CN210894205U - Integrating electrode structure and biosensor - Google Patents
Integrating electrode structure and biosensor Download PDFInfo
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- CN210894205U CN210894205U CN201921558934.1U CN201921558934U CN210894205U CN 210894205 U CN210894205 U CN 210894205U CN 201921558934 U CN201921558934 U CN 201921558934U CN 210894205 U CN210894205 U CN 210894205U
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Abstract
The utility model discloses an integral electrode structure, which comprises a first electrode and a second electrode, wherein the first electrode consists of an integral electrode I and a transmission electrode I which is stacked on the same side with the integral electrode I; the second electrode consists of a second integration electrode and a second transmission electrode which is stacked on the same side with the second integration electrode; the first integration electrode and the second integration electrode are formed by separating a serpentine trace. The utility model also discloses a biosensor. The utility model can obtain uniform signals from each electrode 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, the reagent area is fully utilized, each electrode can obtain the maximum signal during 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 utility model belongs to the biosensor field especially relates to an integral electrode structure, 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.
SUMMERY OF THE UTILITY MODEL
In order to overcome the deficiency of the prior art, the utility model provides a can make full use of reaction area, each electrode can obtain even and the signal of maximum, the integral electrode structure that signal intensity is high, has the biosensor of this integral electrode structure when reaction reagent and analyte react.
The utility model provides a technical scheme that its technical problem adopted is: an integrating electrode structure comprising a first electrode and a second electrode,
the first electrode consists of a first integration electrode and a first transmission electrode which is stacked on the same side with the first integration electrode;
the second electrode consists of a second integration electrode and a second transmission electrode which is stacked on the same side with the second integration electrode;
the first integration electrode and the second integration electrode are formed by separating a serpentine trace.
Preferably, the traces are blank separation lines formed by laser firing or bombardment.
The utility model 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 consists of a first integral electrode and a first transmission electrode stacked on the same side of the first integral electrode, the second electrode consists of a second integral electrode and a second transmission electrode stacked on the same side of the second integral electrode, and the first integral electrode and the second integral electrode are formed by separating a snake-shaped trace;
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 utility model also discloses a manufacturing method of integral electrode biosensor, including 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 utility model discloses according to the method of calculus principle solution circle or oval area, become a plurality of with circle or oval parallel cutting, calculate the area sum of the different length rectangles of each equal part and be the area of circle promptly, also carry out a class circular shape electrode region parallel cutting many times, and every adjacent two parts are connected to positive negative pole both ends respectively after being cut, design the electrode region of calculus formula promptly, as shown in fig. 1.
The utility model provides an electrode of integral type decomposes and evenly distributed in whole reagent district with the mode of integral, has increased the quantity of electrode, burns the mode decomposition electrode of perhaps bombardment with laser, under the condition that does not thoroughly change technology, makes the electrode spacing reduce, has improved the electrode and has accounted for the ratio at whole reaction zone area.
The utility model 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 burr, ripple 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 utility model has the advantages 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 the integrating electrode structure of the present invention.
Fig. 2 is the utility model discloses biosensor awaits measuring sample reaction area's decomposition structure sketch map.
Fig. 3 is another schematic diagram of the integrating electrode structure according to the present invention.
Fig. 4 is a schematic structural diagram of the biosensor of the present invention.
FIG. 5 is a schematic structural diagram of the biosensor (two reaction reagent system) according to the present invention.
Fig. 6 is a schematic structural diagram of the biosensor (with auxiliary traces) according to the present invention.
Fig. 7 is a manufacturing flow chart of the biosensor of the present invention.
Detailed Description
In order to make the technical solution of the present invention better understood, the following figures in the embodiments of the present invention are combined to clearly and completely describe the technical solution in the embodiments of the present invention, and it is obvious that the described embodiments are only some embodiments of the present invention, not all embodiments. Based on the embodiments in the present invention, all other embodiments obtained by a person skilled in the art without creative efforts shall belong to the protection scope of the present invention.
As shown in fig. 1 and 2, an integrating electrode structure comprises a first electrode 401 and a second electrode 402, wherein the first electrode 401 comprises a first integrating electrode 4011 and a first transmission electrode 4012, the first transmission electrode 4012 is arranged on one side of the first integrating electrode 4011, the first transmission electrode 4012 and the first integrating electrode 4011 are stacked up and down, the second electrode 402 comprises a second integrating electrode 4021 and a second transmission electrode 4022, the second transmission electrode 4022 is arranged on one side of the second integrating electrode 4021, and the second transmission electrode 4022 and the second integrating electrode 4021 are stacked up and down; 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 transmitting electrode 4012, the first transmitting electrode 4012 is arranged on one side where the first integrating electrode 4011 is located, the first transmitting electrode 4012 and the first integrating electrode 4011 are stacked up and down, the second electrode 402 is composed of a second integrating electrode 4021 and a second transmitting electrode 4022, the second transmitting electrode 4022 is arranged on one side where the second integrating electrode 4021 is located, and the second transmitting electrode 4022 and the second integrating electrode 4021 are stacked up and down; 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 having a sample reaction area to be measured as shown in fig. 2, a sample channel (not shown) being provided in the sample reaction area to be measured, an electrode layer 501 including a first electrode and a second electrode, the first electrode being 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 being provided on a side where the integrating electrode 5011 is located, and the transmitting electrode 5012 and the integrating electrode 5011 being stacked up and down; the second electrode consists of a second integral electrode 5021, a second transmission electrode 5022 and a second contact 506 positioned at the end part of the second transmission electrode 5022, the second transmission electrode 5022 is arranged on one side where the second integral electrode 5021 is located, and the second transmission electrode 5022 and the second integral electrode 5021 are stacked up and down;
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 includes a first integration electrode, a first transmission electrode, and a first contact 607, the first transmission electrode and the first integration electrode are stacked on the same side, the second electrode 602 includes a second integration electrode, a second transmission electrode, and a second contact 606, the second transmission electrode and the second integration electrode are stacked on the same side, the third electrode 608 includes a third integration electrode, a third transmission electrode, and a third contact 611, the third transmission electrode and the third integration electrode are stacked on the same side, the fourth electrode 609 includes a fourth integration electrode, a fourth transmission electrode, and a fourth contact 610, and the fourth transmission electrode and the fourth integration electrode are stacked on the same side. 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, where the first electrode 701 is composed of a first integration electrode, a first transmission electrode, and a first contact 707, the first transmission electrode and the first integration electrode are stacked on the same side, the second electrode 702 is composed of a second integration electrode, a second transmission electrode, and a second contact 706, the second transmission electrode and the second integration electrode are stacked on the same side, the third electrode 708 is composed of a third integration electrode, a third transmission electrode, and a third contact 711, the third transmission electrode and the third integration electrode are stacked on the same side, the fourth electrode 709 is composed of a fourth integration electrode, a fourth transmission electrode, and a fourth integration electrode 710, and the fourth transmission electrode and the fourth integration electrode are stacked on the same side. The horizontal dividing line 7002 is formed by laser burning or bombardment, and the reaction systems corresponding to both sides of the horizontal dividing line 7002 respectively correspond to the serpentine traces 7001 and 7005, the serpentine traces 7001, the serpentine traces 7005 and the dividing line 7002 combination, thereby forming 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 above detailed description is provided for illustrative purposes, and is not intended to limit the present invention, and any modifications and variations of the present invention are within the spirit and scope of the following claims.
Claims (6)
1. An integrating electrode structure comprising a first electrode and a second electrode, characterized in that:
the first electrode consists of a first integration electrode and a first transmission electrode which is stacked on the same side with the first integration electrode;
the second electrode consists of a second integration electrode and a second transmission electrode which is stacked on the same side with the second integration electrode;
the first integration electrode and the second integration electrode are formed by separating a serpentine trace.
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 consists of a first integral electrode and a first transmission electrode stacked on the same side of the first integral electrode, the second electrode consists of a second integral electrode and a second transmission electrode stacked on the same side of the second integral electrode, and the first integral electrode and the second integral electrode are formed by separating a snake-shaped trace;
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 according to 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.
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| CN201921558934.1U CN210894205U (en) | 2019-09-19 | 2019-09-19 | Integrating electrode structure and biosensor |
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| CN201921558934.1U CN210894205U (en) | 2019-09-19 | 2019-09-19 | Integrating electrode structure and biosensor |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112525959A (en) * | 2019-09-19 | 2021-03-19 | 杭州微策生物技术股份有限公司 | Integrating electrode structure, biosensor and manufacturing method of integrating electrode biosensor |
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2019
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112525959A (en) * | 2019-09-19 | 2021-03-19 | 杭州微策生物技术股份有限公司 | Integrating electrode structure, biosensor and manufacturing method of integrating electrode biosensor |
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Address after: 2 / F, building 2, 146 Chaofeng East Road, Yuhang Economic and Technological Development Zone, Hangzhou, Zhejiang 310000 Patentee after: Hangzhou Weice Biotechnology Co.,Ltd. Address before: 311100 second floor, building 2, No. 146, Chaofeng East Road, Yuhang Economic and Technological Development Zone, Hangzhou City, Zhejiang Province Patentee before: VivaChek Biotech (Hangzhou) Co.,Ltd. |
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