CN116392133A - Flexible myoelectricity electrode and preparation method thereof - Google Patents
Flexible myoelectricity electrode and preparation method thereof Download PDFInfo
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- CN116392133A CN116392133A CN202111633138.1A CN202111633138A CN116392133A CN 116392133 A CN116392133 A CN 116392133A CN 202111633138 A CN202111633138 A CN 202111633138A CN 116392133 A CN116392133 A CN 116392133A
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/251—Means for maintaining electrode contact with the body
- A61B5/256—Wearable electrodes, e.g. having straps or bands
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
- A61B5/296—Bioelectric electrodes therefor specially adapted for particular uses for electromyography [EMG]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
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- Y02E—REDUCTION OF GREENHOUSE GAS [GHG] EMISSIONS, RELATED TO ENERGY GENERATION, TRANSMISSION OR DISTRIBUTION
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Abstract
The application belongs to the technical field of biological information detection, and particularly relates to a flexible stretchable myoelectric electrode and a preparation method thereof. A flexible stretchable myoelectric electrode of the present application comprising: the device comprises a flexible substrate film, a first conductive layer, a second conductive layer, a flexible insulating layer, a PEDOT layer and a polydopamine layer; the surface of the flexible substrate film is provided with a detection site area, a connection circuit area and an insulation area; the first electrode is arranged on the surface of the detection site area; the connecting circuit is arranged on the surface of the connecting circuit area; the connecting circuit is connected with the first electrode; the second electrode is arranged on the surface of the first electrode; the PEDOT layer is arranged on the surface of the second electrode; the polydopamine layer is arranged on the surface of the skin contact surface of the flexible stretchable myoelectric electrode. The flexible stretchable myoelectric electrode can effectively solve the technical problems that an existing myoelectric signal metal dry electrode and a gel wet electrode cannot be stretched and are easy to fall off from skin and the like and is poor in wearability.
Description
Technical Field
The application belongs to the technical field of biological information detection, and particularly relates to a flexible stretchable myoelectric electrode and a preparation method thereof.
Background
The surface electromyographic signal (Surface Electromyography, SEMG) is an electrical signal transmitted at the surface of a muscle, accompanied by muscle movement. When the electrode plate is placed on the skin surface of human body, the weak potential difference generated by the contraction of muscle on the skin surface can be recorded, and the weak potential signal is amplified and converted by the myoelectric acquisition circuit to form a surface myoelectric signal which can be used as treatment. The surface muscle electric signal extraction and recognition technology is widely applied to the fields of medical diagnosis, human body behavioural analysis, human-computer interaction and the like.
At present, a metal dry electrode and a gel wet electrode are mostly adopted for electromyographic signal acquisition. The metal dry electrode has low cost, but has poor fit with human body, and in the process of movement, the friction between the equipment and the skin is easy to generate movement artifacts. Compared with a metal dry electrode, the gel wet electrode can form good fit with skin, so that high-quality electromyographic signals can be obtained. However, the gel tends to deform with water loss, resulting in poor adhesion to the skin, and thus poor measured signals. Meanwhile, the gel has poor biocompatibility, and skin anaphylactic reaction is easy to cause after long-term wearing. Because of the difference of human body structures, the muscle sizes and the muscle distributions of different people are different, however, the structural design of the two electrodes is poor, and therefore, customization of the electrodes is not easy to realize, and accurate measurement of the myoelectric signals of different individuals is realized. In addition, human body exercise often accompanies stretching of muscles, but the existing method for myoelectricity detection of the stretching of muscles of human body exercise mostly uses metal dry electrodes, which cannot stretch, and slippage occurs between the electrodes and the muscles during the stretching of the muscles, so that signals are distorted.
Disclosure of Invention
In view of the above, the application provides a flexible stretchable myoelectric electrode and a preparation method thereof, which can effectively solve the defects of the conventional myoelectric signal metal dry electrode and gel wet electrode and further solve the technical problems of poor wearability such as incapability of stretching, easy falling off from skin and the like.
The first aspect of the present application provides a flexible myoelectric electrode comprising:
the device comprises a flexible substrate film, a first conductive layer, a second conductive layer, a flexible insulating layer, a PEDOT layer and a polydopamine layer;
the surface of the flexible substrate film is divided into a detection site area, a connection circuit area and an insulation area;
a part of the first conductive layer is arranged on the surface of the detection site area to form a first electrode; a part of the first conductive layer is arranged on the surface of the connecting circuit area to form a connecting circuit; one end of the connecting circuit is connected with the first electrode, and the other end of the connecting circuit is a connecting port of an external circuit;
the second conductive layer is arranged on the surface of the first electrode to form a second electrode;
the flexible insulating layer is arranged to form insulating coverage on the connecting circuit area and not to form insulating coverage on the detection site area;
the PEDOT layer is arranged on the surface of the second electrode;
the upper surface of the flexible myoelectricity electrode is a skin contact surface; the polydopamine layer is arranged on the surface of the skin contact surface of the flexible myoelectricity electrode.
Based on the structure, the flexible myoelectric electrode has stable electrical performance under stretching and can still have stable signals when muscles are stretched.
Specifically, PEDOT herein is a polymer of EDOT (3, 4-ethylenedioxythiophene monomer).
In particular, the PEDOT layer of the present application may be used to reduce resistance and increase biocompatibility.
Specifically, the second electrode is arranged on the surface of the first electrode, so that the detection site area protrudes out and forms better contact with the skin.
In another embodiment, the shape of the connection circuit is a serpentine, wavy or straight line.
In another embodiment, the first conductive layer is disposed on the surface of the detection site region and the surface of the connection circuit region by a screen printing technique or an inkjet printing technique.
In another embodiment, the first electrode is arranged on the surface of the detection site area through a screen printing technology, and the mesh number of the first electrode is 150-500 meshes; the first electrode is arranged on the surface of the connecting circuit area through a screen printing technology, and the mesh number of the first electrode is 150-500 meshes.
In another embodiment, the first electrode and the second electrode are silver electrodes, silver/silver chloride electrodes, gold electrodes, or copper electrodes; the thickness of the first electrode is 10-200 micrometers, and the thickness of the second electrode is 10-400 micrometers.
In another embodiment, the PEDOT layer is disposed on the surface of the second electrode by spin coating or drop coating, the spin coating including spin coating a PEDOT solution on the surface of the second electrode, the drop coating including drop coating a PEDOT solution on the surface of the second electrode; wherein the concentration of PEDOT in the PEDOT solution is 0.1% -5%;
or the PEDOT layer is arranged on the surface of the second electrode through an electrochemical deposition method, wherein the electrochemical deposition method comprises the step of electrochemically depositing a PEDOT electrolyte on the surface of the second electrode, and the PEDOT electrolyte comprises EDOT with the concentration of 0.01-0.1M and PSS with the concentration of 0.01-0.1M.
Specifically, the PSS is sodium polystyrene sulfonate.
In another embodiment, the method for disposing the polydopamine layer includes: immersing the skin contact surface of the flexible myoelectricity electrode in (poly) dopamine solution, and forming a polydopamine layer on the surface of the skin contact surface of the flexible myoelectricity electrode after drying; the concentration of the polydopamine solution is 0.1-10 mg/mL, preferably 0.1-2 mg/mL. The (poly) dopamine solution refers to a solution containing solute which can be dopamine, polydopamine or a mixture of the dopamine and polydopamine.
In another embodiment, the flexible substrate film is made of one or more materials selected from PU, silica gel, PDMS, ecoflex; the flexible insulating layer is made of one or more selected from PU, silica gel, PDMS and Ecoflex.
In another embodiment, the number of the first electrodes is at least one, preferably at least two, and the number of the connection circuits is at least one, preferably at least two;
optionally, the connection circuit includes a longitudinal section circuit and a transverse section circuit, and the longitudinal section circuit and the transverse section circuit are connected with each other in an L shape;
in a specific scheme, the first electrodes are arranged on the same straight line at preset distances; in another specific scheme, the first electrodes are respectively arranged on two straight lines at a preset distance;
one end of a longitudinal section circuit of the connecting circuit is connected with the first electrode, and one end of a transverse section circuit of the connecting circuit is connected with the external circuit;
longitudinal section circuits of adjacent connecting circuits are parallel to each other, and transverse section circuits of adjacent connecting circuits are parallel to each other.
The second aspect of the application provides a preparation method of the flexible stretchable myoelectric electrode, which comprises the following steps:
and 6, soaking the upper surface of the flexible myoelectric electrode in (poly) dopamine solution, and drying to form a poly-dopamine layer to prepare the flexible myoelectric electrode.
Specifically, the flexible lining board is made of PET or PVC.
Specifically, the other end of the connecting circuit electrode is a connecting port of an external circuit and is connected with the signal receiving processing end, the port is used for transmitting signals, and the other end of the connecting circuit electrode is converged to form the connecting port of the external circuit.
The flexible stretchable myoelectric electrode can be used as a wearable electrode for detecting myoelectric signals.
The detection site electrode and the connecting circuit are arranged on the flexible substrate film through a screen printing process or an ink-jet printing process, and the electrode has further improved stretchability due to the structure of the connecting circuit. In order to further reduce the electrochemical impedance of the detection site electrode, a PEDOT layer is arranged on the surface of the detection site electrode to serve as a modification layer, and the detection site electrode is of a stacked structure formed by connecting the PEDOT layer and a metal electrode, so that the rapid transmission of electromyographic signals and the stability of the detection site electrode are ensured, and meanwhile, the impedance of the electrode is reduced and the biocompatibility of the electrode is improved. In addition, the first electrode row is also provided with a second electrode, so that the protruding thickness of the detection site electrode is increased, and the contact degree of the detection site electrode and the skin is increased; the flexible stretchable myoelectric electrode is provided with the self-adhesive polydopamine layer, so that the whole electrode is ensured to be in good contact with the skin. In summary, the flexible stretchable myoelectric electrode has stable electrical performance under stretching and can still have stable signals when the muscle stretches. The method can be used for preparing the detection site electrode and the connecting circuit by adopting a screen printing method or an ink-jet printing method, is simple, and is more suitable for mass production. The flexible stretchable myoelectric electrode is easy to wear on the skin surface of a human body, and can record weak potential difference generated on the skin surface due to muscle contraction, so that the muscle state can be evaluated in the medical field, and gesture recognition can be performed in the human-computer interaction field.
It can be seen that the flexible stretchable myoelectric electrode of the present application has the advantages:
(1) The flexible stretchable electromyographic electrode has better conductivity with the detection site electrode and the connecting circuit, and is convenient for electromyographic signal derivation.
(2) The preparation method of the flexible stretchable myoelectric electrode is simpler and more convenient, and is suitable for mass production.
(3) The flexible stretchable myoelectric electrode is of a stacked structure of the PEDOT layer and the metal electrode, so that the rapid transmission and the stability of the myoelectric signal are ensured, and meanwhile, the impedance of the electrode is reduced and the biocompatibility of the electrode is improved.
(4) The flexible stretchable myoelectric electrode has self-adhesion, can form better contact with skin, and has lower interface impedance.
(5) The flexible stretchable myoelectric electrode has stretchability and can adapt to different wearing conditions.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below.
Fig. 1 is a schematic structural diagram of a flexible stretchable myoelectric electrode according to an embodiment of the present application, where a is a cross-sectional view of a connection circuit area of the flexible stretchable myoelectric electrode, and B is a cross-sectional view of a detection site area of the flexible stretchable myoelectric electrode;
FIG. 2 is a first design drawing of a detection site electrode and a connection circuit of a flexible substrate membrane of a flexible stretchable myoelectric electrode provided in an embodiment of the present application;
FIG. 3 is a second design drawing of a detection site electrode and connection circuitry of a flexible substrate membrane of a flexible stretchable myoelectric electrode provided in an embodiment of the present application;
FIG. 4 is a pictorial view of a flexible stretchable myoelectric electrode provided in an embodiment of the present application;
FIG. 5 is an optical microscope image of a connection circuit for a flexible stretchable myoelectric electrode provided in an embodiment of the present application;
FIG. 6 is an optical microscope image of a detection site electrode of a flexible stretchable myoelectric electrode provided in an embodiment of the present application;
FIG. 7 is a graph showing the electrical resistance of a flexible stretchable myoelectric electrode provided in an embodiment of the present application under different stretching conditions;
fig. 8 is an external view of a flexible stretchable myoelectric electrode according to an embodiment of the present application after being worn;
fig. 9 is a graph showing electromyographic signal results after a fist-making gesture and a splay gesture performed after the flexible stretchable electromyographic electrode is worn in fig. 8, wherein an enlarged upper right graph shows a fist-making gesture and a splay gesture evaluation rate graph, and an enlarged lower right graph shows electromyographic signal results measured by the flexible stretchable electromyographic electrode.
Detailed Description
The application provides a flexible stretchable myoelectric electrode and a preparation method thereof, which are used for solving the technical defects that a myoelectric signal metal dry electrode and a gel wet electrode in the prior art cannot be stretched and are easy to fall off from skin and the like and have poor wearability.
The following description of the technical solutions in the embodiments of the present application will be clear and complete, and it is obvious that the described embodiments are only some embodiments of the present application, but not all embodiments. All other embodiments, which can be made by one of ordinary skill in the art without undue burden from the present disclosure, are within the scope of the present disclosure.
Wherein, the raw materials or reagents used in the following examples are all commercially available or self-made.
The structure of the flexible stretchable myoelectric electrode is shown in fig. 1 to 3, fig. 1A is a cross-sectional view of a connection circuit area of the flexible stretchable myoelectric electrode, fig. 1B is a cross-sectional view of a detection site area of the flexible stretchable myoelectric electrode, and fig. 2 is a first design drawing of a detection site electrode and a connection circuit of a flexible substrate film of the flexible stretchable myoelectric electrode provided in the embodiment of the present application; fig. 3 is a second design drawing of a detection site electrode and a connection circuit of a flexible substrate film of a flexible stretchable myoelectric electrode provided in an embodiment of the present application.
The detection site area and the connection circuit area are used for dividing different functional areas in the two-dimensional plane of the flexible stretchable electrode structure; the first conductive layer and the second conductive layer are used for distinguishing the multi-layer vertical structure. The first conductive layer forms a first electrode in the detection site area, and a multi-layer structure is arranged subsequently to form an integral detection site electrode, and in the specific description which does not relate to the sequence of the preparation method, the detection site area, the first electrode and the detection site electrode can refer to the part of the flexible stretchable electrode for acquiring the electromyographic signals; the second conductive layer is formed only on the surface of the first electrode, and the second conductive layer and the first conductive layer can be replaced by each other in the specific description which does not relate to the sequence of the preparation method.
The flexible stretchable myoelectric electrode of the present application comprises: a flexible substrate film 2, a first conductive layer 3, a second conductive layer (second electrode) 4, a flexible insulating layer 6, a PEDOT layer 5 and a polydopamine layer 7; the surface of the flexible substrate film 2 is provided with a detection site area, a connection circuit area and an insulation area; the first conductive layer 3 is arranged on the surface of the detection site area to form a first electrode 3-2; the first conductive layer 3 is arranged on the surface of the connection circuit area to form a connection circuit 3-1; one end of the connecting circuit is connected with the first electrode, and the other end of the connecting circuit is a connecting port of the external circuit 8; the second electrode 4 is arranged on the surface of the first electrode 3-2; the flexible insulating layer 6 is arranged on at least the surface of the connection circuit area; the PEDOT layer 5 is arranged on the surface of the second electrode 4; the upper surface of the flexible stretchable myoelectric electrode is a skin contact surface; the polydopamine layer 7 is provided on the surface of the skin contact surface of the flexible stretchable myoelectric electrode.
Referring to fig. 2 and 3, as a typical design, the connection circuit 3-1 includes a longitudinal section circuit 3-1A and a lateral section circuit 3-1B, the longitudinal section circuit 3-1A and the lateral section circuit 3-1B being connected to each other in an L shape; the first electrodes 3-2 are arranged on the same straight line at a preset distance or on two straight lines at a preset distance respectively; one end of a longitudinal section circuit 3-1A of the connecting circuit is connected with the first electrode, and one end of a transverse section circuit 3-1B of the connecting circuit is connected with the external circuit 8; the longitudinal segment circuits 3-1A of adjacent connection circuits are parallel to each other and the transverse segment circuits 3-1B of adjacent connection circuits are parallel to each other. The longitudinal section circuits 3-1A of adjacent connection circuits are spaced apart by a preset distance.
Referring to fig. 2 and 3, the number of the first electrodes is preferably at least two, and the number of the connection circuits is at least two; the number of the first electrodes 3-2 in fig. 2 is 16; the number of first electrodes 3-2 in fig. 3 is 32. The first electrode and connection circuitry of fig. 3 may be used when there are more muscle groups to be measured, and the first electrode and connection circuitry of fig. 2 may be used when there are fewer muscle groups to be measured.
Wherein, 16 first electrodes 3-2 in fig. 3 are arranged on a first straight line at a preset distance; one end of a longitudinal section circuit 3-1A of the connecting circuit is connected with the first electrode, and one end of a transverse section circuit 3-1B of the connecting circuit is connected with the external circuit 8; the longitudinal segment circuits 3-1A of adjacent connection circuits are parallel to each other and the transverse segment circuits 3-1B of adjacent connection circuits are parallel to each other. The remaining 16 first electrodes 3-2 in fig. 3 are disposed on the second straight line at a preset distance; one end of a longitudinal section circuit 3-1A of the connecting circuit is connected with the first electrode, and one end of a transverse section circuit 3-1B of the connecting circuit is connected with the external circuit 8; the longitudinal segment circuits 3-1A of adjacent connection circuits are parallel to each other and the transverse segment circuits 3-1B of adjacent connection circuits are parallel to each other. The 16 first electrodes 3-2 located on the first straight line are arranged in two rows with the 16 first electrodes 3-2 located on the second straight line.
The flexible stretchable myoelectric electrode of the present application is prepared on a flexible backing plate 1.
The preparation method of the flexible stretchable myoelectric electrode comprises the following steps:
1. and (3) design: according to the size and characteristics of the muscle group, the distribution position, size and number of the detection site electrodes are designed, and the distribution of the connection circuit electrodes connected with the detection site electrodes is designed.
(1) In the step 1, determining the peripheral size of the myoelectricity electrode according to the size of the part to be measured; (2) According to the positions of the muscles of the part to be detected, namely the positions of the detection site electrodes, the number of the mainly used muscles is the minimum number of the detection site electrodes, so that the detection site electrodes can cover the muscle groups of the part to be detected; (3) According to the application requirement, the positions and the number of the detection site electrodes are optimized, for example, in the application of gesture recognition, if only the recognition of the opening gesture is performed, the gesture action is simple, and one detection site electrode can be deployed on the extensor muscle group which is mainly used. When continuous gesture recognition is required, the number of electrodes at the detection site can be properly increased to ensure that enough electromyographic signals are acquired because of diversity and irregularity of hand movements and numerous forearm muscle groups, which results in extremely complex electromyographic signals of the forearm. (4) After the detection site electrodes are determined, the distribution of the connecting circuit is determined, and the detection site electrodes are collected to the interface by the connecting circuit, so that the connection between the later stage and the data receiving processing end is facilitated. The shape of the connecting circuit is a bending shape such as a serpentine, wave shape and the like so as to adapt to the stretching deformation of muscles.
2. And coating a flexible substrate material on the flexible lining plate, and forming a flexible substrate film on the surface of the flexible lining plate after curing. Wherein, the flexible lining board is selected from PET, PVC, etc., the coating method includes spin coating, knife coating, coater, slit coating, etc., the flexible substrate material includes: PU, silica gel, ecoflex, PDMS, etc., and the thickness of the flexible substrate film is 10-500 micrometers. The curing temperature is 50-120 ℃.
3. The detection site area and the connection circuit area of the flexible substrate film are provided with first conductive layers through screen printing or ink-jet printing, a first electrode and a connection circuit are formed, one end of the connection circuit is connected with the first electrode, and the other end of the connection circuit is a connection port of an external circuit; the detection site electrode is used for collecting electromyographic signals, and the connection circuit is used for transmitting the signals. The material of the first conductive layer is selected from Ag, ag/AgCl, gold, copper and the like, and the thickness range of the first conductive layer is: 10-200 micrometers; number of printed mesh of first electrode: 150-500 mesh.
3. At least the connection circuit area of the flexible substrate film is coated with an insulating material to form a flexible insulating layer, the flexible insulating layer exposes the detection site electrode, and the insulating layer material comprises PDMS, silica gel, ecoflex, PU and the like.
4. And (3) carrying out screen printing or ink-jet printing, dispensing or spraying a second electrode on the surface of the first electrode, increasing the thickness of the electrode at the detection site, and preparing the second electrode with a convex structure, wherein the material of the second electrode is selected from Ag, ag/AgCl and the like, and the thickness of the second electrode is 10-400 microns.
5. In order to further reduce the electrochemical impedance of the second electrode, a PEDOT layer may be provided on the surface of the second electrode; the setting method includes spin coating, drip coating or electrochemical deposition. The concentration of the PEDOT solution in the spin coating method and the drop coating method is 0.1-5%, and the concentration of the EDOT in the electrochemical deposition method is 0.01-0.1M, PSS and 0.01-0.1M.
Specifically, the spin coating method includes spin coating a PEDOT solution on the surface of the second electrode; the dropping method comprises the steps of dropping the PEDOT solution on the surface of the second electrode, wherein the concentration of the PEDOT in the PEDOT solution is 0.1% -5%; the PEDOT layer is arranged on the surface of the second electrode through an electrochemical deposition method, the electrochemical deposition method comprises the step of electrochemically depositing a PEDOT electrolyte on the surface of the second electrode, the PEDOT electrolyte comprises EDOT with the concentration of 0.01-0.1M and PSS with the concentration of 0.01-0.1M, and the electrochemical deposition method is the conventional parameter.
6. The flexible lining board is cut through a laser technology, only the interface at the other end of the connecting circuit is left to serve as welding reinforcement, the other end of the connecting circuit is reserved, and the other end of the connecting circuit can be connected with an external circuit.
7. The upper surface of the flexible stretchable myoelectric electrode is a skin contact surface, and the skin contact surface of the flexible stretchable myoelectric electrode is soaked in (poly) dopamine solution to increase self-adhesion.
Specifically, the setting method of the polydopamine layer comprises the following steps: immersing the skin contact surface of the flexible stretchable myoelectric electrode in (poly) dopamine solution, and forming a polydopamine layer on the surface of the skin contact surface of the flexible stretchable myoelectric electrode after drying; the concentration of the (poly) dopamine solution is 0.1-2 mg/mL, preferably 0.1-2 mg/mL, the soaking time is 10-48h, and the soaking temperature is room temperature.
Example 1
The embodiment of the application provides a flexible stretchable myoelectric electrode for preparing Ag-PDMS by a screen printing method, which comprises the following steps:
1. according to the size and characteristics of human forearm muscle groups, the distribution position, size and number of detection site electrodes, the distribution of connection circuit electrodes and the shape of corresponding PDMS are designed to design 16-channel myoelectricity electrodes and insulating layers, as shown in figures 1 and 2 respectively.
2. Spin coating PDMS on a 250 micrometer thickness PET substrate, wherein the mass ratio of PDMS to curing agent is 10:1, curing at 60 ℃ for 1 hour, to obtain a PDMS flexible substrate film with a thickness of 100 micrometers.
3. A stretchable silver paste with a solid content of 70% was used, and a 200 mesh screen was used as a mask, and first electrodes and connection circuits were printed on the detection site area and connection circuit area of the flexible base film, the first electrodes and connection circuits having a thickness of 50. Mu.m.
4. And printing a PDMS flexible insulating layer on the flexible substrate film at least in the area containing the connecting circuit area, exposing the detection site area, wherein the thickness of the PDMS flexible insulating layer is 50 microns.
5. Raised silver electrodes (forming a second electrode) were printed at the detection site electrodes (first electrode), the second electrode having a thickness of 200 microns.
6. And electrodepositing a PEDOT layer on the surface of the silver electrode (the second electrode) by a chronoamperometry, wherein the deposition time is 5min. The PEDOT layer may be used to reduce impedance and increase biocompatibility.
7. The PET substrate of the whole device is cut by laser, the PET substrate is removed, and PET at the rear end joint is left as welding reinforcement. The other end of the connecting circuit is connected with an external circuit at the rear end.
8. The upper surface of the flexible stretchable myoelectric electrode of the whole device is a skin contact surface, the skin contact surface of the flexible stretchable myoelectric electrode is soaked in (poly) dopamine solution with the concentration of 1.2mg/mL for 24 hours, and the 16-channel flexible stretchable myoelectric electrode is obtained after drying, wherein the polydopamine is used for increasing self-adhesion.
The flexible stretchable myoelectric electrode of the embodiment is shown in fig. 4, and fig. 4 is a physical diagram of the flexible stretchable myoelectric electrode provided in the embodiment of the application.
The microscopic results of the first electrode and the connection circuit of the flexible stretchable myoelectric electrode in the embodiment are shown in fig. 5 to 6, and fig. 5 is an optical microscopic diagram of the connection circuit of the flexible stretchable myoelectric electrode provided in the embodiment of the present application; fig. 6 is an optical microscope image of a first electrode of a flexible stretchable myoelectric electrode provided in an embodiment of the present application.
The tensile property of the flexible stretchable myoelectric electrode of this embodiment is shown in fig. 7, the real image of the flexible stretchable myoelectric electrode after being worn is shown in fig. 8, and the result of the myoelectric signal after the fist-making gesture and the opening gesture after the flexible stretchable myoelectric electrode is worn is shown in fig. 9. As shown in fig. 7 to 9, the flexible stretchable myoelectric electrode did not undergo a large change in resistance even after 10% stretching. The myoelectric electrode is attached to the surface of the forearm in the manner shown in fig. 8, and signal acquisition is performed, and the acquired signals are shown in fig. 9. When the user stretches hands and holds a fist, signal response can be obtained, and the strength and the shape of signals obtained by different gestures are different, so that gesture recognition is performed.
Example 2
The embodiment of the application provides a flexible stretchable myoelectric electrode prepared by an ink-jet printing method, which comprises the following steps:
1. according to the size and characteristics of human forearm muscle groups, the distribution position, size and number of detection site electrodes, the distribution of connection circuit electrodes and the shape of corresponding silica gel are designed to design 32-channel myoelectric electrodes, which are respectively shown in fig. 1 and 3.
2. Spin-coating silica gel on a PET substrate with the thickness of 250 micrometers, wherein the mass ratio of the silica gel A, B gel is 2:1, curing for 2 hours at 60 ℃ to obtain a silica gel flexible substrate film with the thickness of 100 micrometers.
3. The silver ink was printed by an inkjet printer at 30% of the ink jet amount, and the first electrode and the connection circuit were printed in the detection site area and the connection circuit area of the flexible substrate film, and cured in an oven at 150 ℃ for 1 hour, with the thickness of the first electrode and the connection circuit being 20 μm.
4. And spin-coating a PDMS flexible insulating layer on the flexible substrate film at least in the area containing the connection circuit area, exposing the detection site area, wherein the thickness of the flexible insulating layer is 50 micrometers.
5. A raised silver electrode (forming a second electrode) was sprayed at the detection site electrode (first electrode), the second electrode having a thickness of 200 microns.
6. And electrodepositing a PEDOT layer on the surface of the silver electrode (the second electrode) by a chronoamperometry, wherein the deposition time is 5min, and the PEDOT layer can be used for reducing impedance and increasing biocompatibility.
7. The PET substrate of the whole device is cut by laser, and the PET substrate is removed, so that PET at the rear end joint is left as welding reinforcement. The other end of the connecting circuit is connected with an external circuit at the rear end.
8. The upper surface of the flexible stretchable myoelectric electrode of the whole device is a skin contact surface, the skin contact surface of the flexible stretchable myoelectric electrode is soaked in (poly) dopamine solution, the 16-channel flexible stretchable myoelectric electrode is obtained after drying, the soaking time is 24 hours, the dopamine concentration can be 0.1-10 mg/mL, preferably 2mg/mL, and polydopamine is used for increasing the self-adhesion.
In summary, in the flexible stretchable myoelectric electrode provided by the application, the flexible stretchable first electrode and the flexible stretchable second electrode can be designed on the flexible substrate film according to the muscle group, so that the electrodes are ensured to have designability and stretchability; the second electrode enables the detection site electrode to have a protruding structure, and the contact degree of the detection site electrode and the skin is increased. The PEDOT layer is arranged on the surface of the second electrode, and the designed connection circuit electrode can ensure the rapid transmission of electric signals and the stability of the electrode, and simultaneously reduce the impedance of the electrode and improve the biocompatibility of the electrode; the self-adhesion of the flexible substrate and polydopamine modify the surface of the skin contact surface, so that the whole electrode is ensured to be in good contact with the skin.
The foregoing is merely a preferred embodiment of the present application and it should be noted that modifications and adaptations to those skilled in the art may be made without departing from the principles of the present application and are intended to be within the scope of the present application.
Claims (10)
1. A flexible myoelectric electrode, comprising:
the device comprises a flexible substrate film, a first conductive layer, a second conductive layer, a flexible insulating layer, a PEDOT layer and a polydopamine layer;
the surface of the flexible substrate film is divided into a detection site area, a connection circuit area and an insulation area;
a part of the first conductive layer is arranged on the surface of the detection site area to form a first electrode; a part of the first conductive layer is arranged on the surface of the connecting circuit area to form a connecting circuit; one end of the connecting circuit is connected with the first electrode, and the other end of the connecting circuit is a connecting port of an external circuit;
the second conductive layer is arranged on the surface of the first electrode to form a second electrode;
the flexible insulating layer is arranged to form insulating coverage on the connecting circuit area and not to form insulating coverage on the detection site area;
the PEDOT layer is arranged on the surface of the second electrode;
the upper surface of the flexible myoelectricity electrode is a skin contact surface; the polydopamine layer is arranged on the surface of the skin contact surface of the flexible myoelectricity electrode.
2. The flexible myoelectric electrode of claim 1, wherein the connection circuit is shaped as a serpentine, wavy or straight line.
3. The flexible myoelectric electrode according to claim 1, characterized in that the first conductive layer is provided on the surface of the detection site area and the surface of the connection circuit area by a screen printing technique or an inkjet printing technique.
4. A flexible myoelectric electrode according to claim 3, characterized in that the screen printing technique uses a mesh size of 150-500 mesh.
5. The flexible myoelectric electrode of claim 1, wherein the first and second electrodes are silver electrodes, silver/silver chloride electrodes, gold electrodes, or copper electrodes; the thickness of the first electrode is 10-200 micrometers, and the thickness of the second electrode is 10-400 micrometers.
6. The flexible myoelectric electrode according to claim 1, characterized in that the PEDOT layer is provided on the surface of the second electrode by spin coating or drip coating, the spin coating comprising spin coating a PEDOT solution on the surface of the second electrode; the drop coating method comprises the steps of dropping PEDOT solution on the surface of the second electrode; wherein the concentration of PEDOT in the PEDOT solution is 0.1% -5%;
or the PEDOT layer is arranged on the surface of the second electrode through an electrochemical deposition method, wherein the electrochemical deposition method comprises the step of electrochemically depositing a PEDOT electrolyte on the surface of the second electrode, and the PEDOT electrolyte comprises EDOT with the concentration of 0.01-0.1M and PSS with the concentration of 0.01-0.1M.
7. The flexible myoelectric electrode according to claim 1, wherein the method for disposing the polydopamine layer comprises: immersing the skin contact surface of the flexible myoelectricity electrode in a dopamine solution or a polydopamine solution, and forming a polydopamine layer on the surface of the skin contact surface of the flexible myoelectricity electrode after drying; the concentration of the dopamine solution or the polydopamine solution is 0.1-10 mg/mL.
8. The flexible myoelectric electrode according to claim 1, wherein the flexible substrate film is made of one or more selected from PU, silicone, PDMS, ecoflex; the flexible insulating layer is made of one or more selected from PU, silica gel, PDMS and Ecoflex.
9. The flexible myoelectric electrode of any one of claims 1-8, wherein the first electrodes are disposed on a common line a preset distance apart; or the first electrodes are respectively arranged on two straight lines at a preset distance.
10. A method of producing a flexible myoelectric electrode according to any one of claims 1 to 9, comprising:
step 1, coating a flexible substrate material on a flexible lining plate, and forming a flexible substrate film on the surface of the flexible lining plate after curing;
step 2, screen printing or ink-jet printing a first conductive layer on the surfaces of a detection site area and a connection circuit area of the flexible substrate film to form a first electrode and a connection circuit, wherein one end of the connection circuit is connected with the first electrode; coating an insulating material on a region which at least comprises a connecting circuit region and does not comprise a detection site region to form a flexible insulating layer;
step 3, screen printing, ink-jet printing, dispensing or spraying a second electrode on the surface of the first electrode;
step 4, coating or electrochemically depositing a PEDOT layer on the surface of the second electrode;
step 5, cutting the flexible lining board, and reserving the other end of the connecting circuit;
and 6, soaking the upper surface of the flexible myoelectric electrode in a dopamine solution or a polydopamine solution, and drying to form a polydopamine layer to prepare the flexible myoelectric electrode.
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