WO2002093151A1 - Biocapteur - Google Patents
Biocapteur Download PDFInfo
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- WO2002093151A1 WO2002093151A1 PCT/JP2002/004624 JP0204624W WO02093151A1 WO 2002093151 A1 WO2002093151 A1 WO 2002093151A1 JP 0204624 W JP0204624 W JP 0204624W WO 02093151 A1 WO02093151 A1 WO 02093151A1
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- WIPO (PCT)
- Prior art keywords
- acid
- salt
- biosensor
- buffer
- glucose
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Classifications
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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
- C12Q1/005—Enzyme electrodes involving specific analytes or enzymes
- C12Q1/006—Enzyme electrodes involving specific analytes or enzymes for glucose
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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
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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
- C12Q1/54—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions involving glucose or galactose
Definitions
- the present invention relates to a biosensor for quickly and easily quantifying a specific component in a sample.
- a method for quantifying glucose will be described as an example of a method for quantifying components in a sample solution.
- a method of electrochemically determining glucose a method of using glucose oxidase in combination with an oxygen electrode or a hydrogen peroxide electrode is generally well known (for example, Shuichi Suzuki, "Biosensor”). I) Kodansha).
- Glucose oxidase uses oxygen as an electron carrier to selectively oxidize the substrate glucose to dalconolactone. In the presence of oxygen, oxygen is reduced to hydrogen peroxide during the glucose oxidation reaction by glucose oxidase.
- the oxygen electrode measures the amount of oxygen reduction, or the hydrogen peroxide electrode measures the increase in hydrogen peroxide. Since the amount of decrease in oxygen and the amount of increase in hydrogen peroxide are proportional to the content of glucose in the sample solution, glucose can be determined from the amount of decrease in oxygen or the amount of increase in hydrogen peroxide.
- the measurement results are tested as can be inferred from the reaction process. It has the disadvantage of being affected by the concentration of oxygen contained in the sample solution, and cannot be measured if there is no oxygen in the sample solution.
- a glucose sensor instead of using oxygen as an electron carrier, a glucose sensor has been developed that uses an organic compound or metal complex such as potassium ferricyanide, a phenoctene derivative, or a quinone derivative as an electron carrier.
- an organic compound or metal complex such as potassium ferricyanide, a phenoctene derivative, or a quinone derivative
- the electron carrier reducer generated as a result of the enzymatic reaction is oxidized on the electrode, and the dalcos concentration in the sample solution can be determined from the oxidation current.
- these electron carriers are supported on an electrode together with glucose oxidase in an accurate amount and in a stable state, and a reagent is used. A layer can be formed.
- reagent layer can be integrated with the electrode system in a nearly dry state
- disposable glucose sensors based on these technologies have received much attention in recent years.
- a typical example is a biosensor disclosed in Japanese Patent No. 2517153.
- the glucose concentration can be easily measured by simply introducing a sample solution into a sensor detachably connected to the measuring instrument;
- a hydrophilic polymer such as carboxymethylcellulose
- This hydrophilic polymer binds the enzyme slowly to the electrode. It has the advantage of functioning as one.
- the presence of the hydrophilic polymer alters the catalytic activity of glucose oxidase or the thermodynamics of the hydrolysis of dalconolactone to dalconic acid, which is a product of the glucose oxidation reaction. Dalconoractone sometimes accumulated. When dalconolactone accumulates, the reverse reaction proceeds or the rate of glucose oxidation decreases.
- the amount of the reduced form of the electron carrier in a short reaction time decreases, and the magnitude of the response current of the sensor to glucose, that is, the sensitivity, decreases.
- the reaction time in order to obtain sufficient sensitivity for high-concentration glucose, it is necessary to increase the reaction time in order to generate a large amount of reductants of the electron carrier, and the time required for measurement is long. Tended to be.
- the present invention has been made in view of the above-mentioned conventional problems, and has as its object to provide a biosensor having high responsiveness and capable of quantifying a specific component in a sample quickly and with high sensitivity. Disclosure of the invention
- the biosensor of the present invention includes an electrically insulating substrate, an electrode system including a working electrode and a counter electrode disposed on the substrate, an oxidoreductase having a catalytic action on a reaction of oxidizing glucose to dalconolactone, and a darkonolactone.
- a reagent system comprising a buffer, wherein the buffer is phthalic acid and its salt, maleic acid and its salt, succinic acid and its salt, phosphoric acid and its salt, acetic acid and its salt, boric acid and its salt , Cunic acid and its salts, glycine, tris (hydroxymethyl) amino methane, piperazine-N, N'-bis (2-ethanesulfonic acid), N- (2-acetoamide) iminoniacetic acid, N, N- Bis (2-hydroxyethyl) -1-aminoethanesulfonic acid-2-morpholinoethanesulfonic acid, imidazole, dimethyldartaric acid It is selected from the group consisting of triethanolamine hydrochloride, collidine, N-tris (hydroxymethyl) methylglycine, and bis (2-hydroxyethyl) iminotris (hydroxymethyl) methane. BRIEF DESCRIPTION OF THE FIGURES
- FIG. 1 is a perspective view of a biosensor according to one embodiment of the present invention excluding a reagent system.
- FIG. 2 is a longitudinal sectional view of a main part of the biosensor.
- FIG. 3 is a response characteristic diagram of the biosensor.
- FIG. 4 is a longitudinal sectional view of a main part of a biosensor according to another embodiment of the present invention. '. BEST MODE FOR CARRYING OUT THE INVENTION
- the biosensor of the present invention includes an electrically insulating substrate, an electrode system including a working electrode and a counter electrode disposed on the substrate, an oxidoreductase having a catalytic action on a reaction of oxidizing glucose to dalconolactone, , And a test system containing a specific buffer.
- the buffer is phthalic acid, fumarate, maleic acid, maleate, succinic acid, succinate, phosphoric acid, phosphate, acetic acid, acetate, boric acid, boric acid Preferred are those selected from the group consisting of salts, citrate, citrate, glycine, tris (hydroxymethyl) aminomethane, and piperazine mono-N, N, -bis (2-ethanesulfonic acid).
- the buffer is N- (2-acetamido) iminoniacetic acid, N, N-bis (2-hydroxyethyl) -2-aminoethanesulfonic acid, 2-morpholinoe Sulfonic acid, imidazole, dimethyldaltaric acid, triethanolamine hydrochloride, collidine, N-tris (hydroxymethyl) methylglycine, bis (2-hydroxyshethyl) imino tris (hydroxymethyl) methane.
- dalconolactone produced by oxidizing glucose by the action of oxidoreductase is converted to dalconic acid by darconolactonase. Therefore, the glucose oxidation reaction proceeds easily, and sufficient responsiveness can be obtained even when the measurement time is short. Further, by adjusting the pH of the reaction system, the activity of the oxidoreductase or dalconolactonase contained in the biosensor can be improved, so that the response of the sensor is further improved.
- buffers from the viewpoint of sufficiently high solubility, fumaric acid, phthalate, maleic acid, maleate, succinic acid, succinate, and tris (hydroxymethyl) aminoaminomethane are preferred.
- the reagent system further includes an electron carrier.
- an electron carrier such as dissolved oxygen in the sample solution may be used as the electron carrier, it is preferable to include the electron carrier in the reagent system.
- electron carriers include metal complexes such as potassium ferricyanide, osmium toris (bipyridinium) and phenoctene derivatives, quinone derivatives such as P-benzoquinone, phenazine derivatives such as phenazine methsulfate, and methylene blue. Phenothiazine derivatives, nicotinamide dodenine dinucleotide, nicotinamide dodenine dinucleotide phosphate, and the like. One or more of these electron carriers are used.
- the reagent system further comprises a hydrophilic polymer.
- hydrophilic polymers include carboxyethylcellulose, hydroxyethylcellulose, hydroxypropylcellulose, methylcellulose, and ethylcellulose. Ethylhydroxyethylcellulose, carboxymethylethylcellulose, polyvinylpyrrolidone, Such as polyvinyl alcohol and polylysine Polyamino acid, polystyrene sulfonic acid, gelatin and derivatives thereof, polymer of acrylic acid or a salt thereof, polymer of methacrylic acid or a salt thereof, starch and derivatives thereof, polymer of maleic anhydride or a salt thereof, agarose gel and Its derivatives are preferably used.
- the hydrophilic polymer has an advantage that it functions as a binder for slowly immobilizing the enzyme on the electrode.
- a redox enzyme having a catalytic action on the glucose oxidation reaction, dalcononactonase, and a buffer may be supported on the sensor in a mixed state.
- the manufacturing process of the biosensor is simple, and the reagent layer can be easily formed.
- oxidoreductase and dalconolactonase are located in the vicinity, dalconolactone generated by the action of oxidoreductase is more rapidly converted to dalconic acid by dalconolactonase. Therefore, the oxidation reactivity of glucose is improved, and sufficient responsiveness can be obtained even when the measurement time is shorter.
- An oxidoreductase having a catalytic action on the glucose oxidation reaction and a daltonolactonase may be supported on the sensor separately from each other.
- a buffer suitable for each enzyme can be mixed with each enzyme or added to the vicinity of each enzyme, and the activity of each enzyme can be improved more efficiently.
- Darconolactonase is used for Escherichia coli, yeast, human, rat, bush, Aspergillus niger (A spergillusniger), Azotonok yuichi 'Vinelandy (A zotobactervine 1 andii), shodomonas, fluore Sense (Pseud om onasfluorescens), Zymomonas 'Mobilis, Zymomonas nas mo bi 1 is), Streptomyces' Koericolou
- it is derived from one selected from the group consisting of les (S trept omy cescoelicolor), Dinococcus'Deiococcusradiodurans', and Xylera 'Xy le 11 fastidiosa.
- those derived from Escherichia coli, yeast, or Aspergillus' niger are more preferable because they have high productivity and retain
- the buffer carrying amount of the sensor is 5 nmo 1 Zmm 2 or less.
- the sample to be measured should be capable of exhibiting sufficient activity without reducing the solubility of the oxidoreductase and dalconolactonase that have a catalytic effect on the glucose oxidation reaction.
- the pH of the solution can be adjusted.
- the loading amount is the above, the response value to glucose OmgZd1, that is, the blank response value is not increased, so that a highly reliable biosensor can be obtained.
- Further loading of the preferred buffer is 0. 1 ⁇ 3 nmo 1 / mm 2.
- a range of 5 to 1000 nmo 1 is preferred.
- the reagent layer contains a buffer
- the reagent layer formed by developing and drying the solution is smoothed.
- the reagent layer is formed by drying from the aqueous solution.
- the reagent layer becomes uneven due to coarsening of the reagent crystal and the like. In particular, it is remarkable when electronic media contains lithium ferricyanide.
- the reagent layer contains a buffer, a smooth layer without such irregularities can be obtained. The reason may be that the buffer produces finer crystals when the solution is dried.
- the reagent layer When supplying the sample solution to the sensor and dissolving the reagent layer in the sample solution, if the reagent layer has irregularities on the surface, air will intervene between the sample solution and the irregularities of the reagent layer, and the Bubbles may be generated in the dissolved sample solution. If bubbles are generated in the sample liquid, the sample liquid cannot move smoothly in the sample liquid supply path, which will hinder measurement.
- the inconvenience as described above can be solved by smoothing the reagent layer. Furthermore, since the reagent layer is smoothed, the volume or height in the sample liquid supply path can be reduced, and the amount of the sample liquid can be reduced.
- the buffering agent preferably has a buffering capacity in the pH range of 4 to 8.
- a buffering capacity in the pH range of 4 to 8.
- the oxidoreductase having a catalytic action on the glucose oxidation reaction is preferably selected from the group consisting of darcosoxidase, PQQ-dependent glucose dehydrogenase, NAD-dependent glucose dehydrogenase, and vilanose oxidase.
- the buffer has a buffering capacity in the pH range of 4 to 6.
- the buffer is pH 5-8. Those having a buffer capacity in the region are more preferable.
- the biosensor of the present invention further includes a cover member disposed on the substrate and forming a sample liquid supply path to the electrode system with the substrate.
- This configuration has the advantage that the sample amount can be regulated to a constant value.
- a buffer having low solubility it can be separated from the enzyme and supported on the cover member side.
- an amphiphilic compound described later is supported on a biosensor, the following advantages are obtained by separating the amphiphilic compound from the enzyme and supporting the amphiphilic compound on the side of the cover member. That is, to form a layer of the amphipathic compound, a method of applying an organic solvent solution of the amphipathic compound and drying is usually employed.
- the organic solvent in which the amphiphilic compound is dissolved may affect the enzyme. If the layer of the amphiphilic compound is formed separately from the layer containing the enzyme on the side of the cover, the influence of such an organic solvent on the enzyme can be avoided.
- the biosensor of the present invention may further include an amphiphilic compound in the reagent system.
- an amphiphilic compound lecithin, Triton X (TritonX) —100 and the like are particularly preferable.
- the sample liquid supply path of the sensor is hydrophilically treated by the amphipathic action of the amphipathic compound, so that the sample liquid such as blood enters the sample liquid supply path. It is supplied quickly, and furthermore, it is possible to prevent bubbles from being generated in the sample liquid supply path.
- Samples that can be used in the biosensor of the present invention include blood, plasma, serum, aqueous glucose, culture, and fermentation.
- the present invention will be described with reference to Examples, but the present invention is not limited thereto.
- FIG. 1 is an exploded perspective view of the glucose sensor of the present embodiment from which the reagent system is removed.
- Electrically insulating group consisting of polyethylene terephthalate Silver paste was printed on board 1 by screen printing to form leads 2 and 3.
- a conductive carbon paste containing a resin binder was printed on the substrate 1 to form the working electrode 4.
- This working electrode 4 is in contact with the lead 2.
- an insulating paste was printed on the substrate 1 to form an insulating layer 6.
- the insulating layer 6 covers the outer periphery of the working electrode 4, thereby keeping the area of the exposed portion of the working electrode 4 constant.
- a conductive carbon paste containing a resin binder was printed on the substrate 1 so as to be in contact with the leads 3 to form a ring-shaped counter electrode 5.
- the middle cover 8 having the slit 10 and the upper cover 9 having the air hole 11 are positioned as shown by a dashed line in FIG.
- a biosensor was produced by bonding with a relationship.
- a sample liquid supply passage is formed at the slit 10 of the middle cover 8.
- the open end of the slit 10 at the end of the sensor serves as a sample supply port to the sample liquid supply path.
- FIG. 2 is a longitudinal sectional view of the biosensor according to the present embodiment.
- CMC carboxymethylcellulose
- the CMC layer 7a was formed.
- glucose oxidase a kind of redox enzyme having a catalytic action on the glucose oxidation reaction, ferricyanation force rhythm, one kind of electron carrier, and dalconolactonase derived from Aspergillus niger, was dissolved in 1 mM maleic acid buffer (pH 6).
- reagent system 7 consists of CMC layer 7a and reagent layer 7b.
- aqueous solution containing a fixed amount of glucose was used as a sample solution.
- the sample liquid was brought into contact with the open end of the slit 10 of the sensor, the sample liquid was introduced into the sample liquid supply path by capillary action.
- reaction time a voltage of 500 mV was applied to the working electrode 4 with reference to the counter electrode 5, and the current flowing between the working electrode 4 and the counter electrode 5 was measured.
- the ferricyanide ion is reduced to ferrocyanide ion as glucose is oxidized to dalconolactone by the catalytic action of glucose oxidase.
- the concentration of the above-mentioned ferrocyanide ion is proportional to the concentration of glucose in the sample solution. Therefore, the glucose concentration can be measured based on the oxidation current.
- the produced dalconolactone is decomposed by the action of dalconolactonase.
- FIG. 4 is a longitudinal sectional view of the biosensor according to the present embodiment.
- Example 1 The difference from this is that PQQ-dependent glucose dehydrogenase, which is an oxidoreductase having a catalytic action on the glucose oxidation reaction, and dalconolactonase are separated and supported on a sensor.
- PQQ-dependent glucose dehydrogenase which is an oxidoreductase having a catalytic action on the glucose oxidation reaction
- dalconolactonase are separated and supported on a sensor.
- a CMC layer 7a was formed by dropping 51 drops of a 0.5 wt% aqueous solution of CMC, which is a kind of hydrophilic polymer, on the substrate 1 on which the electrode system was formed, followed by drying.
- the Darukonoraku Tonaze from Asuperugirusu and secondary guard, and dissolved in 1 m M potassium hydrogen phthalate buffer solution is a buffer (p H 6).
- the solution 41 was dropped on the CMC layer 7a and dried to form the darconolactonase layer 12.
- the area of the Darkonolactone tongue layer 12 is 12 mm 2
- the loading amount of the hydrogen phthalate real-time buffer is 0.333 nm 1 Zmm 2 .
- PVP polyvinylpyrrolidone
- a 0.5 wt% aqueous solution of polyvinylpyrrolidone (hereinafter referred to as PVP) is dropped on the darconolactonase layer 12 to separate it from the darconolactonase layer 12, and dried.
- PVP layer 13 was formed.
- PQQ-dependent glucose dehydrogenase, a type of oxidoreductase having a catalytic action on the oxidation reaction of glucose, and potassium ferricyanide, a type of electron carrier were added to a 1 mM succinic acid buffer as a buffer. (PH5).
- the solution 41 was dropped on the PVP layer 13 and dried to form a glucose dehydrogenase layer 14.
- the reagent system in this example is composed of a CMC layer 7a, a dalconolactonase layer 12, a PVP layer 13 and a glucose dehydrogenase layer 14.
- a buffer suitable for each enzyme can be added to each.
- the water-soluble polymer such as PVP is.
- the biosensor of this example was measured using an aqueous solution containing a certain amount of glucose as a sample solution, and as a result, the same results as in Example 1 were obtained.
- a buffer suitable for each enzyme can be added near each enzyme. Therefore, even if the reaction time is shorter, a sufficient response value can be obtained when quantifying the concentration of the substrate to be measured, and the measurement time of the sensor can be reduced.
- the voltage applied to the electrode system was set to 500 mV, but the present invention is not limited to this. It is sufficient that the voltage is such that the electron carrier is oxidized at the working electrode.
- a method of detecting current is used as a measuring method, any output that changes with the progress of an electrochemical reaction can be used as a detection target.
- the amount of electric charge applied in a certain time may be detected. Since the amount of electric charge is the integral of the current with respect to time, it can be related to the concentration of the substrate to be measured.
- a water-insoluble carrier may be provided in the sample liquid supply path, and one or more of the reagents included in the reagent system may be immobilized on the carrier.
- immobilization it is preferable to use a covalent bonding method, a cross-linking immobilization method, an adsorption method, or an immobilization method using a coordination bond-specific bonding interaction.
- carbon was used as the electrode material, but it is not limited to this.
- the working electrode material any conductive material, such as carbon, platinum, gold, and palladium, which is not itself oxidized when oxidizing the electron carrier can be used.
- the counter electrode material use any commonly used conductive material such as silver and platinum, including carbon and gold. can do.
- an electrode having a stable potential may be used as the reference electrode. In that case, a voltage will be applied between the reference and working electrodes.
- the shape, arrangement, number and the like of these electrode systems are not limited to those described in the above embodiment.
- the shape, arrangement, number, etc. of the lead terminals of the electrodes are not limited to those described in the above embodiment.
- the case where the reagent system is formed on the electrode system has been described. Alternatively, it may be formed near the electrode system, for example, on one side of the upper cover so as to be exposed to the sample liquid supply path. Industrial applicability
- the biosensor In the biosensor according to the present invention, darconolactone generated by oxidation of glucose by the action of oxidoreductase is converted into dalconic acid by darconolactonase. As a result, the glucose oxidation reaction proceeds smoothly, and sufficient responsiveness can be obtained even when the measurement time is short.
- the buffer enhances the activity of a redox enzyme or dalconolactonase having a catalytic action on the glucose oxidation reaction, thereby improving the responsiveness of the sensor.
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Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
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DE60205702T DE60205702T2 (de) | 2001-05-15 | 2002-05-13 | Biosensor |
EP02724775A EP1308720B1 (en) | 2001-05-15 | 2002-05-13 | Biosensor |
US10/344,671 US7235170B2 (en) | 2001-05-15 | 2002-05-13 | Biosensor |
JP2002589781A JP3621084B2 (ja) | 2001-05-15 | 2002-05-13 | バイオセンサ |
Applications Claiming Priority (2)
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JP2001144382 | 2001-05-15 | ||
JP2001-144382 | 2001-05-15 |
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WO2002093151A1 true WO2002093151A1 (fr) | 2002-11-21 |
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PCT/JP2002/004624 WO2002093151A1 (fr) | 2001-05-15 | 2002-05-13 | Biocapteur |
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US (1) | US7235170B2 (ja) |
EP (1) | EP1308720B1 (ja) |
JP (1) | JP3621084B2 (ja) |
CN (1) | CN1204398C (ja) |
DE (1) | DE60205702T2 (ja) |
WO (1) | WO2002093151A1 (ja) |
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WO2005080953A1 (ja) * | 2004-02-25 | 2005-09-01 | National Institute Of Advanced Industrial Science And Technology | 尿糖バイオセンサ |
JPWO2004083360A1 (ja) * | 2003-03-20 | 2006-06-22 | 旭化成ライフ&リビング株式会社 | 酸素インジケーター及び包装体 |
WO2009008158A1 (ja) * | 2007-07-11 | 2009-01-15 | Panasonic Corporation | バイオセンサ |
WO2009013869A1 (ja) * | 2007-07-25 | 2009-01-29 | Panasonic Corporation | バイオセンサ |
WO2011125750A1 (ja) * | 2010-03-31 | 2011-10-13 | シーシーアイ株式会社 | バイオセンサ |
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Also Published As
Publication number | Publication date |
---|---|
US20030175841A1 (en) | 2003-09-18 |
EP1308720B1 (en) | 2005-08-24 |
DE60205702D1 (en) | 2005-09-29 |
CN1462367A (zh) | 2003-12-17 |
EP1308720A1 (en) | 2003-05-07 |
CN1204398C (zh) | 2005-06-01 |
JP3621084B2 (ja) | 2005-02-16 |
DE60205702T2 (de) | 2006-02-02 |
EP1308720A4 (en) | 2004-03-17 |
JPWO2002093151A1 (ja) | 2004-09-02 |
US7235170B2 (en) | 2007-06-26 |
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