WO2002086483A1 - Biodetecteur - Google Patents
Biodetecteur Download PDFInfo
- Publication number
- WO2002086483A1 WO2002086483A1 PCT/JP2002/003600 JP0203600W WO02086483A1 WO 2002086483 A1 WO2002086483 A1 WO 2002086483A1 JP 0203600 W JP0203600 W JP 0203600W WO 02086483 A1 WO02086483 A1 WO 02086483A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- electrode
- biosensor
- supply path
- sample
- sample supply
- Prior art date
Links
- 239000000758 substrate Substances 0.000 claims abstract description 44
- 238000001514 detection method Methods 0.000 claims abstract description 39
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- 239000000523 sample Substances 0.000 claims description 76
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- 150000003839 salts Chemical class 0.000 description 3
- 238000007650 screen-printing Methods 0.000 description 3
- 238000004544 sputter deposition Methods 0.000 description 3
- AZQWKYJCGOJGHM-UHFFFAOYSA-N 1,4-benzoquinone Chemical compound O=C1C=CC(=O)C=C1 AZQWKYJCGOJGHM-UHFFFAOYSA-N 0.000 description 2
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 2
- 101710088194 Dehydrogenase Proteins 0.000 description 2
- 108091006149 Electron carriers Proteins 0.000 description 2
- 108010015776 Glucose oxidase Proteins 0.000 description 2
- KDLHZDBZIXYQEI-UHFFFAOYSA-N Palladium Chemical compound [Pd] KDLHZDBZIXYQEI-UHFFFAOYSA-N 0.000 description 2
- 230000009471 action Effects 0.000 description 2
- 229910052799 carbon Inorganic materials 0.000 description 2
- 230000008859 change Effects 0.000 description 2
- 238000006243 chemical reaction Methods 0.000 description 2
- 238000012790 confirmation Methods 0.000 description 2
- 238000000151 deposition Methods 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 229920001477 hydrophilic polymer Polymers 0.000 description 2
- JVTAAEKCZFNVCJ-UHFFFAOYSA-N lactic acid Chemical compound CC(O)C(O)=O JVTAAEKCZFNVCJ-UHFFFAOYSA-N 0.000 description 2
- 229910000510 noble metal Inorganic materials 0.000 description 2
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 2
- 229920000515 polycarbonate Polymers 0.000 description 2
- 239000004417 polycarbonate Substances 0.000 description 2
- VEPOHXYIFQMVHW-XOZOLZJESA-N 2,3-dihydroxybutanedioic acid (2S,3S)-3,4-dimethyl-2-phenylmorpholine Chemical compound OC(C(O)C(O)=O)C(O)=O.C[C@H]1[C@@H](OCCN1C)c1ccccc1 VEPOHXYIFQMVHW-XOZOLZJESA-N 0.000 description 1
- SMZOUWXMTYCWNB-UHFFFAOYSA-N 2-(2-methoxy-5-methylphenyl)ethanamine Chemical compound COC1=CC=C(C)C=C1CCN SMZOUWXMTYCWNB-UHFFFAOYSA-N 0.000 description 1
- NIXOWILDQLNWCW-UHFFFAOYSA-N 2-Propenoic acid Natural products OC(=O)C=C NIXOWILDQLNWCW-UHFFFAOYSA-N 0.000 description 1
- 108010024957 Ascorbate Oxidase Proteins 0.000 description 1
- 229920002134 Carboxymethyl cellulose Polymers 0.000 description 1
- 108010089254 Cholesterol oxidase Proteins 0.000 description 1
- LFQSCWFLJHTTHZ-UHFFFAOYSA-N Ethanol Chemical compound CCO LFQSCWFLJHTTHZ-UHFFFAOYSA-N 0.000 description 1
- 108010010803 Gelatin Proteins 0.000 description 1
- 206010052128 Glare Diseases 0.000 description 1
- 239000004366 Glucose oxidase Substances 0.000 description 1
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- CERQOIWHTDAKMF-UHFFFAOYSA-N Methacrylic acid Chemical compound CC(=C)C(O)=O CERQOIWHTDAKMF-UHFFFAOYSA-N 0.000 description 1
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- PCNDJXKNXGMECE-UHFFFAOYSA-N Phenazine Natural products C1=CC=CC2=NC3=CC=CC=C3N=C21 PCNDJXKNXGMECE-UHFFFAOYSA-N 0.000 description 1
- 239000004952 Polyamide Substances 0.000 description 1
- 108010039918 Polylysine Proteins 0.000 description 1
- 229920001328 Polyvinylidene chloride Polymers 0.000 description 1
- 229920002472 Starch Polymers 0.000 description 1
- 108010055297 Sterol Esterase Proteins 0.000 description 1
- 102000000019 Sterol Esterase Human genes 0.000 description 1
- XSQUKJJJFZCRTK-UHFFFAOYSA-N Urea Chemical compound NC(N)=O XSQUKJJJFZCRTK-UHFFFAOYSA-N 0.000 description 1
- 239000011543 agarose gel Substances 0.000 description 1
- 150000001413 amino acids Chemical class 0.000 description 1
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 1
- WQZGKKKJIJFFOK-VFUOTHLCSA-N beta-D-glucose Chemical compound OC[C@H]1O[C@@H](O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-VFUOTHLCSA-N 0.000 description 1
- 239000004202 carbamide Substances 0.000 description 1
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- 235000010948 carboxy methyl cellulose Nutrition 0.000 description 1
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- 239000008112 carboxymethyl-cellulose Substances 0.000 description 1
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- 239000008273 gelatin Substances 0.000 description 1
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- 229940116332 glucose oxidase Drugs 0.000 description 1
- 235000019420 glucose oxidase Nutrition 0.000 description 1
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 description 1
- 239000010931 gold Substances 0.000 description 1
- 229910052737 gold Inorganic materials 0.000 description 1
- 125000001475 halogen functional group Chemical group 0.000 description 1
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- 238000004020 luminiscence type Methods 0.000 description 1
- 238000003754 machining Methods 0.000 description 1
- FPYJFEHAWHCUMM-UHFFFAOYSA-N maleic anhydride Chemical compound O=C1OC(=O)C=C1 FPYJFEHAWHCUMM-UHFFFAOYSA-N 0.000 description 1
- CXKWCBBOMKCUKX-UHFFFAOYSA-M methylene blue Chemical compound [Cl-].C1=CC(N(C)C)=CC2=[S+]C3=CC(N(C)C)=CC=C3N=C21 CXKWCBBOMKCUKX-UHFFFAOYSA-M 0.000 description 1
- 229960000907 methylthioninium chloride Drugs 0.000 description 1
- 229920001778 nylon Polymers 0.000 description 1
- 229910052760 oxygen Inorganic materials 0.000 description 1
- 239000001301 oxygen Substances 0.000 description 1
- 229910052763 palladium Inorganic materials 0.000 description 1
- 238000007747 plating Methods 0.000 description 1
- 229910052697 platinum Inorganic materials 0.000 description 1
- 229920001308 poly(aminoacid) Polymers 0.000 description 1
- 229920000172 poly(styrenesulfonic acid) Polymers 0.000 description 1
- 229920002647 polyamide Polymers 0.000 description 1
- 229920000656 polylysine Polymers 0.000 description 1
- 229940005642 polystyrene sulfonic acid Drugs 0.000 description 1
- 239000004800 polyvinyl chloride Substances 0.000 description 1
- 229920000915 polyvinyl chloride Polymers 0.000 description 1
- 239000005033 polyvinylidene chloride Substances 0.000 description 1
- 238000007639 printing Methods 0.000 description 1
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- KKEYFWRCBNTPAC-UHFFFAOYSA-L terephthalate(2-) Chemical compound [O-]C(=O)C1=CC=C(C([O-])=O)C=C1 KKEYFWRCBNTPAC-UHFFFAOYSA-L 0.000 description 1
- 238000007740 vapor deposition Methods 0.000 description 1
- 229920003169 water-soluble polymer Polymers 0.000 description 1
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 quantifying a substrate contained in a sample solution.
- a biosensor is a sensor that utilizes the molecular recognition capability of biological materials such as microorganisms, enzymes, antibodies, DNA, and RNA, and applies biological materials as molecular identification elements. In other words, it utilizes reactions that occur when the immobilized biological material recognizes the target substrate, consumption of oxygen by respiration of microorganisms, enzymatic reactions, and luminescence.
- enzyme sensors are being put to practical use. For example, enzyme sensors for darcos, lactic acid, urea, and amino acids are used in the medical measurement and food industries.
- an enzyme sensor reduces an electron acceptor by electrons generated by a reaction between a substrate and an enzyme contained in a sample solution, and a measuring device electrochemically measures the reduction amount of the electron acceptor.
- the sample is quantitatively analyzed.
- a biosensor there is, for example, a sensor proposed in PCT / JP00 / 08012.
- a measurement electrode 2 (also referred to as a working electrode) made of an electrically conductive substance, a counter electrode 3 and a detection electrode 4 are placed in close proximity on an insulating substrate 1 such as polyethylene terephthalate.
- a reagent layer 5 containing an enzyme, an electron carrier, a water-soluble polymer, etc., which reacts specifically with a specific component in the sample solution is formed on these electrodes.
- a spacer 6 having a cutout for forming a specimen supply path 7 and a cover 8 (second insulating substrate) having an air hole 9 are laminated and bonded thereon.
- one end of the cutout portion of the spacer 6 communicates with an air hole 9 provided in the cover 8.
- a sample aspiration confirmation system for measuring the content of a substrate in a sample solution as a sample using the conventional biosensor configured as described above will be described below.
- a sample solution is supplied to the inlet of the sample supply path 7 with a constant voltage applied between the counter electrode 3 or the measurement electrode 2 and the detection electrode 4 by a measurement device (not shown) connected to the biosensor. I do.
- the sample solution is sucked into the sample supply channel ⁇ ⁇ ⁇ by capillary action, passes over the counter electrode 3 and the measurement electrode 2, reaches the detection electrode 4, and starts dissolution of the reagent layer 5.
- the measuring device detects an electrical change occurring between the counter electrode 3 or the measuring electrode 2 and the detecting electrode 4, and starts the measuring operation.
- the counter electrode 3, the measurement electrode 2, and the detection electrode 4 are arranged close to each other. For example, as shown in FIG. 5 and FIG. If a sufficient amount of sample liquid is not supplied to the passage 7, the sample liquid will reach the detection electrode 4 without completely covering the measuring electrode 2, and the measurement operation will start. Since it was started, the response value was lower than that in Fig. 7 in which the sample liquid was sufficiently filled, and the performance of the biosensor deteriorated. Note that, in the plan views of FIGS. 5 to 7, the reagent layer 5 is not shown for easy viewing of the drawings.
- the present invention has been made in order to solve the above-mentioned problems, and by improving the position and shape of the arrangement of the detection electrodes, the accuracy of sample detection is increased, and a high-performance biosensor with good measurement accuracy is provided.
- the purpose is to provide. Disclosure of the invention
- a biosensor provides an electrode comprising: a first insulating substrate and a second insulating substrate; and at least a measuring electrode, a counter electrode, and a detecting electrode.
- the electrode section, the sample supply path And the reagent are present between the first insulating substrate and the second insulating substrate, and the electrode unit is one of the first insulating substrate and the second insulating substrate.
- the shape of the detection electrode of the biosensor can be such that the central portion of the detection electrode protrudes in the sample supply path so as to be located closest to the measurement electrode. Roughly, both ends of the detection electrode may be formed at positions farther from the measurement electrode than the central portion. '
- the shape of the detection electrode may be a shape protruding toward the entrance of the sample supply path at a central position in the sample supply path.
- the shape of the detection electrodes located in these sample supply paths can be V-shaped, U-shaped, or convex.
- FIG. 1 is an exploded perspective view and a plan view of a biosensor according to an embodiment 1 of the present invention.
- FIG. 2 is an exploded perspective view and a plan view showing another example of the biosensor according to the embodiment of the present invention.
- FIG. 3 is an exploded perspective view and a plan view showing an example in which air holes according to the embodiment of the present invention are arranged in a sample supply path.
- FIG. 4 is an exploded perspective view and a plan view of a conventional biosensor.
- FIG. 5 is a diagram showing a pattern in which a sample liquid has been introduced into the sample supply path.
- FIG. 6 is a diagram showing a pattern in which a sample liquid has been introduced into the sample supply path.
- FIG. 7 is a view showing a pattern in which the sample liquid has been sufficiently introduced into the sample supply path.
- FIG. 1 is an exploded perspective view and a top view of a biosensor according to the present embodiment.
- reference numeral 1 denotes a first insulating substrate, on which a measuring electrode 2, a counter electrode 3, and a detecting electrode 4 made of an electrically conductive substance are formed. ing.
- the main difference from the conventional biosensor is that the detection electrode 4 is formed at a predetermined distance from the counter electrode 3 and the measurement electrode 2 in the sample supply path 7. Is a point.
- the predetermined distance is a distance that can completely cover the measurement electrode 2 from the time when the sample liquid is supplied to the sample supply path 7 to the time when the sample liquid reaches the detection electrode 4. This can be arbitrarily set according to the width of the sample supply path.
- the predetermined shape means that the shape of the detection electrode 4 is closest to the measurement electrode 2 at the central portion in the sample supply path 7! It is desirable that the shape be located at a position farther than the central portion at both ends of the sample supply path 7.
- Examples of such a shape include a V-shape, a U-shape, a convex shape, and a combination thereof. Among them, the V-shape is the most preferable.
- the space between the measurement electrode 2 and the detection electrode 4 does not function as an electrode, but may be used as a part of the counter electrode 3 as shown in FIG.
- the detection electrode 4 can function not only as an electrode for detecting a shortage of a sample amount but also as a part of a counter electrode.
- FIG. 1 shows an arrangement in which the above-mentioned electrodes are arranged on a first insulating substrate. These electrodes are formed not only on the first insulating substrate 1 but also on a second insulating substrate. It may be arranged separately on the conductive substrate 8.
- suitable materials for the first insulating substrate 1 and the second insulating substrate 8 include polyethylene terephthalate, polycarbonate, polyimide, and the like.
- Examples of the electrically conductive substance constituting each electrode include simple materials such as noble metals such as gold, platinum and palladium, and carbon, and composite materials such as carbon paste and noble metal paste.
- the electrically conductive layer can be easily formed on the first insulating substrate 1 or the second insulating substrate 8 by the sputtering vapor deposition method, and in the latter case, by the screen printing method. Can be.
- the electric conductive layer is formed on the entire surface or a part of the first insulating substrate 1 or the second insulating substrate 8 by the above-described sputtering deposition method, screen printing method, or the like.
- the electrodes can be divided and formed by providing slits using a laser or the like.
- the electrodes can be formed in a similar manner by a screen printing method using a printing plate or a mask plate on which an electrode pattern is formed in advance, a sputtering deposition method, or the like.
- a reagent layer 5 containing an enzyme, an electron carrier, a hydrophilic polymer, and the like is formed on the electrode thus formed.
- the enzymes include glucose oxidase, lactate oxidase, cholesterol oxidase, cholesterol esterase, pericase, ascorbate oxidase, bili / levin oxidase, glucose dehydrogenase, and ratate dehydrogenase.
- glucose oxidase lactate oxidase
- cholesterol oxidase cholesterol esterase
- pericase ascorbate oxidase
- bili / levin oxidase glucose dehydrogenase
- ratate dehydrogenase ratate dehydrogenase.
- p-benzoquinone and its derivatives phenazine methosolephate, methylene blue, phlegmene and its derivatives can be used in addition to the ferricyanidation medium.
- hydrophilic polymers include carboxymethylcellulose, hydroxyethylenosenorelose, hydroxypropinoresenorelose, methinoresenorelose, etinolecellulose, etinolehydroxochetinoresenorelose, and canoleoxymethyl.
- Polyamino acids such as etinoresenorelol, polyvinylinoreal alcohol, polyvinylinopyrrolidone, and polylysine; polystyrenesulfonic acid; gelatin and its derivatives; Acrylic acid and its salts, methacrylic acid and its salts, starch and its derivatives, maleic anhydride and its salts, agarose gel and its derivatives, and the like can be used.
- the first insulating substrate 1 and the second insulating substrate 8 are bonded to a spacer 6 having a notch to form a sample supply path 7 to which a sample liquid is supplied. .
- the width of the sample supply path 7 should be in the range of 0.5 to 2.0 mm, and the thickness of the spacer 6 should be small. (Height) is preferably in the range of 0.05 mm to 0.3 mm.
- suitable materials for the spacer 6 include polyethylene terephthalate, polycarbonate, polyimide, polybutyrene terephthalate, polyamide, polyvinyl chloride, polyvinylidene chloride, polyimide, and nylon.
- sample supply path 7 may be formed by bonding the integrated second insulating substrate 8 and spacer 6 to the first insulating substrate 1.
- the reagent layer 5 may be disposed in the sample supply path 7 to which the sample liquid is supplied as long as the performance of the biosensor is not deteriorated other than being arranged on the entire surface or a part of the electrode. It may be placed at the position of the deviation or deviation.
- the reagent layer 5 is present on or near the detection electrode 4.
- the supply of the sample liquid to the biosensor composed of such a sample supply path 7 is realized by a capillary phenomenon, but in order to realize a smooth supply of the sample liquid, the sample sensor is supplied inside the sample supply path 7 to the outside of the biosensor. Air holes 9 are required to allow air to escape.
- the arrangement of the air holes may be anywhere in the specimen supply path 7 as long as the supply of the sample liquid is not hindered.
- the size of the air hole 9 may be any size as long as it allows air to smoothly escape.
- the shape of the detection electrode as shown in FIG. 3 is most preferable because the sample liquid is easily guided along the edge of the sample supply path. In FIG. 3, an arc-shaped slit is formed around the reagent dropping position.
- a slit 14 in the form of a wavy arc is provided at the tip end of the sensor, and a slit 15 is provided at the back of the supply path, so that the reagent layer 5 is formed when the reagent layer 5 is formed. It facilitates regulation of spread.
- the arc-shaped slit has a higher effect of reagent regulation than the arc-shaped slit disclosed in the above-mentioned PCT application.
- Examples of such a method for hydrophilization include spreading a surfactant or the like on the first insulating substrate 1 or the second insulating substrate 8 itself and the surface thereof, or using a sand-plast treatment, an electric discharge machining, There are methods such as roughening the surface of the substrate material by non-glare treatment, matte treatment, and chemical plating.
- a sample aspiration confirmation system for measuring the content of a substrate in a sample liquid as a sample using the biosensor configured as described above will be described below.
- a sample solution is supplied to the inlet of the sample supply path with a constant voltage applied between the counter electrode or the measurement electrode and the detection electrode by a measurement device (not shown) connected to the biosensor.
- the sample liquid is sucked into the sample supply channel by capillary action, passes over the counter electrode and the measurement electrode, reaches the detection electrode, and begins to dissolve the reagent layer.
- the measuring device detects an electrical change occurring between the counter electrode or the measuring electrode and the detecting electrode, and starts the measuring operation.
- an enzyme sensor has been described as an example of a biosensor.
- the present invention relates to a molecular identification element that specifically reacts with a specific component in a sample solution.
- the present invention can be similarly applied to biosensors used for microorganisms, DNA, RNA, and the like. Industrial applicability
- the detection accuracy of the introduction of the sample liquid into the sample supply path by the detection electrode can be dramatically improved, and a high-performance biosensor with less measurement error can be provided.
- sample liquid necessary for biosensor measurement Therefore, it is possible to provide a biosensor for small specimens that has high user operability.
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2002583962A JP4120400B2 (ja) | 2001-04-16 | 2002-04-11 | バイオセンサ |
EP02718528.9A EP1281955B1 (en) | 2001-04-16 | 2002-04-11 | Biosensor |
US12/823,676 US8475638B2 (en) | 2001-04-16 | 2010-06-25 | Biosensor |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2001116580 | 2001-04-16 | ||
JP2001-116580 | 2001-04-16 |
Related Child Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10297888 A-371-Of-International | 2002-04-11 | ||
US12/823,676 Continuation US8475638B2 (en) | 2001-04-16 | 2010-06-25 | Biosensor |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2002086483A1 true WO2002086483A1 (fr) | 2002-10-31 |
Family
ID=18967297
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/JP2002/003600 WO2002086483A1 (fr) | 2001-04-16 | 2002-04-11 | Biodetecteur |
Country Status (5)
Country | Link |
---|---|
US (2) | US20030175946A1 (ja) |
EP (2) | EP1281955B1 (ja) |
JP (1) | JP4120400B2 (ja) |
CN (1) | CN100401050C (ja) |
WO (1) | WO2002086483A1 (ja) |
Cited By (13)
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JP2007524824A (ja) * | 2003-06-20 | 2007-08-30 | エフ ホフマン−ラ ロッシュ アクチェン ゲゼルシャフト | テストストリップ用の試薬ストライプ |
JP2007524826A (ja) * | 2003-06-20 | 2007-08-30 | エフ ホフマン−ラ ロッシュ アクチェン ゲゼルシャフト | 用量充足電極を使用する検体測定のためのシステムおよび方法 |
JP2009063577A (ja) * | 2007-09-04 | 2009-03-26 | Lifescan Inc | 試薬の被着を改善した分析用の試験片 |
WO2009057793A1 (ja) * | 2007-10-31 | 2009-05-07 | Arkray, Inc. | 分析用具、分析装置、試料不足の検知方法および試料分析方法 |
JP2009533686A (ja) * | 2006-04-11 | 2009-09-17 | ホーム ダイアグナスティックス,インコーポレーテッド | バイオセンサ製造方法 |
US7867369B2 (en) | 2003-06-20 | 2011-01-11 | Roche Diagnostics Operations, Inc. | Biosensor with multiple electrical functionalities |
US8071030B2 (en) | 2003-06-20 | 2011-12-06 | Roche Diagnostics Operations, Inc. | Test strip with flared sample receiving chamber |
WO2012114706A1 (ja) * | 2011-02-23 | 2012-08-30 | パナソニック株式会社 | 生体試料測定装置 |
US8287703B2 (en) | 1999-10-04 | 2012-10-16 | Roche Diagnostics Operations, Inc. | Biosensor and method of making |
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 |
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US8999124B2 (en) | 2010-03-03 | 2015-04-07 | Nippon Kayaku Kabushiki Kaisha | Detection device |
US9410915B2 (en) | 2004-06-18 | 2016-08-09 | Roche Operations Ltd. | System and method for quality assurance of a biosensor test strip |
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US8071384B2 (en) | 1997-12-22 | 2011-12-06 | Roche Diagnostics Operations, Inc. | Control and calibration solutions and methods for their use |
US7073246B2 (en) | 1999-10-04 | 2006-07-11 | Roche Diagnostics Operations, Inc. | Method of making a biosensor |
US6814844B2 (en) * | 2001-08-29 | 2004-11-09 | Roche Diagnostics Corporation | Biosensor with code pattern |
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US7645373B2 (en) | 2003-06-20 | 2010-01-12 | Roche Diagnostic Operations, Inc. | System and method for coding information on a biosensor test strip |
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Also Published As
Publication number | Publication date |
---|---|
JP4120400B2 (ja) | 2008-07-16 |
US8475638B2 (en) | 2013-07-02 |
US20100258438A1 (en) | 2010-10-14 |
US20030175946A1 (en) | 2003-09-18 |
EP1281955B1 (en) | 2013-06-05 |
CN1461410A (zh) | 2003-12-10 |
EP1281955A1 (en) | 2003-02-05 |
CN100401050C (zh) | 2008-07-09 |
EP1281955A4 (en) | 2009-07-22 |
EP2230508A1 (en) | 2010-09-22 |
JPWO2002086483A1 (ja) | 2004-08-12 |
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