CN2715150Y - A nanometer decorated biologic array sensor - Google Patents
A nanometer decorated biologic array sensor Download PDFInfo
- Publication number
- CN2715150Y CN2715150Y CN 200420037314 CN200420037314U CN2715150Y CN 2715150 Y CN2715150 Y CN 2715150Y CN 200420037314 CN200420037314 CN 200420037314 CN 200420037314 U CN200420037314 U CN 200420037314U CN 2715150 Y CN2715150 Y CN 2715150Y
- Authority
- CN
- China
- Prior art keywords
- electrode
- nanometer
- oxidase
- decorated
- array sensor
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Images
Abstract
The utility model discloses a nanometer decorated biologic array sensor, relating to a nanometer biosensor which can simultaneously detect four kinds of contents, such as dextrose, etc. The nanometer decorated biologic array sensor is characterized in that a working electrode (9) is composed of decorative nuclear shell-mold NR-SIO2 nanometer particles and glucose oxidase on four carbon matrix electrodes (20), oxidizing enzyme, L-glutamic acid oxidase or xanthine oxidase. A thin-layer detector cell (8) is polyfluortetraethylene film (18) whose middle is caverned, the bottom of the detector cell is four carbon matrix electrodes (20) which decorates different bioactive enzyme, and the top of the detector cell is the stainless steel electrode (16) of a counter electrode (7) and a liquid inlet pore (6) and a liquid outlet pore (13); the working electrode (9), the thin-layer detector cell (8) and the counter electrode (7) are fixed as integration by a screw (11). The nanometer decorated biologic array sensor has easy production, low cost, high sensitivity, good stability, wide linear range, low detection line and less required sample amount; the nanometer decorated biologic array sensor can directly detect the trace content of the dextrose, the lactic acid, the L-glutamate and the hypoxanthine in various from solutions.
Description
Technical field
The utility model relates to a kind of novel nano-modified biologic array sensor that can detect 4 kinds of content such as glucose simultaneously, belongs to biosensor technology and nano biological detection technique field.
Background technology
The up-to-date AUTHORITATIVE DATA of having issued of the World Health Organization (WHO): global diabetic's number surpasses 1.77 hundred million, expects 2025 and will reach 3.7 hundred million, and the country that comes the diabetes prevalence front three is respectively India, China and the U.S..Startling numeral shows that diabetes have become one of maximum assailant of harm humans health, and the trend of extension and rejuvenation is arranged.The diabetic is because of the insulin deficit in the body or obstacle is arranged, and the metabolism that makes glucose produces disorder, simultaneously the content with the closely-related lactic acid of glycogen metabolism etc. also changes, and glutamic acid is the important amino acid of nervous excitation conduction, and hypoxanthine can be weighed the degree of cellular damage.Measure the content of these 4 kinds of materials simultaneously, can be diabetes and complication patient thereof comparatively comprehensively information of medical diagnosis on disease aspect is provided.
But the function singleness of the biology sensor of glucose, lactic acid equal size in the present existing measurement blood is promptly generally only measured single index.And ubiquity that sensitivity is not high, anti-interference difference and stability is low and the high defective of manufacturing cost.For example Chinese patent application " blood lactic acid electrochemical sensor " (application number 03128815.4) is made up of working electrode that is covered with successively on the substrate that is provided with blood sample surveying work district, the substrate and contrast electrode.Substrate (scope inside, blood sample surveying work district) also is covered with and can reacts with lactic acid, and produces the enzyme reagent reacting film of electron transport.Enzyme reagent reacting film contains Lactate Oxidase, electron transit mediator, stabilizing agent and can make the blood sample rapid osmotic to the inner hydrophilic high mol material that reacts with enzyme of reaction film.Because electron transit mediator has adopted fewrricyanic acid root, but fewrricyanic acid root good water solubility, easily loss makes that the stability of sensor is influenced.Thereby the confidence level of measurement result has been lowered.Chinese patent application " full blood glucose biological sensor " (application number 03129434.0) and " full blood lactic biological sensor " (application number 03129433.2) have proposed responding layer by carboxyl methyl cellulose, carbon nano-tube modified (as electronics second mediator), the biology sensor that the potassium ferricyanide, Lactate Oxidase or glucose oxidase (as the reagent of electronics first mediator), stabilizing agent, buffer preparation become can be used to measure the lactic acid in the blood, the content of glucose.Electronics second mediator of introducing, carbon nano-tube has improved the response sensitivity of sensor, has overcome fewrricyanic acid root and has run off and cause the defective of poor stability.But because responding layer is to be superimposed upon successively in the cavity that is provided with pore, so theirs is higher with the enzyme amount, makes the cost of sensor improve.
Summary of the invention
The purpose of this utility model is that design a kind ofly can be used for detecting simultaneously glucose, lactic acid, L-glutamic acid and hypoxanthine content, and highly sensitive, good stability, the nano-modified biology sensor that required sample size is few, cost of manufacture is cheap.
To achieve these goals, the utility model is performed such: sensor comprises working electrode, contrast electrode and to electrode and solution import and export.Be characterized in: working electrode is made up of polyfluortetraethylene plate and 4 carbon array electrodes that run through this plate.The carbon array electrode respectively is provided with the carbon electrode lead-in wire by carbon electrode and bottom thereof, and the top is modified with four kinds of different enzyme reagent reacting films respectively and constitutes.Enzyme reagent reacting film is by hud typed dimethyl diaminophenazine chloride doped silica (NR-SiO
2) nano particle and bioactive enzyme composition.Bioactive enzyme is respectively glucose oxidase (GOD), Lactate Oxidase (LOD), L-dglutamic oxidase (L-GLOD) or xanthine oxidase (XOD).Be provided with the thin layer detection cell above the working electrode successively and to electrode, and be solidified as a whole with working electrode, thin layer detection cell with to electrode by screw.To electrode by polyfluortetraethylene plate and run through this plate stainless steel electrode, contact conductor and liquid-inlet hole and outlet opening are formed.The thin layer detection cell is the poly tetrafluoroethylene that scrapes out through hole in the middle of a slice, is four carbon array electrodes that are modified with enzyme reagent reacting film at the bottom of the pond, and the top, pond is liquid-inlet hole and the outlet opening that the stainless steel electrode on the electrode and symmetria bilateralis are offered.The liquid-inlet hole directly is connected with the solution inlet port pipe.The liquid outlet hole is connected with sleeve pipe by taking over, and contrast electrode is housed in the sleeve pipe, and sleeve pipe one side is provided with the taphole pipe.
The utlity model has following advantage and effect:
1. because working electrode of the present utility model partly is to be made of 4 carbon array electrodes, and its bottom separately is provided with lead-in wire, the top is modified with different enzyme reagent reacting films respectively.Enzyme reagent reacting film is by hud typed dimethyl diaminophenazine chloride doped silica (NR-SiO
2) nano particle and bioactive enzyme composition.Bioactive enzyme is respectively glucose oxidase (GOD), Lactate Oxidase (LOD), L-dglutamic oxidase (L-GLOD) and xanthine oxidase (XOD).By the electroanalyzer that is attached thereto, can detect glucose, lactic acid, L-glutamic acid and hypoxanthine content in the solution such as blood simultaneously.
2. because the enzyme reagent reacting film that carbon electrode top end surface of the present utility model is modified is with hud typed NR-SiO
2Nano particle is modified, and its nuclear NR has good electrical conductivity, and bioactive enzyme is had catalytic action, its shell SiO
2Have good bio-compatibility and bioaffinity, make its catalytic current increased 3-9 doubly the ampere response of (different bioactive enzymes, the raising of its catalytic effect are also different) so this sensor be 3-9 times of no nano-modified sensor.
3. because the NR-SiO that adopts
2Nano-particles size is 20-100nm, simultaneously, and the shell SiO of this nano particle
2Have good bio-compatibility and bioaffinity, and be tridimensional network, effectively prevented the leakage of nuclear NR electron transit mediator, significantly improved the stability of nuclear NR electron transit mediator.Therefore guaranteed the stability of this sensor.
4. because biology sensor has adopted the thin layer detection cell, required sample size is few when therefore detecting.
5. owing to adopted NR-SiO
2Nano particle, therefore except sensitivity and stability were improved, its range of linearity was wide, can reach 4 orders of magnitude, and the lowest detection line has been reduced to 2.0 * 10
-7MolL
1, can directly detect the solution that contains micro-glucose, lactic acid etc., for example brain dialyzate etc.
6. because biology sensor only needs glucose oxidase, the Lactate Oxidase of 0.2 unit of activity, the L-dglutamic oxidase of 0.04 unit of activity and the hypoxanthine oxidase of 0.05 unit of activity of 0.4 unit of activity.And usually, as the bioactive enzyme of number of patent application 03129433.2 and 03129434.0 lactic acid and 1-2 unit of activity of glucose sensor need.Therefore cheap for manufacturing cost.
Description of drawings
Fig. 1 is the cut-open view of biology sensor of the present utility model;
Fig. 2 is the vertical view to electrode of biology sensor of the present utility model;
Fig. 3 is the vertical view of the thin layer detection cell of biology sensor of the present utility model;
Fig. 4 is the vertical view of the working electrode of biology sensor of the present utility model;
Illustration
Retainer plate 1, taphole pipe 2, contrast electrode 3, to contact conductor 4, solution inlet port pipe 5, solution inlet port hole 6, to electrode 7, thin layer detection cell 8, working electrode 9, carbon electrode lead-in wire 10, screw 11, pilot hole 12, taphole hole 13, take over 14, sleeve pipe 15, stainless steel electrode 16, polyfluortetraethylene plate 17, through hole 18,19,4 carbon array electrodes 20 of poly tetrafluoroethylene.
Embodiment
See also accompanying drawing 1,2,3,4.Sensor comprises working electrode 9, electrode 7 and contrast electrode 3 and solution import and export pipe 5 and 2 is constituted.Contrast electrode 3 is a saturated calomel electrode.Be characterized in, working electrode 9 is made up of polyfluortetraethylene plate (claiming insulativity Teflon base material again) 17 and 4 carbon array electrodes 20 that run through this plate 17, and the carbon electrode lead-in wire 10 that carbon array electrode 20 respectively is provided with by carbon electrode and bottom thereof, the different enzyme reagent reacting film that the top is modified are formed.Enzyme reagent reacting film is by a kind of composition the in hud typed dimethyl diaminophenazine chloride doped silica nano particle and the 4 kinds of bioactive enzymes.4 kinds of bioactive enzymes are respectively glucose oxidase (GOD, from Aspergillus niger, EC 1.1.3.4.150 000units/g), Lactate Oxidase (LOD, from Pediococcus species, 37U/mg), L-dglutamic oxidase (L-GLOD, EC 1.4.3.11, from Streptomyces sp., 10.8U/mg) or xanthine oxidase (XOD, EC1.1.3.22, Grade I from Buttermilk, 1U (mg Protein)
-1, 34.7mg Protein mL
-1).These enzymes all can commercially availablely be buied.Can apply the Nafion methanol solution of one deck 1% on the enzyme reagent reacting film surface again, form the Nafion film that the anti-negative ion of one deck disturbs, can further strengthen the interference free performance of this sensor.Be provided with thin layer detection cell 8 above the working electrode 9 successively and to electrode 7, thickness separately is respectively: 12mm, 0.15mm and 12mm, and all have 4 pilot holes 12 all around, penetrate pilot hole 12 by screw 11 and be solidified as a whole with working electrode 9, thin layer detection cell 8 with to electrode 7 threes.To electrode 7 by polyfluortetraethylene plate 17 and run through this plate 17 stainless steel electrode 16 and with stainless steel electrode 16 affixed contact conductor 4 is formed.Thin layer detection cell 8 is to scrape out the poly tetrafluoroethylene 19 that diameter is the through hole 18 of 8mm in the middle of a slice, at the bottom of the pond four carbon array electrodes 20 that are modified with enzyme reagent reacting film, the top, pond is liquid-inlet hole 6 and the outlet opening 13 that stainless steel electrode on the electrode 7 16 and symmetria bilateralis are offered, and forming volume thus is 9.66 μ L thin layer detection cells 8.By being fixed in the nut on the electrode 7 directly is connected solution inlet port pipe 5 with liquid-inlet hole 6.Liquid outlet hole 13 is threaded with sleeve pipe 15 by taking over 14.Contrast electrode 3 is housed in the sleeve pipe 15, and is fixed in the sleeve pipe 15 with contrast electrode retainer plate 1.Sleeve pipe 15 1 sides are provided with taphole pipe 2.
During test sample, can be connected by little injector of microchannel with the flow injection instruments of sensor outside.Open solution import and export pipe 5 and 2, then testing liquid is a moving phase, if close solution import and export pipe 5,2, testing liquid is non-moving phase.Start the electroanalyzer that is connected with contrast electrode 1 with working electrode 9, to electrode 7, can detect the ampere signal of glucose in blood or brain dialyzate or other solution or lactic acid or L-glutamic acid or hypoxanthic concentration change, according to the corresponding work curve, just can obtain its content.
Claims (1)
1. nano-modified biologic array sensor, comprise working electrode (9), to electrode (7) and contrast electrode (3) and solution inlet port pipe (5) and outlet (2), it is characterized in that: working electrode (9) is made up of polyfluortetraethylene plate (17) and four carbon array electrodes (20) of running through plate (17), carbon array electrode (20) bottom is provided with lead-in wire (10) separately, the top is modified with enzyme reagent reacting film, and enzyme reagent reacting film is by hud typed dimethyl diaminophenazine chloride doped silica nano particle and glucose oxidase, Lactate Oxidase, four kinds of bioactive enzymes of L-dglutamic oxidase or xanthine oxidase are formed; Be provided with thin layer detection cell (8) above the working electrode (9) successively and to electrode (7), and be solidified as a whole with working electrode (9), thin layer detection cell (8) with to electrode (7) by screw (11); To electrode (7) by polyfluortetraethylene plate (17) and run through this plate (17) stainless steel electrode (16), contact conductor (4) and liquid-inlet hole (6) and outlet opening (13) are formed; Thin layer detection cell (8) is the poly tetrafluoroethylene (19) that scrapes out through hole (18) in the middle of a slice, be four carbon array electrodes (20) that are modified with different enzyme reagent reacting films at the bottom of the pond, the top, pond is liquid-inlet hole (6) and the outlet opening (13) that stainless steel electrode (16) on the electrode (7) and symmetria bilateralis are offered; Liquid-inlet hole (6) directly is connected with solution inlet port pipe (5); Liquid outlet hole (13) is connected with sleeve pipe (15) by taking over (14), and contrast electrode (3) is housed in the sleeve pipe (15), and sleeve pipe (15) one sides are provided with taphole pipe (2).
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 200420037314 CN2715150Y (en) | 2004-07-08 | 2004-07-08 | A nanometer decorated biologic array sensor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 200420037314 CN2715150Y (en) | 2004-07-08 | 2004-07-08 | A nanometer decorated biologic array sensor |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN2715150Y true CN2715150Y (en) | 2005-08-03 |
Family
ID=34871656
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN 200420037314 Expired - Fee Related CN2715150Y (en) | 2004-07-08 | 2004-07-08 | A nanometer decorated biologic array sensor |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN2715150Y (en) |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101968450A (en) * | 2010-09-29 | 2011-02-09 | 重庆大学 | Embedded porphyrin sensor array-based saliva sugar and urine sugar detector |
| CN101231287B (en) * | 2008-02-22 | 2011-09-14 | 东南大学 | Method for preparing biosensor by arraying nanometer particles in external field evoked electrode |
| CN105102972A (en) * | 2013-01-11 | 2015-11-25 | 东北大学 | Saliva glucose monitoring system |
| CN108828043A (en) * | 2018-06-25 | 2018-11-16 | 湖北中医药大学 | A kind of flexibility perspiration sensor and its preparation method and application |
| CN110873751A (en) * | 2018-08-31 | 2020-03-10 | 佛山市顺德区美的电热电器制造有限公司 | Purine sensor and purine uptake control method |
-
2004
- 2004-07-08 CN CN 200420037314 patent/CN2715150Y/en not_active Expired - Fee Related
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101231287B (en) * | 2008-02-22 | 2011-09-14 | 东南大学 | Method for preparing biosensor by arraying nanometer particles in external field evoked electrode |
| CN101968450A (en) * | 2010-09-29 | 2011-02-09 | 重庆大学 | Embedded porphyrin sensor array-based saliva sugar and urine sugar detector |
| CN105102972A (en) * | 2013-01-11 | 2015-11-25 | 东北大学 | Saliva glucose monitoring system |
| CN108828043A (en) * | 2018-06-25 | 2018-11-16 | 湖北中医药大学 | A kind of flexibility perspiration sensor and its preparation method and application |
| CN110873751A (en) * | 2018-08-31 | 2020-03-10 | 佛山市顺德区美的电热电器制造有限公司 | Purine sensor and purine uptake control method |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| Jaffari et al. | Recent advances in amperometric glucose biosensors for in vivo monitoring | |
| Norouzi et al. | Glucose biosensor based on MWCNTs-gold nanoparticles in a nafion film on the glassy carbon electrode using flow injection FFT continuous cyclic voltammetry | |
| Palmisano et al. | Simultaneous monitoring of glucose and lactate by an interference and cross-talk free dual electrode amperometric biosensor based on electropolymerized thin films | |
| US6893552B1 (en) | Microsensors for glucose and insulin monitoring | |
| Miertuš et al. | Amperometric biosensors based on solid binding matrices applied in food quality monitoring | |
| KR101531384B1 (en) | Reagent composition for biosensor and biosensor comprising the same | |
| Haghighi et al. | Direct electron transfer from glucose oxidase immobilized on an overoxidized polypyrrole film decorated with Au nanoparticles | |
| Xu et al. | A 3D porous graphene aerogel@ GOx based microfluidic biosensor for electrochemical glucose detection | |
| ITMI951441A1 (en) | NEW ELECTROCHEMICAL BIOSENSORS BASED ON NEW COMPOSITE TRANSDUCERS | |
| JPH0617889B2 (en) | Biochemical sensor | |
| CN205067415U (en) | Uric acid test test paper | |
| Wang et al. | Biocomposite of cobalt phthalocyanine and lactate oxidase for lactate biosensing with MnO2 nanoparticles as an eliminator of ascorbic acid interference | |
| CN105572199A (en) | Working electrode biological reactant and electrode type test strip | |
| CN107436316A (en) | The preparation of glucose sensor based on graphene and graphene oxide composite material | |
| Wang et al. | Glucose in human serum determined by capillary electrophoresis with glucose micro-biosensor | |
| Petersson | Amperometric assay of glucose and lactic acid by flow injection analysis | |
| Rhemrev-Boom et al. | On-line continuous monitoring of glucose or lactate by ultraslow microdialysis combined with a flow-through nanoliter biosensor based on poly (m-phenylenediamine) ultra-thin polymer membrane as enzyme electrode | |
| Li et al. | A new handheld biosensor for monitoring blood ketones | |
| CN2715150Y (en) | A nanometer decorated biologic array sensor | |
| Rodriguez et al. | Highly selective first generation glucose biosensor based on carbon paste containing copper and glucose oxidase | |
| CN1912626A (en) | Preparation of disposable carbon-base glucose chip and electrochemical detection method | |
| CN112485312A (en) | Nafion/glucose oxidase/graphene oxide/nano porous platinum electrode and preparation method and application thereof | |
| Yamamoto et al. | Evaluation of an amperometric glucose biosensor based on a ruthenium complex mediator of low redox potential | |
| CN1815215A (en) | Glucose biological sensor capable of eliminating interference | |
| JP2020523565A (en) | Electrochemical biosensor |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| C19 | Lapse of patent right due to non-payment of the annual fee | ||
| CF01 | Termination of patent right due to non-payment of annual fee |