WO2004081553A1 - 排気口付き分析用具 - Google Patents
排気口付き分析用具 Download PDFInfo
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- WO2004081553A1 WO2004081553A1 PCT/JP2004/003448 JP2004003448W WO2004081553A1 WO 2004081553 A1 WO2004081553 A1 WO 2004081553A1 JP 2004003448 W JP2004003448 W JP 2004003448W WO 2004081553 A1 WO2004081553 A1 WO 2004081553A1
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- WIPO (PCT)
- Prior art keywords
- flow path
- exhaust port
- substrate
- sample
- moving
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- 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 an analytical tool used for analyzing a specific component (for example, glucose, cholesterol or lactic acid) in a sample (for example, a biochemical sample such as blood or urine).
- a specific component for example, glucose, cholesterol or lactic acid
- a sample for example, a biochemical sample such as blood or urine.
- FIG. 20 As a simple method for measuring the glucose concentration in the blood, a method using a disposable dalkose sensor has been adopted (for example, see Japanese Patent Publication No. 8-10208).
- a glucose sensor for example, as shown in FIG. 20, FIG. 21A, and FIG. 21B of the present application, there is a sensor configured to measure a glucose concentration by an electrochemical method.
- the glucose sensor 9 shown in these figures has a working electrode 90 and a counter electrode 91, and is configured to measure a response current value required for calculating a blood sugar level using these electrodes 90 and 91. ing.
- the glucose sensor 9 has a configuration in which a cover 94 is laminated on a substrate 92 via a spacer 93 on which a slit 93a is formed.
- a flow path 95 is defined by these elements 92 to 94.
- the channel 95 is intended to move the blood by a capillary force, an inlet 95a for introducing blood, the internal passage 95 of the gas in the interior of the blood flow channel 9 5 moves And an exhaust port 95b for exhaust.
- the surface of the cover 94 that defines the flow path 95 is usually subjected to a hydrophilic treatment so that blood can be appropriately moved in the flow path 95.
- a reagent layer 96 containing acid oxidoreductase and an electron transfer substance is provided on the substrate 92.
- the reagent layer 96 has a high melting angle so that a liquid phase reaction system is established inside the flow channel 95 when blood is introduced. For this reason, the surface of the substrate 92 that defines the flow channel 95 is made substantially hydrophilic by the reagent layer 96.
- the reagent layer 96 is dissolved by the supply of blood, and a liquid phase reaction system is established.
- a voltage can be applied to this liquid phase reaction system using the working electrode 90 and the counter electrode 91, and the response current value at that time can be measured using the working electrode 90 and the counter electrode 91.
- the response current value is obtained as a reflection of the amount of electrons transferred between the electron mediator and the working electrode 90 in the liquid phase reaction system. That is, the response current value is related to the amount (concentration) of the electron mediator present around the working electrode 90 and capable of transferring electrons to and from the working electrode 90.
- the exhaust port 95b is generally in a circular shape.
- blood B proceeds in the form as shown in FIG. 21B, blood B cannot reach the portion adjacent to the exhaust port 95b as indicated by reference numeral 97 in FIG. 21C.
- blood B may gradually move over time or may suddenly move so as to fill cavity 97. If such a phenomenon occurs while measuring the response current value, the amount (concentration) of the electron mediator present around the working electrode 90 changes drastically, and the measured response current value is originally obtained. It deviates from the expected value.
- the movement phenomenon of blood B does not occur every time the blood glucose level is measured, and the timing at which the movement phenomenon of blood B occurs is not uniform for each glucose sensor. Measurement reproducibility, fins, and, in turn, the reproducibility of the calculated blood glucose level will be poor. Disclosure of the invention
- An object of the present invention is to improve the reproducibility of sample analysis in an analytical tool provided with a channel for moving a sample.
- an analysis tool in which a flow path for moving a sample in a specific direction is set on a substrate, wherein the flow path is viewed in a thickness direction of the substrate.
- the edge of the exhaust port is a sample.
- An analysis tool is provided, which has a linear portion extending in the width direction or substantially the width direction at a portion located on the upstream side in the moving direction of the device.
- the flow path is configured such that, for example, the moving speed of the sample moving in the central portion in the width direction is higher than the other portions.
- the dimension of the linear portion is preferably the same or substantially the same as the dimension of the flow path in the width direction, or is preferably larger than the dimension of the flow path in the width direction.
- the exhaust port is formed, for example, in a polygonal shape. Typically, the outlet is formed in a rectangular or triangular shape.
- the exhaust port may have another shape such as a semicircle.
- an analysis tool in which a flow path for moving a sample in a specific direction is set on a substrate, wherein the flow path is viewed in a thickness direction of the substrate.
- the flow path is in the width direction
- the moving speed of the sample moving in the central portion of the sample is configured to be faster than the other portions.
- the edge of the exhaust port is located at the portion located on the upstream side in the sample moving direction, and the central portion is positioned at the center.
- An analytical instrument with an exhaust port characterized in that it has a concave portion toward the downstream side in the moving direction of the sample as compared with both end portions, is provided.
- the concave portion has, for example, an arc shape.
- the analysis tool has, for example, a form in which a cover is laminated on a substrate, and a flow path is defined by the substrate and the cover.
- the cover has a through hole that penetrates in the plate thickness direction and forms an exhaust port.
- the cover is laminated to the substrate via a spacer, for example.
- the spacer defines the flow path.
- the part of the flow path defined by the spacer is the flow path It is configured such that the shrinkage is greater than the other parts that define.
- an analysis tool in which a flow path for moving a sample in a specific direction is set on a substrate, wherein the flow path is viewed in a thickness direction of the substrate.
- An analytical instrument with an exhaust port having a certain dimension in a width direction orthogonal to the specific direction and having an exhaust port for discharging gas inside the flow path, The edge of the sample, which is located on the upstream side in the moving direction of the sample, is made to correspond to the shape in the thickness direction at the leading edge of the sample moving inside the flow path.
- a mouth analysis tool is provided.
- an analysis tool in which a flow path for moving a sample in a specific direction is set on the substrate, wherein the flow path is viewed in the thickness direction of the substrate.
- the flow path includes the flow path.
- the moving speed of the sample moving in the central portion in the width direction of the passage is configured to be higher than that of the other portion.
- An analysis tool with an exhaust port is provided, which is provided with a stopper for preventing movement of a sample moving at both ends in the width direction inside.
- An analysis tool has a form in which a force par is laminated on a substrate via a spacer in which a slit is formed, for example.
- the flow path is defined by the cover and the cover.
- the stopper portion has a smaller width dimension in the portion adjacent to the exhaust port than in the portion adjacent to the sample inlet. It is provided by making it smaller.
- the one or more stopper portions are configured to include, for example, first and second stopper portions that protrude inward in the flow path and are provided at intervals in the above-described direction.
- the first and second stopper portions are provided, for example, at a portion located on the upstream side in the moving direction of the sample, and have a linear portion extending in the width direction or substantially the width direction.
- the first and second stoppers are located upstream in the moving direction of the sample. It can also be configured as having an arcuate portion provided at the portion where it is placed.
- the channel is configured to move the sample by capillary force.
- the sample may be moved inside the flow channel using the power of a pump or the like.
- FIG. 1 is an overall perspective view showing a glucose sensor according to a first embodiment of the present invention.
- FIG. 2 is an exploded perspective view of the glucose sensor shown in FIG.
- FIG. 3 is a sectional view taken along the line H--in FIG.
- FIG. 4 is a plan view showing an end of the glucose sensor shown in FIG. 1 with a cover removed.
- FIG. 5 is a cross-sectional view corresponding to FIG. 3 for explaining the progress of blood in the glucose sensor shown in FIG.
- FIG. 6 is a plan view corresponding to FIG. 4 for explaining the progress of blood in the glucose sensor shown in FIG.
- FIG. 7 is a plan view corresponding to FIG. 4 for explaining the progress of blood in the glucose sensor shown in FIG.
- FIG. 8A and 8B are overall perspective views showing another example of the glucose sensor.
- FIG. 9 is an overall perspective view showing a glucose sensor according to the second embodiment of the present invention.
- FIG. 10 is a plan view corresponding to FIG. 4, showing a state in which the movement of blood in the glucose sensor shown in FIG. 9 has stopped.
- FIG. 11 is an overall perspective view showing a glucose sensor according to a third embodiment of the present invention.
- FIG. 12 shows an end of the Darcos sensor shown in FIG. 11 as a plan view corresponding to FIG.
- FIGS. 13A and 13B are diagrams for explaining another example of the stopper portion, and show an end of the glucose sensor as a plan view corresponding to FIG. 14A to 14C are graphs showing measurement results of response current values in Example 1 as time courses.
- 15A to 15C are graphs showing measurement results of response current values in Example 2 as a time course.
- 16A to 16C are graphs showing measurement results of the response current value in Example 3 as a time course.
- 17A to 17C are graphs showing the measurement results of the response current value in Comparative Example 1 as a time course.
- 18A to 18C are graphs showing the measurement results of the response current value in Comparative Example 2 as a time course.
- 19A to 19C are graphs showing measurement results of the response current value in Comparative Example 3 as a time course.
- FIG. 20 is an overall perspective view showing an example of a conventional glucose sensor.
- FIG. 21A to 21C are for explaining the progress of blood in the glucose sensor shown in FIG. 20, FIG. 21A is a cross-sectional view of the end of the glucose sensor, and FIG. 21B and FIG. FIG. 5 is a plan view showing an end of the sensor with a cover removed.
- the glucose sensor XI shown in FIGS. 1 to 4 is configured to be disposable, and is used by being attached to a concentration measuring device (not shown).
- This Darco's sensor has a form in which a cover 3 is stacked on a long rectangular substrate 1 via a spacer 2.
- each element 1 to 3 defines a flow path 4 extending in the longitudinal direction of the substrate 1.
- the flow path 4 moves the blood introduced from the opening (introduction port) 40 in the longitudinal direction of the substrate 1 by utilizing the capillary phenomenon and introduces the blood. It is for holding the blood that has been collected.
- the spacer 2 is for defining the distance from the upper surface 10 of the substrate 1 to the lower surface 30 of the cover 3, that is, the height dimension of the flow path 4.
- the spacer 2 is provided with a slit 20 having an open end.
- the slit 20 is for defining the width dimension of the flow path 4, and the open end portion of the slit 20 forms an inlet 40 for introducing blood into the flow path 4.
- the spacer 2 is formed using, for example, an acrylic emulsion-based material.
- the cover 3 has a through hole 31 formed therein.
- the through hole 31 is for exhausting gas inside the flow path 4 to the outside, and is formed in a square shape.
- the through hole 31 is provided such that the edge 31a is located on the side of the inlet 40, and the edge 31a extends in the width direction of the flow path 4 (the short direction of the substrate 1).
- the surface of the cover 3 has higher hydrophilicity than the spacer 2.
- the cover 3 is made of, for example, vinylon so as to have high hydrophilicity as a whole, or a surface facing the flow path 4 is subjected to a hydrophilic treatment.
- the hydrophilic treatment is performed, for example, by irradiating ultraviolet rays or by applying a surfactant such as lecithin.
- a working electrode 11, a counter electrode 12, and a reagent section 13 are formed on the upper surface 10 of the substrate 1.
- the working electrode 11 and the counter electrode 12 extend in the longitudinal direction of the substrate 1 as a whole.
- the ends lla and 12a of the working electrode 11 and the counter electrode 12 extend in the lateral direction of the substrate 1 and are arranged in the longitudinal direction.
- the ends lib and 12b of the working electrode 11 and the counter electrode 12 constitute a terminal portion for contacting a terminal provided in a concentration measuring device (not shown).
- the upper surface 10 of the substrate 1 is covered with the insulating film 14 such that the ends 11a, lib, 12a, and 12b of the working electrode 11 and the counter electrode 12 are exposed.
- the insulating film 14 is formed of, for example, an ultraviolet curable resin containing a water repellent, and has high hydrophobicity.
- the reagent section 13 is provided so as to bridge between the ends lla and 12a of the working electrode 11 and the counter electrode 12, and includes, for example, a solid medium containing an electron transfer substance and a relatively small amount of acid capita reductase. It is formed in a shape.
- the reagent section 13 is formed so as to be easily dissolved in blood. Therefore, when blood is introduced into the flow path 4, the sample easily moves along the surface of the substrate 1, and the inside of the flow path 4 contains an electron transfer substance, an oxidoreductase, and glucose. A liquid phase reaction system is established.
- oxidoreductase for example, glucose oxidase (GOD) or glucose dehydrogenase (GDH) can be used, and PQQGDH is typically used.
- GOD glucose oxidase
- GDH glucose dehydrogenase
- the electron mediator for example, can use ruthenium complex Ya iron complex, the Scripture type, it is possible to use the [Ru (H 3) 6] Cl 3 or K 3 [Fe (CN) 6 ] .
- the Dalcos sensor XI In the measurement of the blood glucose level using the Dalcos sensor XI, the Dalcos sensor XI is attached to a concentration measuring device (not shown), and the blood is supplied to the flow channel 4 through the inlet 40 of the glucose sensor ⁇ As a result, the measurement is automatically performed in a concentration measuring device (not shown).
- the glucose sensor XI When the glucose sensor XI is attached to the concentration measuring device (not shown), the working electrode 11 and the counter electrode 12 of the glucose sensor XI contact the terminals (not shown) of the concentration measuring device.
- a voltage can be applied to the liquid phase reaction system constructed after the introduction of blood using the working electrode 11 and the counter electrode 12, or a response current value when the voltage is applied can be measured.
- the portion of the cover 3 facing the flow path 4 is made more hydrophilic, and the substrate 1 is provided with the reagent layer 13 having high melting angle needles. Therefore, compared to the portion facing the flow path 4 in the spacer 2, the blood is more likely to progress in the portion of the substrate 1 and the cover 3 facing the flow path 4. Therefore, in the flow path 4, as shown in FIG. 5, when observing the moving state of the blood B from the side, the portion along the surface of the substrate 1 and the surface of the cover 13 is compared with the central portion. Blood B actively progresses. On the other hand, as shown in Fig. 6, when the movement state of blood B is observed from above, blood B is more aggressive at the center in the width direction of channel 4 than at both ends. You. The progress of the blood B ends when the blood reaches the edge 31a of the through hole 31 as shown in FIG.
- oxidoreductase reacts specifically with glucose in blood to extract electrons from glucose, and the electrons are supplied to an electron mediator to convert the electron mediator into a reduced form.
- the working electrode 11 is charged from the reduced electron transfer material. A child is supplied. Therefore, in the concentration measuring device, for example, the amount of electrons supplied to the working electrode 11 can be measured as a response current value.
- a blood glucose level is calculated based on a response current value measured when a certain period of time has elapsed since the supply of blood to the flow path 4.
- the through hole 31 is formed in a square shape, and the edge 31a of the through hole 31 for stopping the progress of blood is formed in a straight line extending in the width direction of the flow path 4. Therefore, as can be seen by comparing FIG. 7 and FIG. 21C, in the glucose sensor XI, compared to the case where the through hole (exhaust port 95b) is circular, at the end of the flow path 4 (95), If blood is not supplied, the possibility that the cavity 47 (97) is formed is reduced, and even if the cavity 47 is formed, the volume is reduced.
- the glucose sensor XI there is a small possibility that the blood B moves to the hollow portion 47 after the movement of the blood B is once stopped, and even if the movement of the blood B occurs, the movement amount is small. .
- the possibility that the amount (concentration) of the electron mediator existing around the end 11a of the working electrode 11 changes abruptly is reduced, and the measured response current value is closer to the value that should be originally obtained. It becomes. Therefore, in the glucose sensor XI, the reproducibility of the measurement of the response current value and the reproducibility of the calculated blood glucose level can be improved.
- the force with which the through-hole 31 of the cover 3 is formed in a square shape In order to obtain the above-described effect, the edge of the through-hole that stops the progress of blood is formed as a straight line extending in the width direction of the flow path. It should just be. Therefore, as shown in FIG. 8A, the shape of the through-hole 31 ; may be triangular, or as shown in FIG. 8B, the shape of the through-hole 31 "may be a semicircle, or any other shape. Is also good.
- FIG. 9 a glucose sensor according to a second embodiment of the present invention will be described with reference to FIG. 9 and FIG.
- the same elements as those of the above-described darkness sensor XI are denoted by the same reference numerals, and redundant description is omitted here.
- the glucose sensor X2 shown in FIGS. 9 and 10 is different from the glucose sensor XI (see FIG. 1) according to the first embodiment described above in the form of the through hole 31A of the cover 3.
- the through-hole 31A is formed in an arc shape in which an edge 31Aa for stopping the progress of the blood is depressed in the direction of the blood flow.
- the center in the width direction of the flow path 4 proceeds more aggressively than the both ends, and as a result, the edge in the blood traveling direction Is arcuate.
- the shape of the edge 31Aa in the through-hole 31A that stops the progress of the blood B is formed in an arc shape that is concave in the direction of the blood B, the progress of the blood is simultaneously stopped in the entire edge 31Aa. Will be able to do it.
- a hollow portion where blood B is not supplied at the end of the flow path 4 (47) It is possible to further reduce the possibility of occurrence of cavitation, and further reduce the volume of the cavity (47) even if it occurs. Therefore, in the glucose sensor X2, the measurement reproducibility of the response current value and, consequently, the reproducibility of the calculated blood sugar level can be further improved.
- the glucose sensor X3 shown in FIGS. 11 and 12 is provided with a stopper 22 at the end of the flow path 4 on the blood traveling direction side.
- the stopper portion 22 is constituted by a pair of projections 22C provided on the spacer 2. Protrusions 22 C is for projecting inward in the width direction of the channel 4, it has an arcuate a stop surface 22 c.
- the stopper portion 22 is located at an end in the width direction at an end in the longitudinal direction of the flow path 4. In other words, when blood is introduced into the flow channel 4, it is formed at a site where a cavity can be formed (see FIG. 7). Therefore, the provision of the spout 1 and the wrapper section 22 makes it possible to suppress the occurrence of a cavity in the flow path 4 after blood is introduced.
- the stopper portion 22 allows the blood flowing in the widthwise central portion of the flow path 4 to flow before or simultaneously with contact with the edge of the exhaust port 31C. It is preferable that the blood traveling at the widthwise end of the road 4 is configured to be in contact with the blood.
- the configuration of the stopper portion 22 is not limited to the configuration described above.
- a stopper 22 ′ may be provided by providing a step 22C ′ on the spacer 2 ′, and as shown in FIG.
- the stove portion may be formed by other configurations.
- the present invention is not limited to the glucose sensors according to the above-described first to third embodiments.
- the present invention provides, for example, a glucose sensor for measuring glucose using a sample other than blood, a component other than glucose in blood, or a sample liquid other than blood for analyzing components other than glucose. It can also be applied to analytical tools.
- Glucose sensors used in Examples 1 to 3 and Comparative Examples 1 to 3 were prepared by the same method with respect to the substrate and each component provided on the substrate (see FIG. 2).
- a working electrode and a counter electrode were formed on a PET substrate by screen printing using carbon ink.
- the substrate was covered with an insulating film using a UV curable resin having a contact angle of 5 degrees so that both ends of the working electrode and the counter electrode were exposed.
- a reagent part having a two-layer structure consisting of an electron transfer layer and an enzyme-containing layer was formed.
- the electron transfer layer 0.4 L of the first material liquid containing the electron transfer substance is applied to the part where the working electrode and the counter electrode are exposed on the substrate, and then the first material liquid is blown dry (30 ° C, 10% Rh) It was formed by doing.
- the enzyme-containing layer was formed by applying 0.3 ⁇ L of the second material solution containing oxidoreductase on the electron transport layer, and then drying the second material solution with air (30 ° C, 10% Rh). .
- the first material liquid is prepared by mixing the materials shown in Tables 1 to 4 in the order indicated by the numbers and leaving them for 1 to 3 days, and then adding the electron mediator to this mixture.
- the electron mediator [ ⁇ (3) 6] (were used: 1 3 (Dojini ⁇ Institute "111722").
- Table 1 Composition of the first material liquid (excluding electron mediator)
- S is an abbreviation for so-called center center S
- CHAPS is an abbreviation for so-called center center S
- ACES 3- [(3-cholamidopropyl) dimethylammonioj propanesulfonic acid; ACES is an abbreviation for N- (2-acetamido) -2-aminoethanesidfonic acid. “3150” manufactured by Corp Chemical Co., Ltd. was used as SWN, “KC062” manufactured by Dojin Chemical Laboratories was used as CHAPS, and “ED067” manufactured by Dojin Chemical Laboratories was used as ACES. The ACES solution was prepared to have a pH of 7.5.
- the second material solution was prepared by dissolving the acid reductase in 0.1% CHAPS.
- PQQGDH having an enzyme activity of 500 U / mg was used as the acid capita reductase.
- an acryl emulsion emulsion-based adhesive was applied on the insulating film so as to avoid the reagent part, and a glucose sensor was formed by laminating a force par.
- the reproducibility was evaluated based on the time course of the response current value.
- the time course of the response current value was determined using three types of blood (Hct values of 20%, 42% and 70%) with a glucose concentration of 400 mg / dL and different Hct values. It was measured 30 times.
- the voltage application between the working electrode and the counter electrode was started 5 seconds after the start of blood supply at an applied voltage value of 200 mV, and the response current value was measured over time every 50 msec from the start of the voltage application.
- Example 2 In this example, as shown in Table 2, the response current value was measured in the same manner as in Example 1, except that a glucose sensor having a cover thickness set to 200 mm was used.
- Example 2 As shown in Table 2, except that a glucose sensor employing a cover having a through hole (exhaust port) as shown in FIGS. 9 and 10 was used, the same as in Example 1 was used. To measure the response current value.
- the edge of the through-hole that stops the blood from proceeding was an arc-shaped concave edge with a radius of curvature of lram that was recessed in the direction of blood flow.
- the response current was the same as in Example 1 except that a glucose sensor using a cover having a circular through hole (exhaust port) having a diameter of 2 mm was used. The value was measured.
- the response current value was measured in the same manner as in Comparative Example 1, except that a glucose sensor having a length dimension of 60 mm was used as the glucose sensor.
- Figures 18A to 18C show the measurement results of the time course, and Table 2 shows the turbulence occurrence rate on the time course.
- FIGS 19A to 19C show the measurement results of the time course. The rates are shown in Table 2.
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EP04720725A EP1605254A4 (en) | 2003-03-14 | 2004-03-15 | EXHAUST ORIFICE ANALYSIS TOOL |
US10/548,894 US20060228254A1 (en) | 2003-03-14 | 2004-03-15 | Analyzing tool with exhaust port |
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JP2003-069353 | 2003-03-14 | ||
JP2003069353A JP3910148B2 (ja) | 2003-03-14 | 2003-03-14 | 排気口付き分析用具 |
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EP (2) | EP2554983A1 (ja) |
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USD673287S1 (en) | 2010-11-24 | 2012-12-25 | Sony Corporation | Micro flow channel chip |
USD869308S1 (en) | 2010-04-29 | 2019-12-10 | Sony Corporation | Micro flow channel chip |
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JP5102334B2 (ja) * | 2010-06-25 | 2012-12-19 | 日本電波工業株式会社 | 感知装置 |
US9086338B2 (en) | 2010-06-25 | 2015-07-21 | Nihon Dempa Kogyo Co., Ltd. | Sensing device |
US9903829B2 (en) | 2011-04-12 | 2018-02-27 | Panasonic Healthcare Holdings Co., Ltd. | Biosensor and measuring device using same |
WO2012172772A1 (ja) * | 2011-06-16 | 2012-12-20 | パナソニック株式会社 | センサおよびこれを備えたセンサシステム |
JP2013257310A (ja) * | 2012-05-18 | 2013-12-26 | Arkray Inc | バイオセンサ |
TWI477772B (zh) | 2013-02-25 | 2015-03-21 | Apex Biotechnology Corp | 電極試片及感測試片及其系統 |
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 |
JP6610025B2 (ja) * | 2015-06-22 | 2019-11-27 | 株式会社村田製作所 | バイオセンサ |
EP3559664B1 (en) * | 2016-12-23 | 2020-12-09 | Radiometer Medical ApS | Multiple-use sensor assembly for body fluids |
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2003
- 2003-03-14 JP JP2003069353A patent/JP3910148B2/ja not_active Expired - Fee Related
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2004
- 2004-03-15 WO PCT/JP2004/003448 patent/WO2004081553A1/ja active Application Filing
- 2004-03-15 EP EP12178129A patent/EP2554983A1/en not_active Withdrawn
- 2004-03-15 CN CN200910005129.0A patent/CN101482557B/zh not_active Expired - Lifetime
- 2004-03-15 EP EP04720725A patent/EP1605254A4/en not_active Withdrawn
- 2004-03-15 CN CN200910005128.6A patent/CN101482556B/zh not_active Expired - Lifetime
- 2004-03-15 CN CNB2004800065439A patent/CN100541192C/zh not_active Expired - Lifetime
- 2004-03-15 US US10/548,894 patent/US20060228254A1/en not_active Abandoned
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Also Published As
Publication number | Publication date |
---|---|
JP3910148B2 (ja) | 2007-04-25 |
CN101482557A (zh) | 2009-07-15 |
JP2004279150A (ja) | 2004-10-07 |
EP1605254A1 (en) | 2005-12-14 |
CN1759310A (zh) | 2006-04-12 |
CN101482556B (zh) | 2013-03-27 |
EP1605254A4 (en) | 2010-10-06 |
CN101482557B (zh) | 2013-02-06 |
CN100541192C (zh) | 2009-09-16 |
CN101482556A (zh) | 2009-07-15 |
US20060228254A1 (en) | 2006-10-12 |
EP2554983A1 (en) | 2013-02-06 |
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