A capacitance bioelectrode internal resistance testing system and its testing method

Abstract

The capacitance bioelectrode internal resistance testing system and method provided by the present application, wherein the conductive layer is disposed on the surface of the dielectric layer, the dielectric layer is in contact with the skin surface, and the composite layer is disposed between the dielectric layer and the skin surface; the electroencephalogram acquisition module is electrically connected to the conductive layer, and the electroencephalogram acquisition module acquires electrophysiological signals; both ends of the impedance testing module are electrically connected to the conductive layer and the composite layer respectively, and the impedance testing module realizes real-time impedance testing. The capacitance bioelectrode internal resistance testing system and its testing method provided by the present application, through the structural design of the composite layer and the adoption of impedance technology, solve the problem that the internal resistance of the electrode cannot be monitored, can realize the real-time detection of brain impedance, and thus realize the detection of the service performance of the electrode.

Description

Technical Field

[0001] This application relates to the technology of physiological electrical signal detection, and particularly to a capacitance bioelectrode internal resistance testing system and a testing method. Background Art

[0002] Physiological electrical signals can help to study physiological states, be applied to disease diagnosis and treatment, and can also be used in emerging fields of artificial intelligence such as brain-computer interfaces. Physiological electrical signals are one of the most important electrophysiological signals. They are caused by the ion concentration difference across the cell membrane. When the organism is in a static state, a resting potential is generated, and when an action occurs, an action potential is generated. The generation of each potential is related to a person's physiological state and behavior. Therefore, it is very important to accurately, real-time, and efficiently detect physiological electrical signals.

[0003] Commonly used technologies include electrocardiogram, electromyogram, and electroencephalogram, etc. An electrocardiogram can help doctors understand the heart's beating condition. An electromyogram is caused by muscle contraction and can help disabled people restore some / all of their activities. An electroencephalogram is helpful for the diagnosis and treatment of brain diseases, such as neurodegenerative diseases like Alzheimer's disease and Parkinson's disease, etc. Common electrical signal acquisition systems include parts such as electrodes, signal amplifiers and converters, signal processors, and displays. Among them, the electrode acquires physiological electrical signals and is a very important core component with an important position.

[0004] Capacitance bioelectrodes are one of the important technologies for acquiring electrophysiological signals. The change in its internal resistance is the main factor affecting signal acquisition. However, during the signal acquisition process, the change in its internal resistance cannot be monitored in real time. Summary of the Invention

[0005] In view of this, it is necessary to provide a capacitance bioelectrode internal resistance testing system that can test the change in its internal resistance in real time to address the defect in the prior art that the change in the internal resistance of a capacitance bioelectrode cannot be monitored in real time during the signal acquisition process.

[0006] To solve the above problems, this application adopts the following technical solutions:

[0007] A capacitance bioelectrode internal resistance testing system provided by this application includes: a conductive layer, a dielectric layer, a composite layer, an electroencephalogram acquisition module, and an impedance testing module, where:

[0008] The conductive layer is placed on the surface of the dielectric layer, the dielectric layer is in contact with the skin surface, the composite layer is arranged between the dielectric layer and the skin surface, the electroencephalogram acquisition module is electrically connected to the conductive layer, the electroencephalogram acquisition module is used to acquire electrophysiological signals, and both ends of the impedance testing module are electrically connected to the conductive layer and the composite layer respectively, and the impedance testing module is used to achieve real-time impedance testing.

[0009] In some of these embodiments, the conductive layer includes, but is not limited to, organic materials and inorganic materials.

[0010] In some of these embodiments, the organic materials include, but are not limited to, PEDOT, MOF, polyaniline, polypyrrole, and polyacetylene.

[0011] In some of these embodiments, the inorganic materials include, but are not limited to, graphene, silver-based nanomaterials, carbon nanotubes, and silver powder.

[0012] In some of these embodiments, the dielectric layer includes, but is not limited to, various non-conductive substances.

[0013] In some of these embodiments, the non-conductive substances include fabrics, oxides, plastics, PTFE, PET, and PI.

[0014] In some of these embodiments, the composite layer includes, but is not limited to, electrical conductive devices composed of organic or inorganic materials.

[0015] In some of these embodiments, the electrical conductive devices include, but are not limited to, PEDOT, MOF, polyaniline, polypyrrole, polyacetylene, graphite, lithium iron phosphate, lithium cobalt oxide, water, EC, PC, and DMC.

[0016] In some of these embodiments, the electrophysiological signals include, but are not limited to, electroencephalogram (EEG), electromyogram (EMG), or electrocardiogram (ECG).

[0017] In some of these embodiments, the impedance test module includes, but is not limited to, alternating current impedance and direct current resistance.

[0018] In some of these embodiments, the composite layer includes, but is not limited to, being placed at the edge or center position between the dielectric layer and the skin surface.

[0019] In some of these embodiments, the contact method between the dielectric layer and the skin surface includes, but is not limited to, using conductive adhesive.

[0020] In some of these embodiments, the thickness of the conductive layer is 1 μm - 10 cm; the thickness of the dielectric layer is 10 nm - 1 cm; the thickness of the composite layer is 10 nm - 1 cm.

[0021] In addition, the present application also provides a test method for the capacitance bioelectrode internal resistance test system described above, including the following steps:

[0022] Place the conductive layer on the surface of the dielectric layer, the dielectric layer is in contact with the skin surface, and the composite layer is disposed between the dielectric layer and the skin surface;

[0023] Electrically connect the described electroencephalogram acquisition module to the described conductive layer, and the electroencephalogram acquisition module acquires electrophysiological signals;

[0024] Both ends of the described impedance test module are electrically connected to the described conductive layer and the described composite layer respectively, and the impedance test module realizes real-time impedance testing.

[0025] The present application adopts the above technical solutions, and the beneficial effects are as follows:

[0026] The capacitance bioelectrode internal resistance test system and its test method provided by the present application, the described conductive layer is placed on the surface of the dielectric layer, the dielectric layer is in contact with the skin surface, and the composite layer is arranged between the dielectric layer and the skin surface; the described electroencephalogram acquisition module is electrically connected to the described conductive layer, and the electroencephalogram acquisition module acquires electrophysiological signals; both ends of the described impedance test module are electrically connected to the described conductive layer and the described composite layer respectively, and the impedance test module realizes real-time impedance testing. The capacitance bioelectrode internal resistance test system and its test method provided by the present application solve the problem of the inability to monitor the internal resistance of the electrode by adopting the structural design of the composite layer and the impedance technology, can realize the real-time detection of the brain impedance, and thus realize the detection of the service performance of the electrode. Description of the Drawings

[0027] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following will briefly introduce the drawings required to be used in the embodiments of the present application or the description of the prior art. Obviously, the following described drawings are only some embodiments of the present application. For those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative efforts.

[0028] Figure 1 It is a schematic structural diagram of the capacitance bioelectrode internal resistance test system provided in Embodiment 1 of the present application;

[0029] Figure 2 It is a step flow chart of the capacitance bioelectrode internal resistance test method provided in Embodiment 2 of the present application. Detailed Description of the Embodiments

[0030] The following details the embodiments of the present application. The examples of the embodiments are shown in the drawings, where the same or similar reference numerals represent the same or similar elements or elements with the same or similar functions from beginning to end. The embodiments described below by referring to the drawings are exemplary and are intended to explain the present application, and should not be construed as a limitation to the present application.

[0031] In the description of the present application, it should be understood that the orientation or positional relationship indicated by the terms "upper", "lower", "horizontal", "inner", "outer", etc. is based on the orientation or positional relationship shown in the drawings. It is only for the convenience of describing the present application and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore should not be construed as a limitation to the present application.

[0032] In addition, the terms "first" and "second" are only used for descriptive purposes and should not be construed as indicating or implying relative importance or implicitly specifying the quantity of the indicated technical features. Thus, the features defined with "first" and "second" may explicitly or implicitly include one or more of such features. In the description of the present application, the meaning of "a plurality" is two or more unless otherwise specifically defined.

[0033] In order to make the objectives, technical solutions and advantages of the present application more clear and understandable, the present application will be further described in detail below with reference to the drawings and embodiments.

[0034] Embodiment 1

[0035] Please refer to Figure 1 , which is a schematic structural diagram of a capacitance bioelectrode internal resistance testing system provided by an embodiment of the present application, including: a conductive layer 110, a dielectric layer 120, a composite layer 130, an electroencephalogram acquisition module 140, and an impedance testing module 150. The specific structures of each component will be described in detail below.

[0036] The described conductive layer 110 is disposed on the surface of the dielectric layer 120. The conductive layer 110 includes, but is not limited to, organic materials and inorganic materials. The organic materials include, but are not limited to, PEDOT, MOF, polyaniline, polypyrrole, and polyacetylene. The inorganic materials include, but are not limited to, graphene, silver-based nanomaterials, carbon nanotubes, and silver powder.

[0037] The dielectric layer 120 is in contact with the skin surface 100. The dielectric layer 120 includes, but is not limited to, various non-conductive substances. The non-conductive substances include, but are not limited to, fabrics, oxides, plastics, PTFE, PET, and PI.

[0038] Further, the contact method between the dielectric layer 120 and the skin surface includes, but is not limited to, using conductive glue.

[0039] The composite layer 130 is disposed between the dielectric layer 120 and the skin surface 100. The composite layer 130 includes, but is not limited to, electrical conductive devices composed of organic or inorganic materials. The electrical conductive devices include, but are not limited to, PEDOT, MOF, polyaniline, polypyrrole, polyacetylene, graphite, lithium iron phosphate, lithium cobalt oxide, water, EC, PC, and DMC.

[0040] Further, the composite layer 130 includes but is not limited to being placed at the edge or the center position between the dielectric layer 120 and the skin surface.

[0041] The electroencephalogram (EEG) acquisition module 140 is electrically connected to the conductive layer 110, and the EEG acquisition module 140 is used to acquire electrophysiological signals. The electrophysiological signals include EEG, electromyogram (EMG), or electrocardiogram (ECG).

[0042] Both ends of the impedance test module 150 are electrically connected to the conductive layer 110 and the composite layer 130 respectively, and the impedance test module 150 is used to perform real-time impedance testing. The impedance test module 150 includes but is not limited to alternating current impedance and direct current resistance.

[0043] Further, the thickness of the conductive layer 110 is 1 μm - 10 cm; the thickness of the dielectric layer 120 is 10 nm - 1 cm; the thickness of the composite layer 130 is 10 nm - 1 cm.

[0044] For the capacitance bioelectrode internal resistance test system provided in the above embodiments of the present application, the conductive layer is placed on the surface of the dielectric layer, the dielectric layer is in contact with the skin surface, and the composite layer is arranged between the dielectric layer and the skin surface; the EEG acquisition module is electrically connected to the conductive layer, and the EEG acquisition module acquires electrophysiological signals; both ends of the impedance test module are electrically connected to the conductive layer and the composite layer respectively, and the impedance test module performs real-time impedance testing. The capacitance bioelectrode internal resistance test system and its test method provided by the present application solve the problem of the inability to monitor the internal resistance of the electrode by adopting the structural design of the composite layer and the impedance technology, can realize the real-time detection of brain impedance, and thus realize the detection of the service performance of the electrode.

[0045] Embodiment 2

[0046] Please refer to Figure 2 , which is the test method of the capacitance bioelectrode internal resistance test system provided in Embodiment 2 of the present application, and includes the following steps:

[0047] Step S110: Place the conductive layer on the surface of the dielectric layer, the dielectric layer is in contact with the skin surface, and the composite layer is arranged between the dielectric layer and the skin surface.

[0048] Specifically, the conductive layer includes but is not limited to organic materials and inorganic materials. The organic materials include but are not limited to PEDOT, MOF, polyaniline, polypyrrole, and polyacetylene. The inorganic materials include but are not limited to graphene, silver-based nanomaterials, carbon nanotubes, and silver powder.

[0049] Specifically, the dielectric layer includes but is not limited to various non-conductive substances. The non-conductive substances include but are not limited to fabrics, oxides, plastics, PTFE, PET, and PI. Further, the contact method between the dielectric layer and the skin surface includes but is not limited to using conductive glue.

[0050] Further, the composite layer includes but is not limited to electrical devices composed of organic or inorganic materials. The electrical devices include but are not limited to PEDOT, MOF, polyaniline, polypyrrole, polyacetylene, graphite, lithium iron phosphate, lithium cobalt oxide, water, EC, PC, and DMC.

[0051] Further, the composite layer is disposed at the edge or center position between the dielectric layer 120 and the skin surface.

[0052] Step S120: Electrically connect the electroencephalogram acquisition module to the conductive layer, and the electroencephalogram acquisition module acquires electrophysiological signals.

[0053] Specifically, the electrophysiological signals include electroencephalogram, electromyogram, or electrocardiogram.

[0054] Step S130: Connect the two ends of the impedance test module to the conductive layer and the composite layer respectively, and the impedance test module realizes real-time impedance testing.

[0055] Specifically, the impedance test module includes but is not limited to alternating current impedance and direct current resistance.

[0056] For the capacitance bioelectrode internal resistance test method provided by the above embodiments of the present application, the conductive layer is disposed on the surface of the dielectric layer, the dielectric layer is in contact with the skin surface, and the composite layer is arranged between the dielectric layer and the skin surface; the electroencephalogram acquisition module is electrically connected to the conductive layer, and the electroencephalogram acquisition module acquires electrophysiological signals; the two ends of the impedance test module are respectively electrically connected to the conductive layer and the composite layer, and the impedance test module realizes real-time impedance testing. The capacitance bioelectrode internal resistance test system and its test method provided by the present application solve the problem of the inability to monitor the internal resistance of the electrode by adopting the structural design of the composite layer and the impedance technology, and can realize the real-time detection of brain impedance, thereby realizing the detection of the service performance of the electrode.

[0057] The above are only preferred embodiments of the present application, and only specifically describe the technical principles of the present application. These descriptions are only for explaining the principles of the present application and cannot be interpreted as limiting the scope of protection of the present application in any way. Based on the explanation here, any modifications, equivalent substitutions and improvements made within the spirit and principles of the present application, and other specific implementation methods of the present application that can be associated with the technicians in this field without creative work, should be included in the scope of protection of the present application.

Claims

1. A capacitance bioelectrode internal resistance testing system, characterized in that, it includes: a conductive layer, a dielectric layer, a composite layer, an electroencephalogram acquisition module and an impedance testing module, where: the conductive layer is placed on the surface of the dielectric layer, the dielectric layer is in contact with the skin surface, the composite layer is arranged between the dielectric layer and the skin surface, the electroencephalogram acquisition module is electrically connected to the conductive layer, the electroencephalogram acquisition module is used to acquire electrophysiological signals, and both ends of the impedance testing module are respectively electrically connected to the conductive layer and the composite layer, and the impedance testing module is used to realize real-time impedance testing.

2. The capacitance bioelectrode internal resistance testing system according to claim 1, characterized in that, the conductive layer includes but is not limited to organic materials and inorganic materials.

3. The capacitance bioelectrode internal resistance testing system according to claim 2, characterized in that, the organic materials include but are not limited to PEDOT, MOF, polyaniline, polypyrrole, polyacetylene.

4. The capacitance bioelectrode internal resistance testing system according to claim 2, characterized in that, the inorganic materials include but are not limited to graphene, silver-based nanomaterials, carbon nanotubes, silver powder.

5. The capacitance bioelectrode internal resistance testing system according to claim 1, characterized in that, the dielectric layer includes but is not limited to various non-conductive substances.

6. The capacitance bioelectrode internal resistance testing system according to claim 5, characterized in that, the non-conductive substances include but are not limited to fabrics, oxides, plastics, PTFE, PET, PI.

7. The capacitance bioelectrode internal resistance testing system according to claim 1, characterized in that, the composite layer includes but is not limited to electrical devices composed of organic or inorganic materials.

8. The capacitance bioelectrode internal resistance testing system according to claim 7, characterized in that, the electrical devices include but are not limited to PEDOT, MOF, polyaniline, polypyrrole, polyacetylene, graphite, lithium iron phosphate, lithium cobalt oxide, water, EC, PC, DMC.

9. The capacitance bioelectrode internal resistance testing system according to claim 1, characterized in that, the electrophysiological signals include electroencephalogram or electromyogram or electrocardiogram.

10. The capacitance bioelectrode internal resistance testing system according to claim 1, characterized in that, the impedance testing module includes but is not limited to alternating current impedance and direct current resistance.

11. The capacitance bioelectrode internal resistance testing system according to claim 1, characterized in that, the composite layer includes but is not limited to being placed at the edge or center position between the dielectric layer and the skin surface.

12. The capacitance bioelectrode internal resistance testing system according to claim 1, characterized in that, the contact method between the dielectric layer and the skin surface includes but is not limited to using conductive glue.

13. The capacitance bioelectrode internal resistance testing system according to claim 1, characterized in that, the thickness of the conductive layer is 1 μm - 10 cm; the thickness of the dielectric layer is 10 nm - 1 cm; the thickness of the composite layer is 10 nm - 1 cm.

14. A testing method for a capacitance bioelectrode internal resistance testing system according to any one of claims 1 to 13, characterized in that, it comprises the following steps: placing the conductive layer on the surface of the dielectric layer, the dielectric layer being in contact with the skin surface, and the composite layer being disposed between the dielectric layer and the skin surface; electrically connecting the electroencephalogram acquisition module to the conductive layer, and the electroencephalogram acquisition module acquires electrophysiological signals; both ends of the impedance testing module are electrically connected to the conductive layer and the composite layer respectively, and the impedance testing module realizes real-time impedance testing.

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