CN112525959A - Integrating electrode structure, biosensor and manufacturing method of integrating electrode biosensor - Google Patents
Integrating electrode structure, biosensor and manufacturing method of integrating electrode biosensor Download PDFInfo
- Publication number
- CN112525959A CN112525959A CN201910885466.7A CN201910885466A CN112525959A CN 112525959 A CN112525959 A CN 112525959A CN 201910885466 A CN201910885466 A CN 201910885466A CN 112525959 A CN112525959 A CN 112525959A
- Authority
- CN
- China
- Prior art keywords
- electrode
- integral
- integration
- transmission
- layer
- 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.)
- Pending
Links
Images
Classifications
-
- 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
-
- 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
-
- 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
Abstract
The invention discloses an integral electrode structure, which comprises a first electrode and a second electrode, wherein the first electrode consists of a first integral electrode and a first transmission electrode; the second electrode consists of a second integration electrode and a second transmission electrode; the first integration electrode and the second integration electrode are formed by separating a snake-shaped trace; the first transmission electrode is arranged on one side of the first integration electrode, and the second transmission electrode is arranged on one side of the second integration electrode. The invention also discloses a biosensor and a manufacturing method thereof. The electrodes can obtain uniform signals when the reaction reagent and the analyte react; the reagent area is divided into a first electrode and a second electrode by a trace line and is fully utilized, each electrode can obtain the maximum signal in reaction, and the signal intensity is high; two reaction reagent systems can be arranged in the same reaction area, two reactants in a sample to be detected can be detected simultaneously, more signals can be obtained in the same area, and the detection result is more accurate; the manufacturing method is simple, the processing precision is high, and the difference between different batches is small.
Description
Technical Field
The invention belongs to the field of biosensors, and particularly relates to an integrating electrode structure, a biosensor and a manufacturing method of the integrating electrode biosensor.
Background
Screen printing is a common method for manufacturing biosensors, and is widely used due to its low cost and simple manufacturing process. However, the method has inherent defects and low processing precision, so that the printed electrode edge is easy to have the problems of burrs, ripples and the like, and the testing precision is influenced to a certain extent.
On the other hand, when the biosensor is manufactured without the support of the enzyme layer screen printing technology, the reaction reagent is generally arranged on the electrode in a liquid dispensing mode, whether the diffusion and distribution conditions of the solution in the liquid dispensing area are uniform or not affects the performance of the biosensor, and the solution is easily diffused unevenly in the liquid dispensing process and the solution drying process.
When the reaction reagents are arranged in a screen printing electrode processing and point-of-use liquid mode and applied simultaneously, the corresponding problems are also aggravated, and certain intra-batch difference and inter-batch difference are shown.
Disclosure of Invention
In order to overcome the defects of the prior art, the invention provides an integrating electrode structure which can fully utilize a reaction area, can obtain uniform and maximum signals when each electrode reacts with a reaction reagent and an analyte, has high signal intensity, a biosensor with the integrating electrode structure and a manufacturing method of the integrating electrode biosensor.
The technical scheme adopted by the invention for solving the technical problems is as follows: an integrating electrode structure comprising a first electrode and a second electrode,
the first electrode consists of a first integrating electrode and a first transmission electrode;
the second electrode consists of a second integration electrode and a second transmission electrode;
the first integrating electrode and the second integrating electrode are formed by separating a snake-shaped trace;
the first transmission electrode is arranged on one side of the first integration electrode, and the second transmission electrode is arranged on one side of the second integration electrode.
Preferably, the traces are blank separation lines formed by laser firing or bombardment.
The invention also discloses a biosensor, which comprises a substrate layer, an electrode layer and an insulating layer,
the insulating layer is provided with a reagent area, and the reagent area is used for arranging a reaction reagent;
the electrode layer is provided with an integral electrode structure, the integral electrode structure comprises a first electrode and a second electrode, the first electrode is composed of a first integral electrode and a first transmission electrode, the second electrode is composed of a second integral electrode and a second transmission electrode, the first integral electrode and the second integral electrode are formed by separating a snake-shaped trace, the first transmission electrode is arranged on one side of the first integral electrode, and the second transmission electrode is arranged on one side of the second integral electrode;
the first transmission electrode is provided with a first contact which can be electrically connected with the detection instrument, and the second transmission electrode is provided with a second contact which can be electrically connected with the detection instrument.
Furthermore, a first auxiliary trace line is arranged on the first integration electrode; or a first auxiliary trace line is arranged on the second integration electrode; or the first integration electrode is provided with a first auxiliary trace line, and the second integration electrode is provided with a second auxiliary trace line.
Furthermore, the electrode layer further comprises a third electrode consisting of a third integration electrode and a third transmission electrode, and a fourth electrode consisting of a fourth integration electrode and a fourth transmission electrode, wherein the third transmission electrode is provided with a third contact electrically connected with the detection instrument, and the fourth transmission electrode is provided with a fourth contact electrically connected with the detection instrument.
Furthermore, a plurality of snake-shaped traces are arranged in the electrode layer, and horizontal dividing lines are arranged between areas where adjacent traces are located and are formed by laser burning or bombardment.
The invention also discloses a manufacturing method of the integral electrode biosensor, which comprises the following steps:
1) selecting a substrate layer;
2) printing and curing a conductive material to the substrate layer to form an integral electrode base layer;
3) printing and curing a conductive material to a substrate layer to form a transfer electrode and a contact;
4) burning or bombarding the integration electrode base layer by laser to make the conductive material at the burnt or bombarded position separate from the substrate layer to form a snake-shaped trace extending in a snake-shaped bending way, thus completing the manufacture of the integration electrode;
5) printing and curing an insulating layer on the substrate layer on which the electrode layer is manufactured, wherein the insulating layer is provided with a hollowed reagent area for setting a reaction reagent;
6) the reaction reagent is arranged in the reagent area, and the sample channel is laid in the reaction area.
Further, the conductive material in step 2) is conductive carbon paste, the conductive carbon paste is printed on the substrate layer of the reaction area by a screen printing method to form an integral electrode base layer with a thickness, and the integral electrode base layer is cured to the substrate layer by high temperature.
Further, the conductive material in the step 3) is conductive silver paste, the conductive silver paste is printed to a specific position on the substrate layer by a screen printing manner, a transmission electrode and a contact are formed, and the transmission electrode and the contact are cured to the substrate layer by high temperature.
Further, the insulating layer in the step 5) is obtained by screen printing of insulating ink, a hollow reagent area is formed, and the insulating layer is cured by irradiation of an ultraviolet curing lamp.
Furthermore, the substrate layer is a uniform plastic substrate with a compact and non-porous surface, and the thickness is 0.1-5 mm.
The invention refers to a method for solving the area of a circle or an ellipse by referring to the principle of calculus, the circle or the ellipse is cut into a plurality of parts in parallel, the sum of the areas of rectangles with different lengths of each part is calculated to be the area of the circle, a similar circular electrode area is also cut in parallel for a plurality of times, and every two adjacent parts are respectively connected to the two ends of a positive electrode and a negative electrode after being cut, namely the design of a calculus electrode area is shown in figure 1.
The invention provides an integral electrode, which decomposes and uniformly distributes the electrode in the whole reagent area in an integral mode, increases the number of the electrodes, decomposes the electrode in a laser burning or bombarding mode, reduces the electrode spacing under the condition of not thoroughly changing the process, and improves the ratio of the electrode in the whole reaction area.
The invention overcomes the problem of low processing precision of silk-screen printing, the edge precision of laser cutting is superior to the edge of carbon ink printing, and the problems of burrs, ripples and the like are avoided; the problem of signal difference is generated after reaction caused by uneven diffusion of a reaction reagent is solved, the area of a reaction area is fully utilized, the coverage rate of an electrode is improved, and the uniformity of reagent diffusion is improved, so that the coverage of the electrode with a larger area is realized in a limited area, the signal intensity is improved, and different substances in a sample can be detected by arranging a plurality of reagent areas in the same reaction area.
The invention has the beneficial effects that: 1) when the areas of the first electrode and the second electrode of the integrating electrode structure are equal, each electrode can obtain uniform signals when the reaction reagent and the analyte react; 2) the reagent area is divided into a first electrode and a second electrode by a trace line, and the reagent area is fully utilized, so that each electrode can obtain the maximum signal when the reaction reagent and the analyte react, and the signal intensity is high; 3) the areas of the first electrode and the second electrode of the integral electrode structure can also be unequal, so that the accessible area of electron transfer is increased, and the signal intensity is increased; 4) two reaction reagent systems can be arranged in the same reaction area, two reactants in a sample to be detected can be detected simultaneously, more signals can be obtained in the same area compared with a common electrode, and the obtained detection result is more accurate; 5) the integrated electrode biosensor has the advantages of simple manufacturing method, high processing precision and small difference among different batches.
Drawings
FIG. 1 is a schematic diagram of an integrating electrode structure according to the present invention.
FIG. 2 is an exploded view of the reaction region of the sample to be measured of the biosensor of the present invention.
FIG. 3 is another schematic diagram of the integrating electrode structure of the present invention.
FIG. 4 is a schematic structural view of a biosensor according to the present invention.
FIG. 5 is a schematic view showing the structure of a biosensor (two reaction reagent system) according to the present invention.
FIG. 6 is a schematic diagram of the structure of a biosensor (with auxiliary traces) according to the present invention.
FIG. 7 is a flow chart of the manufacturing process of the biosensor according to the present invention.
Detailed Description
In order to make the technical solutions of the present invention better understood, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
As shown in fig. 1 and 2, an integrating electrode structure includes a first electrode 401 and a second electrode 402, the first electrode 401 is composed of a first integrating electrode 4011 and a first transmitting electrode 4012, the first transmitting electrode 4012 is disposed on one side of the first integrating electrode 4011, the second electrode 402 is composed of a second integrating electrode 4021 and a second transmitting electrode 4022, and the second transmitting electrode 4022 is disposed on one side of the second integrating electrode 4021; the first integrating electrode 4011 and the second integrating electrode 4021 are formed by separating through a snake-shaped trace 4001, the first integrating electrode 4011 and the second integrating electrode 4021 can be spliced seamlessly, the first integrating electrode 4011 and the second integrating electrode 4021 are identical in structure and different in arrangement direction, the moving position of the first integrating electrode 4011 can coincide with the second integrating electrode 4021 after the first integrating electrode 4011 rotates 180 degrees anticlockwise, the trace 4001 is a blank separation line formed by laser cauterization or bombardment of conductive carbon paste between the first integrating electrode 4011 and the second integrating electrode 4021, and the conductive carbon paste is bombarded and gasified and separated.
As shown in fig. 1 and 2, a reaction area 400 of a sample to be measured of a biosensor sequentially includes a substrate layer 403, an electrode layer 405 and an insulating layer 404 from bottom to top, a hollowed elliptical area framed by the insulating layer 404 is a reagent area 2, the reagent area 2 is an area for setting a reaction reagent, the electrode layer 405 includes a first electrode 401 and a second electrode 402, the first electrode 401 is composed of a first integrating electrode 4011 and a first transmission electrode 4012, the first transmission electrode 4012 is arranged on one side where the first integrating electrode 4011 is located, the second electrode 402 is composed of a second integrating electrode 4021 and a second transmission electrode 4022, and the second transmission electrode 4022 is arranged on one side where the second integrating electrode 4021 is located; the first integrating electrode 4011 and the second integrating electrode 4021 are formed by separating through a snake-shaped trace 4001, the first integrating electrode 4011 and the second integrating electrode 4021 can be spliced seamlessly, the first integrating electrode 4011 and the second integrating electrode 4021 are identical in structure and different in arrangement direction, the moving position of the first integrating electrode 4011 can coincide with the second integrating electrode 4021 after the first integrating electrode 4011 rotates 180 degrees anticlockwise, the trace 4001 is a blank separation line formed by laser cauterization or bombardment of conductive carbon paste between the first integrating electrode 4011 and the second integrating electrode 4021, and the conductive carbon paste is bombarded and gasified and separated.
The trace 4001 divides the electrode layer 405 into at least two electrodes in an integral manner such that the reagents are uniformly distributed to the electrodes when disposed on the first electrode 401 and the second electrode 402, that is, the electrodes can obtain the same volume of the reagents, and the reaction area is sufficiently utilized, so that the electrodes can obtain a uniform and maximum amount of signal when the reagents react with the analyte, thereby increasing the intensity of the signal.
In the above structure, the structures of the first electrode 401 and the second electrode 402 are the same, as shown in fig. 3, the structures of the first electrode and the second electrode may also be different, that is, the electrode areas of the two comb-shaped structures into which the serpentine trace is divided may also be asymmetric, the widths of the respective comb teeth may be different, the serpentine trace extending in a serpentine bending manner may be a vertical bending, or a bending with a radian, or any other bending manner, for example, the comb-shaped area corresponding to the working electrode is enlarged, the comb-shaped area corresponding to the counter electrode/reference electrode is reduced, the passing area of electron transfer may be further increased, and the signal intensity is increased.
As shown in fig. 4, a biosensor 500 has a sample reaction area to be measured as shown in fig. 2, a sample channel (not shown) is disposed in the sample reaction area to be measured, an electrode layer 501 includes a first electrode and a second electrode, the first electrode is composed of an integrating electrode 5011, a transmitting electrode 5012 and a first contact 507 at an end of the transmitting electrode 5012, the transmitting electrode 5012 is disposed at a side where the integrating electrode 5011 is located; the second electrode consists of a second integration electrode 5021, a second transmission electrode 5022 and a second contact 506 positioned at the end part of the second transmission electrode 5022, and the second transmission electrode 5022 is arranged at one side of the second integration electrode 5021;
the first integrating electrode 5011 and the second integrating electrode 5021 are formed by separating through a snake-shaped trace 5001, the first integrating electrode 5011 and the second integrating electrode 5021 can be spliced seamlessly, the trace 5001 is formed by the fact that conductive carbon paste between the first integrating electrode 4011 and the second integrating electrode 4021 is burned or bombarded by laser, and the conductive carbon paste is bombarded and gasified to separate from formed blank separation lines.
The biosensor 500 is electrically connected to the detection instrument through the first contact 506 and the second contact 507.
As shown in fig. 5, a biosensor 600 has a reaction region of a sample to be tested as shown in fig. 2, a sample channel (not shown) is disposed in the reaction region of the sample to be tested, and the reaction region has two reaction reagent systems, which can simultaneously detect two reactants in the sample to be tested. Specifically, the biosensor 600 includes a first electrode 601, a second electrode 602, a third electrode 608, and a fourth electrode 609, where the first electrode 601 is composed of a first integrating electrode, a first transmitting electrode, and a first contact 607, the second electrode 602 is composed of a second integrating electrode, a second transmitting electrode, and a second contact 606, the third electrode 608 is composed of a third integrating electrode, a third transmitting electrode, and a third contact 611, and the fourth electrode 609 is composed of a fourth integrating electrode, a fourth transmitting electrode, and a fourth contact 610. The two reaction reagent systems are separated by a horizontal dividing line 6002, the horizontal dividing line 6002 is formed by laser burning or bombardment, the reaction systems corresponding to the two sides of the horizontal dividing line 6002 correspond to the serpentine trace 6001 and the serpentine trace 6005, respectively, and the serpentine trace 6001, the serpentine trace 6005 and the dividing line 6002 are combined to form the first electrode 601, the second electrode 602, the third electrode 608 and the fourth electrode 609. The biosensor is electrically connected to the detection instrument through the first contact 607, the second contact 606, the third contact 611, and the fourth contact 610. Of course, a plurality of reaction reagent systems can be arranged, adjacent reaction reagent systems are separated by a horizontal dividing line, and each reaction reagent system is internally provided with a serpentine trace obtained by laser burning or bombardment. The integration electrode is arranged in the reaction area of the biosensor, so that the area of the area is fully utilized, and when a plurality of reactants in a sample to be detected are detected simultaneously, compared with a common electrode, more signals can be obtained in the same area, and the obtained detection result is more accurate.
As shown in fig. 6, a biosensor 700 includes a first electrode 701, a second electrode 702, a third electrode 708, and a fourth electrode 709, the first electrode 701 is composed of a first integrating electrode, a first transmitting electrode, and a first contact 707, the second electrode 702 is composed of a second integrating electrode, a second transmitting electrode, and a second contact 706, the third electrode 708 is composed of a third integrating electrode, a third transmitting electrode, and a third contact 711, and the fourth electrode 709 is composed of a fourth integrating electrode, a fourth transmitting electrode, and a fourth contact 710. The horizontal dividing line 7002 is formed by laser burning or bombardment, the reaction systems corresponding to both sides of the horizontal dividing line 7002 correspond to the serpentine trace 7001 and the serpentine trace 7005, respectively, and the serpentine trace 7001, the serpentine trace 7005, and the dividing line 7002 are combined to form the first electrode 701, the second electrode 702, the third electrode 708, and the fourth electrode 709. The biosensor is electrically connected to the detection instrument through the first contact 707, the second contact 706, the third contact 711, and the fourth contact 710.
The difference from fig. 5 is that in fig. 6, the integrating electrode three is also provided with a first auxiliary trace 7003 formed by laser ablation or bombardment, and the integrating electrode four is also provided with a second auxiliary trace 7004 formed by laser ablation or bombardment; when printing, the obtained hollowed reagent area has a certain deviation with a set area, the first auxiliary trace 7003 can be arranged to adjust the effective areas of the integration electrode III corresponding to the reagent area, the area defined by the first auxiliary trace 7003 and the trace 7001 at the upper end of the reagent area is removed, and similarly, the second auxiliary trace 7004 can be arranged to adjust the effective areas of the integration electrode IV corresponding to the reagent area, and the area defined by the second auxiliary trace 7004 and the trace 7001 at the lower end of the reagent area is removed, so that the purpose of increasing the deviation accommodating space is achieved, namely the fault tolerance of printing is increased. Of course, it is also possible to provide the first auxiliary trace only on integrating electrode three, or to provide the first auxiliary trace only on integrating electrode four. Or, an auxiliary trace is arranged on the first integrating electrode or an auxiliary trace is arranged on the second integrating electrode, so that the aim of increasing the printing fault tolerance rate is fulfilled.
As shown in fig. 7, a method for manufacturing an integral electrode biosensor includes the steps of:
1) presetting a snake-shaped trace in a laser device;
2) selecting a plastic substrate with a compact and non-porous surface, such as polypropylene, polyethylene or polystyrene, and cutting the plastic substrate into uniform thin-layer sheets with the thickness of 0.1-5mm as a substrate layer;
3) printing conductive carbon paste on a substrate layer of the reaction area in a screen printing mode to form an integral electrode base layer with a certain thickness, and curing the integral electrode base layer on the substrate layer at high temperature;
4) printing conductive silver paste to a specific position on a substrate layer by a screen printing mode to form a transmission electrode and a contact, and curing the transmission electrode and the contact on the substrate layer at high temperature;
5) laser equipment performs laser burning or bombardment on the integration electrode base layer according to a preset serpentine trace, so that the conductive carbon slurry on the trace path is bombarded and gasified to be separated from the surface of the substrate layer, and a blank trace is formed;
6) printing insulating ink on a specific position on a substrate by a screen printing mode to form an insulating layer, wherein the insulating layer is provided with a hollow reagent area for arranging a reaction reagent, a part of an electrode layer can be observed through the reagent area, and the electrode layer is cured on a substrate layer by irradiation of an ultraviolet curing lamp;
7) a pre-fabricated hydrophilic layer and spacer layer are laid on the reaction area to form a built-in capillary sample channel.
The electrode layer comprises the integration electrode base layer, the trace, the transmission electrode and the contact.
The foregoing detailed description is intended to illustrate and not limit the invention, which is intended to be within the spirit and scope of the appended claims, and any changes and modifications that fall within the true spirit and scope of the invention are intended to be covered by the following claims.
Claims (10)
1. An integrating electrode structure comprising a first electrode and a second electrode, characterized in that:
the first electrode consists of a first integrating electrode and a first transmission electrode;
the second electrode consists of a second integration electrode and a second transmission electrode;
the first integrating electrode and the second integrating electrode are formed by separating a snake-shaped trace;
the first transmission electrode is arranged on one side of the first integration electrode, and the second transmission electrode is arranged on one side of the second integration electrode.
2. The integrating electrode structure of claim 1 wherein: the traces are blank separation lines formed by laser burning or bombardment.
3. A biosensor comprising a substrate layer, an electrode layer and an insulating layer, wherein:
the insulating layer is provided with a reagent area, and the reagent area is used for arranging a reaction reagent;
the electrode layer is provided with an integral electrode structure, the integral electrode structure comprises a first electrode and a second electrode, the first electrode is composed of a first integral electrode and a first transmission electrode, the second electrode is composed of a second integral electrode and a second transmission electrode, the first integral electrode and the second integral electrode are formed by separating a snake-shaped trace, the first transmission electrode is arranged on one side of the first integral electrode, and the second transmission electrode is arranged on one side of the second integral electrode;
the first transmission electrode is provided with a first contact which can be electrically connected with the detection instrument, and the second transmission electrode is provided with a second contact which can be electrically connected with the detection instrument.
4. The biosensor according to claim 3, wherein: a first auxiliary trace line is arranged on the first integration electrode; or a first auxiliary trace line is arranged on the second integration electrode; or the first integration electrode is provided with a first auxiliary trace line, and the second integration electrode is provided with a second auxiliary trace line.
5. The biosensor according to claim 3 or 4, wherein: the electrode layer further comprises a third electrode consisting of a third integration electrode and a third transmission electrode, and a fourth electrode consisting of a fourth integration electrode and a fourth transmission electrode, wherein the third transmission electrode is provided with a third contact electrically connected with the detection instrument, and the fourth transmission electrode is provided with a fourth contact electrically connected with the detection instrument.
6. The biosensor in accordance with claim 3, wherein: a plurality of snake-shaped traces are arranged in the electrode layer, horizontal dividing lines are arranged between areas where adjacent traces are located, and the dividing lines are formed by laser burning or bombardment.
7. A manufacturing method of an integral electrode biosensor is characterized by comprising the following steps:
1) selecting a substrate layer;
2) printing and curing a conductive material to the substrate layer to form an integral electrode base layer;
3) printing and curing a conductive material to a substrate layer to form a transfer electrode and a contact;
4) burning or bombarding the integration electrode base layer by laser to make the conductive material at the burnt or bombarded position separate from the substrate layer to form a snake-shaped trace extending in a snake-shaped bending way, thus completing the manufacture of the integration electrode;
5) printing and curing an insulating layer on the substrate layer on which the electrode layer is manufactured, wherein the insulating layer is provided with a hollowed reagent area for setting a reaction reagent;
6) the reaction reagent is arranged in the reagent area, and the sample channel is laid in the reaction area.
8. The method for manufacturing an integral electrode biosensor according to claim 7, wherein: the conductive material in the step 2) is conductive carbon paste, the conductive carbon paste is printed on a substrate layer of the reaction area in a screen printing mode to form an integral electrode base layer with a thickness, and the integral electrode base layer is cured to the substrate layer at a high temperature.
9. The method for manufacturing an integral electrode biosensor according to claim 7, wherein: the conductive material in the step 3) is conductive silver paste, the conductive silver paste is printed to a specific position on the substrate layer through a screen printing mode to form a transmission electrode and a contact, and the transmission electrode and the contact are solidified to the substrate layer through high temperature.
10. The method for manufacturing an integral electrode biosensor according to claim 7, wherein: the insulating layer in the step 5) is obtained by screen printing of insulating ink, a hollow reagent area is formed, and the insulating layer is cured by irradiation of an ultraviolet curing lamp; the substrate layer is a uniform plastic substrate with a compact surface and no holes, and the thickness is 0.1-5 mm.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201910885466.7A CN112525959A (en) | 2019-09-19 | 2019-09-19 | Integrating electrode structure, biosensor and manufacturing method of integrating electrode biosensor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201910885466.7A CN112525959A (en) | 2019-09-19 | 2019-09-19 | Integrating electrode structure, biosensor and manufacturing method of integrating electrode biosensor |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN112525959A true CN112525959A (en) | 2021-03-19 |
Family
ID=74973949
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201910885466.7A Pending CN112525959A (en) | 2019-09-19 | 2019-09-19 | Integrating electrode structure, biosensor and manufacturing method of integrating electrode biosensor |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN112525959A (en) |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0973028A2 (en) * | 1998-07-14 | 2000-01-19 | Oxley Developments Company Limited | Electrode array |
| US20030155237A1 (en) * | 2001-11-16 | 2003-08-21 | Surridge Nigel A. | Electrodes, methods, apparatuses comprising micro-electrode arrays |
| US6645359B1 (en) * | 2000-10-06 | 2003-11-11 | Roche Diagnostics Corporation | Biosensor |
| US20040178066A1 (en) * | 1999-11-15 | 2004-09-16 | Shoji Miyazaki | Biosensor, thin film electrode forming method, quantification apparatus, and quantification method |
| US20050112544A1 (en) * | 2002-12-20 | 2005-05-26 | Xiao Xu | Impedance based devices and methods for use in assays |
| US20090020439A1 (en) * | 2006-01-25 | 2009-01-22 | Michael Marquant | Electrochemical biosensor analysis system |
| JP2015133574A (en) * | 2014-01-10 | 2015-07-23 | コニカミノルタ株式会社 | Interdigital electrode, formation method of interdigital electrode, and device using interdigital electrode |
| CN210894205U (en) * | 2019-09-19 | 2020-06-30 | 杭州微策生物技术有限公司 | Integrating electrode structure and biosensor |
-
2019
- 2019-09-19 CN CN201910885466.7A patent/CN112525959A/en active Pending
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0973028A2 (en) * | 1998-07-14 | 2000-01-19 | Oxley Developments Company Limited | Electrode array |
| US20040178066A1 (en) * | 1999-11-15 | 2004-09-16 | Shoji Miyazaki | Biosensor, thin film electrode forming method, quantification apparatus, and quantification method |
| US6645359B1 (en) * | 2000-10-06 | 2003-11-11 | Roche Diagnostics Corporation | Biosensor |
| US20030155237A1 (en) * | 2001-11-16 | 2003-08-21 | Surridge Nigel A. | Electrodes, methods, apparatuses comprising micro-electrode arrays |
| US20050112544A1 (en) * | 2002-12-20 | 2005-05-26 | Xiao Xu | Impedance based devices and methods for use in assays |
| US20090020439A1 (en) * | 2006-01-25 | 2009-01-22 | Michael Marquant | Electrochemical biosensor analysis system |
| JP2015133574A (en) * | 2014-01-10 | 2015-07-23 | コニカミノルタ株式会社 | Interdigital electrode, formation method of interdigital electrode, and device using interdigital electrode |
| CN210894205U (en) * | 2019-09-19 | 2020-06-30 | 杭州微策生物技术有限公司 | Integrating electrode structure and biosensor |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US6787013B2 (en) | Biosensor | |
| US6004441A (en) | Biosensor | |
| CN1104645C (en) | Eelctrochemical cell | |
| KR100767204B1 (en) | Continuous process for manufacture of disposable electro-chemical sensor | |
| US20010008389A1 (en) | Force sensor | |
| CN1313619C (en) | Biosensor | |
| CN103353475B (en) | Electrochemical cell and the method producing electrochemical cell | |
| JPH05196595A (en) | Manufacture of glucose sensor | |
| CA2529657A1 (en) | Test strip with slot vent opening | |
| KR20080052671A (en) | Biosensor and method of making cross-reference to related applications | |
| CA2368783A1 (en) | Electrochemical biosensor test strip, fabrication method thereof and electrochemical biosensor | |
| KR20100117173A (en) | Electrochemical biosensor electrode strip and preparing method thereof | |
| CN210894205U (en) | Integrating electrode structure and biosensor | |
| CN211927776U (en) | Electrochemical test strip with integrated electrode | |
| JP2007278981A (en) | Planar electrode and electrochemical detection sensor using the same | |
| CN112525959A (en) | Integrating electrode structure, biosensor and manufacturing method of integrating electrode biosensor | |
| CN100451639C (en) | Analytical tool | |
| WO1996024958A1 (en) | Solid polymer fuel cell comprising humidity-exchanging areas | |
| KR20170125957A (en) | Gas sensor manufacturing method and corresponding gas sensor | |
| CN218571391U (en) | Atomizing core and atomizing equipment | |
| CN102770756A (en) | Laminated electrochemical sensor with controlled variation of working electrode | |
| US11821864B2 (en) | Sulfurization detection sensor | |
| JP2021012068A (en) | Sulfuration detection sensor and method for manufacturing sulfuration detection sensor | |
| EP3234982B1 (en) | Sensor array with anti-diffusion region(s) to extend shelf life | |
| CN112384998B (en) | Method for manufacturing a plurality of resistor units on a ceramic substrate |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination |