, Inc. Integrated delivery device for continuous glucose sensor
US7774145B2 (en) 2003-08-01 2010-08-10 Dexcom, Inc. Transcutaneous analyte sensor
US20140121989A1 (en) 2003-08-22 2014-05-01 Dexcom, Inc. Systems and methods for processing analyte sensor data
US7920906B2 (en) 2005-03-10 2011-04-05 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US8282576B2 (en) 2003-09-29 2012-10-09 Sanofi-Aventis Deutschland Gmbh Method and apparatus for an improved sample capture device
US9351680B2 (en) 2003-10-14 2016-05-31 Sanofi-Aventis Deutschland Gmbh Method and apparatus for a variable user interface
US9247900B2 (en) 2004-07-13 2016-02-02 Dexcom, Inc. Analyte sensor
EP3399047A1 (de) * 2003-12-04 2018-11-07 PHC Holdings Corporation Biosensor
US8287453B2 (en) 2003-12-05 2012-10-16 Dexcom, Inc. Analyte sensor
US8423114B2 (en) 2006-10-04 2013-04-16 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8364231B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US20100185071A1 (en) * 2003-12-05 2010-07-22 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
EP1711790B1 (de) 2003-12-05 2010-09-08 DexCom, Inc. Kalibrationsmethoden für einen kontinuierlich arbeitenden analytsensor
US8774886B2 (en) 2006-10-04 2014-07-08 Dexcom, Inc. Analyte sensor
US11633133B2 (en) 2003-12-05 2023-04-25 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
EP2316331B1 (de) 2003-12-09 2016-06-29 Dexcom, Inc. Signalverarbeitung in einem durchgehenden Analytsensor
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
US8808228B2 (en) 2004-02-26 2014-08-19 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US20050245799A1 (en) * 2004-05-03 2005-11-03 Dexcom, Inc. Implantable analyte sensor
US8792955B2 (en) 2004-05-03 2014-07-29 Dexcom, Inc. Transcutaneous analyte sensor
US8277713B2 (en) 2004-05-03 2012-10-02 Dexcom, Inc. Implantable analyte sensor
EP1751546A2 (de) 2004-05-20 2007-02-14 Albatros Technologies GmbH & Co. KG Bedruckbares wassergel für biosensoren
US9820684B2 (en) 2004-06-03 2017-11-21 Sanofi-Aventis Deutschland Gmbh 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
US8452368B2 (en) 2004-07-13 2013-05-28 Dexcom, Inc. Transcutaneous analyte sensor
US7783333B2 (en) 2004-07-13 2010-08-24 Dexcom, Inc. Transcutaneous medical device with variable stiffness
US20080242961A1 (en) * 2004-07-13 2008-10-02 Dexcom, Inc. Transcutaneous analyte sensor
US7905833B2 (en) 2004-07-13 2011-03-15 Dexcom, Inc. Transcutaneous analyte sensor
US8565848B2 (en) 2004-07-13 2013-10-22 Dexcom, Inc. Transcutaneous analyte sensor
US8886272B2 (en) 2004-07-13 2014-11-11 Dexcom, Inc. Analyte sensor
US20090054811A1 (en) * 2004-12-30 2009-02-26 Dirk Boecker Method and apparatus for analyte measurement test time
US8652831B2 (en) 2004-12-30 2014-02-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for analyte measurement test time
US7935063B2 (en) * 2005-03-02 2011-05-03 Roche Diagnostics Operations, Inc. System and method for breaking a sterility seal to engage a lancet
JP5020832B2 (ja) * 2005-03-04 2012-09-05 バイエル・ヘルスケア・エルエルシー 電気化学的バイオセンサでの酵素活性の安定化
US20090076360A1 (en) 2007-09-13 2009-03-19 Dexcom, Inc. Transcutaneous analyte sensor
US8133178B2 (en) 2006-02-22 2012-03-13 Dexcom, Inc. Analyte sensor
US8744546B2 (en) 2005-05-05 2014-06-03 Dexcom, Inc. Cellulosic-based resistance domain for an analyte sensor
ES2333166T3 (es) 2005-08-05 2010-02-17 Bayer Healthcare, Llc Procedimiento para distinguir sensores electroquimicos.
WO2007028271A2 (en) * 2005-09-09 2007-03-15 F. Hoffmann-La Roche Ag A system, tools, devices and a program for diabetes care
US20090134043A1 (en) * 2005-11-10 2009-05-28 Kevin Ward Non-biofouling, universal redox electrode and measurement system
RU2008130869A (ru) * 2005-12-27 2010-02-10 Байер Хелткэр Ллк (Us) Способ изготовления электродов для тестовых датчиков
US9757061B2 (en) 2006-01-17 2017-09-12 Dexcom, Inc. Low oxygen in vivo analyte sensor
EP1991110B1 (de) 2006-03-09 2018-11-07 DexCom, Inc. Systeme und verfahren zur aufbereitung von analytensensordaten
US8163162B2 (en) 2006-03-31 2012-04-24 Lifescan, Inc. Methods and apparatus for analyzing a sample in the presence of interferents
BRPI0711337A2 (pt) * 2006-05-08 2011-08-30 Bayer Healthcare Llc sensor teste eletroquìmico com volume de amostra reduzido
US20080064937A1 (en) 2006-06-07 2008-03-13 Abbott Diabetes Care, Inc. Analyte monitoring system and method
DE102006043718B4 (de) * 2006-09-18 2014-12-31 Alexander Adlassnig Bestimmung von Wasserstoffperoxidkonzentrationen
US7831287B2 (en) 2006-10-04 2010-11-09 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
AU2007303239A1 (en) 2006-10-04 2008-04-10 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
WO2008040982A1 (en) * 2006-10-05 2008-04-10 Lifescan Scotland Limited Method for determining hematocrit corrected analyte concentrations
EP2082222B1 (de) 2006-10-05 2012-11-21 Lifescan Scotland Limited Systeme und verfahren zur bestimmung einer weitgehend hämatokrit-unabhängigen analytkonzentration
US9046480B2 (en) 2006-10-05 2015-06-02 Lifescan Scotland Limited Method for determining hematocrit corrected analyte concentrations
EP2080022B1 (de) 2006-10-05 2015-05-13 Lifescan Scotland Ltd Verfahren zur bestimmung einer analytkonzentration mit verwendung von signalprozessierungsalgorithmen
TW200823456A (en) * 2006-11-24 2008-06-01 Health & Life Co Ltd Biosensor
KR100909620B1 (ko) * 2007-04-20 2009-07-27 주식회사 영텍 캘리브레이션 장치
BRPI0810515A2 (pt) * 2007-04-27 2014-10-21 Abbott Diabetes Care Inc Métodos e sensores de analisado sem calibragem
US9063070B2 (en) * 2007-05-18 2015-06-23 Luoxis Diagnostics, Inc. Measurement and uses of oxidative status
US8709709B2 (en) 2007-05-18 2014-04-29 Luoxis Diagnostics, Inc. Measurement and uses of oxidative status
CA2688184A1 (en) 2007-06-08 2008-12-18 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
TWI336782B (en) * 2007-07-05 2011-02-01 Apex Biotechnology Corp Composite modified electrode trip
KR101522322B1 (ko) * 2007-07-26 2015-05-21 아가매트릭스, 인코포레이티드 전기화학적 테스트 스트립
EP2227132B1 (de) 2007-10-09 2023-03-08 DexCom, Inc. Integriertes insulin-abgabesystem mit kontinuierlichem glucosesensor
US8417312B2 (en) 2007-10-25 2013-04-09 Dexcom, Inc. Systems and methods for processing sensor data
US8290559B2 (en) 2007-12-17 2012-10-16 Dexcom, Inc. Systems and methods for processing sensor data
US9143569B2 (en) 2008-02-21 2015-09-22 Dexcom, Inc. Systems and methods for processing, transmitting and displaying sensor data
US8396528B2 (en) 2008-03-25 2013-03-12 Dexcom, Inc. Analyte sensor
US20090247856A1 (en) * 2008-03-28 2009-10-01 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US8583204B2 (en) * 2008-03-28 2013-11-12 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US8682408B2 (en) 2008-03-28 2014-03-25 Dexcom, Inc. Polymer membranes for continuous analyte sensors
US11730407B2 (en) 2008-03-28 2023-08-22 Dexcom, Inc. Polymer membranes for continuous analyte sensors
EP2265324B1 (de) 2008-04-11 2015-01-28 Sanofi-Aventis Deutschland GmbH Integriertes System zur Messung von Analyten
EP2326944B1 (de) 2008-09-19 2020-08-19 Dexcom, Inc. Partikelhaltige membran und partikelelektrode für analytsensoren
US8956308B2 (en) 2008-09-29 2015-02-17 Bayer Healthcare Llc Integrated-testing system
US8986208B2 (en) * 2008-09-30 2015-03-24 Abbott Diabetes Care Inc. Analyte sensor sensitivity attenuation mitigation
US8012428B2 (en) * 2008-10-30 2011-09-06 Lifescan Scotland, Ltd. Analytical test strip with minimal fill-error sample viewing window
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
KR100918027B1 (ko) * 2009-02-19 2009-09-18 주식회사 올메디쿠스 코드전극을 구비한 바이오센서와 이의 제조방법, 및 이의 센서 정보 획득 방법
US9446194B2 (en) 2009-03-27 2016-09-20 Dexcom, Inc. Methods and systems for promoting glucose management
US20110048972A1 (en) * 2009-08-31 2011-03-03 Lifescan Scotland Limited Multi-analyte test strip with shared counter/reference electrode and inline electrode configuration
US9212380B2 (en) * 2009-08-31 2015-12-15 Panasonic Healthcare Holdings Co., Ltd. Sensor and concentration measurement method
KR101109857B1 (ko) * 2009-09-29 2012-02-14 광운대학교 산학협력단 더블 펄스 방식을 이용한 바이오센서
GB201005357D0 (en) 2010-03-30 2010-05-12 Menai Medical Technologies Ltd Sampling plate
GB201005359D0 (en) 2010-03-30 2010-05-12 Menai Medical Technologies Ltd Sampling plate
US20120238841A1 (en) * 2010-04-15 2012-09-20 Mark Castle Sample capture in one step for test strips
US8965476B2 (en) 2010-04-16 2015-02-24 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
JP5925285B2 (ja) * 2010-04-22 2016-05-25 アークレイ株式会社 バイオセンサ
JP5753720B2 (ja) * 2010-04-22 2015-07-22 アークレイ株式会社 バイオセンサ
US8940141B2 (en) 2010-05-19 2015-01-27 Lifescan Scotland Limited Analytical test strip with an electrode having electrochemically active and inert areas of a predetermined size and distribution
US20110290668A1 (en) * 2010-05-27 2011-12-01 Lifescan Scotland Limited Analytical test strip with crossroads exposed electrode configuration
EP2601518A4 (de) * 2010-08-06 2017-01-18 Schlumberger Technology B.V. Elektrochemischer sensor
AU2011303639B2 (en) 2010-09-13 2015-05-14 Lifescan Scotland Limited Analyte measurement method and system with hematocrit compensation
RU2564923C2 (ru) * 2010-12-31 2015-10-10 Цилаг Гмбх Интернэшнл Системы и способы измерений аналита с высокой точностью
KR20140034720A (ko) 2011-02-28 2014-03-20 로익스 다이어그노스틱스, 아이엔씨. 산화-환원 전위를 측정하기 위한 방법 및 장치
WO2012133633A1 (ja) * 2011-03-29 2012-10-04 株式会社テクノメデイカ 使い捨てリジンセンサ
EP3575796B1 (de) 2011-04-15 2020-11-11 DexCom, Inc. Erweiterte analytsensorkalibrierung und fehlererkennung
TWI427291B (zh) * 2011-07-06 2014-02-21 Bionime Corp 使用電化學感測片測量樣本的方法
USD703208S1 (en) * 2012-04-13 2014-04-22 Blackberry Limited UICC apparatus
US8936199B2 (en) 2012-04-13 2015-01-20 Blackberry Limited UICC apparatus and related methods
EA201491808A1 (ru) 2012-04-19 2015-03-31 Луоксис Дайэгностикс, Инк. Многослойный гель
USD701864S1 (en) * 2012-04-23 2014-04-01 Blackberry Limited UICC apparatus
JP2013242171A (ja) * 2012-05-18 2013-12-05 Tanita Corp 濃度測定装置
TWI513978B (zh) 2012-06-08 2015-12-21 Hmd Biomedical Inc 檢測試片、檢測裝置及檢測方法
US20130341207A1 (en) * 2012-06-21 2013-12-26 Lifescan Scotland Limited Analytical test strip with capillary sample-receiving chambers separated by stop junctions
US9128038B2 (en) * 2012-06-21 2015-09-08 Lifescan Scotland Limited Analytical test strip with capillary sample-receiving chambers separated by a physical barrier island
US8877023B2 (en) * 2012-06-21 2014-11-04 Lifescan Scotland Limited Electrochemical-based analytical test strip with intersecting sample-receiving chambers
GB2505694B (en) * 2012-09-07 2017-03-22 Lifescan Scotland Ltd Electrochemical-based analytical test strip with bare interferent electrodes
SG11201401110WA (en) 2012-10-23 2014-06-27 Luoxis Diagnostics Inc Methods and systems for measuring and using the oxidation-reduction potential of a biological sample
US9244036B2 (en) 2012-11-16 2016-01-26 Cilag Gmbh International System and method for determination of a concentration of at least one interfering substance and correction of glucose concentration based on the concentration of the interfering substance
TWI493186B (zh) 2013-02-08 2015-07-21 Hmd Biomedical Inc 檢測試片、檢測裝置及檢測方法
US9121050B2 (en) 2013-03-15 2015-09-01 American Sterilizer Company Non-enzyme based detection method for electronic monitoring of biological indicator
US8858884B2 (en) 2013-03-15 2014-10-14 American Sterilizer Company Coupled enzyme-based method for electronic monitoring of biological indicator
JP5813171B2 (ja) * 2013-05-02 2015-11-17 アークレイ株式会社 分析用具、その製造方法、及びそれを用いた測定装置
GB2514846B (en) * 2013-06-07 2015-09-30 Lifescan Scotland Ltd Electrochemical-based analytical test strip with a soluble electrochemically-active coating opposite a bare electrode
GB2518165B (en) * 2013-09-11 2016-04-27 Cilag Gmbh Int Electrochemical-based analytical test strip with ultra-thin discontinuous metal layer
US20150068893A1 (en) * 2013-09-12 2015-03-12 Joinsoon Medical Technology Co., Ltd. Biosensor test strip for biosensor test device
JP6404681B2 (ja) * 2013-11-08 2018-10-10 アークレイ株式会社 測定装置、及び測定方法
US20150176049A1 (en) * 2013-12-23 2015-06-25 Cilag Gmbh International Determining usability of analytical test strip
EP3172570A4 (de) 2014-07-25 2017-12-27 Becton, Dickinson and Company Analytteststreifenassays und teststreifen und kits zur verwendung beim üben davon
EP3183246B1 (de) 2014-08-22 2020-09-23 Roche Diagnostics GmbH Redoxindikatoren
ES2883115T3 (es) 2014-08-25 2021-12-07 Hoffmann La Roche Tira reactiva de dos electrodos que compensan la interferencia
GB201419472D0 (en) 2014-10-31 2014-12-17 Inside Biometrics Ltd Method of using and electrochemical device
AU2015373937A1 (en) * 2014-12-31 2017-07-27 Trividia Health, Inc. Glucose test strip with interference correction
WO2016183044A1 (en) * 2015-05-10 2016-11-17 Gordhanbhai Patel Uv cured indicating devices
ES2720780T3 (es) 2016-03-14 2019-07-24 Hoffmann La Roche Método para detectar una contribución interferente en un biosensor
CN112698021B (zh) * 2016-12-23 2024-09-20 雷迪奥米特医学公司 用于体液的多次使用传感器组件
WO2019006413A1 (en) * 2017-06-30 2019-01-03 Abbott Diabetes Care METHOD AND APPARATUS FOR ANALYTE DETECTION USING ELECTROCHEMICAL BIOSENSOR
DK3700416T3 (da) 2017-10-24 2024-09-30 Dexcom Inc På forhånd forbundne analytsensorer
US11331022B2 (en) 2017-10-24 2022-05-17 Dexcom, Inc. Pre-connected analyte sensors
US10330628B2 (en) 2017-11-21 2019-06-25 Uxn Co., Ltd. Glucose-sensing electrode and device with nanoporous layer
WO2019118920A1 (en) * 2017-12-15 2019-06-20 Uxn Co., Ltd Colloid with a nanoporous structure and device and system for non-enzymatic glucose-sensing
CN110082418B (zh) * 2019-05-27 2021-10-15 三诺生物传感股份有限公司 一种尿酸电化学测量方法
CN112067604B (zh) * 2019-08-01 2023-01-10 杭州博拓生物科技股份有限公司 一种检测装置
CN112294319B (zh) * 2019-08-02 2024-08-20 华广生技股份有限公司 植入式微型生物传感器的制造方法
ES2915406B2 (es) * 2020-12-21 2024-03-14 Bioquochem S L Metodo para medir una concentracion de un compuesto de analisis o una actividad enzimatica en una muestra compleja mediante la cuantificacion de peroxido de hidrogeno de forma selectiva
WO2023001292A1 (zh) * 2021-07-22 2023-01-26 华广生技股份有限公司 微型生物传感器及其感测结构
US20230314340A1 (en) * 2022-03-29 2023-10-05 Medtronic, Inc. Noise reduction for sensor apparatus

Citations (25)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4431004A (en) * 1981-10-27 1984-02-14 Bessman Samuel P Implantable glucose sensor
US4655880A (en) * 1983-08-01 1987-04-07 Case Western Reserve University Apparatus and method for sensing species, substances and substrates using oxidase
US5120420A (en) * 1988-03-31 1992-06-09 Matsushita Electric Industrial Co., Ltd. Biosensor and a process for preparation thereof
US5298146A (en) * 1991-11-08 1994-03-29 Bayer Aktiengesellschaft Device for the simultaneous detection of dissimilar gas components
US5354447A (en) * 1991-12-12 1994-10-11 Kyoto Daiichi Kagaku Co., Ltd. Biosensor and method of quantitative analysis using the same
US5582697A (en) * 1995-03-17 1996-12-10 Matsushita Electric Industrial Co., Ltd. Biosensor, and a method and a device for quantifying a substrate in a sample liquid using the same
US5628890A (en) * 1995-09-27 1997-05-13 Medisense, Inc. Electrochemical sensor
US5650062A (en) * 1995-03-17 1997-07-22 Matsushita Electric Industrial Co., Ltd. Biosensor, and a method and a device for quantifying a substrate in a sample liquid using the same
US5653918A (en) * 1996-01-11 1997-08-05 E. I. Du Pont De Nemours And Company Flexible thick film conductor composition
US5708247A (en) * 1996-02-14 1998-01-13 Selfcare, Inc. Disposable glucose test strips, and methods and compositions for making same
US5830343A (en) * 1994-07-11 1998-11-03 Fraunhofer-Gesellschaft Zur Foerderung Der Angewandten Forschung E.V. Electrochemical analysis process
US5985116A (en) * 1996-12-24 1999-11-16 Matsushita Electric Industrial Co., Ltd. Biosensor
US6046051A (en) * 1997-06-27 2000-04-04 Hemosense, Inc. Method and device for measuring blood coagulation or lysis by viscosity changes
US6212417B1 (en) * 1998-08-26 2001-04-03 Matsushita Electric Industrial Co., Ltd. Biosensor
US6256229B1 (en) * 1997-01-08 2001-07-03 Micron Technology, Inc. Apparatus and method for programming voltage protection in a non-volatile memory system
US6287451B1 (en) * 1999-06-02 2001-09-11 Handani Winarta Disposable sensor and method of making
US6340428B1 (en) * 1998-04-02 2002-01-22 Matsushita Electric Industrial Co., Inc. Device and method for determining the concentration of a substrate
US20020092612A1 (en) * 2000-03-28 2002-07-18 Davies Oliver William Hardwicke Rapid response glucose sensor
US20020157947A1 (en) * 2001-03-23 2002-10-31 Craig Rappin Electrochemical sensor and method thereof
US20020168290A1 (en) * 2002-05-09 2002-11-14 Yuzhakov Vadim V. Physiological sample collection devices and methods of using the same
US6540891B1 (en) * 1998-05-08 2003-04-01 Abbott Laboratories Test strip
US6599406B1 (en) * 1997-07-22 2003-07-29 Kyoto Daiichi Kagaku Co., Ltd. Concentration measuring apparatus, test strip for the concentration measuring apparatus, biosensor system and method for forming terminal on the test strip
US6730200B1 (en) * 1999-06-18 2004-05-04 Abbott Laboratories Electrochemical sensor for analysis of liquid samples
US20040120848A1 (en) * 2002-12-20 2004-06-24 Maria Teodorczyk Method for manufacturing a sterilized and calibrated biosensor-based medical device
US6881322B2 (en) * 2000-01-25 2005-04-19 Matsushita Electric Industrial Co., Ltd. Measuring device using biosensor and biosenor used for it, and dedicated standard liquid

Family Cites Families (45)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US565062A (en) * 1896-08-04 Samuel l
US4233031A (en) * 1978-12-11 1980-11-11 Environmental Sciences Associates, Inc. Electrochemical testing system and method
JPS613048A (ja) * 1984-06-18 1986-01-09 Matsushita Electric Works Ltd バイオセンサを用いた測定法
EP0331696A1 (de) 1987-08-28 1989-09-13 HARMAN, John N. III Lärmverminderungstechnik für elektrochemische zellen
FR2661548B1 (fr) * 1990-04-30 1992-07-17 Telemecanique Appareil contacteur inverseur a verrouillage.
JPH04240558A (ja) * 1991-01-25 1992-08-27 Sumitomo Metal Ind Ltd 酵素電極
JP2960265B2 (ja) * 1991-10-18 1999-10-06 松下電器産業株式会社 バイオセンサおよびそれを用いた測定方法
JP2658769B2 (ja) * 1991-10-21 1997-09-30 松下電器産業株式会社 バイオセンサ
ZA938555B (en) * 1992-11-23 1994-08-02 Lilly Co Eli Technique to improve the performance of electrochemical sensors
US5592551A (en) * 1992-12-01 1997-01-07 Scientific-Atlanta, Inc. Method and apparatus for providing interactive electronic programming guide
JPH09129236A (ja) * 1995-08-25 1997-05-16 Furukawa Battery Co Ltd:The リチウム二次電池用負極活物質並びにリチウム二次電池
US5650052A (en) * 1995-10-04 1997-07-22 Edelstein; Sergio Variable cell size collimator
JP2000512762A (ja) * 1996-06-17 2000-09-26 マーキュリー ダイアグノスティックス インコーポレイテッド 電気化学テスト装置および関連する方法
KR100193716B1 (ko) * 1996-10-16 1999-06-15 윤종용 전계 밀도차에 의한 유전영동력을 이용하는 잉크젯 프린팅 방법 및 장치
JP3394262B2 (ja) * 1997-02-06 2003-04-07 セラセンス、インク． 小体積インビトロ被検体センサー
BR7700267U (pt) * 1997-03-20 1998-11-03 Wahler Metalurgica Ltda Termostato integrado
US6139718A (en) 1997-03-25 2000-10-31 Cygnus, Inc. Electrode with improved signal to noise ratio
BR9811609A (pt) 1997-09-05 2000-09-05 Abbott Lab Sensor eletroquìmico com áreas de elétrodo equalizadas
JP3267907B2 (ja) * 1997-09-29 2002-03-25 松下電器産業株式会社 バイオセンサおよびそれを用いた基質の定量法
US6001239A (en) * 1998-09-30 1999-12-14 Mercury Diagnostics, Inc. Membrane based electrochemical test device and related methods
JP3267933B2 (ja) * 1998-01-27 2002-03-25 松下電器産業株式会社 基質の定量法
AU5683599A (en) 1998-08-31 2000-03-21 Cubus Corporation Computer product for networking a document development system using message headers associated with message files
US6338790B1 (en) * 1998-10-08 2002-01-15 Therasense, Inc. Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator
JP3462401B2 (ja) * 1998-10-15 2003-11-05 日本電信電話株式会社 電気化学検出器
JP5073129B2 (ja) * 1999-03-31 2012-11-14 株式会社日本触媒 （メタ）アクリル酸の精製方法
US6258229B1 (en) * 1999-06-02 2001-07-10 Handani Winarta Disposable sub-microliter volume sensor and method of making
US6616819B1 (en) * 1999-11-04 2003-09-09 Therasense, Inc. Small volume in vitro analyte sensor and methods
EP2151683A3 (de) * 1999-11-15 2010-07-28 Panasonic Corporation Biosensor, Verfahren zur Ausbildung einer Dünnschichtelektrode, Quantifizierungsvorrichtung und Quantifizierungsverfahren
GB0005564D0 (en) 2000-03-08 2000-05-03 Inverness Medical Ltd Measurjement of substances in liquid
CA2402354C (en) 2000-03-28 2011-10-04 Inverness Medical Technology, Inc. Rapid response glucose sensor
JP2002055076A (ja) * 2000-09-08 2002-02-20 Nec Corp 電気化学センサ
GB0030929D0 (en) 2000-12-19 2001-01-31 Inverness Medical Ltd Analyte measurement
EP1369684A4 (de) * 2001-01-17 2009-07-22 Arkray Inc Quantitatives analyseverfahren und quantitativer analysierer mit sensor
JP3672099B2 (ja) * 2001-06-14 2005-07-13 松下電器産業株式会社 バイオセンサ
DE10158420A1 (de) 2001-11-29 2003-06-12 Basf Ag Glycidyl(meth)acrylat enthaltende Klebstoff
US6837976B2 (en) * 2002-04-19 2005-01-04 Nova Biomedical Corporation Disposable sensor with enhanced sample port inlet
DE10218828A1 (de) 2002-04-26 2003-11-06 Siemens Ag Mobilfunkgerät mit Sendeleistungsbeschränkung
KR100485671B1 (ko) 2002-09-30 2005-04-27 주식회사 인포피아 바이오 센서의 시료 반응결과 측정장치 및 그 방법
CA2504311C (en) 2002-10-30 2011-12-20 Inverness Medical Limited Preconditioning of a substrate in a continuous process for manufacture of electrochemical sensors
US20040149578A1 (en) * 2003-01-30 2004-08-05 Chun-Mu Huang Method for manufacturing electrochemical sensor and structure thereof
US7132041B2 (en) 2003-02-11 2006-11-07 Bayer Healthcare Llc Methods of determining the concentration of an analyte in a fluid test sample
US7462265B2 (en) * 2003-06-06 2008-12-09 Lifescan, Inc. Reduced volume electrochemical sensor
US7655119B2 (en) * 2003-10-31 2010-02-02 Lifescan Scotland Limited Meter for use in an improved method of reducing interferences in an electrochemical sensor using two different applied potentials
CA2543961A1 (en) 2003-10-31 2005-05-19 Lifescan Scotland Limited Electrochemical test strip for reducing the effect of direct and mediated interference current
US7875461B2 (en) * 2007-07-24 2011-01-25 Lifescan Scotland Limited Test strip and connector

Patent Citations (28)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4431004A (en) * 1981-10-27 1984-02-14 Bessman Samuel P Implantable glucose sensor
US4655880A (en) * 1983-08-01 1987-04-07 Case Western Reserve University Apparatus and method for sensing species, substances and substrates using oxidase
US5120420A (en) * 1988-03-31 1992-06-09 Matsushita Electric Industrial Co., Ltd. Biosensor and a process for preparation thereof
US5120420B1 (en) * 1988-03-31 1999-11-09 Matsushita Electric Ind Co Ltd Biosensor and a process for preparation thereof
US5298146A (en) * 1991-11-08 1994-03-29 Bayer Aktiengesellschaft Device for the simultaneous detection of dissimilar gas components
US5354447A (en) * 1991-12-12 1994-10-11 Kyoto Daiichi Kagaku Co., Ltd. Biosensor and method of quantitative analysis using the same
US5830343A (en) * 1994-07-11 1998-11-03 Fraunhofer-Gesellschaft Zur Foerderung Der Angewandten Forschung E.V. Electrochemical analysis process
US5582697A (en) * 1995-03-17 1996-12-10 Matsushita Electric Industrial Co., Ltd. Biosensor, and a method and a device for quantifying a substrate in a sample liquid using the same
US5650062A (en) * 1995-03-17 1997-07-22 Matsushita Electric Industrial Co., Ltd. Biosensor, and a method and a device for quantifying a substrate in a sample liquid using the same
US5628890A (en) * 1995-09-27 1997-05-13 Medisense, Inc. Electrochemical sensor
US5653918A (en) * 1996-01-11 1997-08-05 E. I. Du Pont De Nemours And Company Flexible thick film conductor composition
US5708247A (en) * 1996-02-14 1998-01-13 Selfcare, Inc. Disposable glucose test strips, and methods and compositions for making same
US5985116A (en) * 1996-12-24 1999-11-16 Matsushita Electric Industrial Co., Ltd. Biosensor
US6256229B1 (en) * 1997-01-08 2001-07-03 Micron Technology, Inc. Apparatus and method for programming voltage protection in a non-volatile memory system
US6046051A (en) * 1997-06-27 2000-04-04 Hemosense, Inc. Method and device for measuring blood coagulation or lysis by viscosity changes
US6599406B1 (en) * 1997-07-22 2003-07-29 Kyoto Daiichi Kagaku Co., Ltd. Concentration measuring apparatus, test strip for the concentration measuring apparatus, biosensor system and method for forming terminal on the test strip
US6790327B2 (en) * 1998-04-02 2004-09-14 Matsushita Electric Industrial Co., Ltd. Device and method for determining the concentration of a substrate
US6340428B1 (en) * 1998-04-02 2002-01-22 Matsushita Electric Industrial Co., Inc. Device and method for determining the concentration of a substrate
US6540891B1 (en) * 1998-05-08 2003-04-01 Abbott Laboratories Test strip
US6212417B1 (en) * 1998-08-26 2001-04-03 Matsushita Electric Industrial Co., Ltd. Biosensor
US6287451B1 (en) * 1999-06-02 2001-09-11 Handani Winarta Disposable sensor and method of making
US6730200B1 (en) * 1999-06-18 2004-05-04 Abbott Laboratories Electrochemical sensor for analysis of liquid samples
US6881322B2 (en) * 2000-01-25 2005-04-19 Matsushita Electric Industrial Co., Ltd. Measuring device using biosensor and biosenor used for it, and dedicated standard liquid
US20020092612A1 (en) * 2000-03-28 2002-07-18 Davies Oliver William Hardwicke Rapid response glucose sensor
US20020157947A1 (en) * 2001-03-23 2002-10-31 Craig Rappin Electrochemical sensor and method thereof
US20020168290A1 (en) * 2002-05-09 2002-11-14 Yuzhakov Vadim V. Physiological sample collection devices and methods of using the same
US20030143113A2 (en) * 2002-05-09 2003-07-31 Lifescan, Inc. Physiological sample collection devices and methods of using the same
US20040120848A1 (en) * 2002-12-20 2004-06-24 Maria Teodorczyk Method for manufacturing a sterilized and calibrated biosensor-based medical device

Cited By (31)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20100018878A1 (en) * 2003-10-31 2010-01-28 Lifescan Scotland Ltd. Method of reducing interferences in an electrochemical sensor using two different applied potentials
US20050183965A1 (en) * 2003-10-31 2005-08-25 Davies Oliver William H. Method of reducing interferences in an electrochemical sensor using two different applied potentials
US20050109618A1 (en) * 2003-10-31 2005-05-26 Davies Oliver W.H. Meter for use in an improved method of reducing interferences in an electrochemical sensor using two different applied potentials
US20070276621A1 (en) * 2003-10-31 2007-11-29 Davies Oliver William H Method of Reducing the Effect of Direct Interference Current in an Electrochemical Test Strip
US7655119B2 (en) 2003-10-31 2010-02-02 Lifescan Scotland Limited Meter for use in an improved method of reducing interferences in an electrochemical sensor using two different applied potentials
US7618522B2 (en) 2003-10-31 2009-11-17 Lifescan Scotland Limited Method of reducing interferences in an electrochemical sensor using two different applied potentials
US7653492B2 (en) * 2003-10-31 2010-01-26 Lifescan Scotland Limited Method of reducing the effect of direct interference current in an electrochemical test strip
US9034250B2 (en) 2005-03-02 2015-05-19 Roche Diagnostics Operations, Inc. Dynamic integrated lancing test strip with sterility cover
US9445756B2 (en) 2005-03-02 2016-09-20 Roche Diabetes Care, Inc. Dynamic integrated lancing test strip with sterility cover
US20070111196A1 (en) * 2005-08-19 2007-05-17 Javier Alarcon Sterilization of Biosensors
US8647487B2 (en) * 2006-05-04 2014-02-11 Nipro Diagnostics, Inc. System and methods for automatically recognizing a control solution
US20110192721A1 (en) * 2006-05-04 2011-08-11 Nipro Diagnostics, Inc. System and methods for automatically recognizing a control solution
WO2008050145A1 (en) * 2006-10-27 2008-05-02 Suresensors Ltd Measurement device
USD612279S1 (en) 2008-01-18 2010-03-23 Lifescan Scotland Limited User interface in an analyte meter
USD612274S1 (en) 2008-01-18 2010-03-23 Lifescan Scotland, Ltd. User interface in an analyte meter
US9626480B2 (en) 2008-03-21 2017-04-18 Lifescan Scotland Limited Analyte testing method and system
US8917184B2 (en) 2008-03-21 2014-12-23 Lifescan Scotland Limited Analyte testing method and system
US20100327886A1 (en) * 2008-03-27 2010-12-30 Toshifumi Nakamura Measurement device, measurement system, and concentration measurement method
USD611151S1 (en) 2008-06-10 2010-03-02 Lifescan Scotland, Ltd. Test meter
USD611372S1 (en) 2008-09-19 2010-03-09 Lifescan Scotland Limited Analyte test meter
US20110144915A1 (en) * 2009-12-11 2011-06-16 Lifescan Scotland Ltd. Fill sufficiency method and system
US8936713B2 (en) 2009-12-11 2015-01-20 Lifescan Scotland Limited Fill sufficiency method and system
US9335291B2 (en) 2009-12-11 2016-05-10 Lifescan Scotland Limited Fill sufficiency method and system
US10605758B2 (en) 2010-05-07 2020-03-31 Pa Knowledge Limited Devices and methods for testing analytes
US20130112573A1 (en) * 2010-05-07 2013-05-09 Exacsys Limited Devices and methods for testing analytes
US20120048746A1 (en) * 2010-08-30 2012-03-01 Cilag Gmbh International Analyte test strip with electrically distinguishable divided electrode
CN109270145A (zh) * 2018-11-20 2019-01-25 三诺生物传感股份有限公司 一种双电极的电化学试条的测试方法
US10920259B2 (en) 2018-11-20 2021-02-16 Changsha Sinocare Inc. Two electrodes functioning as three electrodes in the fluid chamber of a test strip
AU2020210301B2 (en) * 2019-08-02 2021-12-16 Bionime Corporation Micro Biosensor and Method for Reducing Measurement Interference Using the Same
US11950902B2 (en) 2019-08-02 2024-04-09 Bionime Corporation Micro biosensor and method for reducing measurement interference using the same
DE102022107214B4 (de) 2022-03-28 2024-07-18 Senslab - Gesellschaft Zur Entwicklung Und Herstellung Bioelektrochemischer Sensoren Mbh Verfahren und Sensor zur Bestimmung einer plasmabezogenen Analytkonzentration in Vollblut

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PL1678489T3 (pl) 2007-08-31
PL1678490T3 (pl) 2009-12-31
JP2007524846A (ja) 2007-08-30
JP2007514929A (ja) 2007-06-07
US20100018878A1 (en) 2010-01-28
DE602004004929T2 (de) 2007-10-31
CA2543957C (en) 2013-01-22
IL175322A0 (en) 2006-09-05
WO2005045415A1 (en) 2005-05-19
JP4611313B2 (ja) 2011-01-12
EP1678491A1 (de) 2006-07-12
US20050139489A1 (en) 2005-06-30
SG131942A1 (en) 2007-05-28
DE602004006148D1 (de) 2007-06-06
JP4694498B2 (ja) 2011-06-08
JP2007514931A (ja) 2007-06-07
IL175324A0 (en) 2006-09-05
AU2004288011A1 (en) 2005-05-19
DK1678489T3 (da) 2007-08-06
JP2007514930A (ja) 2007-06-07
HK1091896A1 (en) 2007-01-26
ES2285536T3 (es) 2007-11-16
IL175321A0 (en) 2006-09-05
KR20070027497A (ko) 2007-03-09
CA2543797C (en) 2013-01-22
PL1685393T3 (pl) 2007-07-31
KR20060131765A (ko) 2006-12-20
KR101179998B1 (ko) 2012-09-07
DK1685393T3 (da) 2007-04-30
IL175323A0 (en) 2006-09-05
EP1678490A1 (de) 2006-07-12
ES2282898T3 (es) 2007-10-16
EP1678489B1 (de) 2007-04-25
DE602004006148T2 (de) 2007-12-27
KR20060120152A (ko) 2006-11-24
AU2004288004B2 (en) 2009-06-11
WO2005045417A1 (en) 2005-05-19
HK1091898A1 (en) 2007-01-26
CA2543957A1 (en) 2005-05-19
JP2007514927A (ja) 2007-06-07
WO2005045416A1 (en) 2005-05-19
KR20070027496A (ko) 2007-03-09
AU2004288012B2 (en) 2008-04-03
CA2551058A1 (en) 2005-05-19
WO2005045414A1 (en) 2005-05-19
DE602004021835D1 (de) 2009-08-13
EP1685393A1 (de) 2006-08-02
EP1678490B1 (de) 2009-07-01
AU2004288008B2 (en) 2008-04-17
SG131941A1 (en) 2007-05-28
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DE602004025960D1 (de) 2010-04-22

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