CN101561411B - Biosensor - Google Patents
Biosensor Download PDFInfo
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- CN101561411B CN101561411B CN 200910302101 CN200910302101A CN101561411B CN 101561411 B CN101561411 B CN 101561411B CN 200910302101 CN200910302101 CN 200910302101 CN 200910302101 A CN200910302101 A CN 200910302101A CN 101561411 B CN101561411 B CN 101561411B
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- 108090000790 Enzymes Proteins 0.000 claims abstract description 38
- 102000004190 Enzymes Human genes 0.000 claims abstract description 38
- 238000001914 filtration Methods 0.000 claims abstract description 35
- 238000006243 chemical reaction Methods 0.000 claims abstract description 23
- 239000000758 substrate Substances 0.000 claims abstract description 22
- 239000003153 chemical reaction reagent Substances 0.000 claims abstract description 17
- 238000009413 insulation Methods 0.000 claims abstract description 16
- 239000012528 membrane Substances 0.000 claims description 59
- 206010020633 Hyperglobulinaemia Diseases 0.000 claims description 4
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 2
- 210000002381 plasma Anatomy 0.000 abstract description 10
- 210000000601 blood cell Anatomy 0.000 abstract description 7
- 239000007788 liquid Substances 0.000 abstract description 5
- 230000003647 oxidation Effects 0.000 abstract description 4
- 238000007254 oxidation reaction Methods 0.000 abstract description 4
- 230000009467 reduction Effects 0.000 abstract description 2
- 102000004316 Oxidoreductases Human genes 0.000 abstract 1
- 108090000854 Oxidoreductases Proteins 0.000 abstract 1
- 238000009828 non-uniform distribution Methods 0.000 abstract 1
- 229940088598 enzyme Drugs 0.000 description 26
- 210000004369 blood Anatomy 0.000 description 11
- 239000008280 blood Substances 0.000 description 11
- 238000000034 method Methods 0.000 description 6
- 239000000126 substance Substances 0.000 description 5
- WQZGKKKJIJFFOK-GASJEMHNSA-N Glucose Natural products OC[C@H]1OC(O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-GASJEMHNSA-N 0.000 description 4
- XEEYBQQBJWHFJM-UHFFFAOYSA-N Iron Chemical compound [Fe] XEEYBQQBJWHFJM-UHFFFAOYSA-N 0.000 description 4
- 238000006911 enzymatic reaction Methods 0.000 description 4
- 239000008103 glucose Substances 0.000 description 4
- 229920002521 macromolecule Polymers 0.000 description 4
- 230000015572 biosynthetic process Effects 0.000 description 3
- 239000011248 coating agent Substances 0.000 description 3
- 238000000576 coating method Methods 0.000 description 3
- 239000000499 gel Substances 0.000 description 3
- 238000004519 manufacturing process Methods 0.000 description 3
- 239000000203 mixture Substances 0.000 description 3
- 238000007639 printing Methods 0.000 description 3
- 230000008569 process Effects 0.000 description 3
- BQCADISMDOOEFD-UHFFFAOYSA-N Silver Chemical compound [Ag] BQCADISMDOOEFD-UHFFFAOYSA-N 0.000 description 2
- 230000009286 beneficial effect Effects 0.000 description 2
- 230000000975 bioactive effect Effects 0.000 description 2
- 230000008859 change Effects 0.000 description 2
- 239000003795 chemical substances by application Substances 0.000 description 2
- 238000005516 engineering process Methods 0.000 description 2
- 229910052742 iron Inorganic materials 0.000 description 2
- -1 iron radon potassium Chemical class 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 229910052709 silver Inorganic materials 0.000 description 2
- 239000004332 silver Substances 0.000 description 2
- 229920001817 Agar Polymers 0.000 description 1
- 108010010803 Gelatin Proteins 0.000 description 1
- 108010015776 Glucose oxidase Proteins 0.000 description 1
- 239000004366 Glucose oxidase Substances 0.000 description 1
- 241001597008 Nomeidae Species 0.000 description 1
- ZLMJMSJWJFRBEC-UHFFFAOYSA-N Potassium Chemical compound [K] ZLMJMSJWJFRBEC-UHFFFAOYSA-N 0.000 description 1
- 229920001131 Pulp (paper) Polymers 0.000 description 1
- 229920002472 Starch Polymers 0.000 description 1
- 239000008272 agar Substances 0.000 description 1
- 235000010419 agar Nutrition 0.000 description 1
- 238000003556 assay Methods 0.000 description 1
- 239000006172 buffering agent Substances 0.000 description 1
- 239000001913 cellulose Substances 0.000 description 1
- 229920002678 cellulose Polymers 0.000 description 1
- 150000004696 coordination complex Chemical class 0.000 description 1
- 230000009089 cytolysis Effects 0.000 description 1
- 238000000354 decomposition reaction Methods 0.000 description 1
- 230000007812 deficiency Effects 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000009792 diffusion process Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000003411 electrode reaction Methods 0.000 description 1
- 238000006056 electrooxidation reaction Methods 0.000 description 1
- 239000008273 gelatin Substances 0.000 description 1
- 229920000159 gelatin Polymers 0.000 description 1
- 235000019322 gelatine Nutrition 0.000 description 1
- 235000011852 gelatine desserts Nutrition 0.000 description 1
- 239000003365 glass fiber Substances 0.000 description 1
- 150000002303 glucose derivatives Chemical class 0.000 description 1
- 229940116332 glucose oxidase Drugs 0.000 description 1
- 235000019420 glucose oxidase Nutrition 0.000 description 1
- 239000011159 matrix material Substances 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 239000004745 nonwoven fabric Substances 0.000 description 1
- 150000002894 organic compounds Chemical class 0.000 description 1
- 239000000123 paper Substances 0.000 description 1
- 210000002706 plastid Anatomy 0.000 description 1
- 229920002401 polyacrylamide Polymers 0.000 description 1
- 229920000139 polyethylene terephthalate Polymers 0.000 description 1
- 229920000642 polymer Polymers 0.000 description 1
- 229910052700 potassium Inorganic materials 0.000 description 1
- 239000011591 potassium Substances 0.000 description 1
- 150000004059 quinone derivatives Chemical class 0.000 description 1
- 229910052704 radon Inorganic materials 0.000 description 1
- SYUHGPGVQRZVTB-UHFFFAOYSA-N radon atom Chemical compound [Rn] SYUHGPGVQRZVTB-UHFFFAOYSA-N 0.000 description 1
- 239000002994 raw material Substances 0.000 description 1
- 229920005989 resin Polymers 0.000 description 1
- 239000011347 resin Substances 0.000 description 1
- 230000004044 response Effects 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 239000008107 starch Substances 0.000 description 1
- 235000019698 starch Nutrition 0.000 description 1
- 239000002699 waste material Substances 0.000 description 1
Images
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- Apparatus Associated With Microorganisms And Enzymes (AREA)
- Investigating Or Analysing Biological Materials (AREA)
Abstract
The invention discloses a biosensor, comprising an insulated substrate, a reaction layer containing an oxidoreductase and an electronic mediator, an insulation layer and an upper cover; the reaction layer comprises an electrode system and an enzyme film; the enzyme film is provided with a reaction reagent; two layers of filter films used for filtering blood cells are arranged between the insulation layer and the upper cover; the blood plasma of the blood cells filtered by the two layers of the filter films on an electric board is attracted by the biosensor by a capillarity. The biosensor leadsthe sample liquid to uniformly disperse, cover the whole filter film and sufficiently contact and react with the reaction reagent on the enzyme film. The biosensor has no phenomena that a series of c hemical reactions such as enzymolysis are not uniform due to non-uniform distribution and the oxidation and reduction current is affected. After the reagent is consumed in the reaction process, the reagent can be continued to be added to the enzyme film by a suction inlet, which is convenient and quick.
Description
Technical field
The present invention relates to can be rapidly, high sensitivity and the biology sensor of the special component in the quantitative sample easily.
Background technology
Take glucose sensor as example, in typical biology sensor, on the insulativity substrate, form by methods such as serigraphys and comprise at least and measure electrode and to the electrode system of electrode, on this electrode system, form the enzyme reaction layer that contains hydrophilic macromolecule, oxidoreducing enzyme and electron mediator.In oxidoreducing enzyme, use glucose oxidase, in electron mediator with the metal complex such as iron radon potassium, ring iron derivant, quinone derivative or organic compound etc. in enzyme reaction layer, add as required buffering agent.Contain the test liquid of zymolyte if drip in the enzyme reaction layer of this glucose sensor, then pure responding layer is held and is separated, and enzyme and zymolyte react.Along with this reaction, electron mediator is reduced.After enzyme reaction finished, the oxidation current value that produces when this electron mediator that has reduced is carried out electrochemical oxidation can be obtained the concentration of the zymolyte in the test liquid.
That is to say, in this class glucose sensor, come the Reduction Body of the resultant electron mediator of oxydase reaction by electrode, obtain concentration of glucose according to its oxidation current value.This biology sensor is by being the enzyme of zymolyte in order to the determination object material.
The interfacial agent that contains in the sensor reactive system has bad impact to hyperglobulinemia, therefore is not suitable for measuring whole blood itself.Chinese patent 01805717.9 is disclosed a kind ofly can will send to rapidly the biology sensor of electrode system with the blood that has filtered hyperglobulinemia.But the reaction reagent of this sensing system partly is designed to be pressed in sensor internal, this step of the reactive agent of interpolation will be arranged in the sensor manufacture process so, and biology sensor is easy to pollute reaction reagent in the manufacture process of back, also can cause the enzyme in the reaction reagent to lose biologically active or sex change if any all chemical factors such as high temperature manufacturing states, affect result of use, also caused the waste of raw material.
Summary of the invention
For solving problems of the prior art and deficiency, the object of the present invention is to provide a kind of response height and precision good, can measure the biology sensor of whole blood.
Purpose of the present invention realizes by following technical scheme: a kind of biology sensor, and comprise the insulativity substrate, contain responding layer, insulation course and the loam cake of oxidoreducing enzyme and electron mediator, it is characterized in that described responding layer comprises electrode system and enzyme membrane; Be provided with two-layer filtering membrane be used to filtering hyperglobulinemia between described insulation course and the loam cake.
For better implementing the present invention:
Described electrode system is directly to be printed on the enzyme membrane, as the assay method of oxidation current, more preferably adopt comprise measure electrode, to three electrode modes of electrode and contrast electrode, three electrode modes can more correctly be measured.
The outside of described insulativity substrate and loam cake is respectively equipped with corresponding sample suction inlet, and by insulativity substrate, insulation course and on cover corresponding through hole and be connected.The suction inlet of loam cake side can connect syringe needle, sucks blood sample.The suction inlet of substrate-side can connect the needle tubing part of syringe, absorbs after filtering through two-layer filtering membrane with the enzyme membrane responding layer blood plasma behind the chemical enzymolysis reaction test occurs, and is beneficial to clinical manipulation.
Used filtering membrane is comprised of the porous body semi-permeable diaphragm by space part among the present invention.Test liquid enters from loam cake side draught entrance by capillarity, moves to the responding layer that comprises enzyme membrane and electrode system through two-layer filtering membrane, the effect that has the difference of the circulating resistance by blood plasma and blood cell to filter blood cell.The material of filtering membrane can be used fibrous nonwoven fabrics, filter paper or other porous plastids by glass fibre, cellulose or paper pulp etc.In addition, semi-permeable diaphragm preferably has water wettability.
Described insulativity substrate is provided with and is fit to the recess that enzyme membrane is put into, and described through hole is positioned at recess; Cover on described and be provided with the recess that suitable filtering membrane is put into, through hole is positioned at recess.
On the biology sensor enzyme membrane of the present invention with reaction reagent, after the sensor assembly is good, suction inlet by substrate-side drips to dry forming on the enzyme membrane, can not affect the biologically active of reagent, greatly improve blood through out-of-date reaction rate and reaction efficiency, thereby can reduce the error of test result.And after reagent is consumed in course of reaction, still can continue by the suction inlet of substrate-side to add reaction reagent toward enzyme membrane.
Reaction reagent adopts bioactive molecule is embedded in method in the grid of gel or polymer architecture.The mild condition that this method requires has various available gels or polymkeric substance (such as polyacrylamide, starch, gelatin and agar isogel), is applicable to various bioactive molecules, is known technology.
In addition, for guard electrode, suppress peeling off of formed responding layer, preferably then form the hydrophilic macromolecule layer on the electrode system.Also not only on the electrode system, and form the hydrophilic macromolecule layer as the bottom of responding layer, perhaps contain the hydrophilic macromolecule layer in undermost responding layer.
Compared with prior art, the present invention has following beneficial effect:
Biology sensor of the present invention is to be touched the whole surface of filtering membrane because blood directly sucks.According to this formation, when blood arrives filtering membrane through the aperture of loam cake side draught entrance, beginning is to the filtering membrane diffusion that reaches the second layer all around, speed around blood is diffused into is identical, therefore can spread uniformly and cover whole filtering membrane, and the abundant contact reaction of reaction reagent on last and the enzyme membrane, the test result precision is high.Do not exist skewness to cause the series of chemical such as enzymolysis inhomogeneous, affect the phenomenon of redox electric current.
Biology sensor of the present invention, the plasma uniform after can removing blood cell is supplied with to electrode system rapidly, and can be in time, fast, easily to responding layer postreaction reagent and do not pollute.
Description of drawings
Fig. 1 be biology sensor of the present invention a kind of preferred implementation decomposition diagram.
Fig. 2 is the side view of Fig. 1.
Embodiment
With reference to the accompanying drawings and embodiment, the present invention done further describing in detail, but implementation of the present invention is not limited to this.
1, the structure of biology sensor:
As depicted in figs. 1 and 2, biology sensor of the present invention mainly is comprised of substrate 1, enzyme membrane 2, electroplax 3, insulation course 4, filtering membrane 5, filtering membrane 6 and loam cake 7.
In addition, seal coat on the specific region on electroplax 3, namely insulation course 4.Insulation course 4 is taken as recess 10 areas at three electrode places constant, does not print the insulativity paste in this circular area, thereby does not form insulation course.Insulation course 4 partly covers three lead-in wires 11 mostly from substrate 1 left side to the right.Article three, the terminal pin of lead-in wire 11 does not have insulation course, in order to be connected on the tester.
And then cover filtering membrane 5 and filtering membrane 6 above the electrode at three.This filtering membrane 5,6 is semi-permeable diaphragm.
After this be loam cake 7, the periphery in the same size of the periphery of loam cake 7 and insulation course.In the bottom side of loam cake 7 part of corresponding two-layer filtering membrane have similar recess 10 upper recess, this recess is in order to make things convenient for the fixing of electrode upper two layers filtering membrane, and the combining closely of loam cake 7 and insulation course 4.Simultaneously, also there be the hole similar and corresponding with substrate 1 in loam cake 7 recess central authorities, are connected with the suction inlet 12 of loam cake upside.
2, the assembling of biology sensor:
For assembling this sensor, get substrate 1, enzyme membrane is covered the hole 8 of substrate 1 and place recess 10 interior rear fixing, adopt serigraphy to take the printed silver paste, formation is with the electrode system of three lead-in wires, the coating scope of three electrodes is printed in substrate 1 recess 10, and three lead-in wire 11 printings extend to the substrate right-hand member.Thereby printing forms electroplax 3, and at this moment, enzyme membrane 2 forms responding layer with electrode system.And then in specified scope the printing insulation course 4.Get filtering membrane 5, filtering membrane 6 places and is fixed on the matrix area at electrode system place, does not print the insulativity paste in this spill area, filtering membrane 5, filtering membrane 9 complete overlapping placements.Add at last loam cake 7, the recess that makes loam cake 7 is the two-layer filtering membrane 5 and 6 above the counter electrode plate 3 just in time, and this recess depths is identical with two-layer filtering membrane thickness.
3, the use of biology sensor:
For measuring certain composition in the blood with this sensor, the blood of sample is supplied to the recess at two-layer filtering membrane place from the opening of suction inlet 12.The blood that supplies to here soaks in 5 to its through filter membrane 6, filtering membrane.Because in filtering membrane 5 and 6, the wetting-out rate of blood cell is compared to the blood plasma of liquid component and wants slow, so blood plasma oozes out from the bottom of filtering membrane 5.Then, the series of chemical such as redox occur in the gel reaction reagent that the enzyme membrane of this blood plasma lysis electrodes alliance below of oozing out 2 is entrained on the enzyme membrane 2, and existing electric current 11 is transferred on the analyser that connects by going between on the electrode.
Through the process that this blood cell filters, occur through behind the certain hour, to be measured current value by electrode reaction, quantitatively the composition in the blood plasma by the chemical reaction of the mensuration composition in enzyme membrane 2 that blood plasma dissolved and the blood plasma.
Above-described embodiment is the better embodiment of the present invention; but embodiments of the present invention are not restricted to the described embodiments; other any do not deviate from change, the modification done under Spirit Essence of the present invention and the principle, substitutes, combination, simplify; all should be the substitute mode of equivalence, be included within protection scope of the present invention.
Claims (4)
1. biology sensor comprises the insulativity substrate, contains responding layer, insulation course and the loam cake of oxidoreducing enzyme and electron mediator, and it is characterized in that: described responding layer comprises electrode system and enzyme membrane, and reagent responds on the enzyme membrane; Be provided with two-layer filtering membrane be used to filtering hyperglobulinemia between described insulation course and the loam cake; Described electrode system is directly to be printed on the enzyme membrane; Used filtering membrane is comprised of the porous body semi-permeable diaphragm by space part; Described semi-permeable diaphragm has water wettability.
2. biology sensor according to claim 1 is characterized in that: the outside of described insulativity substrate and loam cake is respectively equipped with corresponding sample suction inlet, and by the insulativity substrate, on cover corresponding through hole and be communicated with filtering membrane and enzyme membrane respectively.
3. biology sensor according to claim 2 is characterized in that: described insulativity substrate is provided with and is fit to the recess that enzyme membrane is put into, and described through hole is positioned at recess; Cover on described and be provided with the recess that suitable filtering membrane is put into, through hole is positioned at recess.
4. biology sensor according to claim 1, it is characterized in that: the reaction reagent on the described enzyme membrane is after sensor assembles, suction inlet by substrate-side drips to dry forming on the enzyme membrane.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 200910302101 CN101561411B (en) | 2009-05-05 | 2009-05-05 | Biosensor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 200910302101 CN101561411B (en) | 2009-05-05 | 2009-05-05 | Biosensor |
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| Publication Number | Publication Date |
|---|---|
| CN101561411A CN101561411A (en) | 2009-10-21 |
| CN101561411B true CN101561411B (en) | 2013-01-16 |
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| Application Number | Title | Priority Date | Filing Date |
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| CN 200910302101 Active CN101561411B (en) | 2009-05-05 | 2009-05-05 | Biosensor |
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Families Citing this family (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| TWI439689B (en) | 2010-09-23 | 2014-06-01 | Bionime Corp | Electrochemical test specimen |
| CN102445471B (en) * | 2010-10-09 | 2014-04-09 | 华广生技股份有限公司 | Electrochemical sensory test piece |
| CN109781804A (en) * | 2017-11-10 | 2019-05-21 | 上海瀚联医疗技术股份有限公司 | A kind of blood sugar test module |
| CN109781821B (en) * | 2017-11-10 | 2023-10-24 | 上海瀚联医疗技术股份有限公司 | Blood sugar detector |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1219676A (en) * | 1997-12-08 | 1999-06-16 | 美国生物医学有限公司 | Bi-mediator-based glucose biosensor and its use method |
| EP1235068B1 (en) * | 1999-11-15 | 2006-01-25 | ARKRAY, Inc. | Biosensor |
| CN2890919Y (en) * | 2006-04-11 | 2007-04-18 | 中国人民解放军第三军医大学第二附属医院 | Cylindrical Body Fluid Glucose Electrochemical Sensor |
| CN201497726U (en) * | 2009-05-05 | 2010-06-02 | 尹良红 | Biosensor |
-
2009
- 2009-05-05 CN CN 200910302101 patent/CN101561411B/en active Active
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1219676A (en) * | 1997-12-08 | 1999-06-16 | 美国生物医学有限公司 | Bi-mediator-based glucose biosensor and its use method |
| EP1235068B1 (en) * | 1999-11-15 | 2006-01-25 | ARKRAY, Inc. | Biosensor |
| CN2890919Y (en) * | 2006-04-11 | 2007-04-18 | 中国人民解放军第三军医大学第二附属医院 | Cylindrical Body Fluid Glucose Electrochemical Sensor |
| CN201497726U (en) * | 2009-05-05 | 2010-06-02 | 尹良红 | Biosensor |
Non-Patent Citations (1)
| Title |
|---|
| JP昭64-23153A 1989.01.25 |
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| CN101561411A (en) | 2009-10-21 |
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Application publication date: 20091021 Assignee: Guangzhou En Deshi medical article Industrial Co., Ltd. Assignor: Yin Lianghong Contract record no.: 2015440000891 Denomination of invention: Method for raising reading value resolution of biological sensor Granted publication date: 20130116 License type: Exclusive License Record date: 20151230 |
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Effective date of registration: 20160823 Address after: The science city of Guangzhou hi tech Industrial Development Zone, Guangdong province 510663 Guangzhou Nanxiang Road OTLAN Technology Park No. 68 owned plant a four floor room 402 Patentee after: Guangzhou En Deshi medical article Industrial Co., Ltd. Address before: 120, room 20, building 601, 510632 Ru court, West Whampoa Road, Guangzhou, Guangdong Patentee before: Yin Lianghong |