Biological detection device, system and method

Abstract

The present disclosure provides a biological detection device, a biological detection system, and a biological detection method. The biological detection device may include a flexible substrate and a biosensor. The biosensor is disposed on the flexible substrate and is used to obtain substance information of an organism. The present disclosure can detect the substance information of an organism.

Description

Technical Field

[0001] The present disclosure relates to the technical field of sensors, and in particular, to a biological detection device, a biological detection system, and a biological detection method. Background Art

[0002] During human movement, abnormal changes in the components of sweat are related to the blood concentration level or directly indicate the health status of the human body. For example, sodium ions are the most abundant electrolytes in human sweat and are an important basis for sweat secretion. Its concentration can reflect different types of water-salt metabolism disorders in the human body. Therefore, the detection of sodium ions, potassium ions, etc. in sweat during exercise is of great significance for both athletes and ordinary people in terms of health guidance. However, in the prior art, it is impossible to detect the information of substances such as sodium ions and potassium ions. Summary of the Invention

[0003] An object of the present disclosure is to provide a biological detection device, a biological detection system, and a biological detection method, which can detect the substance information of an organism.

[0004] According to one aspect of the present disclosure, there is provided a biological detection device, including:

[0005] A flexible substrate;

[0006] A biosensor disposed on the flexible substrate and configured to obtain the substance information of an organism.

[0007] Further, the biological detection device further includes:

[0008] A communication module configured to send the substance information to a terminal.

[0009] Further, the biological detection device further includes:

[0010] An analog-to-digital converter configured to perform analog-to-digital conversion on the substance information and send the converted substance information to the communication module.

[0011] Further, the biosensor is disposed on a side of the flexible substrate facing the organism and is located within the boundary of the flexible substrate.

[0012] Further, at least a part of the biosensor is located outside the boundary of the flexible substrate.

[0013] Further, the biological detection device further includes:

[0014] A temperature sensor disposed on a side of the flexible substrate facing the organism and configured to detect the temperature information of the organism.

[0015] Further, the biological detection device further includes:

[0016] A heart rate sensor is disposed on one side of the flexible substrate facing the organism and is used to detect the heart rate information of the organism.

[0017] Further, the biological detection device further includes:

[0018] A power supply component is disposed on one side of the flexible substrate and is used to supply power to the biological sensor.

[0019] Further, the power supply component is disposed on the side of the flexible substrate facing away from the organism.

[0020] Further, the biological sensor includes a microelectrode structure, and the microelectrode structure includes:

[0021] A first insulating layer;

[0022] An electrode layer is disposed on one side of the first insulating layer.

[0023] Further, the biological sensor includes a microelectrode structure, and the microelectrode structure includes:

[0024] A first insulating layer;

[0025] A protrusion is disposed on one side of the first insulating layer;

[0026] The electrode layer conformally covers the first insulating layer and the protrusion.

[0027] Further, the microelectrode structure further includes:

[0028] A second insulating layer is disposed on the side of the electrode layer facing away from the first insulating layer. The second insulating layer is provided with an opening, and the protrusion extends out of the opening.

[0029] Further, the included angle between the side surface and the bottom surface of the protrusion is an acute angle.

[0030] Further, the protrusion is a conical structure.

[0031] Further, the maximum width of the protrusion in the direction parallel to the first insulating layer is less than or equal to 10 μm.

[0032] Further, the protrusion is made of an insulating material.

[0033] Further, the protrusion and the first insulating layer are of an integral structure.

[0034] Further, the electrode layer includes one or more electrode regions, and the plurality of electrode regions are spaced apart from each other. A plurality of the protrusions are provided on the surface of the first insulating layer corresponding to each of the electrode regions.

[0035] Further, the electrode layer includes a reference electrode region and one or more working electrode regions; or

[0036] the electrode layer includes a reference electrode region, a counter electrode region, and one or more working electrode regions.

[0037] Further, the distance between two adjacent electrode regions is 0.5 cm - 2 cm.

[0038] Further, the microelectrode structure further includes:

[0039] a first sensitive functional layer that covers at least the region of the electrode layer corresponding to the protrusion.

[0040] Further, the microelectrode structure further includes:

[0041] an auxiliary layer that covers at least the region of the first sensitive functional layer corresponding to the protrusion, and is provided with a first through-hole exposing the first sensitive functional layer, and the distance between the auxiliary layer and the electrode layer is less than or equal to 100 μm.

[0042] Further, the microelectrode structure further includes:

[0043] a second sensitive functional layer that covers the auxiliary layer and fills the first through-hole to contact the first sensitive functional layer.

[0044] Further, the protrusion is a conical structure, and the first through-hole is provided in the region of the auxiliary layer corresponding to the top of the protrusion.

[0045] Further, the first sensitive functional layer is a sodium ion sensitive functional layer, a potassium ion sensitive functional layer, a calcium ion sensitive functional layer, a hydrogen ion sensitive functional layer, or a chloride ion sensitive functional layer.

[0046] Further, the first insulating layer is provided with a second through-hole exposing the electrode layer.

[0047] Further, a protrusion is formed on one side of the first insulating layer, and the protrusion is provided on the protrusion.

[0048] Further, the biosensor is used to detect the substance information in the sweat of the organism.

[0049] According to one aspect of the present disclosure, there is provided a biological detection system including the above biological detection device.

[0050] According to one aspect of the present disclosure, there is provided a biological detection method, the biological detection method using the above biological detection device, the biological detection method including:

[0051] Obtain the first substance information of the organism by using the biological detection device;

[0052] Replace the biosensor of the biological detection device to obtain the second substance information of the organism.

[0053] In the process of using the biological detection device, biological detection system and biological detection method of the present disclosure, the flexible substrate is attached to the skin surface of the organism to be tested, and the biosensor is oriented towards the organism to be tested, so that the substance information of the organism can be detected by the biosensor. Description of the Drawings

[0054] Figure 1 It is a schematic diagram of the microelectrode structure of the embodiment of the present disclosure.

[0055] Figure 2 It is a schematic diagram of the microelectrode structure with protrusions of the embodiment of the present disclosure.

[0056] Figure 3 It is a plan view of the microelectrode structure of the embodiment of the present disclosure.

[0057] Figure 4 It is another schematic diagram of the microelectrode structure of the embodiment of the present disclosure.

[0058] Figure 5 It is yet another schematic diagram of the microelectrode structure of the embodiment of the present disclosure.

[0059] Figure 6 It is a flowchart of the preparation method of the microelectrode structure of the embodiment of the present disclosure.

[0060] Figure 7 It is a schematic diagram after forming the electrode layer in the preparation method of the microelectrode structure of the embodiment of the present disclosure.

[0061] Figure 8 It is a schematic diagram after forming the second sensitive functional layer in the preparation method of the microelectrode structure of the embodiment of the present disclosure.

[0062] Figure 9 It is another flowchart of the preparation method of the microelectrode structure of the embodiment of the present disclosure.

[0063] Figure 10 It is a schematic diagram of the template in the preparation method of the microelectrode structure of the embodiment of the present disclosure.

[0064] Figure 11 It is a schematic diagram after forming the first insulating layer in the preparation method of the microelectrode structure of the embodiment of the present disclosure.

[0065] Figure 12 It is another schematic diagram after forming the first insulating layer in the preparation method of the microelectrode structure of the embodiment of the present disclosure.

[0066] Figure 13 It is another schematic diagram after forming the first sensitive functional layer in the preparation method of the microelectrode structure according to the embodiments of the present disclosure.

[0067] Figure 14 It is a schematic diagram of the biological detection device according to the embodiments of the present disclosure.

[0068] Figure 15 It is Figure 14 a bottom view of the structure shown.

[0069] Figure 16 It is Figure 14 a top view of the structure shown.

[0070] Figure 17 It is Figure 14 a schematic diagram of the flexible substrate and the biosensor in the structure shown.

[0071] Figure 18 It is a schematic diagram of the biosensor in the biological detection device according to the embodiments of the present disclosure.

[0072] Figure 19 It is Figure 18 a schematic diagram of another side of the structure shown.

[0073] Figure 20 It is a cross-sectional schematic diagram of the biosensor in the biological detection device according to the embodiments of the present disclosure.

[0074] Figure 21 It is another schematic diagram of the biosensor in the biological detection device according to the embodiments of the present disclosure.

[0075] Figure 22 It is another schematic diagram of the biological detection device according to the embodiments of the present disclosure.

[0076] Figure 23 It is Figure 22 a cross-sectional schematic diagram of the structure shown.

[0077] Explanation of reference numerals: 1, first insulating layer; 101, protrusion; 2, protruding portion; 3, electrode layer; 301, working electrode region; 302, reference electrode region; 4, second insulating layer; 5, second through hole; 6, first sensitive functional layer; 7, auxiliary layer; 8, second sensitive functional layer; 9, support plate; 10, template; 101, recessed portion; 11, sacrificial layer; 12, flexible substrate; 13, biosensor; 14, power supply assembly; 15, analog-to-digital converter; 16, temperature sensor; 17, heart rate sensor; 18, communication module; 19, first conductive connection member; 20, second conductive connection member. Detailed implementation manners

[0078] Exemplary embodiments will be described in detail herein, and examples thereof are shown in the accompanying drawings. When the following description refers to the accompanying drawings, unless otherwise indicated, the same numbers in different drawings represent the same or similar elements. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with the present disclosure. On the contrary, they are merely examples of devices consistent with some aspects of the present disclosure as detailed in the appended claims.

[0079] The terms used in the present disclosure are for the purpose of describing specific embodiments only and are not intended to limit the present disclosure. Unless otherwise defined, the technical terms or scientific terms used in the present disclosure should have the ordinary meanings understood by those of ordinary skill in the art to which the present disclosure pertains. The terms "first", "second" and similar terms used in the specification and claims of the present disclosure do not denote any order, quantity or importance, but are only used to distinguish different components. Similarly, the terms such as "a" or "an" do not denote a limitation of quantity, but mean that there is at least one. "Plurality" or "several" means two or more. Unless otherwise specified, terms such as "front", "rear", "lower" and / or "upper" are for convenience of description only and are not limited to a position or a spatial orientation. The terms such as "comprising" or "including" mean that the elements or items appearing before "comprising" or "including" cover the elements or items listed after "comprising" or "including" and their equivalents, and do not exclude other elements or items. The terms such as "connected" or "coupled" are not limited to physical or mechanical connections, and may include electrical connections, whether direct or indirect. The singular forms "a", "the" and "said" used in the specification and claims of the present disclosure are also intended to include the plural forms unless the context clearly dictates otherwise. It should also be understood that the term "and / or" as used herein refers to and encompasses any and all possible combinations of one or more of the associated listed items.

[0080] An embodiment of the present disclosure provides a biological detection device. The biological detection device may be a wearable biological detection device, and of course, may also be an attachable biological detection device, such as a patch. The biological detection device may include a flexible substrate and a biosensor. The biosensor is disposed on the flexible substrate and is used to obtain substance information of a living body. Further, the biosensor is used to detect substance information in the sweat of a living body. The biosensor and the flexible substrate are two independent components, and the biosensor does not belong to a part of the flexible substrate.

[0081] In the process of using the biological detection device according to the embodiment of the present disclosure, the flexible substrate is attached to the skin surface of the living body to be measured, and the biosensor is oriented towards the living body to be measured, so that the substance information of the living body can be detected by the biosensor.

[0082] The above-mentioned biosensor may include a microelectrode structure. In one embodiment of the present disclosure, as Figure 1 shown, the microelectrode structure may include a first insulating layer 1 and an electrode layer 3. The electrode layer 3 may be disposed on one side of the first insulating layer 1. Among them, the first insulating layer 1 may be disposed on the side of the flexible substrate facing the organism, and the electrode layer 3 may be disposed on the side of the first insulating layer 1 facing away from the flexible substrate. The microelectrode structure may include a second insulating layer 4. The electrode layer 3 may be located between the first insulating layer 1 and the second insulating layer 4. The second insulating layer 4 may be provided with a window exposing the electrode layer 3.

[0083] In another embodiment of the present disclosure, as Figure 2 shown, the microelectrode structure may include a first insulating layer 1, a protrusion 2, and an electrode layer 3, wherein:

[0084] The protrusion 2 is disposed on one side of the first insulating layer 1. The electrode layer 3 conformally covers the first insulating layer 1 and the protrusion 2.

[0085] In the electrode structure of the embodiment of the present disclosure, the protrusion 2 is disposed on the first insulating layer 1, and the electrode layer 3 conformally covers the first insulating layer 1 and the protrusion 2, so that the area of the electrode layer 3 corresponding to the protrusion 2 also bulges outwards, thereby increasing the area of the electrode layer 3 disposed on the first insulating layer 1, and further improving the contact area between the electrode layer 3 and the object to be measured, thereby improving the detection accuracy.

[0086] The following will detail each part of the microelectrode structure of the embodiment of the present disclosure:

[0087] As Figure 2 shown, the material of the first insulating layer 1 may be an organic material, such as a polymer material, so that the microelectrode structure has good flexibility, ensures good contact between the microelectrode structure and biological tissue, and at the same time can reduce implantation damage. The polymer material may be polyimide, parylene, polydimethylsiloxane, etc. In other embodiments of the present disclosure, the material of the first insulating layer 1 may also be an inorganic material, such as a silicon-based material, so that the microelectrode structure has good biocompatibility and the advantage of being compatible with the microelectronic processing technology of CMOS. The first insulating layer 1 may include opposite first and second surfaces. In addition, as Figure 13 shown, a protrusion 101 may be formed on one side of the first insulating layer 1. Among them, the protrusion 101 may be a part of the first insulating layer 1.

[0088] As Figure 2As shown, the protrusion 2 can be provided on the first insulating layer 1. Among them, the protrusion 2 can be provided on the first surface of the first insulating layer 1. The protrusion 2 can include a bottom surface and a side surface connected to each other. The bottom surface of the protrusion 2 faces the first surface of the first insulating layer 1 and cooperates with the first surface of the first insulating layer 1. The angle between the side surface of the protrusion 2 and the bottom surface of the protrusion 2 can be an acute angle, that is, the cross-section of the protrusion 2 gradually decreases along the direction away from the first insulating layer 1. Further, the protrusion 2 can be a conical structure, such as a cone. In other embodiments of the present disclosure, the protrusion 2 can be a cylindrical structure, a prismatic structure, a frustum structure, etc. The maximum width of the protrusion 2 in the direction parallel to the first insulating layer 1 can be less than or equal to 10 μm. Taking the first protrusion 2 as a cone as an example, the diameter of the bottom surface of the cone is less than or equal to 10 μm. Since the maximum width of the protrusion 2 in the direction parallel to the first insulating layer 1 is small, more protrusions 2 can be formed per unit area of the first insulating layer 1. In other embodiments of the present disclosure, the maximum width of the protrusion 2 in the direction parallel to the first insulating layer 1 can be greater than 10 μm and less than 100 μm. The height of the protrusion 2 can be less than or equal to 10 μm. Of course, the height of the protrusion 2 can also be greater than 10 μm. The material of the protrusion 2 can be an insulating material, such as an inorganic insulating material, an organic insulating material, etc. The organic insulating material can be polyimide, parylene, polydimethylsiloxane, etc. Among them, the material of the protrusion 2 can be the same as the material of the first insulating layer 1. Further, the protrusion 2 and the first insulating layer 1 are an integral structure, that is to say, the protrusion 2 and the first insulating layer 1 are integrally formed. In addition, the number of the protrusions 2 can be multiple, and the multiple protrusions 2 are arranged at intervals. In addition, as Figure 13 As shown, the protrusion 2 is provided on the protrusion 101. Among them, the protrusion 2 is located within the boundary of the protrusion 101, that is to say, the lateral dimension of the protrusion 2 is smaller than the lateral dimension of the protrusion 101.

[0089] As Figure 2 As shown, the electrode layer 3 conformally covers the first insulating layer 1 and the protrusion 2, that is, the region of the electrode layer 3 corresponding to the protrusion 2 protrudes in the direction away from the protrusion 2. The present disclosure can control the thickness of the electrode layer 3 so that the electrode layer 3 conformally covers the first insulating layer 1 and the protrusion 2. Since the angle between the side surface of the protrusion 2 and the bottom surface of the protrusion 2 is an acute angle, the electrode layer 3 covering the protrusion 2 is not easily broken. The material of the electrode layer 3 can be a metal material, such as Au, Ag, Pd, Pt, etc. In addition, the above-mentioned first insulating layer 1 can also be provided with a second through hole 5 exposing the electrode layer 3 so that an external circuit is electrically connected to the electrode layer 3 through the second through hole 5.

[0090] As Figure 3As shown, the electrode layer 3 may include one or more electrode regions. Taking the case where the electrode layer 3 includes multiple electrode regions as an example, the multiple electrode regions are spaced apart from each other. The distance between two adjacent electrode regions may be 0.5 cm - 2 cm, such as 0.5 cm, 0.8 cm, 1.3 cm, 1.5 cm, 2 cm, etc. In an embodiment of the present disclosure, the electrode layer 3 is a two - electrode system, that is, the multiple electrode regions may include a reference electrode region 302 and one or more working electrode regions 301. In another embodiment of the present disclosure, the electrode layer 3 is a three - electrode system, that is, the multiple electrode regions may include a reference electrode region 302, a counter - electrode region, and one or more working electrode regions 301. A plurality of protrusions 2 are provided on the surface of the first insulating layer 1 corresponding to each electrode region.

[0091] As Figure 4 shown, the micro - electrode structure of the embodiment of the present disclosure may further include a second insulating layer 4. The second insulating layer 4 may be provided on the side of the electrode layer 3 facing away from the first insulating layer 1. The second insulating layer 4 may be provided with an opening, and the protrusions 2 extend out of the opening of the second insulating layer 4 so that the protrusions 2 can be in close contact with the biological tissue, improving the detection efficiency and detection accuracy. Taking the case where the number of protrusions 2 is multiple as an example, the number of the openings may also be multiple, and the multiple protrusions 2 extend out of the multiple openings in a one - to - one correspondence. In other embodiments of the present disclosure, each of the above - mentioned electrode regions corresponds to one opening, that is, the multiple protrusions 2 corresponding to each electrode region are exposed through one opening. The material of the second insulating layer 4 may be an organic material, such as a polymer material. The polymer material may be polyimide, parylene, polydimethylsiloxane, etc. In other embodiments of the present disclosure, the material of the second insulating layer 4 may also be an inorganic material, such as a silicon - based material. Among them, the material of the second insulating layer 4 may be the same as that of the first insulating layer 1, or of course, different.

[0092] As Figure 4As shown, the microelectrode structure of the present disclosure embodiment may further include a first sensitive functional layer 6. In an embodiment of the present disclosure, the first sensitive functional layer 6 may include an ionophore or the like, so that the electrode layer 3 forms an ion-selective electrode, and further the microelectrode structure can be used to measure ions. For example, the first sensitive functional layer 6 may be a sodium ion sensitive functional layer, a potassium ion sensitive functional layer, a calcium ion sensitive functional layer, a hydrogen ion sensitive functional layer, or a chloride ion sensitive functional layer, so that the microelectrode structure can be used to measure sodium ions, potassium ions, calcium ions, hydrogen ions, chloride ions, etc. In another embodiment of the present disclosure, the first sensitive functional layer 6 may include an enzyme, such as glucose oxidase, so that the microelectrode structure can be used to analyze glucose. Of course, the first sensitive functional layer 6 can also be used to analyze lactic acid, etc. The first sensitive functional layer 6 at least covers the region of the electrode layer 3 corresponding to the protrusion 2. Further, taking the microelectrode structure including the second insulating layer 4 as an example, the first sensitive functional layer 6 at least covers the region of the portion of the electrode layer 3 corresponding to the protrusion 2 extending out of the opening. The microelectrode structure of the present disclosure embodiment may further include an auxiliary layer 7. The auxiliary layer 7 at least covers the region of the first sensitive functional layer 6 corresponding to the protrusion 2. The auxiliary layer 7 is provided with a first through hole exposing the first sensitive functional layer 6. The first through hole is located outside the opening, that is, the portion of the first sensitive functional layer 6 located outside the opening is exposed through the first through hole. The distance between the auxiliary layer 7 and the electrode layer 3 is less than or equal to 100 μm, so that a capillary channel is formed between the auxiliary layer 7 and the electrode layer 3 to generate capillary force, further improving the extraction and adsorption ability of the microelectrode structure for biological body tissue fluid, sweat and other liquids. Wherein, the distance between the auxiliary layer 7 and the electrode layer 3 may be less than or equal to 10 μm, such as 10 μm, 9 μm, 7 μm, 6 μm, 5 μm, etc. In addition, taking the protrusion 2 as a conical structure as an example, the first through hole may be provided in the region of the auxiliary layer 7 corresponding to the top of the protrusion 2. The material of the auxiliary layer 7 may be an inorganic material, such as a metal material, etc. Of course, the material of the auxiliary layer 7 may also be an organic material. Wherein, the material of the auxiliary layer 7 may be the same as the material of the electrode layer 3. The microelectrode structure of the present disclosure embodiment may further include a second sensitive functional layer 8. The second sensitive functional layer 8 may cover the auxiliary layer 7 and fill the first through hole to contact the first sensitive functional layer 6. Through the second sensitive functional layer 8, the extraction and adsorption ability of the microelectrode structure can be further improved. The second sensitive functional layer 8 has the same composition as the first sensitive functional layer 6. In addition, when there are multiple protrusions 2 on the first insulating layer 1, the formed microelectrode structure is as Figure 5 shown.

[0093] As Figure 3 and Figure 4As shown, taking the electrode layer 3 including the working electrode region 301 and the reference electrode region 302 as an example, the first sensitive functional layer 6 covers the working electrode region 301. A conductive organic layer may also be provided between the working electrode region 301 and the first sensitive functional layer 6. The material of the conductive organic layer may be PEDOT:PSS, PEDOT:PEGDA, etc. Among them, the PEDOT is poly(3,4-ethylenedioxythiophene), the PSS is poly(styrenesulfonate), and the PEGDA is poly(ethylene glycol) diacrylate. PEDOT:PSS represents a blend of PEDOT and PSS. PEDOT:PEGDA represents a blend of PEDOT and PEGDA. Taking the material of the conductive organic layer as PEDOT:PSS as an example, the preparation process of the conductive organic layer is as follows: Prepare a solution containing 0.01 m EDOT and 0.1 m NaPSS, and deposit it onto the working electrode region 301 by constant current electrochemical polymerization of an external Ag / AgCl electrode, and apply a constant current of 2 mA cm -2 to generate polymerization charge on each working electrode region 301.

[0094] When measuring sodium ions, the first sensitive functional layer 6 can be a sodium ion selective thin film. The preparation process of the sodium ion selective thin film is as follows: Prepare a membrane mixture containing sodium ionophore X (1% w / w), Na-TFPB (0.55% w / w), PVC (33% w / w), and DOS (65.45% w / w), and dissolve 100 mg of the membrane mixture in 660 μL of THF to form an ion-selective solution; Using the formed ion-selective solution as a raw material, form the first sensitive functional layer 6 by a liquid phase deposition process. Among them, the sodium ionophore X is 4-tert-butylcalix[4]-arene-tetraacetic acid tetraethyl ester. The microelectrode structure of the present disclosure has a high detection sensitivity for ion concentration. Taking sodium as an example, it can reach 70 - 80 mv / dec.

[0095] When measuring potassium ions, the first sensitive functional layer 6 can be a potassium ion selective thin film. The preparation process of the potassium ion selective thin film is as follows: Prepare a membrane mixture containing valinomycin (2% w / w), Na-TFPB (0.5% w / w), PVC (32.7% w / w), and DOS (64.7% w / w), and dissolve 100 mg of the membrane mixture in 350 μL of cyclohexanone to form an ion-selective solution; Using the formed ion-selective solution as a raw material, form the first sensitive functional layer 6 by a liquid phase deposition process.

[0096] When measuring chloride ions, the first sensitive functional layer 6 can be a chloride ion-selective thin film. The preparation process of the chloride ion-selective thin film is as follows: Use a micropipette to place 0.1M FeCl3 solution on top of the evaporated Ag electrode for 1 minute to form Ag / AgCl.

[0097] When measuring calcium ions, the first sensitive functional layer 6 can be a calcium ion-selective thin film. The preparation process of the calcium ion-selective thin film is as follows: Prepare a membrane mixture containing ETH129 (1% w / w), Na-TFPB (0.5% w / w), PVC (33% w / w), and DOS (65.45% w / w), and dissolve 100 mg of the membrane mixture in 660 μL of THF to form an ion-selective solution; Using the formed ion-selective solution as a raw material, form the first sensitive functional layer 6 by means of liquid-phase deposition process.

[0098] When measuring hydrogen ions, the first sensitive functional layer 6 can be a hydrogen ion-selective thin film. The preparation process of the hydrogen ion-selective thin film is as follows: Distill aniline at a vapor temperature of 100 °C and a pressure of 13 mmHg; Form polyaniline (PANI) in a 0.1M aniline / 0.1M HCl solution; Use cyclic voltammetry to perform 25 cycles of PANI deposition from -0.2V to 1V at 200 mV / s to form the first sensitive functional layer 6.

[0099] When measuring ions, the reference electrode region 302 can also be covered with a functional layer. The preparation process of the functional layer is as follows: Dissolve 79.1 mg of PVB and 50 mg of NaCl in 1 mL of Methanol to prepare a mixture, add 2 mg of F127 and 0.2 mg of Multiwall carbon nanotubes to the membrane mixture solution, and form the functional layer on the reference electrode region 302 by means of liquid-phase deposition.

[0100] The embodiments of the present disclosure also provide a preparation method for a microelectrode structure for preparing the above-mentioned microelectrode structure. As Figure 6 shown, the preparation method of the microelectrode structure can include steps S100 - S130, where:

[0101] Step S100, form a first insulating layer on a support plate.

[0102] Step S110, form a protrusion on the side of the first insulating layer away from the support plate.

[0103] Step S120, form an electrode layer, and the electrode layer conformally covers the first insulating layer and the protrusion.

[0104] Step S130, remove the support plate.

[0105] The microelectrode structure prepared by the preparation method of the microelectrode structure according to the embodiments of the present disclosure is the same as the microelectrode structure in the above embodiments of the microelectrode structure. Therefore, it has the same beneficial effects, and the present disclosure will not elaborate herein.

[0106] The following will detail each step of the preparation method of the microelectrode structure according to the embodiments of the present disclosure:

[0107] In step S100, a first insulating layer is formed on a support plate.

[0108] As Figure 7 shown, the material of the support plate 9 can be inorganic oxide, plastic, etc. The first insulating layer 1 can be prepared by liquid phase deposition, such as spin coating process, but the present disclosure does not make special limitations thereon.

[0109] Step S110: Form a protrusion on the side of the first insulating layer away from the support plate.

[0110] As Figure 7 shown, the present disclosure can form a protrusion 2 on the side of the first insulating layer 1 away from the support plate 9 by an imprinting process or a transfer printing process. Since the protrusion 2 is prepared by an imprinting process or a transfer printing process, a protrusion 2 with a relatively large size can be prepared. For example, the height of the protrusion 2 can be between 10 μm and 100 μm.

[0111] Step S120: Form an electrode layer, and the electrode layer conformally covers the first insulating layer and the protrusion.

[0112] As Figure 7 shown, taking the material of the electrode layer 3 as a metal material and the electrode layer 3 including a plurality of mutually separated electrode regions as an example, forming the electrode layer 3 may include: forming an electrode material layer, and the electrode material layer conformally covers the first insulating layer 1 and the protrusion 2; patterning the electrode material layer to form the electrode layer 3. The electrode material layer can be prepared by an evaporation process. The present disclosure can pattern the electrode material layer by a photolithography process to form an electrode layer 3 including a plurality of electrode regions. Taking the material of the electrode layer 3 as a conductive polymer as an example, the present disclosure can form an electrode layer 3 including a plurality of electrode regions by inkjet printing, but the present disclosure does not make special limitations thereon.

[0113] Step S130: Remove the support plate.

[0114] The present disclosure can remove the support plate 9 by a chemical etching and peeling process, but the present disclosure does not make special limitations thereon. Before removing the support plate 9, as Figure 8As shown, the method for preparing the microelectrode structure of the present disclosure may further include: forming a second insulating layer 4 on the side of the electrode layer 3 facing away from the first insulating layer 1, the second insulating layer 4 being provided with an opening, and the protruding portion 2 protruding out of the opening. Specifically, forming the second insulating layer 4 may include: forming an insulating material layer on the side of the electrode layer 3 facing away from the first insulating layer 1; patterning the insulating material layer to form the second insulating layer 4, the second insulating layer 4 being provided with an opening, and the protruding portion 2 protruding out of the opening. Among them, the insulating material layer may be prepared by liquid phase deposition, such as a spin coating process, but the present disclosure does not make special limitations thereon. The present disclosure may pattern the insulating material layer by a photolithography process.

[0115] Before removing the support plate 9, as Figure 8 As shown, the method for preparing the microelectrode structure of the present disclosure may further include: forming a first sensitive functional layer 6, the first sensitive functional layer 6 at least covering the region of the electrode layer 3 corresponding to the protruding portion 2. The first sensitive functional layer 6 may be prepared by a spin coating process. After forming the first sensitive functional layer 6, the method for preparing the microelectrode structure of the present disclosure may further include: forming an auxiliary layer 7, the auxiliary layer 7 at least covering the region of the first sensitive functional layer 6 corresponding to the protruding portion 2, and being provided with a first through hole exposing the first sensitive functional layer 6, the distance between the auxiliary layer 7 and the electrode layer 3 being less than or equal to 100 μm. Taking the material of the auxiliary layer 7 as a metal material as an example, the auxiliary layer 7 may be prepared by an evaporation process. After forming the auxiliary layer 7, the method for preparing the microelectrode structure of the present disclosure may further include: forming a second sensitive functional layer 8, the second sensitive functional layer 8 covering the auxiliary layer 7 and filling the first through hole to contact the first sensitive functional layer 6. The second sensitive functional layer 8 may be prepared by a spin coating process. In addition, the first through hole in the auxiliary layer 7 is located outside the opening of the second insulating layer 4 described above.

[0116] The method for preparing the microelectrode structure in the embodiment of the present disclosure and the microelectrode structure belong to the same inventive concept, and the descriptions of related details and beneficial effects can be referred to each other and will not be elaborated here.

[0117] The embodiment of the present disclosure also provides a method for preparing a microelectrode structure for preparing the above-mentioned microelectrode structure. As Figure 9 shown, the method for preparing the microelectrode structure may include steps S200 - S230, wherein:

[0118] Step S200, providing a template, one surface of the template having a recessed portion.

[0119] Step S210, forming an electrode layer on the side of the template having the recessed portion, the electrode layer conformally covering the recessed portion.

[0120] Step S220: Form a first insulating layer on the side of the electrode layer facing away from the template, and form a protruding portion in the area of the first insulating layer corresponding to the recessed portion.

[0121] Step S230: Remove the template.

[0122] The microelectrode structure prepared by the preparation method of the microelectrode structure according to the embodiment of the present disclosure is the same as the microelectrode structure in the embodiment of the above microelectrode structure. Therefore, it has the same beneficial effects, and the present disclosure will not repeat them here.

[0123] The following will elaborate on each step of the preparation method of the microelectrode structure according to the embodiment of the present disclosure:

[0124] In step S200, provide a template, and one surface of the template has a recessed portion.

[0125] As Figure 10 shown, the material of the template 10 can be silicone rubber, etc. The side surface of the recessed portion 101 can form an obtuse angle with the surface of the template 10, that is, the recessed portion 101 can have a flared structure. Further, the recessed portion 101 can be a conical structure, such as a cone.

[0126] In step S210, form an electrode layer on the side of the template having the recessed portion, and the electrode layer conformally covers the recessed portion.

[0127] For example, as Figure 11 shown, forming the electrode layer 3 may include: forming a sacrificial layer 11 on the side of the template 10 having the recessed portion 101, and the sacrificial layer 11 conformally covers the recessed portion 101; forming an electrode layer 3 on the side of the sacrificial layer 11 facing away from the template 10, and the electrode layer 3 conformally covers the area of the sacrificial layer 11 located in the recessed portion 101. The material of the sacrificial layer 11 can be aluminum, but the embodiment of the present disclosure does not make special limitations on this. The sacrificial layer 11 conformally covers the recessed portion 101, that is, the area of the sacrificial layer 11 corresponding to the recessed portion 101 protrudes toward the recessed portion 101. The electrode layer 3 can be prepared by an evaporation process. Of course, it can also be prepared by an inkjet printing process.

[0128] In another embodiment of the present disclosure, as Figure 12 shown, forming the electrode layer 3 on the side of the template 10 having the recessed portion 101 includes: forming a second insulating layer 4 on the side of the template 10 having the recessed portion 101, the second insulating layer 4 has an opening, and the recessed portion 101 is exposed through the opening; forming an electrode layer 3 covering the second insulating layer 4 and the recessed portion 101. The second insulating layer 4 can be prepared by a spin coating process. Of course, the second insulating layer 4 can also be formed on the side of the above sacrificial layer 11 facing away from the template 10.

[0129] In step S220, a first insulating layer is formed on the side of the electrode layer facing away from the template, and a protruding portion is formed in the region of the first insulating layer corresponding to the recessed portion.

[0130] As Figure 11 and Figure 12 shown, a protruding portion 2 is formed in the region of the first insulating layer 1 corresponding to the recessed portion 101, that is, the first insulating layer 1 is formed non-conformally on the side of the electrode layer 3 facing away from the template 10. The first insulating layer 1 can be prepared by a spin coating process. The height of the protruding portion 2 can be less than or equal to 10 μm.

[0131] In step S230, the template is removed.

[0132] Taking the example that the sacrificial layer 11 is formed between the electrode layer 3 and the template 10, removing the template 10 may include: removing the sacrificial layer 11 and the template 10. Specifically, the present disclosure can remove the sacrificial layer 11 by an etching solution. The etching rate of the etching solution for the sacrificial layer 11 is greater than the etching rate of the etching solution for the electrode layer 3. Taking the material of the electrode layer 3 as Au and the material of the sacrificial layer 11 as Al as an example, the etching solution may include an acidic etching solution.

[0133] As Figure 11 and Figure 4 shown, if the second insulating layer 4 is not formed in the above step S210, after removing the template 10, the method for preparing the microelectrode structure according to the embodiment of the present disclosure may further include: forming a second insulating layer 4 on the side of the electrode layer 3 facing away from the first insulating layer 1, the second insulating layer 4 is provided with an opening, and the protruding portion 2 extends out of the opening.

[0134] In addition, as Figure 4 shown, the method for preparing the microelectrode structure according to the present disclosure may further include: forming a first sensitive functional layer 6, the first sensitive functional layer 6 at least covers the region of the electrode layer 3 corresponding to the protruding portion 2. The first sensitive functional layer 6 can be prepared by a spin coating process. After forming the first sensitive functional layer 6, the method for preparing the microelectrode structure according to the present disclosure may further include: forming an auxiliary layer 7, the auxiliary layer 7 at least covers the region of the first sensitive functional layer 6 corresponding to the protruding portion 2, and is provided with a first through hole exposing the first sensitive functional layer 6, and the distance between the auxiliary layer 7 and the electrode layer 3 is less than or equal to 100 μm. Taking the material of the auxiliary layer 7 as a metal material as an example, the auxiliary layer 7 can be prepared by an evaporation process. After forming the auxiliary layer 7, the method for preparing the microelectrode structure according to the present disclosure may further include: forming a second sensitive functional layer 8, the second sensitive functional layer 8 covers the auxiliary layer 7, and fills the first through hole to contact the first sensitive functional layer 6. The second sensitive functional layer 8 can be prepared by a spin coating process. In addition, the first through hole on the auxiliary layer 7 is located outside the opening of the second insulating layer 4. Among them, in Figure 12On the basis of the shown structure, the structure of the first sensitive functional layer 6 is as follows Figure 13 as shown.

[0135] As Figures 14 to 16 , Figure 22 and Figure 23 shown, the biological detection device of the embodiments of the present disclosure may include a flexible substrate 12 and a biosensor 13, where:

[0136] The biosensor 13 is disposed on the flexible substrate 12 and is used to obtain the substance information of the organism.

[0137] During the use of the biological detection device of the embodiments of the present disclosure, the flexible substrate 12 is attached to the skin surface of the organism to be measured, and the biosensor 13 is oriented towards the organism to be measured, so that the substance information of the organism can be detected by the biosensor 13.

[0138] The following will detail each part of the biological detection device of the embodiments of the present disclosure:

[0139] As Figure 14 shown, the flexible substrate 12 is a support structure of the biological detection device. The flexible substrate 12 can be attached to the skin of the organism. The material of the flexible substrate 12 can be a polymer material with good elasticity and good ductility, so that the flexible substrate 12 can deform and extend along with the skin of the organism. For example, the material of the flexible substrate 12 can be polyethylene terephthalate (PET), polyimide (PI), polydimethylsiloxane (PDMS), etc. The flexible substrate 12 can include opposite first and second surfaces. When the flexible substrate 12 is attached to the skin of the organism, the first surface of the flexible substrate 12 faces the skin of the organism. In addition, as Figure 17 shown, a second conductive connector 20 can be provided on the flexible substrate 12.

[0140] As Figure 14 , Figure 15 and Figures 17 to 21 shown, the biosensor 13 is disposed on the flexible substrate 12 and is used to obtain the substance information of the organism. Among them, as Figure 14 and Figure 15As shown, the biosensor 13 can be disposed on the side of the flexible substrate 12 facing the organism and within the boundary of the flexible substrate 12. The biosensor 13 being within the boundary of the flexible substrate 12 means that when the flexible substrate 12 is laid flat, the biosensor 13 is within the boundary of the flexible substrate 12 in a direction parallel to the flexible substrate 12. Among them, the biosensor 13 can be disposed on the first surface of the flexible substrate 12 so that the biosensor 13 can contact the organism and detect the substance information of the organism. The substance information can be ion information, glucose information, lactate information, etc. The ion information can be sodium ion information, potassium ion information, chloride ion information, calcium ion information, hydrogen ion information, etc. Among them, the ion information can be the ion information in the sweat of the organism. In another embodiment of the present disclosure, as Figure 22 and Figure 23 shown, at least a part of the biosensor 13 is located outside the boundary of the flexible substrate 12. The biosensor 13 can be provided with the above-mentioned working electrode region 301 and reference electrode region 302. The biosensor 13 can be connected to the second conductive connector 20 on the flexible substrate 12 through the first conductive connector 19. Among them, the first conductive connector 19 and the second conductive connector 20 are detachably connected, for example, by plugging. Since the first conductive connector 19 and the second conductive connector 20 are detachably connected, the biosensor 13 on the flexible substrate 12 can be replaced, and the replaced biosensor 13 can be used to obtain different substance information, and of course, it can also be used to obtain the same substance information.

[0141] As Figure 14 and Figure 15 shown, the biological detection device according to the embodiment of the present disclosure may further include a temperature sensor 16. Taking the biosensor 13 being disposed on the first surface of the flexible substrate 12 as an example, the temperature sensor 16 can be disposed on the side of the flexible substrate 12 facing the organism, that is, the temperature sensor 16 is also disposed on the first surface of the flexible substrate 12. The temperature sensor 16 is used to detect the temperature information of the organism.

[0142] As Figure 14 and Figure 15 shown, the biological detection device according to the embodiment of the present disclosure may further include a heart rate sensor 17. Taking the biosensor 13 being disposed on the first surface of the flexible substrate 12 as an example, the heart rate sensor 17 can be disposed on the side of the flexible substrate 12 facing the organism, that is, the heart rate sensor 17 is also disposed on the first surface of the flexible substrate 12. The heart rate sensor 17 is used to detect the heart rate information of the organism.

[0143] As Figures 14 to 16As shown in the figure, the biological detection device according to the embodiments of the present disclosure may further include a communication module 18. The communication module 18 may be disposed on the second surface of the flexible substrate 12. The communication module 18 may include a Bluetooth antenna and the like. The communication module 18 is connected to the biosensor 13 and can send the substance information to the terminal. Of course, the communication module 18 may also be connected to both the temperature sensor 16 and the heart rate sensor 17 for sending the temperature information and the heart rate information to the terminal. The terminal may be a mobile phone, and of course, it may also be a computer or the like.

[0144] As Figures 14 to 16 shown in the figure, the biological detection device according to the embodiments of the present disclosure may further include an analog-to-digital converter 15. The analog-to-digital converter 15 may be disposed on the second surface of the flexible substrate 12. The analog-to-digital converter 15 is connected to both the biosensor 13 and the communication module 18, and is used for performing analog-to-digital conversion on the substance information detected by the biosensor 13 and sending the converted substance information to the communication module 18. Of course, the analog-to-digital converter 15 may also be connected to both the temperature sensor 16 and the heart rate sensor 17 for performing analog-to-digital conversion on the temperature information and the heart rate information and sending the converted temperature information and heart rate information to the communication module 18. Among them, the information before analog-to-digital conversion is an analog signal, and the information after analog-to-digital conversion is a digital signal.

[0145] As Figures 14 to 16 shown in the figure, the biological detection device according to the embodiments of the present disclosure may further include a power supply component 14. The power supply component 14 is disposed on the side of the flexible substrate 12 facing away from the organism, that is, the power supply component 14 is disposed on the second surface of the flexible substrate 12. Taking the biosensor 13 being disposed on the first surface of the flexible substrate 12 as an example, since the biosensor 13 and the power supply component 14 are located on opposite sides of the flexible substrate 12, it is possible to avoid the biosensor 13 and the power supply component 14 being on the same side of the flexible substrate 12, so that the biosensor 13 and the power supply component 14 can be disposed on the flexible substrate 12 with a relatively small area at the same time. In other embodiments of the present disclosure, the power supply component 14 may also be disposed on the first surface of the flexible substrate 12. The power supply component 14 is connected to the biosensor 13 to supply power to the biosensor 13. Among them, the power supply component 14 may be connected to the above-mentioned second conductive connector 20 so that the power supply component 14 is connected to the biosensor 13. The power supply component 14 is further connected to the temperature sensor 16, the heart rate sensor 17, the communication module 18, and the analog-to-digital converter 15 to supply power to the temperature sensor 16, the heart rate sensor 17, the communication module 18, and the analog-to-digital converter 15. The power supply component 14 may have a sheet-like structure, such as a thin film battery or the like. Among them, the area of the bonding surface of the sheet-like power supply component 14 and the flexible substrate 12 is increased, so that the power supply component 14 can be firmly disposed on the flexible substrate 12.

[0146] The above-mentioned biosensor 13 may include the microelectrode structure in the above embodiments. As Figure 14 shown, the first insulating layer of the microelectrode structure may be provided on the first surface of the flexible substrate 12. The electrode layer may be provided on the side of the first insulating layer facing away from the flexible substrate 12. During use, the microelectrode structure contacts the organism. As Figure 17 shown, since the first conductive connecting member 19 and the second conductive connecting member 20 are detachably connected, the biosensor 13 on the flexible substrate 12 can be replaced. Among them, taking the microelectrode structure including the protrusion as an example, the height of the protrusion in the microelectrode structure included in the biosensor 13 before and after replacement may be different to measure different substance information.

[0147] Embodiments of the present disclosure may also provide a biological detection system. The biological detection system may include the biological detection device described in any of the above embodiments. Of course, the biological detection system may also include a terminal. The terminal may be communicatively connected to the biosensor to process or display the substance information detected by the biosensor. The terminal may be a mobile phone, a computer, etc. Since the biological detection device included in the biological detection system of the embodiments of the present disclosure is the same as the biological detection device in the embodiments of the above biological detection device, therefore, it has the same beneficial effects, and the present disclosure will not be elaborated herein.

[0148] Embodiments of the present disclosure may also provide a biological detection method. The biological detection method may employ the biological detection device described in any of the above embodiments. The biological detection method may include: obtaining first substance information of an organism using the biological detection device; replacing the biosensor of the biological detection device to obtain second substance information of the organism. The first substance information and the second substance information may have the same meaning as the substance information in the embodiments of the above biological detection device. For example, the first substance information or the second substance information is the concentration of sodium ions, potassium ions, calcium ions, hydrogen ions or chloride ions. Further, based on the first substance information or the second substance information, medical personnel cannot directly obtain the diagnosis result or health condition of the organism, which is a further limitation on the first substance information and the second substance information.

[0149] The above are only the preferred embodiments of the present disclosure, and do not impose any form of limitation on the present disclosure. Although the present disclosure has been disclosed above in the preferred embodiments, it is not intended to limit the present disclosure. Any person skilled in the art, without departing from the scope of the technical solution of the present disclosure, may make some changes or modifications to the above-disclosed technical content to obtain equivalent embodiments with equivalent changes. However, as long as it does not depart from the content of the technical solution of the present disclosure, any simple modification, equivalent change and modification made to the above embodiments according to the technical essence of the present disclosure still fall within the scope of the technical solution of the present disclosure.

Claims

1. A biological detection device, characterized in that, Comprising: A flexible substrate; A biosensor disposed on the flexible substrate and configured to obtain substance information of an organism; The biosensor includes a microelectrode structure, and the microelectrode structure includes: A first insulating layer; A protrusion disposed on one side of the first insulating layer, and the protrusion is a conical structure; An electrode layer conformally covering the first insulating layer and the protrusion; A first sensitive functional layer at least covering a region of the electrode layer corresponding to the protrusion; An auxiliary layer at least covering a region of the first sensitive functional layer corresponding to the protrusion, and having a first through-hole exposing the first sensitive functional layer, and a distance between the auxiliary layer and the electrode layer is less than or equal to 100 μm; A second sensitive functional layer covering the auxiliary layer and filling the first through-hole to contact the first sensitive functional layer.

2. The biological detection device according to claim 1, characterized in that The biological detection device further includes: A communication module configured to send the substance information to a terminal.

3. The biological detection device according to claim 2, wherein The biological detection device further includes: An analog-to-digital converter configured to perform analog-to-digital conversion on the substance information and send the converted substance information to the communication module.

4. The biological detection device according to claim 1, characterized in that, The biosensor is disposed on a side of the flexible substrate facing the organism and is located within the boundary of the flexible substrate.

5. The biological detection device according to claim 1, characterized in that At least a part of the biosensor is located outside the boundary of the flexible substrate.

6. The biological detection device according to claim 4 or 5, characterized in that, The biological detection device further includes: A temperature sensor disposed on a side of the flexible substrate facing the organism and configured to detect temperature information of the organism.

7. The biological detection device according to claim 4 or 5, characterized in that, The biological detection device further includes: A heart rate sensor disposed on a side of the flexible substrate facing the organism and configured to detect heart rate information of the organism.

8. The biological detection device according to claim 4 or 5, characterized in that, The biological detection device further includes: A power supply component disposed on one side of the flexible substrate and configured to supply power to the biosensor.

9. The biological detection device according to claim 8, wherein, The power supply component is disposed on a side of the flexible substrate facing away from the organism.

10. The biological detection device according to claim 1, wherein The microelectrode structure further includes: A second insulating layer disposed on a side of the electrode layer facing away from the first insulating layer, the second insulating layer having an opening, and the protrusion protruding through the opening.

11. The biological detection device according to claim 1, characterized in that, A maximum width of the protrusion in a direction parallel to the first insulating layer is less than or equal to 10 μm.

12. The biological detection device according to claim 1, wherein, The protrusion is made of an insulating material.

13. The biological detection device according to claim 1, wherein, The protrusion and the first insulating layer are of an integral structure.

14. The biological detection device according to claim 1, characterized in that, The electrode layer includes one or more electrode regions, and the plurality of electrode regions are spaced apart from each other, and a plurality of the protrusions are provided on a surface of the first insulating layer corresponding to each of the electrode regions.

15. The biological detection device according to claim 14, wherein, The electrode layer includes a reference electrode region and one or more working electrode regions; or The electrode layer includes a reference electrode region, a counter electrode region, and one or more working electrode regions.

16. The biological detection device according to claim 14, characterized in that, A distance between two adjacent electrode regions is 0.5 cm - 2 cm.

17. The biological detection device according to claim 1, wherein, The protrusion is a conical structure, and the first through-hole is provided in a region of the auxiliary layer corresponding to a top end of the protrusion.

18. The biological detection device according to claim 1, wherein The first sensitive functional layer is a sodium ion sensitive functional layer, a potassium ion sensitive functional layer, a calcium ion sensitive functional layer, a hydrogen ion sensitive functional layer, or a chloride ion sensitive functional layer.

19. The biological detection device according to claim 1, wherein, The first insulating layer has a second through-hole exposing the electrode layer.

20. The biological detection device according to claim 1, characterized in that A protrusion is formed on one side of the first insulating layer, and the protruding portion is provided on the protrusion.

21. The biological detection device according to claim 1, characterized in that, The biosensor is used to detect the substance information in the sweat of the organism.

22. A biological detection system, characterized in that, It includes the biological detection device according to any one of claims 1-21.

23. A biological detection method, characterized in that, The biological detection method uses the biological detection device according to any one of claims 1-21, and the biological detection method includes: Using the biological detection device to obtain the first substance information of the organism; Replacing the biosensor of the biological detection device to obtain the second substance information of the organism.

24. The biological detection method according to claim 23, wherein The first substance information or the second substance information is sodium ion concentration, potassium ion concentration, calcium ion concentration, hydrogen ion concentration or chloride ion concentration.

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