Flexible electrode for collecting dual-mode signal and preparation method and application thereof

Abstract

The present application belongs to the technical field of flexible wearable devices, and discloses a flexible electrode for collecting dual-mode signals and a preparation method and application thereof. The flexible electrode comprises a first electrode layer, an insulating film, a flexible dielectric layer, a second electrode layer, a flexible insulating layer and a myoelectric electrode layer. The two surfaces of the flexible dielectric layer opposite to each other are respectively provided with the insulating films, and the surfaces of the two insulating films away from the flexible dielectric layer are respectively provided with the first electrode layer and the second electrode layer. The flexible insulating layer is arranged on the surface of the second electrode layer away from the insulating film. The myoelectric electrode layer is arranged on the side of the flexible insulating layer away from the second electrode layer. The present application can realize dual-mode sensing, high skin conformality and good biocompatibility.

Description

TECHNICAL FIELD

[0001] The present application belongs to the technical field of flexible wearable devices, and more particularly relates to a flexible electrode for collecting dual-mode signals and a preparation method and application thereof. BACKGROUND

[0002] Flexible wearable devices refer to electronic devices or equipment that have mechanical flexibility and can be directly or indirectly closely attached to the skin. Flexible wearable devices have greater mechanical flexibility and can adapt to different working environments to a certain extent and meet the deformation requirements of the human body for the equipment. At present, the research and application of flexible wearable devices have entered many aspects of human daily life, such as electronic skin, wearable physiological monitoring and treatment devices, flexible conductive fabric, flexible circuit boards, etc. Flexible wearable devices have developed rapidly in the fields of biological medicine and military equipment, and the portable and diversified collection of various human signals has become the main research direction, which will become an important auxiliary means for future medical diagnosis and the main basis for the research and development of flexible exoskeleton devices.

[0003] The monitoring of human motion signals has always been a key problem, and the human body structure has characteristics such as redundancy, complexity, and variable stiffness. In order to collect human motion signals, researchers have used joint angle measurement, optical capture systems, EMG measurement, electrical impedance imaging, ultrasonic processing, etc. These human motion signal detection methods can represent the human motion state in some way. Traditional joint angle measurement measures the angle information by pasting marker points on the human body measurement site, adjusting the camera, and using a three-dimensional coordinate algorithm, but its rigid structure will hinder normal human movement and be greatly limited by the site; EMG collects surface myoelectric signals by attaching to the muscle surface, which can be used to predict the type of movement and reflect muscle force, but the surface myoelectric signal is complex and has a low signal-to-noise ratio, and needs to be processed by filtering, rectification, and integration to extract effective information, which has a large error; electrical impedance imaging reconstructs the deformation mode of the muscle by measuring the impedance change of the muscle cross section, has a relatively complete calculation algorithm, but the azimuth angle of the measurement is small, and the measurement range needs to be increased by adding electrodes, which affects the motion state. And most sensors can only collect one kind of motion signal, while human motion characteristics are often related to multiple signals, so the current flexible wearable device is difficult to meet the collection demand of multiple signals, and the processing technology is complex, which is difficult to meet the requirements of economicization, low cost, and high yield. SUMMARY

[0004] In view of the technical problems of single-mode signal collection, complex structure, and poor adhesion of the existing flexible wearable devices, the present application provides a flexible electrode for collecting dual-mode signals and a preparation method and application thereof, which realizes dual-mode sensing, high skin conformability, and good biocompatibility through structural design.

[0005] To achieve the above object, according to one aspect of the present application, a flexible electrode for collecting muscle deformation and electromyographic signals simultaneously is provided, which comprises a first electrode layer, an insulating film, a flexible medium layer, a second electrode layer, a flexible insulating layer and an electromyographic electrode layer, the two surfaces of the flexible medium layer are respectively provided with the insulating films, the surfaces of the two insulating films away from the flexible medium layer are respectively provided with the first electrode layer and the second electrode layer; the flexible insulating layer is arranged on the surface of the second electrode layer away from the insulating film; and the electromyographic electrode layer is arranged on the side of the flexible insulating layer away from the second electrode layer.

[0006] Further, the flexible insulating layer is provided with a groove for fixing the electromyographic electrode layer.

[0007] Further, the number of the grooves and the number of the electromyographic electrode layers are both two, and the two grooves are respectively used for fixing the two electromyographic electrode layers; and the electromyographic electrode layer is prepared by mixing a flexible base material with a conductive material.

[0008] Further, the flexible medium layer is obtained by immersing a flexible porous foam material in a preset solution, and then performing constant temperature drying after the preset solution fills the pores of the flexible porous foam material.

[0009] Further, the flexible porous material is composed of a flexible porous material doped with a conductive material.

[0010] Further, the elastic modulus of the flexible insulating layer is greater than the elastic modulus of the electromyographic electrode layer.

[0011] Further, the thickness of the flexible insulating layer is 1-2 mm, and the elastic modulus is greater than 10 MPa.

[0012] The present application also provides a preparation method of the flexible electrode for collecting dual-mode signals as described above, which comprises the following steps:

[0013] (1) immersing a flexible porous foam material in a preset solution, and then performing constant temperature drying to obtain a flexible medium layer;

[0014] (2) preparing an insulating film on each of the two opposite surfaces of the flexible medium layer, and respectively attaching a first electrode layer and a second electrode layer on the two insulating films;

[0015] (3) preparing a flexible insulating layer by a mold, and then pouring an Eclflex30 solution doped with a conductive filler into the groove of the flexible insulating layer to obtain an electromyographic electrode layer;

[0016] (4) arranging the flexible insulating layer on the second electrode layer to obtain the flexible electrode.

[0017] Further, the method further comprises the step of disposing a circuit board on the surface of the first electrode layer away from the insulating film; the flexible porous foam material is polyurethane sponge, and the preset solution is a calcium copper titanate solution or a PEDOT:PSS aqueous solution; the mass ratio of the PDMS solution body to the catalyst is 10:1.

[0018] The application further provides an application of the flexible electrode for collecting a dual-mode signal in a wearable device.

[0019] Overall, compared with the prior art, the flexible electrode for collecting a dual-mode signal and the preparation method and application thereof provided by the application mainly have the following beneficial effects:

[0020] 1. The flexible electrode comprises a first electrode layer, a flexible dielectric layer, a second electrode layer, a flexible insulating layer, and a myoelectricity electrode layer, the first electrode layer, the flexible dielectric layer, the surface insulating film thereof, and the second electrode layer constitute a multi-stage parallel-plate capacitor, the flexible dielectric layer uses a porous flexible material to reduce the elastic modulus and dopes a conductive substance to increase the dielectric constant, the insulating film separates the dielectric layer from the first electrode layer and the second electrode layer to constitute a series parallel-plate capacitor, when the muscle swells or shrinks, the muscle extrudes the flexible dielectric layer, the distance between the electrode plates changes, thereby changing the size of the parallel-plate capacitor, and the transmission signal of the copper wire changes; at the same time, the myoelectricity electrode layer is used to collect myoelectricity signals, so that the flexible electrode can collect the muscle deformation and the myoelectricity signals at the same time.

[0021] 2. The flexible insulating layer is provided with a groove for fixing the myoelectricity electrode layer and reducing the sliding of the myoelectricity electrode on the skin surface, so that the myoelectricity electrode layer can be fixed well while ensuring that the compression deformation generated by the muscle deformation is basically borne by the flexible dielectric layer, the deformation of the myoelectricity electrode layer in the direction perpendicular to the skin surface is reduced, and the action potential generated in the muscle fiber during the movement process is truly fed back.

[0022] 3. The flexible dielectric layer is prepared by doping a conductive filler with a flexible material to increase the dielectric constant and reduce the elastic modulus.

[0023] 4. The myoelectricity electrode layer uses a flexible material doped with a conductive filler as raw material and is solidified by a deposition forming method to form, the prepared myoelectricity electrode has good contact impedance with the skin and has high skin conformability and biocompatibility, and can improve the stability and reliability of myoelectricity signal detection.

[0024] 5. The elastic modulus of the flexible insulating layer is much greater than that of the myoelectricity electrode, which reduces the deformation of the myoelectricity electrode in the direction perpendicular to the skin surface and ensures the stability and accuracy of the muscle deformation signal and the myoelectricity signal.

[0025] 6. The mass ratio of the configured PDMS solution bulk to the catalyst is 10:1, which ensures that the elastic modulus after curing is 20 MPa, which is much larger than the myoelectric electrode layer, so that when the muscle deformation signal is transmitted upward, the deformation of the myoelectric electrode layer in the direction perpendicular to the skin surface is reduced, and the stability and accuracy of the myoelectric signal are improved. BRIEF DESCRIPTION OF DRAWINGS

[0026] Figure 1 is a structural schematic diagram of a flexible electrode for collecting dual-mode signals provided by the present application;

[0027] Figure 2 (a) and (b) in the above are respectively schematic diagrams of the muscle deformation monitoring mechanism of the embodiments of the present application;

[0028] Figure 3 is a schematic diagram of the surface myoelectric signal monitoring mechanism;

[0029] Figure 4 is a schematic diagram of a flexible dielectric layer;

[0030] Figure 5 is a schematic diagram of a myoelectric electrode layer and a flexible insulating layer;

[0031] Figure 6 is a flowchart of the preparation method of the flexible electrode;

[0032] Figure 7 is a working flowchart of the detection unit when simultaneously collecting muscle deformation and myoelectric signals;

[0033] Figure 8 is a schematic diagram of the muscle deformation signal obtained by the present application;

[0034] Figure 9 is a schematic diagram of the myoelectric signal obtained by the present application.

[0035] In all the drawings, the same reference signs are used to represent the same elements or structures, wherein: 1-circuit board, 2-first electrode layer, 3-insulating film, 4-flexible dielectric layer, 5-second electrode layer, 6-flexible insulating layer, 7-myoelectric electrode layer, 8-copper wire, 9-flexible electrode, 10-skeletal muscle, 11-bone, 12-neuron and muscle fiber. DETAILED DESCRIPTION

[0036] In order to make the purpose, technical solutions and advantages of the present application clearer, the present application will be further described in detail below in combination with the drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain the present application and do not limit the present application. In addition, the technical features involved in each embodiment of the present application described below can be combined with each other as long as they do not conflict with each other.

[0037] The monitoring of human motion signals has always been a key issue of research. Human structure has the characteristics of redundancy, complexity, variable stiffness, etc. In order to collect human motion signals, researchers have adopted joint angle measurement, optical capture system, EMG measurement, electrical impedance imaging, ultrasonic processing and other methods. These human motion signal detection methods can represent the human motion state in some way. Traditional joint angle measurement can obtain angle information by pasting marker points on the human measurement part, adjusting the camera, and using three-dimensional coordinate algorithm, but its rigid structure will hinder the normal movement of the human body, and is greatly limited by the site; EMG can be used to predict the type of movement and reflect muscle force by collecting surface muscle signal through attachment on the muscle surface, but the surface electromyogram is complex and has low signal-to-noise ratio, and needs to be processed by filtering, rectification and integration to extract effective information, which has large error; electrical impedance imaging can reconstruct the deformation mode of muscle by measuring the impedance change of muscle cross section, and has a relatively complete calculation algorithm, but the azimuth angle of measurement is small, and the measurement range needs to be increased by adding electrodes, which affects the motion state. And most sensors can only collect one kind of motion signal, while human motion characteristics are often related to multiple signals, so multi-mode information sensing, high flexibility and biocompatibility are the key to the breakthrough of flexible electronics.

[0038] Please refer to Figure 1 , Figure 2 and Figure 3 , based on the above, the present application provides a flexible electrode 9 for collecting dual-mode signals, which can simultaneously collect muscle deformation and electromyogram signals. The flexible electrode 9 comprises a circuit board 1, a first electrode layer 2, an insulating film 3, a flexible dielectric layer 4, a second electrode layer 5, a flexible insulating layer 6, an electromyogram electrode layer 7 and a copper wire 8. The opposite surfaces of the flexible dielectric layer 4 are respectively provided with insulating films 3, and the surfaces of the two insulating films 3 away from the flexible dielectric layer 4 are respectively provided with the first electrode layer 2 and the second electrode layer 5. The circuit board 1 is arranged on the surface of the first electrode layer 2 away from the insulating film 3. The flexible insulating layer 6 is arranged on the surface of the second electrode layer 5 away from the insulating film 3. The electromyogram electrode layer 7 is arranged on one side of the flexible insulating layer 6 away from the second electrode layer 5. The electromyogram electrode layer 7 transmits signals to other elements through the copper wire 8.

[0039] Among them, Figure 2 The setting of the flexible electrode and the state of the skeletal muscle 10 and the bone 11 in the flexible deformation process are shown. Figure 3 The neurons and muscle fibers 12 are shown in the figure. The neurons transmit nerve signals to the muscle fibers, generate action potentials, and the volume conductor formed by the muscle, subcutaneous tissue and skin is monitored by the electromyogram electrode.

[0040] Please refer to Figure 7 ,Figure 8 and Figure 9 In the embodiment, the bottom of the circuit board is provided with an insulating base formed by curing PMDS or Ecoflex. The flexible dielectric layer is prepared by filling a flexible material doped with a conductive material to increase the dielectric constant and reduce the elastic modulus.

[0041] The flexible insulating layer is used to decouple the muscle deformation and the electromyographic signal, to transmit the muscle deformation signal to the flexible dielectric layer without loss, to fix the electromyographic electrode layer, to reduce the sliding of the electromyographic electrode layer on the skin surface, and to reduce the deformation of the electromyographic electrode layer in the direction perpendicular to the skin surface, thereby ensuring the stability and accuracy of the muscle deformation signal and the electromyographic signal.

[0042] The electromyographic electrode layer is prepared by mixing a flexible base material with a conductive material, which is in direct contact with the skin to collect the action potential in the muscle fiber, has a low skin contact impedance and a high biocompatibility, and always maintains a good conformal contact with the skin surface during signal collection to reduce the generation of motion artifacts. Copper wires are drawn from the first electrode layer and the second electrode layer for transmitting the muscle deformation signal, and copper wires are drawn from the two measuring electrodes of the electromyographic electrode layer for transmitting the electromyographic signal.

[0043] The flexible insulating layer is connected to the second electrode layer by a silicone adhesive. This structure can not only collect the muscle deformation signal, but also collect the electromyographic signal, and the flexible insulating layer can ensure good contact with the skin and high-quality muscle movement signal collection.

[0044] The flexible dielectric layer, the micrometer-level insulating film on the surface thereof, and the second electrode layer constitute a multi-stage parallel plate capacitor. The flexible dielectric layer is prepared from a porous flexible material to reduce the elastic modulus and doped with a conductive substance to increase the dielectric constant.

[0045] The insulating film separates the flexible dielectric layer from the first electrode layer and the second electrode layer to form a series parallel plate capacitor. When the muscle expands or contracts, the muscle presses the flexible dielectric layer, the distance between the plates changes, and the size of the parallel plate capacitor changes, thereby changing the transmission signal through the copper wire.

[0046] The number of the myoelectric electrode layers is two, the two myoelectric electrode layers constitute two measuring electrodes for collecting myoelectric signals, which are prepared by doping conductive fillers in flexible silicone rubber materials, so as to have good biocompatibility and skin conformability, are embedded in the grooves of the flexible insulating layer, reduce the deformation of the myoelectric electrode layers in the vertical skin surface direction when collecting myoelectric signals, so as to reduce the coupling of the dual-mode signals, form a volume conductor with the skin, subcutaneous tissue, muscle and the like to monitor the action potential generated in the muscle fibers, and transmit signals through the copper wires.

[0047] In an embodiment, the flexible medium layer, the first electrode layer and the second electrode layer constitute a parallel plate capacitor model for collecting muscle deformation signals; the thickness of the flexible medium layer is 3-5 mm, the elastic modulus is less than 100 KPa, and preferably the elastic modulus is 80 KPa, the flexible medium layer is in a long strip shape, is more easy to fit the surface of the muscle belly, is used for absorbing the deformation generated by the muscle deformation, and common materials meeting the characteristics are Ecoflex30 solidified product, polyurethane sponge and polyvinyl alcohol gel and the like.

[0048] Please refer to Figure 4 In an embodiment, the flexible medium layer is obtained by immersing a flexible porous foam material in a preset solution, performing constant temperature drying after the preset solution fills the pores of the flexible porous foam material. The preset solution can be a copper calcium titanate solution or a PEDOT:PSS aqueous solution, in order to avoid the problem of breakdown of the parallel plate capacitor, a layer of micron-level insulating film is formed on the upper and lower surfaces of the flexible medium layer by using a rod coating method with fast curing silicone rubber as raw material, and the fast curing silicone rubber can be Ecoflex35 solution.

[0049] In an embodiment, the first electrode layer and the second electrode layer use a welding method or a conductive silver paste to lead out the wires to access the circuit board. The first electrode layer and the second electrode layer are prepared by using conductive fabric, which not only has good conductivity, but also has the characteristics of lightness, thinness, easy cutting, high flexibility and the like, and improves the adhesion of the human body surface.

[0050] In one embodiment, the flexible insulation layer is formed by configuring a PDMS solution to solidify in a preformed mold, leaving two grooves on the lower surface for fixing the electromyographic electrode layer. The thickness of the flexible insulation layer is 1-2 mm, the elastic modulus is greater than 10 MPa, preferably the elastic modulus is 20 MPa, the shape is uniform with the flexible medium layer, and is long strip-shaped, much larger than the elastic modulus of the electromyographic electrode layer, to ensure the accuracy of the muscle deformation signal, decouple the muscle deformation signal and the electromyographic signal through the insulation characteristics of the flexible insulation layer, and improve the signal-to-noise ratio of the dual-mode signal sensing. The flexible insulation layer of the above structure can well fix the electromyographic electrode layer while ensuring that the compression deformation generated by the muscle deformation is basically borne by the flexible medium layer, reducing the deformation of the electromyographic electrode layer in the vertical skin surface direction, and truly feeding back the action potential generated in the muscle fiber during the movement process.

[0051] In one embodiment, referring to Figure 5 , the electromyographic electrode layer is formed by using a deposition forming method to solidify a flexible material doped with conductive fillers. Preferably, the flexible material uses a PMDS solution or an Ecoflex30 solution, and the conductive filler uses carbon nanotubes or silver nanowires. The uniformly mixed solution is poured into the reserved groove of the flexible insulation layer, and the electromyographic electrode layer is obtained after solidification, which reduces the deformation of the electromyographic electrode layer in the vertical skin surface direction when collecting electromyographic signals to reduce the coupling of dual-mode signals, and ensures the safety, stability and accuracy of collecting electromyographic signals. At the same time, the electromyographic electrode prepared by the above material has good contact impedance with the skin, high skin conformability and biocompatibility, and can improve the stability and reliability of electromyographic signal detection.

[0052] The thickness of the electromyographic electrode layer is 0.5-0.8 mm, the elastic modulus is less than or equal to 100 KPa, the surface resistance is less than 20 Ω / sq, the skin contact impedance is less than 100 KΩ under the condition of 100 Hz frequency test, and the surface resistance changes less than 5% when the strain rate is greater than 30%. Preferably, the elastic modulus of the electromyographic electrode layer is 100 KPa, the surface resistance is 10 Ω / sq, the skin contact impedance is 80 KΩ under the condition of 100 Hz frequency test, and the strain rate is 50%. This structure can be well attached to the muscle extension direction, thereby improving the accuracy of electromyographic signal detection.

[0053] The flexible insulation layer with the electromyographic electrode layer is connected to the second electrode layer by a silicone adhesive. This structure can ensure that the muscle deformation signal is transmitted upward to the flexible medium layer, and ensure that the electromyographic electrode layer maintains good conformal contact with the skin, reducing the generation of motion artifacts.

[0054] Referring to Figure 6 , the application also provides a preparation method of the flexible electrode for collecting dual-mode signals, which mainly comprises the following steps:

[0055] S1: Put the flexible porous foam material into the preset solution and soak it, and use an ultrasonic container to oscillate it thoroughly.

[0056] Preferably, the flexible porous foam material is a polyurethane sponge, the preset solution is a calcium copper titanate solution or a PEDOT:PSS aqueous solution, and the oscillation time is 40 min.

[0057] S2: Take out the flexible porous foam material and place it in a constant temperature drying oven for 1 hour to obtain a flexible medium layer.

[0058] Preferably, the thickness of the flexible medium layer is 3-5 mm, the elastic modulus is 80 KPa, and the shape is a long strip, which can be well attached to the surface of the muscle belly.

[0059] S3: Apply Ecoflex 35 solution on the upper and lower surfaces of the flexible medium layer to form a flexible insulation layer, and attach a first electrode layer and a second electrode layer.

[0060] Preferably, the Ecoflex 35 solution is applied using a bar coating method to ensure that the formed insulation surface has sufficient flexibility and minimizes the decrease in dielectric constant, and can ensure that the formed parallel plate capacitor is not broken down when collecting muscle deformation signals.

[0061] Preferably, the first electrode layer and the second electrode layer are cut from conductive fabric, which has good conductivity and ensures that the overall size is light and thin and has good adhesion to the human body surface.

[0062] S4: Pour the prepared PDMS solution into a pre-made mold and form a flexible insulation layer after solidification.

[0063] Preferably, the pre-made mold is manufactured using a 3D printing process to reduce processing difficulty.

[0064] Preferably, the mass ratio of the prepared PDMS solution body to the catalyst is 10:1, which ensures that the elastic modulus after solidification is 20 MPa, which is much larger than the electromyographic electrode layer, so that when the muscle deformation signal is transmitted upward, the deformation of the electromyographic electrode layer in the direction perpendicular to the skin surface is reduced, improving the stability and accuracy of the electromyographic signal.

[0065] Preferably, the lower surface of the flexible insulation layer is reserved with a groove for solidification of the electromyographic electrode layer.

[0066] S5: Prepare an Eclflex 30 solution, dope it with conductive fillers, pour it into the groove of the flexible insulation layer, and form an electromyographic electrode layer after solidification.

[0067] Preferably, the conductive filler uses carbon nanotubes or silver nanowires, the mass fraction of the conductive filler in the Ecoflex 30 solution is 4-8 wt%, for example 4.5 wt%, 5 wt%, 6 wt% or 8 wt%, and the myoelectric electrode layer using such material has good skin contact impedance, ensuring the accuracy and stability of the myoelectric signal acquisition.

[0068] Preferably, the thickness of the myoelectric electrode layer is 0.5-0.8 mm, the shape is a narrow strip, the interval is 2-3 cm, the elastic modulus is 100 KPa, the surface resistance is 10 Ω / sq, the skin contact impedance is 80 KΩ under the condition of 100 Hz frequency test, and the strain rate is 50%, so as to ensure good fit in the muscle extension direction.

[0069] Preferably, the temperature during the curing of the myoelectric electrode layer is 40-80 degrees Celsius, and the time is 20-60 minutes.

[0070] S6: connecting the flexible insulating layer and the second electrode layer using a silicone adhesive to obtain a flexible electrode body.

[0071] Preferably, the flexible electrode with such structure can stably collect myoelectric signals while completely transmitting the muscle deformation signals to the flexible dielectric layer, has good flexibility and excellent biocompatibility, and avoids causing damage to the skin during long-term signal collection.

[0072] The application also provides an application of the flexible electrode for collecting dual-mode signals in a wearable device.

[0073] In summary, the flexible electrode of the application first uses a layered structure to simultaneously collect muscle deformation signals and myoelectric signals, has low contact impedance between the myoelectric electrode layer and the skin, good flexibility and biocompatibility, ensures good conformal contact between the skin during the collection of myoelectric signals, and uses a flexible dielectric layer made of a flexible multi-celled foam material soaked in a conductive solution, which has high dielectric constant and low elastic modulus, and uses a flexible insulating layer to isolate the upper and lower electrodes, preventing the parallel plate capacitor from being broken down during the collection of muscle deformation signals, resulting in signal distortion. The flexible electrode with such structure can be well attached to the skin surface when simultaneously collecting muscle deformation and myoelectric signals, reduces the generation of motion artifacts, reduces the interference between dual-mode signals, and thus realizes the collection of muscle multi-source information during human motion.

[0074] Secondly, the first electrode layer is used to bear the bottom of the collection circuit board with an insulating base, and the flexible electrode body and the collection circuit board are connected in this way, which can reduce the length of the lead wire, reduce parasitic capacitance and motion artifacts, and thus ensure the stability and accuracy of the human motion muscle signal collection.

[0075] Those skilled in the art can easily understand that the above description is only the preferred embodiment of the present application, and is not intended to limit the present application. Any modification, equivalent replacement and improvement made within the spirit and principle of the present application shall be included in the protection scope of the present application.

Claims

1. A flexible electrode for acquiring dual-mode signals, the flexible electrode being used to simultaneously acquire muscle deformation and electromyographic signals, characterized in that: The flexible electrode includes a first electrode layer, an insulating film, a flexible dielectric layer, a second electrode layer, a flexible insulating layer, and a myoelectric electrode layer. The insulating film is disposed on two opposite surfaces of the flexible dielectric layer. The first electrode layer and the second electrode layer are disposed on the surfaces of the two insulating films away from the flexible dielectric layer, respectively. The flexible insulating layer is disposed on the surface of the second electrode layer away from the insulating film. The myoelectric electrode layer is disposed on the side of the flexible insulating layer away from the second electrode layer. The flexible insulating layer has grooves for fixing the electromyographic electrode layer; the number of grooves and the number of electromyographic electrode layers are both two, and the two grooves are used to fix the two electromyographic electrode layers respectively.

2. The flexible electrode for acquiring dual-mode signals as described in claim 1, characterized in that: The electromyography electrode layer is made of a flexible substrate material mixed with a conductive material.

3. The flexible electrode for acquiring dual-mode signals as described in any one of claims 1-2, characterized in that: The flexible medium layer is obtained by immersing a flexible porous foam material in a preset solution, filling the pores of the flexible porous foam material with the preset solution, and then drying it at a constant temperature.

4. The flexible electrode for acquiring dual-mode signals as described in claim 3, characterized in that: The flexible porous foam material is composed of flexible porous material doped with conductive material.

5. The flexible electrode for acquiring dual-mode signals as described in any one of claims 1-2, characterized in that: The elastic modulus of the flexible insulating layer is greater than that of the electromyography electrode layer.

6. The flexible electrode for acquiring dual-mode signals as described in claim 4, characterized in that: The thickness of the flexible insulating layer is 1-2 mm, and the elastic modulus is greater than 10 MPa.

7. A method for fabricating a flexible electrode for acquiring dual-mode signals as described in any one of claims 1-6, characterized in that: The preparation method includes the following steps: (1) The flexible porous foam material is immersed in a preset solution and then dried at a constant temperature to obtain a flexible medium layer; (2) Prepare insulating films on two surfaces opposite to each other of the flexible dielectric layer, and attach the first electrode layer and the second electrode layer to the two insulating films respectively; (3) A flexible insulating layer is prepared by means of a mold, and then Eclflex30 solution is doped with conductive filler and poured into the groove of the flexible insulating layer to obtain an electromyography electrode layer. (4) A flexible insulating layer is disposed on the second electrode layer to obtain the flexible electrode.

8. The method for fabricating a flexible electrode for acquiring dual-mode signals as described in claim 7, characterized in that: It also includes the step of placing the circuit board on the surface of the first electrode layer away from the insulating film; the flexible porous foam material is polyurethane sponge, and the preset solution is copper calcium titanate solution or PEDOT:PSS aqueous solution; the mass ratio of PDMS solution bulk to catalyst is 10:

1.

9. The application of a flexible electrode for acquiring dual-mode signals as described in any one of claims 1-6 in a wearable device.

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