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US20040020777A1 - Biosensor - Google Patents

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Publication number
US20040020777A1
US20040020777A1 US10/452,936 US45293603A US2004020777A1 US 20040020777 A1 US20040020777 A1 US 20040020777A1 US 45293603 A US45293603 A US 45293603A US 2004020777 A1 US2004020777 A1 US 2004020777A1
Authority
US
United States
Prior art keywords
reaction layer
layer
fine particles
biosensor
base plate
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US10/452,936
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English (en)
Inventor
Yoshiko Miyamoto
Tomohiro Yamamoto
Miwa Hasegawa
Toshihiko Yoshioka
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Panasonic Holdings Corp
Original Assignee
Individual
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Individual filed Critical Individual
Assigned to MATSUSHITA ELECTRIC INDUSTRIAL CO., LTD. reassignment MATSUSHITA ELECTRIC INDUSTRIAL CO., LTD. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: YOSHIOKA, TOSHIHIKO, MIYAMOTO, YOSHIKO, YAMAMOTO, TOMOHIRO, HASEGAWA, MIWA
Publication of US20040020777A1 publication Critical patent/US20040020777A1/en
Abandoned legal-status Critical Current

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Classifications

    • 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
    • G01N27/28—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
    • G01N27/3272—Test elements therefor, i.e. disposable laminated substrates with electrodes, reagent and channels

Definitions

  • the present invention relates to a biosensor for determining the quantity of a substrate (specific component) contained in a sample, e.g., biological samples such as blood and urea, materials and products in food industries and fruit juice, in a highly accurate, speedy and easy manner.
  • a substrate e.g., biological samples such as blood and urea, materials and products in food industries and fruit juice
  • a biosensor capable of easily determining the quantity of a specific component (substrate) in biological samples and foods without diluting or stirring the sample solution.
  • Japanese Laid-Open Patent Publication No. HEI 3-202764 discloses a biosensor including an electrode system formed on an electrically insulating base plate by screen printing and a reaction layer formed on the electrode system.
  • the reaction layer contains oxidoreductase and an electron mediator (electron acceptor).
  • This biosensor determines the substrate concentration in a sample in the following manner.
  • a sample solution is dropped onto the reaction layer of the biosensor. Then, the reaction layer dissolves to cause an enzyme reaction between the substrate in the sample solution and oxidoreductase in the reaction layer. Subsequently to the enzyme reaction, the electron mediator is reduced. After a predetermined time, a voltage is applied to the electrode of the sensor to electrochemically oxidize the reduced electron mediator. At that time, an oxidation current is obtained, from which the substrate concentration in the sample solution is determined.
  • reaction layer of the prior art biosensor is formed by a method of dropping and drying a solution containing a water-soluble component, it is difficult to form the reaction layer into a thin film. Further, it is also difficult to dry the reaction layer uniformly throughout its thickness and the performance of the sensor may unfavorably vary depending on the dry state of the surface of the reaction layer. Accordingly, the enzyme needs to be contained in an excessive amount in the reaction layer as compared with the amount of the substrate contained in the sample. Further, since the reagent is contained in a large amount in the reaction layer, it takes long time to dissolve the reaction layer.
  • Japanese Laid-Open Patent Publication No. 2001-208716 discloses a sensor strip comprising an electrode support, an electrode set formed thereon and microscopic grains.
  • the microscopic grains are used to reduce the amount of the sample required for the measurement, thereby increasing the dissolution rate of the reagent.
  • an object of the present invention is to provide a biosensor of good response characteristic in which the reaction layer containing the enzyme dissolves rapidly into a small amount of a sample solution and the enzyme reaction is effectively utilized.
  • Another object of the present invention is to provide a biosensor in which the above-described reaction layer is easily formed.
  • the present invention provides a biosensor comprising an electrically insulating base plate, an electrode system including a working electrode and a counter electrode formed on the base plate, and a reaction layer formed on or in the vicinity of the electrode system, at least a surface of the reaction layer being porous.
  • the porosity of the reaction layer is preferably 50% or more and the upper limit thereof may be about 90%.
  • the fine particles are made of a material selected from the group consisting of a polymer compound, ceramic, glass, diamond and carbon.
  • the biosensor of the present invention comprises an electrically insulating base plate, an electrode system including a working electrode and a counter electrode formed on the base plate, and a reaction layer formed on or in the vicinity of the electrode system.
  • the biosensor is characterized in that at least a surface of the reaction layer is porous.
  • the fine particles used herein are preferably made of a material selected from the group consisting of a polymer compound, ceramic such as silica, alumina and titanium oxide, glass, diamond and carbon.
  • the amount of the fine particles contained in the reaction layer is suitably 10 to 99% by volume ratio with respect to the reaction layer with a view to forming a thin enzyme layer on the fine particle surface.
  • the porous reaction layer which dissolves easily into the sample solution is formed. More preferably, the volume ratio is 10 to 20%.
  • Examples of the enzyme used in the present invention include glucose oxidase, glucose dehydrogenase, lactate oxygenase, lactate dehydrogenase, fructose oxidase, cholesterol oxidase, cholesterol dehydrogenase, cholesterol esterase, mutarotase, invertase, ascorbate oxidase, alcohol oxidase and the like. Among them, one or a combination of two or more may be used.
  • the electron mediator is mixed with the enzyme to form the reaction layer, the activity of the enzyme may be deteriorated by the electron mediator during storage. Accordingly, it is preferred that the electron mediator is contained in a layer isolated from the enzyme.
  • the electron mediator is preferably contained in a layer isolated from the enzymes.
  • the reaction layer of the biosensor according to the present invention may contain a hydrophilic polymer in addition to the enzymes and the electron mediator.
  • the addition of the hydrophilic polymer to the reaction layer prevents the reaction layer from peeling off the base plate or the surface of the electrode system. Further, the fracture of the reaction layer surface is also prevented, which is effective in enhancing the reliability of the biosensor.
  • the hydrophilic polymer may cover the electrode system, causing the same effect as the above.
  • hydrophilic polymer examples include carboxymethyl cellulose, hydroxyethyl cellulose, hydroxypropyl cellulose, methyl cellulose, ethyl cellulose, ethyl hydroxyethyl cellulose, carboxy methyl ethyl cellulose, polyvinylpyrrolidone, polyvinyl alcohol, polyamino acid such as polylysine, polystyrene sulfonate, gelatin and derivatives thereof, polymers of acrylic acid or derivatives thereof, polymers of maleic anhydride or salts thereof and starch or derivatives thereof.
  • carboxymethyl cellulose is particularly preferred.
  • An oxidation current may be measured by a measurement method on a two-electrode system using only a measuring electrode and a counter electrode or a three-electrode system using a reference electrode in addition, among which the three-electrode system allows measurement with greater accuracy.
  • FIG. 1 is a perspective view of a disassembled biosensor according to an embodiment of the present invention excluding a reaction layer.
  • Reference numeral 1 indicates an electrically insulating base plate made of polyethylene terephthalate.
  • leads 2 and 3 made of silver paste are formed by screen printing.
  • an electrode system including a working electrode 4 and a counter electrode 5 made of conductive carbon paste containing a resin binder, and an electrically insulating layer 6 made of electrically insulating paste.
  • the electrically insulating layer 6 exposes a certain area of the working electrode 4 and the counter electrode 5 and partially covers the leads. In other words, the electrically insulating layer 6 defines the exposed area.
  • the biosensor is assembled from the insulating base plate 1 made of polyethylene terephthalate, a cover 9 , and a spacer 8 sandwiched between the base plate 1 and the cover 9 . These components are bonded in a positional relationship as indicated by dashed lines shown in FIG. 1 to form the biosensor.
  • the spacer 8 is provided with a slit 10 for forming a sample solution supply pathway and the cover 9 includes an air aperture 11 .
  • a cavity is formed as a sample solution supply pathway between the base plate 1 and the cover 9 .
  • the cavity includes an opening end of the slit as a sample solution supply port and terminates at the air aperture 11 .
  • the cover 9 and the spacer 8 are combined as a covering member. However, a single member having a groove corresponding to the slit 10 of the spacer 8 may be used.
  • reaction layers 7 containing at least an enzyme, an electron mediator and fine particles are formed on the insulating base plate 1 provided with the electrode system as shown in FIG. 1, i.e., in the slit of the covering member.
  • the reaction layer is not necessarily formed on the electrode system as long as it is formed in a position exposed to the sample solution supply pathway and the sample solution flows over the electrode system while dissolving the reaction layer.
  • reaction layer 7 On the electrode system on the base plate 1 shown in FIG. 1, an aqueous solution containing fine particles of polystylene having an average diameter of 0.5 ⁇ m, potassium ferricyanide and glucose oxidase (EC1. 1. 3. 4, GOD) was dropped and dried in a warm-air dryer at 50° C. for 10 minutes to form a reaction layer 7 .
  • the obtained reaction layer 7 contained 1 mg of the fine particles, 1 mg of potassium ferricyanide and 0.05 mg of GOD, per cm 2 .
  • the base plate was combined with the spacer and the cover to complete the sensor and sensor characteristic as a glucose sensor was evaluated.
  • FIG. 3 shows the response characteristic obtained in the measurement for 10 seconds, together with the response characteristics obtained in Example 2 and Comparative Example 1.
  • FIG. 4 shows a photomicrograph taken under a magnification of 42.5 times. As seen in FIG. 4, the surface of the reaction layer 7 was porous.
  • the porosity of the reaction layer was obtained as a percentage of a volume of components in the reaction layer, which was obtained from the weight and specific gravity thereof, with respect to a volume of the reaction layer after drying.
  • the porosity of the reaction layer was about 79.5%.
  • An aqueous solution containing potassium ferricyanide was prepared, which was dropped and dried on the electrodes on the base plate 1 shown in FIG. 1 to form a first layer.
  • the content of potassium ferricyanide in the first layer was 1 mg per cm 2 .
  • an aqueous solution containing GOD and fine polymer particles same as those of Example 1 was prepared, which was dropped on the first layer and dried in a warm-air dryer at 50° C. for 10 minutes to form a second layer.
  • the obtained second layer contained 1.0 mg of the fine polymer particles and 0.1 mg of GOD, per cm 2 of the second layer.
  • the first and second layers were formed to function as the reaction layer 7 .
  • Example 2 In the same manner as Example 1, the response current value of the sensor with respect to a standardized glucose solution was measured. As a result, the response current value showed favorable linearity with respect to the glucose concentration in both of the measurements for 30 seconds and 10 seconds. The porosity of the reaction layer was about 79%.
  • Example 2 In the same manner as Example 1, the response current value of the sensor with respect to a standardized glucose solution was measured. As a result, the response current value and the glucose concentration showed favorable linearity in the measurement for 30 seconds. However, the linearity was not obtained with respect to glucose of high concentration in the measurement for 10 seconds.
  • An aqueous solution containing fine particles of amorphous silicon having an average diameter of 0.3 ⁇ m, potassium ferricyanide and GOD was prepared.
  • the reaction layer 7 was formed on the electrodes on the base plate 1 shown in FIG. 1 in the same manner as Example 1.
  • the reaction layer 7 contained 1.5 mg of the fine particles, 1 ⁇ g of potassium ferricyanide and 0.05 ⁇ g of GOD, per cm 2 .
  • Example 2 In the same manner as Example 1, the response current value of the sensor with respect to a standardized glucose solution was measured. As a result, the response current value showed favorable linearity with respect to the glucose concentration in both of the measurements for 30 seconds and 10 seconds. The porosity of the reaction layer was about 74.5%.
  • An aqueous solution containing potassium ferricyanide was prepared, which was dropped and dried on the electrodes on the base plate 1 shown in FIG. 1 to form a first layer.
  • the content of potassium ferricyanide in the first layer was 1 mg per cm 2 .
  • an aqueous solution containing GOD and fine particles of amorphous silicon same as those in Example 3 was prepared, which was dropped on the first layer and dried in a warm-air dryer at 50° C. for 10 minutes to form a second layer.
  • the content of the fine polymer particles was 1.5 mg and the GOD content was 0.1 mg, per cm 2 .
  • the first and second layers were formed to function as the reaction layer 7 .
  • Example 2 In the same manner as Example 1, the response current value of the sensor with respect to a standardized glucose solution was measured. As a result, the response current value showed favorable linearity with respect to the glucose concentration in both of the measurements for 30 seconds and 10 seconds. The porosity of the reaction layer was about 74%.
  • An aqueous solution containing potassium ferricyanide was prepared, which was dropped and dried on the electrodes on the base plate 1 shown in FIG. 1 to form a first layer.
  • the content of potassium ferricyanide in the first layer was 1 mg per cm 2 .
  • Example 2 In the same manner as Example 1, the response current value of the sensor with respect to a standardized glucose solution-was measured. The response current value was dependent on the glucose concentration in both of the measurements for 30 seconds and 10 seconds. However, when plural sensors were subjected to the measurement of the response current value with respect to the same standardized glucose solution, the response current values were varied in a wide range.
  • a cholesterol sensor was fabricated in the same manner as the production of the glucose sensor and the response current value of the sensor with respect to a sample solution containing cholesterol was measured. As a result, the response current value showed favorable linearity with respect to the cholesterol concentration in the measurements for 3 minutes and 1 minute.
  • FIG. 5 shows the response characteristics of the sensors of this example and Comparative Example 3 in the measurement for 10 seconds.
  • the porosity of the above reaction layer was about 74.5%.
  • reaction layer 7 contained 1 mg of potassium ferricyanide, 0.1 mg of cholesterol oxidase and 0.05 mg of cholesterol esterase, per cm 2 of the reaction layer 7 .
  • reaction layer 7 On a platinum electrode system formed on the base plate 1 shown in FIG. 1, an aqueous solution containing glucose oxidase (GOD) and fine particles (beads) of polystylene having an average diameter of 0.8 ⁇ m was dropped to form a reaction layer 7 .
  • the obtained reaction layer 7 contained 0.03 mg of GOD and 1.5 mg of the fine particles, per cm 2 of the reaction layer.
  • a sample solution containing glucose was supplied.
  • Glucose in the sample solution was oxidized by GOD to generate hydrogen peroxide.
  • a voltage of +1.0V with respect to the counter electrode 5 was applied to the working electrode 4 to measure a current value after 5 seconds. This current value was proportional to the substrate concentration in the sample solution, from which the glucose concentration in the sample solution was obtained.
  • the effective size of the fine particles is in the range of not smaller than 0.1 ⁇ m and not larger than 1 ⁇ m.
  • the response characteristic of the sensor becomes very favorable even in measuring a sample solution containing various components such as hemocytes and protein, e.g., blood.
  • the present invention is also applicable to other sensors such as a glucose or cholesterol sensor using other enzymes, a lactic acid sensor, a fructose sensor, a sucrose sensor, an alcohol sensor, an ascorbic acid sensor and the like.

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  • Measuring Or Testing Involving Enzymes Or Micro-Organisms (AREA)
US10/452,936 2002-06-03 2003-06-03 Biosensor Abandoned US20040020777A1 (en)

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JP2002161740 2002-06-03

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Cited By (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040157339A1 (en) * 1997-12-22 2004-08-12 Burke David W. System and method for analyte measurement using AC excitation
US20040157337A1 (en) * 1997-12-22 2004-08-12 Burke David W. System and method for analyte measurement using AC phase angle measurements
US20040259180A1 (en) * 2003-06-20 2004-12-23 Burke David W. System and method for analyte measurement employing maximum dosing time delay
US20040256248A1 (en) * 2003-06-20 2004-12-23 Burke David W. System and method for analyte measurement using dose sufficiency electrodes
US20050008537A1 (en) * 2003-06-20 2005-01-13 Dan Mosoiu Method and reagent for producing narrow, homogenous reagent stripes
US20050016846A1 (en) * 2003-06-20 2005-01-27 Henning Groll System and method for coding information on a biosensor test strip
US20050019945A1 (en) * 2003-06-20 2005-01-27 Henning Groll System and method for coding information on a biosensor test strip
US20050019212A1 (en) * 2003-06-20 2005-01-27 Bhullar Raghbir S. Test strip with flared sample receiving chamber
US20050103624A1 (en) * 1999-10-04 2005-05-19 Bhullar Raghbir S. Biosensor and method of making
US20050221276A1 (en) * 2002-10-11 2005-10-06 Case Western Reserve University Sensor system
US20050236361A1 (en) * 2001-11-16 2005-10-27 Stefan Ufer Biomedical electrochemical sensor array and method of fabrication
US20050284758A1 (en) * 2004-06-18 2005-12-29 Tom Funke Novel electrode design for biosensor
US20070131548A1 (en) * 2005-12-12 2007-06-14 Nova Biomedical Corporation Disposable urea sensor and system for determining creatinine and urea nitrogen-to-creatinine ratio in a single device
US20070278097A1 (en) * 2003-06-20 2007-12-06 Bhullar Raghbir S Biosensor with laser-sealed capillary space and method of making
US7569126B2 (en) 2004-06-18 2009-08-04 Roche Diagnostics Operations, Inc. System and method for quality assurance of a biosensor test strip
US7604721B2 (en) 2003-06-20 2009-10-20 Roche Diagnostics Operations, Inc. System and method for coding information on a biosensor test strip
US7645421B2 (en) 2003-06-20 2010-01-12 Roche Diagnostics Operations, Inc. System and method for coding information on a biosensor test strip
US7718439B2 (en) 2003-06-20 2010-05-18 Roche Diagnostics Operations, Inc. System and method for coding information on a biosensor test strip
US20100170807A1 (en) * 2003-06-20 2010-07-08 Diebold Eric R System and method for determining the concentration of an analyte in a sample fluid
US8071384B2 (en) 1997-12-22 2011-12-06 Roche Diagnostics Operations, Inc. Control and calibration solutions and methods for their use
US8206565B2 (en) 2003-06-20 2012-06-26 Roche Diagnostics Operation, Inc. System and method for coding information on a biosensor test strip
US20190078131A1 (en) * 2007-12-10 2019-03-14 Ascensia Diabetes Care Holdings Ag Method of Determining An Analyte Concentration in a Sample
WO2022079555A1 (fr) * 2020-10-12 2022-04-21 BIOMETRICA S.r.l. Capteur physiologique électrochimique

Families Citing this family (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9493805B2 (en) 2001-06-01 2016-11-15 Colorado State University Research Foundation Enzymatic biosensors with enhanced activity retention for detection of organic compounds
US9493806B2 (en) 2001-06-01 2016-11-15 Colorado State University Research Foundation Enzymatic biosensing systems
JPWO2006057225A1 (ja) * 2004-11-25 2008-06-05 松下電器産業株式会社 センサデバイス
US9796998B2 (en) 2007-04-09 2017-10-24 Colorado State University Research Foundation Oxygenase-based biosensing systems for measurement of halogenated alkene concentrations
US10024797B2 (en) 2010-11-22 2018-07-17 Colorado State University Research Foundation Biosensing systems for measurement of lactose
WO2013019982A2 (fr) 2011-08-02 2013-02-07 Colorado State University Research Foundation Système de biocaptage avec durée de vie prolongée via un recyclage de cofacteur
GB2588780A (en) * 2019-11-06 2021-05-12 Georgia Bousiakou Lida Biocompatible electrodes for electro-chemical biosensors

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5171689A (en) * 1984-11-08 1992-12-15 Matsushita Electric Industrial Co., Ltd. Solid state bio-sensor
US5185256A (en) * 1985-06-21 1993-02-09 Matsushita Electric Industrial Co., Ltd. Method for making a biosensor
US5589347A (en) * 1986-12-18 1996-12-31 Fuji Photo Film Co., Ltd. Multilayer analysis elements for the determination of total cholesterol
US6117289A (en) * 1996-12-20 2000-09-12 Matsushita Electric Industrial Co., Ltd. Cholesterol sensor and method for producing the same
US20040146958A1 (en) * 2001-07-07 2004-07-29 Byung-Woo Bae Glucose strip sensor and glucose measurement using the glucose strip sensor

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB8817997D0 (en) * 1988-07-28 1988-09-01 Cambridge Life Sciences Enzyme electrodes & improvements in manufacture thereof
JP3272882B2 (ja) * 1994-09-22 2002-04-08 松下電器産業株式会社 バイオセンサおよびその製造方法
US6627057B1 (en) * 1999-12-23 2003-09-30 Roche Diagnostic Corporation Microsphere containing sensor
JP4184074B2 (ja) * 2000-07-31 2008-11-19 松下電器産業株式会社 バイオセンサ

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5171689A (en) * 1984-11-08 1992-12-15 Matsushita Electric Industrial Co., Ltd. Solid state bio-sensor
US5185256A (en) * 1985-06-21 1993-02-09 Matsushita Electric Industrial Co., Ltd. Method for making a biosensor
US5589347A (en) * 1986-12-18 1996-12-31 Fuji Photo Film Co., Ltd. Multilayer analysis elements for the determination of total cholesterol
US6117289A (en) * 1996-12-20 2000-09-12 Matsushita Electric Industrial Co., Ltd. Cholesterol sensor and method for producing the same
US20040146958A1 (en) * 2001-07-07 2004-07-29 Byung-Woo Bae Glucose strip sensor and glucose measurement using the glucose strip sensor

Cited By (62)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040157337A1 (en) * 1997-12-22 2004-08-12 Burke David W. System and method for analyte measurement using AC phase angle measurements
US8071384B2 (en) 1997-12-22 2011-12-06 Roche Diagnostics Operations, Inc. Control and calibration solutions and methods for their use
US20040157339A1 (en) * 1997-12-22 2004-08-12 Burke David W. System and method for analyte measurement using AC excitation
US8551308B2 (en) 1999-10-04 2013-10-08 Roche Diagnostics Operations, Inc. Biosensor and method of making
US8287703B2 (en) 1999-10-04 2012-10-16 Roche Diagnostics Operations, Inc. Biosensor and method of making
US20090020502A1 (en) * 1999-10-04 2009-01-22 Bhullar Raghbir S Biosensor and method of making
US20050103624A1 (en) * 1999-10-04 2005-05-19 Bhullar Raghbir S. Biosensor and method of making
US20060006141A1 (en) * 2001-11-16 2006-01-12 Stefan Ufer Biomedical electrochemical sensor array and method of fabrication
US20050236361A1 (en) * 2001-11-16 2005-10-27 Stefan Ufer Biomedical electrochemical sensor array and method of fabrication
US20050221276A1 (en) * 2002-10-11 2005-10-06 Case Western Reserve University Sensor system
US7964390B2 (en) * 2002-10-11 2011-06-21 Case Western Reserve University Sensor system
US7749437B2 (en) 2003-06-20 2010-07-06 Roche Diagnostics Operations, Inc. Method and reagent for producing narrow, homogenous reagent stripes
US7892849B2 (en) 2003-06-20 2011-02-22 Roche Diagnostics Operations, Inc. Reagent stripe for test strip
US8679853B2 (en) 2003-06-20 2014-03-25 Roche Diagnostics Operations, Inc. Biosensor with laser-sealed capillary space and method of making
US20050019945A1 (en) * 2003-06-20 2005-01-27 Henning Groll System and method for coding information on a biosensor test strip
US8663442B2 (en) 2003-06-20 2014-03-04 Roche Diagnostics Operations, Inc. System and method for analyte measurement using dose sufficiency electrodes
US20070278097A1 (en) * 2003-06-20 2007-12-06 Bhullar Raghbir S Biosensor with laser-sealed capillary space and method of making
US7452457B2 (en) 2003-06-20 2008-11-18 Roche Diagnostics Operations, Inc. System and method for analyte measurement using dose sufficiency electrodes
US20050016846A1 (en) * 2003-06-20 2005-01-27 Henning Groll System and method for coding information on a biosensor test strip
US20090045076A1 (en) * 2003-06-20 2009-02-19 Burke David W System and method for analyte measurement using dose sufficiency electrodes
US20090162532A1 (en) * 2003-06-20 2009-06-25 Dan Mosoiu Method and reagent for producing narrow, homogenous reagent strips
US8586373B2 (en) 2003-06-20 2013-11-19 Roche Diagnostics Operations, Inc. System and method for determining the concentration of an analyte in a sample fluid
US20040259180A1 (en) * 2003-06-20 2004-12-23 Burke David W. System and method for analyte measurement employing maximum dosing time delay
US7597793B2 (en) 2003-06-20 2009-10-06 Roche Operations Ltd. System and method for analyte measurement employing maximum dosing time delay
US7604721B2 (en) 2003-06-20 2009-10-20 Roche Diagnostics Operations, Inc. System and method for coding information on a biosensor test strip
US7645373B2 (en) 2003-06-20 2010-01-12 Roche Diagnostic Operations, Inc. System and method for coding information on a biosensor test strip
US7645421B2 (en) 2003-06-20 2010-01-12 Roche Diagnostics Operations, Inc. System and method for coding information on a biosensor test strip
US20100111764A1 (en) * 2003-06-20 2010-05-06 Henning Groll System and method for coding information on a biosensor test strip
US7718439B2 (en) 2003-06-20 2010-05-18 Roche Diagnostics Operations, Inc. System and method for coding information on a biosensor test strip
US7727467B2 (en) 2003-06-20 2010-06-01 Roche Diagnostics Operations, Inc. Reagent stripe for test strip
US20050016844A1 (en) * 2003-06-20 2005-01-27 Burke David W. Reagent stripe for test strip
US20100170807A1 (en) * 2003-06-20 2010-07-08 Diebold Eric R System and method for determining the concentration of an analyte in a sample fluid
US7829023B2 (en) 2003-06-20 2010-11-09 Roche Diagnostics Operations, Inc. Test strip with vent opening
US20110000610A1 (en) * 2003-06-20 2011-01-06 Burke David W Test strip with slot vent opening
US20110011738A1 (en) * 2003-06-20 2011-01-20 Burke David W Test strip with slot vent opening
US7879618B2 (en) 2003-06-20 2011-02-01 Roche Diagnostics Operations, Inc. Method and reagent for producing narrow, homogenous reagent strips
US20050019212A1 (en) * 2003-06-20 2005-01-27 Bhullar Raghbir S. Test strip with flared sample receiving chamber
US20050013731A1 (en) * 2003-06-20 2005-01-20 Burke David W. Test strip with slot vent opening
US8058077B2 (en) 2003-06-20 2011-11-15 Roche Diagnostics Operations, Inc. Method for coding information on a biosensor test strip
US20050008537A1 (en) * 2003-06-20 2005-01-13 Dan Mosoiu Method and reagent for producing narrow, homogenous reagent stripes
US8071030B2 (en) 2003-06-20 2011-12-06 Roche Diagnostics Operations, Inc. Test strip with flared sample receiving chamber
US8083993B2 (en) 2003-06-20 2011-12-27 Riche Diagnostics Operations, Inc. System and method for coding information on a biosensor test strip
US8507289B1 (en) 2003-06-20 2013-08-13 Roche Diagnostics Operations, Inc. System and method for coding information on a biosensor test strip
US8119414B2 (en) 2003-06-20 2012-02-21 Roche Diagnostics Operations, Inc. Test strip with slot vent opening
US8142721B2 (en) 2003-06-20 2012-03-27 Roche Diagnostics Operations, Inc. Test strip with slot vent opening
US8148164B2 (en) 2003-06-20 2012-04-03 Roche Diagnostics Operations, Inc. System and method for determining the concentration of an analyte in a sample fluid
US8206565B2 (en) 2003-06-20 2012-06-26 Roche Diagnostics Operation, Inc. System and method for coding information on a biosensor test strip
US8211379B2 (en) 2003-06-20 2012-07-03 Roche Diagnostics Operations, Inc. Test strip with slot vent opening
US8222044B2 (en) 2003-06-20 2012-07-17 Roche Diagnostics Operations, Inc. Test strip with flared sample receiving chamber
US20040256248A1 (en) * 2003-06-20 2004-12-23 Burke David W. System and method for analyte measurement using dose sufficiency electrodes
US8293538B2 (en) 2003-06-20 2012-10-23 Roche Diagnostics Operations, Inc. System and method for coding information on a biosensor test strip
US8298828B2 (en) 2003-06-20 2012-10-30 Roche Diagnostics Operations, Inc. System and method for determining the concentration of an analyte in a sample fluid
US8092668B2 (en) 2004-06-18 2012-01-10 Roche Diagnostics Operations, Inc. System and method for quality assurance of a biosensor test strip
US7569126B2 (en) 2004-06-18 2009-08-04 Roche Diagnostics Operations, Inc. System and method for quality assurance of a biosensor test strip
US7556723B2 (en) 2004-06-18 2009-07-07 Roche Diagnostics Operations, Inc. Electrode design for biosensor
US20050284758A1 (en) * 2004-06-18 2005-12-29 Tom Funke Novel electrode design for biosensor
US9410915B2 (en) 2004-06-18 2016-08-09 Roche Operations Ltd. System and method for quality assurance of a biosensor test strip
US8617366B2 (en) * 2005-12-12 2013-12-31 Nova Biomedical Corporation Disposable urea sensor and system for determining creatinine and urea nitrogen-to-creatinine ratio in a single device
US20070131548A1 (en) * 2005-12-12 2007-06-14 Nova Biomedical Corporation Disposable urea sensor and system for determining creatinine and urea nitrogen-to-creatinine ratio in a single device
US20190078131A1 (en) * 2007-12-10 2019-03-14 Ascensia Diabetes Care Holdings Ag Method of Determining An Analyte Concentration in a Sample
WO2022079555A1 (fr) * 2020-10-12 2022-04-21 BIOMETRICA S.r.l. Capteur physiologique électrochimique
EP3981330A3 (fr) * 2020-10-12 2022-06-29 Biometrica S.r.l. Capteur physiologique électrochimique

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