CN217688691U

CN217688691U - Biological sensing detection device

Info

Publication number: CN217688691U
Application number: CN202221766754.4U
Authority: CN
Inventors: 韩照网; 陈新铭
Original assignee: Qingdao Yasi Biotechnology Co ltd
Current assignee: Qingdao Yasi Biotechnology Co ltd
Priority date: 2022-07-08
Filing date: 2022-07-08
Publication date: 2022-10-28
Anticipated expiration: 2032-07-08

Abstract

The utility model relates to a biosensing detection device, it is including exempting from to transfer yard test paper (1) and detection module (2), exempt from to transfer yard test paper (1) including interconnect's the reaction layer body (11) and verify the layer body (12), wherein, the reaction layer body (11) is used for bearing biomaterial, detection module (2) pass through verify in the layer body (12) parameter identification module (13) accomplish under the condition of the correction of detection parameter, detection module (2) detection unit (21) can be to the biomaterial that reaction layer body (11) bore carries detects; the parameter identification module (13) provides different correction parameters for the detection module (2) by limiting the positions and the number of the contacts (132) arranged on the electrode plate (131), so that the detection module (2) selects different detection units (21) to perform detection according to the distribution condition of the contacts (132).

Description

Biological sensing detection device

Technical Field

The utility model relates to a biosensing equipment technical field especially relates to a biosensing detection device.

Background

POCT (Point of Care Testing) is a short term for Point of Care Testing, and is a sub-industry of In Vitro Diagnosis (IVD) industry. Through simplified design and technical innovation, the POCT realizes convenient and fast on-site examination at the side of a patient and fast obtains a diagnosis result. At present, POCT products are widely applied to ICU (intensive care unit) in hospitals, operations, emergency treatment, clinics and patient homes, and can detect most of conventional clinical indexes. As a POCT product with the largest market share, the blood sugar detection system can realize self-detection of a patient at home and monitor the blood sugar concentration in real time.

In production, due to the influence of factors such as environment, process and the like, the performance of each batch of blood sugar products is inconsistent, and the blood sugar detection result is influenced. Before products leave a factory, a group of codes are set for each batch of blood sugar products by blood sugar product manufacturing enterprises to correct detection results so as to ensure the accuracy of the detection results.

US11056089 discloses that calibration information is integrated into a code-modulation-free test paper, and when the test paper is in contact with a detection module, the detection module can automatically recognize calibration parameters corresponding to the test paper, so as to complete calibration and detection of the detection module. The biosensor comprises a parameter identification module for correcting parameter difference values among different batches of test paper, wherein the parameter identification module obtains different parameter information by adjusting the resistance value of an element, but the thickness of the parameter identification module deviates in the production process, so that the accurate resistance value is difficult to obtain, and the detection result is inaccurate.

In addition, the specific electrochemical code-adjusting-free test paper needs to be matched with a detection module of a specific model to finish final detection. The application provides the test paper with the correction parameters, so that the detection module can correct the detection parameters by using the parameter identification module on the test paper before detecting the test paper, and the accuracy of detection data obtained by detecting biological materials on the test paper is ensured.

Furthermore, on the one hand, due to the differences in understanding to the person skilled in the art; on the other hand, since the inventor studied a lot of documents and patents when making the present invention, but the space did not list all details and contents in detail, however, this is by no means the present invention does not possess these prior art features, but on the contrary the present invention has possessed all features of the prior art, and the applicant reserves the right to increase the related prior art in the background art.

SUMMERY OF THE UTILITY MODEL

To the deficiency of the prior art, the technical scheme of the utility model is to provide a biosensing detection device, it includes exempts from to transfer sign indicating number test paper and detection module, exempt from to transfer the sign indicating number test paper and include interconnect's reaction layer body and verification layer body, wherein, the reaction layer body is used for bearing biomaterial detection module passes through under the condition that the parameter identification module in the verification layer body accomplishes the correction of detection parameter, detection module's detecting element can detect the biomaterial that reaction layer body born; the parameter identification module provides different correction parameters for the detection module by limiting the positions and the number of the contacts arranged on the electrode plate, so that the detection module selects different detection units for detection according to the distribution condition of the contacts.

According to a preferred embodiment, the electrode plate comprises a base plate body and a conductive layer arranged on the base plate body, wherein the contacts are arranged on the conductive layer in such a way that the positions and the number of the contacts are adjustable, so that the contacts and the conductive layer can form electrode structures with different conduction logics, and the electrode structures correspond to correction parameters.

According to a preferred embodiment, the contacts are formed by cutting holes on the surface of the conductive layer, the contacts are formed on the surface of the conductive layer, which is far away from the base plate body, and when the code-modulation-free test paper is inserted into the detection port of the detection module, the contacts are in contact with the detection module, so that the detection module completes the correction of the detection parameters by using the contacts with a specific distribution condition.

According to a preferred embodiment, adjacent contacts are connected through a connecting resistor with an adjustable resistance value, and the starting end and the tail end of a contact chain formed by connecting a plurality of contacts are connected with the electrodes of the detection module through connecting electrodes.

According to a preferred embodiment, the reactive layer body includes a first insulating layer, a reactive layer and a second insulating layer connected in sequence, wherein a side of the second insulating layer away from the reactive electrode is connected to the verification layer body.

According to a preferred embodiment, the second insulating layer is connected to the conductive layer, and the substrate plate also covers the surface of the reactive layer body.

According to a preferred embodiment, a flow guide channel is formed on the base plate, one end of the flow guide channel is connected with the reaction layer, and the other end of the flow guide channel is connected with an electrical contact layer arranged on the base plate.

According to a preferred embodiment, the surface of the channel wall of the second insulating layer for constructing the flow-conducting channel is further provided with a reagent unit for generating a measurable electrochemical signal by means of reaction with the biological material in the flow-conducting channel.

According to a preferable embodiment, the surface of the reaction layer is further provided with a groove, and the groove is communicated with the flow guide channel, so that the biological material in the groove flows along the flow guide channel.

According to a preferred embodiment, a power supply electrically connected with the detection unit is further arranged inside the detection module.

The utility model has the advantages of:

the device is provided with the contacts with adjustable distribution conditions on the conducting layer, so that the detection module can obtain signal combinations in various forms through detecting the contacts, and thus, a plurality of groups of different conducting logics are formed, and a plurality of groups of correction parameter values corresponding to the code adjustment-free test paper are obtained. The device can automatically identify the matched detection module and a group of correction parameter values corresponding to the batch of test paper through the special parameter identification module on the test paper, does not need to insert a storage card or adjust the setting of the detection module, reduces the detection operation steps, and avoids the condition that an operator forgets to input or input a wrong password or does not insert the storage card to cause a wrong detection result.

Drawings

FIG. 1 is a schematic structural diagram of a preferred biosensing detection device of the present invention;

fig. 2 is a schematic plan view of a substrate plate of a preferred biosensing detection device according to the present invention.

List of reference numerals

1: code adjustment-free test paper; 2: a detection module; 11: a reactive layer body; 12: verifying the layer body; 13: a parameter identification module; 14: a flow guide channel; 15: an electrical contact layer; 16: a reactant unit; 21: a detection unit; 22: a detection port; 23: a power source; 111: a first insulating layer; 112: a reaction layer; 113: a second insulating layer; 131: an electrode plate; 132: a contact point; 133: a base layer plate body; 134: a conductive layer; 135: connecting a resistor; 136: connecting the electrodes; 1121: and (4) a groove.

Detailed Description

The following detailed description is made with reference to the accompanying drawings.

Example 1

The application relates to a biosensing detection device, which at least comprises code-adjusting-free test paper 1 and a detection module 2.

According to a specific embodiment shown in fig. 1, before the code modulation-free test strip 1 is inserted into the detection module 2 for biological material detection, the parameter identification module 13 in the code modulation-free test strip 1 can be in contact with and electrically connected with the detection module 2, so as to provide the detection module 2 with the calibration parameters corresponding to the code modulation-free test strip 1, so that the detection module 2 can complete the calibration of the detection parameters without separately inserting a code modulation card.

Preferably, the code-adjustment-free test paper 1 comprises a reaction layer body 11 and a verification layer body 12 which are connected with each other. Preferably, the reactive layer body 11 is used for carrying biological materials. In the case that the detection module 2 completes the correction of the detection parameters through the parameter identification module 13 in the verification layer body 12, the detection unit 21 of the detection module 2 can detect the biological material carried by the reaction layer body 11. Preferably, the parameter identification module 13 provides different calibration parameters for the detection module 2 by limiting the positions and the number of the contacts 132 formed on the electrode plate 131, so that the detection module 2 selects different detection units 21 for detection according to the distribution of the contacts 132. Preferably, the electrode plate 131 includes a base plate body 133 and a conductive layer 134 disposed on the base plate body 133. Preferably, the contacts 132 are arranged on the conductive layer 134 in such a way that their position and number can be adjusted, so that the contacts 132 and the conductive layer 134 form an electrode structure with different conduction logics, and the electrode structure corresponds to the correction parameters. Preferably, the detection module 2 can perform a targeted detection parameter calibration operation according to the electrode structure contained in different modulation-free test strips 1, so that the detection unit 21 can perform accurate detection and identification on the biological material on the modulation-free test strips 1. Preferably, contact 132 is opened by making a hole in the surface of conductive layer 134. Preferably, the conductive layer 134 may be any one of a carbon electrode, a silver electrode, and a gold electrode. The conductive layer 134 is formed with contacts 132 on its surface by a hole-cutting process, so that the parameter identification module 13 forms different forms of electrode structures according to the positions and the number of the contacts 132. Preferably, the electrode structure may be formed from two different sets of contacts 132, and each set of contacts 132 also represents a plurality of different electrode forms, each electrode form corresponding to a particular set of calibration parameter values. When the code modulation-free test paper 1 with specific correction parameters is connected with the detection module 2, the detection module 2 can automatically identify the detection unit 21 and the correction parameters matched with the detection module. Preferably, when the code adjustment-free test paper 1 is inserted into the detection module 2, each type of electrode structure can automatically identify the matched detection unit 21, and each type of electrode structure corresponds to a set of calibration parameters. Preferably, the hole cutting manner includes, but is not limited to, a punching process, a laser cutting process; the pattern of the hole cutting process includes, but is not limited to, circle, triangle, square, and polygon. The hole cutting process can be primary punching, secondary punching, tertiary punching and the like.

Preferably, the contacts 132 are opened on the surface of the conductive layer 134 away from the base plate 133, and when the code adjustment-free test paper 1 is inserted into the detection port 22 of the detection module 2, the contacts 132 are in contact with the detection module 2, so that the detection module 2 uses the contacts 132 with a specific distribution to complete the calibration of the detection parameters. Specifically, when the adjustment-free test paper 1 is inserted into the detection module 2, the respective contacts 132 on the conductive layer 134 of the parameter identification module 13 are in contact with the detection module 2. After the code-adjusting-free test paper 1 is connected with the detection module 2, the detection module 2 detects input values of a first group of three contacts 132 and a second group of two contacts 132 on the conductive layer 134, and compares the input values with preset values of the detection module 2 for confirmation; according to different production batches and response characteristics of the biosensors, the hole cutting positions of the parameter identification module 13 are different, and the input values detected by the detection module 2 are also different; the detection module 2 selects corresponding technical parameters according to the comparison confirmation result, so that a detection result is finally given; when the code modulation-free test paper 1 with the parameter identification module 13 is contacted with the detection module 2, signals with different expression forms are obtained by detecting the parameter identification module 13 with different electrode structures, so that the detection module 2 and the correction parameters matched with the code modulation-free test paper 1 are automatically identified.

As shown in fig. 2, the adjacent contacts 132 are connected by a connecting resistor 135 with an adjustable resistance value, and the starting end and the tail end of the contact chain formed by connecting the plurality of contacts 132 are connected to the electrodes of the detecting module 2 by connecting electrodes 136. Preferably, the reactive layer body 11 includes a first insulating layer 111, a reactive layer 112 and a second insulating layer 113 which are connected in sequence. The side of the second insulating layer 113 away from the reaction electrode is connected to the verification layer 12. The second insulating layer 113 is connected to one end of the conductive layer 134, and the substrate plate 133 also covers the surface of the reactive layer body 11. The base plate 133 is provided with a flow guide channel 14, one end of the flow guide channel 14 is connected to the reaction layer 112, and the other end of the flow guide channel 14 is connected to the electrical contact layer 15 disposed on the base plate 133. The surface of the channel wall of the second insulating layer 113, which is used to construct the flow-conducting channel 14, is further provided with a reagent unit 16, which generates a measurable electrochemical signal by reacting with the biological material in the flow-conducting channel 14. Preferably, the reagent unit 16 may be a chemical agent that can react with blood, thereby facilitating the acquisition of parameter indicators within the blood by the detection module 2. The surface of the reaction layer 112 is further provided with a groove 1121, and the groove 1121 is communicated with the flow guide channel 14, so that the biological material in the groove 1121 flows along the flow guide channel 14. The groove 1121 is used as a sample collection chamber for biological materials such as blood, and the inlet of the groove 1121 is wide, so that an additional air escape port does not need to be provided. When the liquid sample chamber is used, the biological material to be detected can directly enter the flow guide channel 14 through the groove 1121 through capillary action, so that the biological material at any position of the groove 1121 can enter the groove 1121, and the problem that a liquid sample is difficult to enter the liquid sample chamber due to the fact that an inlet is blocked in the prior art is solved. This application is owing to saved the air escape mouth that needs additionally set up among the prior art, consequently simpler when production, more convenient operation.

Preferably, the detection module 2 comprises a detection unit 21, a detection port 22 and a power supply 23. The power supply 23 can provide power for the detection unit 21, so that the detection unit 21 can perform detection and identification along with the code adjustment-free test paper 1. Preferably, the detection unit 21 may be a MAX1358 chip capable of blood glucose detection.

Preferably, the electrode structure has a first set of three contacts 132 and a second set of two contacts 132, and the parameter identification module 13 is capable of forming 8 different forms of electrode structures by cutting holes. When the electrode structure has a first set of four contacts 132 and a second set of two contacts 132, the parameter identification module 13 can form 16 different forms of electrode structures by cutting holes; and each electrode structure corresponds to a group of specific calibration parameter values, so when the code adjustment-free test paper 1 with the specific parameter identification module 13 is connected with the detection module 2, the 6 contacts 132 on the parameter identification module 13 are in contact with the detection module 2, and the code adjustment-free test paper 1 can automatically identify the detection module 2 and the calibration parameters matched with the code adjustment-free test paper. After the parameter identification module 13 is connected to the detection module 2, the detection module 2 measures the input values of the two sets of contacts 132 of the parameter identification module 13, and compares the input values with the preset values of the detection module 2 for confirmation, so that the positions of the cut holes of the parameter identification module 13 are different and the input values detected by the detection module 2 are different according to different batches and response characteristics of biosensor production. The detection module 2 selects corresponding technical parameters according to the comparison confirmation result, and finally provides a detection result. Preferably, when the electrode structure has a first set of four contacts 132 and a second set of two contacts 132, the parameter identification module 13 is capable of forming 32/19/20/21/8 different forms of electrode structures, respectively.

It should be noted that the above-mentioned embodiments are exemplary, and those skilled in the art can devise various solutions in light of the present disclosure, which are also within the scope of the present disclosure and fall within the scope of the present disclosure. It should be understood by those skilled in the art that the present specification and its drawings are illustrative and not restrictive on the claims. The scope of the invention is defined by the claims and their equivalents. Throughout this document, the features referred to as "preferably" are only an optional feature and should not be understood as necessarily requiring that such applicant reserves the right to disclaim or delete the associated preferred feature at any time.

Claims

1. The biosensing detection device comprises code-modulation-free test paper (1) and a detection module (2), and is characterized in that the code-modulation-free test paper (1) comprises a reaction layer body (11) and a verification layer body (12) which are connected with each other,

the reaction layer body (11) is used for carrying biological materials, and under the condition that the detection module (2) completes the correction of detection parameters through the parameter identification module (13) in the verification layer body (12), the detection unit (21) of the detection module (2) can detect the biological materials carried by the reaction layer body (11);

the parameter identification module (13) provides different correction parameters for the detection module (2) by limiting the positions and the number of the contacts (132) arranged on the electrode plate (131), so that the detection module (2) selects different detection units (21) to perform detection according to the distribution condition of the contacts (132).

2. The biosensing detection device according to claim 1, wherein said electrode plate (131) comprises a base plate body (133) and a conductive layer (134) disposed on the base plate body (133), wherein,

the contacts (132) are arranged on the conductive layer (134) in such a way that the positions and the number thereof are adjustable, so that the contacts (132) and the conductive layer (134) can form electrode structures with different conducting logics, and the electrode structures correspond to correction parameters.

3. The biosensing detection device according to claim 2, wherein said contact (132) is formed by cutting a hole in a surface of said conductive layer (134),

the contact (132) is arranged on the surface of the conducting layer (134) far away from the base plate body (133), and when the code modulation-free test paper (1) is inserted into the detection port (22) of the detection module (2), the contact (132) is in contact with the detection module (2), so that the detection module (2) completes the correction of detection parameters by utilizing the contact (132) with specific distribution conditions.

4. The biosensing detecting device according to claim 3, characterized in that adjacent contacts (132) are connected by a connecting resistor (135) with adjustable resistance value, and the starting end and the tail end of a contact chain formed by connecting a plurality of contacts (132) are connected with the electrodes of the detecting module (2) by connecting electrodes (136).

5. The biosensing detecting device according to claim 4, wherein the reaction layer body (11) comprises a first insulating layer (111), a reaction layer (112) and a second insulating layer (113) connected in sequence, wherein,

and one side of the second insulating layer (113) far away from the reaction electrode is connected with the verification layer body (12).

6. The biosensing detection device according to claim 5, wherein said second insulating layer (113) is connected to said conductive layer (134), and said substrate plate (133) further covers the surface of said reactive layer body (11).

7. The biosensing detection device according to claim 6, wherein a flow guide channel (14) is formed on the substrate plate (133), one end of the flow guide channel (14) is connected to the reaction layer (112), and the other end of the flow guide channel (14) is connected to an electrical contact layer (15) disposed on the substrate plate (133).

8. The biosensing detection device according to claim 7, characterized in that the surface of the channel wall of the second insulating layer (113) for constructing the flow guiding channel (14) is further provided with a reagent unit (16) for generating a measurable electrochemical signal by means of reaction with the biological material in the flow guiding channel (14).

9. The biosensing detection device according to claim 8, wherein the surface of the reaction layer (112) is further provided with a groove (1121), and the groove (1121) is communicated with the flow guide channel (14) so that the biological material in the groove (1121) flows along the flow guide channel (14).

10. The biosensing detection device according to claim 9, characterized in that the detection module (2) is internally further provided with a power supply (23) electrically connected with the detection unit (21).