CN117338306A - Epidermal hydrogel hybrid electronic system for electromyography monitoring - Google Patents
Epidermal hydrogel hybrid electronic system for electromyography monitoring Download PDFInfo
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- CN117338306A CN117338306A CN202311653181.3A CN202311653181A CN117338306A CN 117338306 A CN117338306 A CN 117338306A CN 202311653181 A CN202311653181 A CN 202311653181A CN 117338306 A CN117338306 A CN 117338306A
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Classifications
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- A—HUMAN NECESSITIES
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- 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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- A61B5/0004—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by the type of physiological signal transmitted
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- A61B5/0015—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by features of the telemetry system
- A61B5/002—Monitoring the patient using a local or closed circuit, e.g. in a room or building
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- A61B5/25—Bioelectric electrodes therefor
- A61B5/251—Means for maintaining electrode contact with the body
- A61B5/257—Means for maintaining electrode contact with the body using adhesive means, e.g. adhesive pads or tapes
- A61B5/259—Means for maintaining electrode contact with the body using adhesive means, e.g. adhesive pads or tapes using conductive adhesive means, e.g. gels
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- A61B5/25—Bioelectric electrodes therefor
- A61B5/263—Bioelectric electrodes therefor characterised by the electrode materials
- A61B5/266—Bioelectric electrodes therefor characterised by the electrode materials containing electrolytes, conductive gels or pastes
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- A—HUMAN NECESSITIES
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- A—HUMAN NECESSITIES
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
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- C—CHEMISTRY; METALLURGY
- C09—DYES; PAINTS; POLISHES; NATURAL RESINS; ADHESIVES; COMPOSITIONS NOT OTHERWISE PROVIDED FOR; APPLICATIONS OF MATERIALS NOT OTHERWISE PROVIDED FOR
- C09D—COATING COMPOSITIONS, e.g. PAINTS, VARNISHES OR LACQUERS; FILLING PASTES; CHEMICAL PAINT OR INK REMOVERS; INKS; CORRECTING FLUIDS; WOODSTAINS; PASTES OR SOLIDS FOR COLOURING OR PRINTING; USE OF MATERIALS THEREFOR
- C09D11/00—Inks
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
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- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
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- C08J2351/02—Characterised by the use of graft polymers in which the grafted component is obtained by reactions only involving carbon-to-carbon unsaturated bonds; Derivatives of such polymers grafted on to polysaccharides
Abstract
The invention provides a skin hydrogel mixed electronic system for electromyography monitoring, which comprises a flexible frame main body, a stretchable conducting layer and a rear-end wireless core main control module, wherein the stretchable conducting layer is arranged in the flexible frame main body, the conducting wire and the electrode group are integrated, the electrode group extends out of the flexible main body frame, a hydrogel interface layer is adhered to the surface of the electrode group, the hydrogel interface layer comprises a polyvinyl alcohol chain, alginate-catechol functional molecules, amide monomers and ammonium chloride cationic monomers, the stretchable conducting layer contains quaternary ammonium salt chitosan-phenylboronic acid functional molecules, diphenyl iodic chloride/phosphate buffer solution is dripped on the surface of the electrode group, the electrode group is connected with the rear-end wireless core main control module and used for inducing nerve to generate action potential and measuring electromyography signals, and the rear-end wireless core main control module receives data of the electrode group and carries out analysis treatment on the received data and then carries out wireless transmission to an external terminal. The hydrogel interface layer can be rapidly disassembled through ultraviolet irradiation, so that cross infection among patients is avoided.
Description
Technical Field
The invention relates to the technical field of biomedical instruments, in particular to an epidermis hydrogel mixed electronic system for electromyography monitoring.
Background
Electromyography is a commonly used neuro-electrophysiological test method for assessing the function of the nervous system and diagnosing neuropathies. The technique combines nerve conduction velocity measurement with electromyographic recording to provide detailed information about nerve conduction capacity and muscle activity. With advances in technology and advances in theory, neuroelectromyography is becoming an indispensable tool in neurology, rehabilitation medicine, and clinical diagnostics. Nerve electromyography detection mainly comprises two aspects: nerve conduction velocity measurement and electromyography recording. Nerve conduction velocity measurement the velocity and integrity of nerve conduction is assessed by stimulating and recording the electrical signals of nerve fibers. In this process, a stimulation electrode is placed at a specific location of the nerve, nerve fibers are activated by delivering electrical stimulation, and then the conduction time and amplitude of the signal are measured using a recording electrode. By recording the distance between the stimulation points and the conduction time, the nerve conduction velocity and latency can be determined, thereby assessing the abnormal condition of nerve conduction. Electromyography can also be used to diagnose and evaluate a variety of neuropathies, such as peripheral neuropathy, radiculopathy, and neuromuscular diseases.
The current electromyographic recording device mainly comprises a traditional multichannel electrophysiological recorder. These devices play an important role in neuropathological research and clinical diagnosis, but also have some drawbacks. Medical electromyography acquisition devices are often cumbersome and complex, requiring specialized laboratory or clinical settings to operate. This limits its use in field or remote diagnostics. Secondly, the use of conventional equipment requires specialized operating skills and expertise, and requires high demands on operators. This may limit its use in some non-professional settings, such as basic medical institutions or home care environments. In addition, the high price of traditional equipment makes it difficult to popularize and promote in certain resource-starved areas or institutions. Although some emerging portable wireless devices have been developed in recent years, these devices are compact and lightweight and can be conveniently carried and used. They typically employ wireless transmission techniques to enable wireless data transmission and remote monitoring. This allows for more flexible and convenient neuroelectromyographic recording, which is no longer limited to laboratory or clinical settings. The advent of portable wireless devices has provided new possibilities for telemedicine, home care, and mobile diagnostics. However, as the devices are mainly composed of rigid devices, the modulus of the collected and stimulated electrodes is high, and the collected and stimulated electrodes cannot form co-contact with the skin surface, so that the anti-motion artifact capability of the collection system is poor, the wearing comfort is poor, the fidelity of the collected signals is low, and the application of the portable wireless device is severely limited.
In order to further improve the signal fidelity of electromyography, a large number of flexible skin electrodes have been developed in recent years, and as the flexible skin electrodes are made of flexible materials, such as polymers or elastic materials, the flexible skin electrodes can adapt to different skin shapes and movement ranges, and provide comfortable wearing experience. The flexibility also enables the electrode to better contact the skin, and reduces interference of motion or external force on signal recording, thereby improving electromyographic signal quality and accuracy. However, the preparation process of the flexible skin electrode is relatively complex, and precise processing and assembly techniques are required, so in the process of testing electromyography for different patients, in order to avoid cross infection among patients, the electrode is often not reusable, and needs to be replaced in time, which leads to significant improvement of testing cost. Therefore, there is an urgent need to develop an epidermal electronic system capable of acquiring high-quality electromyographic signals, and at the same time, flexible epidermal electrodes of the system need to ensure the on-demand replacement of electrode interfaces so as to avoid cross-infection between patients.
Disclosure of Invention
In order to solve the problems in the background art, the invention provides the epidermis hydrogel mixed electronic system for electromyography monitoring, and the interface of the hydrogel mixed electronic system has the characteristics of low modulus, high flexibility and the like, can be in seamless fit with an electromyography detection area of a patient, can realize rapid disassembly of a hydrogel interface layer through ultraviolet irradiation, and avoids cross infection among patients.
The technical scheme for solving the technical problems is as follows:
the invention provides an epidermis hydrogel mixed electronic system for electromyography monitoring, which comprises a flexible frame main body, a stretchable conducting layer, a hydrogel interface layer and a rear-end wireless core main control module, wherein the flexible frame main body is formed by jointly constructing a flexible basal layer and a flexible packaging layer; the hydrogel interface layer comprises a polyvinyl alcohol chain, alginate-catechol functional molecules, amide monomers, ammonium chloride salt cationic monomers, an initiator and a cross-linking agent, and is formed by ultraviolet initiated polymerization; the electrode material contains quaternary ammonium salt chitosan-phenylboronic acid functional molecules, diphenyl iodized salt/phosphate buffer solution is dripped on the surface of the electrode material, the electrode group is connected with the rear-end wireless core main control module and used for inducing nerves to generate action potentials through pulse voltage signals applied by the rear-end wireless core main control module, electromyographic signals are measured, and the rear-end wireless core main control module receives data of the electrode group, analyzes and processes the received data and then wirelessly transmits the data to an external terminal.
The hydrogel interface layer is laminated on the electrode group of the stretchable conductive layer, and boric acid ester bonds are formed between phenylboric acid in the stretchable conductive layer and polyvinyl alcohol and catechol in the hydrogel interface layer to realize seamless bonding of the two layers. After the electromyography collection of the patient is completed, the hydrogel interface layer is placed under ultraviolet light, diphenyl iodized chloride is reduced to generate hydrogen ions, so that the pH value is reduced, and therefore boric acid ester bonds are formed between phenylboric acid and polyvinyl alcohol and catechol groups to break, the detachment of the hydrogel interface layer is realized, and cross infection of the patient is avoided.
According to the scheme, in the hydrogel interface layer, the mass fractions of the polyvinyl alcohol chain, the alginate-catechol functional molecule, the amide monomer, the ammonium chloride salt cationic monomer, the initiator and the cross-linking agent are respectively 5 wt-10 wt%, 2 wt-8 wt%, 15 wt-30 wt%, 10 wt-15 wt%, 0.01 wt-0.05 wt%, 0.02 wt-0.1 wt%, and the balance of water.
According to the scheme, the molecular weight of the polyvinyl alcohol chain is 10000-750000, the molecular weight of the alginate in the alginate-catechol functional molecule is 7000-350000, the amide monomer is any one or more of acrylamide and acrylamide derivatives, the ammonium chloride salt cationic monomer is acryloyloxyethyl trimethyl ammonium chloride or methacryloyloxyethyl trimethyl ammonium chloride, the initiator is one or two of ammonium persulfate or potassium persulfate, and the cross-linking agent is one or two of N, N' -methylenebisacrylamide or PEGDA and the like.
According to the scheme, the stretchable conductive layer is made of the conductive slurry which can be stretched after solidification, and the conductive slurry comprises silver flake/gallium alloy conductive particles, PEDOT: PSS conductive polymer, amide monomer, quaternary ammonium salt chitosan-phenylboronic acid functional molecule, initiator and cross-linking agent.
According to the scheme, in the conductive slurry, the silver flake/gallium alloy conductive particles, PEDOT: PSS conductive polymer, amide monomer, quaternary ammonium salt chitosan-phenylboronic acid functional molecule, initiator and cross-linking agent account for 10% wt% -15% wt%, 2% wt% -8 wt%, 20% wt% -30% wt%, 5% wt% -15% wt%, 0.01% wt% -0.05% wt% and 0.02% wt% -0.1% wt% by mass respectively.
According to the scheme, the silver flake/gallium-based alloy conductive particles are of a micron level, wherein the mass ratio of the silver flake to the gallium-based alloy is 0.2-1.
According to the scheme, the electrode group comprises a stimulating electrode and a recording electrode;
the back-end wireless core main control module comprises a core processor module, an electric stimulation module, an electromyographic signal acquisition module and a wireless transmitting module;
the stimulating electrode is connected with the electric stimulating module and induces nerve to generate action potential through pulse voltage signals applied by the electric stimulating module, the electromyographic signal acquisition module is connected with the recording electrode to realize real-time acquisition of electromyographic data, and the core processor module is respectively connected with the electric stimulating module and the electromyographic signal acquisition module and is used for inducing the electric stimulating module to operate, store and process the electromyographic signal data and transmitting the electromyographic signal data to an external terminal through the Wifi transmitting module.
According to the scheme, the rear-end wireless core main control module further comprises a lithium battery power supply module and a voltage stabilizing module, and the lithium battery power supply module and the voltage stabilizing module are used for realizing constant voltage supply of the rear-end wireless core main control module.
According to the scheme, the epidermal hydrogel mixed electronic system is prepared by the following method:
s1, dissolving 10-15 mmol of quaternary ammonium salt chitosan in MES solution with PH=5-6, then degassing, fully mixing to obtain a uniform mixed solution, adding 1-5mmol of 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride and 1-5mmol of N-hydroxy thiosuccinimide, magnetically stirring, mixing and degassing;
s2, slowly dissolving 1-10mmol of 4-carboxyphenylboronic acid in the solution, sealing and fully stirring for 10-24 hours, dialyzing and freeze-drying to obtain a quaternary ammonium salt chitosan-phenylboronic acid functional molecule;
s3, dissolving silver flake/gallium alloy conductive particles, PEDOT (polyether-amine) PSS conductive polymers, amide monomers, the synthesized quaternary ammonium salt chitosan-phenylboronic acid functional molecules, an initiator and a cross-linking agent in deionized water, uniformly stirring, and degassing to obtain conductive slurry;
s4, dropwise adding the benzophenone solution into the flexible substrate layer for 5-20min, then patterning and printing the conductive slurry on the flexible substrate layer, heating and curing to obtain a fully polymerized stretchable conductive layer, and bonding a flexible packaging layer on the stretchable conductive layer;
s6, dissolving a polyvinyl alcohol chain, an alginate-catechol functional molecule, a polyamide monomer, an ammonium chloride salt cationic monomer, an initiator and a cross-linking agent in deionized water, magnetically stirring until the polyvinyl alcohol chain, the alginate-catechol functional molecule, the ammonium chloride salt cationic monomer, the initiator and the cross-linking agent are completely dissolved, and injecting the mixture into a circular electrode die for ultraviolet curing after degassing to obtain a hydrogel interface layer;
s7, dropwise adding diphenyl iodized salt/phosphate buffer solution onto the stretchable conductive layer, laminating a hydrogel interface layer for 0.5-1h, and promoting the formation of boric acid ester bonds between phenylboronic acid and polyvinyl alcohol and catechol groups to realize two-layer bonding.
According to the scheme, the flexible substrate layer and the flexible packaging layer are made of polydimethylsiloxane.
According to the scheme, the pH value of the diphenyl iodized salt/phosphate buffer solution is 7.5-10, and the mass fraction of the diphenyl iodized salt is 2-5 wt%.
The beneficial effects of the invention are as follows:
1) The hydrogel interface layer disclosed by the invention has good viscosity, low modulus, good interface shape retention adhesion, good signal to noise ratio in the electromyography monitoring process and strong motion artifact resistance;
2) The flexible packaging layer, the flexible substrate layer and the stretchable electrode layer in the epidermis hydrogel mixed electronic system have outstanding conductive performance, high compatibility with the hydrogel interface layer and strong stretching capability, have the use scene suitable for various deformations, have lower contact impedance, provide lower signal-to-noise ratio and facilitate electromyography monitoring;
3) The skin hydrogel mixed electronic system for electromyography monitoring has a detachable function, after the skin system collects electromyography of a patient, the hydrogel interface layer is irradiated under ultraviolet light to cause reduction of diphenyl iodized salt to generate hydrogen ions, so that the pH value is reduced, the borate ester bond is broken, and the detachment of the hydrogel interface layer and the stretchable conductive layer is realized;
4) The core processor module stores and analyzes the acquired ethical signal data, transmits the acquired ethical signal data to the Wifi module, and wirelessly transmits the acquired ethical signal data to an external terminal to display various index data of the electromyogram in real time so as to realize the on-line diagnosis of the electromyogram;
5) The whole preparation process of the hybrid electronic system is simple, complicated preparation processes such as ultra-clean room and photoetching are not needed, the manufacturing cost of the hybrid electronic system is effectively reduced, and the preparation efficiency of the system is improved.
Drawings
FIG. 1 is a schematic three-dimensional structure of an epidermal hydrogel hybrid electronic system for electromyography monitoring according to the present invention;
FIG. 2 is a schematic diagram of the manufacturing process of the skin hydrogel hybrid electronic system for electromyography monitoring of the invention;
FIG. 3 is a schematic diagram of the conductive interface layer of the epidermal hydrogel hybrid electronic system for electromyography monitoring according to the present invention;
FIG. 4 is a schematic diagram of the principle of interface layer disassembly of the epidermal hydrogel hybrid electronic system for electromyography monitoring of the present invention;
FIG. 5 is a circuit block diagram of an epidermal hydrogel hybrid electronic system for electromyography monitoring of the present invention;
FIG. 6 is a schematic view of the monitoring of the epidermal hydrogel hybrid electronic system for electromyography monitoring of the present invention;
fig. 7 is a graph of myoelectric signals of the epidermal hydrogel mixed electronic system monitoring the median nerve.
Wherein 1 is a hydrogel interface layer, 1-1 is a polyvinyl alcohol chain, 1-2 is an alginate-catechol functional molecule, 1-3 is polymethyl acryloyloxyethyl trimethyl ammonium chloride, 2 is a flexible packaging layer, 3 is a stretchable conducting layer, 3-1 is an electric stimulating electrode cathode, 3-2 is an electric stimulating electrode anode, 3-3 is a collecting electrode, 3-4 is a reference electrode, 3-5 is a ground electrode, 3-6 is a quaternary ammonium salt chitosan-phenylboronic acid functional molecule, 3-7 is PEDOT (poly (styrene-acrylic acid)) conducting polymer, 3-8 is polyacrylamide, 3-9 is silver flake/gallium alloy conducting particles, 4 is a flexible substrate layer, 5 is a soft flat cable socket, 6 is a wireless core main control module, 6-1 is a core processor module, 6-2 is a voltage stabilizing module, 6-3 is a lithium battery power supply module, 6-4 is a clock crystal oscillator module, 6-5 is a program downloading module, 6-6 is a PC upper computer terminal, 6-7 is a Wifi transmitting module, 6-8 is an electric stimulating module, 6-9 is a pre-layer, 9 is a phenyl hydrogen bond solution, 10 is a phenyl chloride solution, and 10 is a solution of a phenyl chloride, and a mask is a solution of a phenyl chloride and/or a solution of a polyvinyl chloride and a polyvinyl chloride is 11. 13 is electrostatic coupling effect, 14 is physical crosslinking, 15 is covalent crosslinking, 16 is boric acid ester bond, 17 is diphenyl iodized salt, 18 is hydroxyl, 19 is hydrogen ion, 20 is biphenyl, 21 is iodized benzene, 22 is patient median nerve movement branch electromyogram, 23 is the electromyogram of the motor branch of the median nerve of a normal person.
Detailed Description
The principles and features of the present invention are described below with reference to the drawings and specific embodiments, the examples being provided for illustration only and not for the purpose of limiting the invention.
As shown in fig. 1, the invention provides an epidermal hydrogel mixed electronic system for electromyography monitoring, which comprises a flexible substrate layer 4, a flexible packaging layer 2, a stretchable conducting layer 3 integrated with wires and electrode groups, a hydrogel interface layer 1 and a rear-end wireless core main control module 6, wherein the flexible packaging layer 2 is arranged on the flexible substrate layer 4 to jointly construct a flexible frame main body, the stretchable conducting layer 3 is arranged in the flexible frame main body, the electrode groups extend out of the flexible main body frame through windows on the flexible packaging layer 2, and the hydrogel interface layer 1 is arranged on the flexible packaging layer 2 and adhered on the electrode groups for adhering with skin tissues; the hydrogel interface layer 1 comprises polyvinyl alcohol chains 1-1, alginate-catechol functional molecules 1-2, amide monomers, ammonium chloride salt cationic monomers, an initiator and a cross-linking agent, and is formed by ultraviolet initiated polymerization; the material of the stretchable conducting layer 3 contains quaternary ammonium salt chitosan-phenylboronic acid functional molecules 3-6, diphenyl iodized salt/phosphate buffer solution 11 is dripped on the surface of the electrode group, and under ultraviolet irradiation, the diphenyl iodized salt is reduced to generate hydrogen ions, so that the pH value is reduced, and boric acid ester bonds formed between phenylboronic acid and polyvinyl alcohol and catechol groups are broken, so that the disassembly of a hydrogel interface layer is realized; the electrode group is connected with the rear-end wireless core main control module 6 and is used for inducing nerves to generate action potential through pulse voltage signals applied by the rear-end wireless core main control module 6 and measuring electromyographic signals, and the rear-end wireless core main control module 6 receives data of the electrode group, analyzes and processes the received data and then wirelessly transmits the data to an external terminal.
The hydrogel interface layer 1 is laminated on the electrode group of the stretchable conducting layer 3, and boric acid ester bonds are formed between phenylboric acid in the stretchable conducting layer 3 and polyvinyl alcohol and catechol in the hydrogel interface layer 1 to realize seamless bonding of the two layers.
The schematic diagram of the disassembly principle of the hydrogel interface layer 1 is shown in fig. 4, after the skin hydrogel mixed electronic system finishes collecting the electromyography of a patient, the hydrogel interface layer 1 is placed under ultraviolet light (254 nm) to irradiate to trigger diphenyl iodine chloride (DPI) 17 to be reduced to generate biphenyl 20, iodized benzene 21 and hydrogen ions 19, the pH value of the joint of the hydrogel interface layer 1 and the stretchable conductive layer 3 is reduced, and finally, the borate ester bond 16 is broken under the surrounding of the hydroxyl 18, so that the disassembly of the hydrogel interface layer 1 and the stretchable conductive layer 3 is realized.
The hydrogel interface layer 1 has the characteristics of low modulus, high flexibility and the like, is suitable for skin surface conformal attachment with large deformation, can realize seamless attachment with an electromyographic monitoring area of a patient, has excellent conductivity and stretchability, meets various application scenes of electromyographic monitoring, and the rear-end wireless core main control module 6 realizes high-fidelity signal detection and wireless transmission of signals.
Preferably, in the hydrogel interface layer 1, the mass fractions of polyvinyl alcohol chain 1-1, alginate-catechol functional molecule 1-2, amide monomer, ammonium chloride salt cationic monomer, initiator and cross-linking agent are respectively 5wt% -10 wt%, 2wt% -8 wt%, 15 wt% -30 wt%, 10 wt% -15 wt%, 0.01 wt% -0.05 wt%, 0.02 wt% -0.1 wt%, and the balance being water, and the prepared hydrogel interface layer is APDH interface layer.
Preferably, the molecular weight of the polyvinyl alcohol chain 1-1 is 10000-750000, the molecular weight of the alginate in the alginate-catechol functional molecule 1-2 is 7000-350000, the amide monomer is any one or more of acrylamide and acrylamide derivatives, the ammonium chloride salt cation monomer is acryloyloxyethyl trimethyl ammonium chloride or methacryloyloxyethyl trimethyl ammonium chloride, the initiator is one or two of ammonium persulfate or potassium persulfate, and the crosslinking agent is one or two of N, N' -methylenebisacrylamide or PEGDA and the like.
Preferably, the stretchable conductive layer 3 is made of a conductive slurry which can be stretched after solidification, wherein the conductive slurry comprises silver flake/gallium alloy conductive particles 3-9, PEDOT: PSS conductive polymer 3-7, an amide monomer, quaternary ammonium salt chitosan-phenylboronic acid functional molecules 3-6, an initiator and a cross-linking agent.
Fig. 3 is a schematic diagram of a conductive interface layer of an epidermal hydrogel mixed electronic system for electromyography monitoring, wherein the stretchable conductive layer 3 contains PEDOT: PSS conductive polymer 3-7, quaternary ammonium salt chitosan-phenylboronic acid functional molecule (QCS-PBA) 3-6, polyacrylamide (PAAM) 3-8 and silver flake/gallium cause alloy conductive particles (SLM) 3-9, and the internal bonding mode comprises hydrogen bonds 12, electrostatic coupling effect 13, physical crosslinking 14 and covalent crosslinking 15. Wherein the hydrogel interface layer 1 contains polyvinyl alcohol chain (PVA) 1-1, alginate-catechol functional molecule (Alg-DA) 1-2 and polymethyl acryloyloxyethyl trimethyl ammonium chloride (PMTAC) 1-3, and the internal combination mode comprises hydrogen bond 12, electrostatic coupling effect 13, physical crosslinking 14 and covalent crosslinking 15.
Preferably, in the conductive slurry, the silver flake/gallium alloy conductive particles 3-9, PEDOT: PSS conductive polymer 3-7, amide monomer, quaternary ammonium salt chitosan-phenylboronic acid functional molecule 3-6, initiator and cross-linking agent account for 10-wt-15-wt%, 2-wt-8-wt%, 20-wt-30-wt%, 5-wt-15-wt%, 0.01-wt-0.05-wt% and 0.02-wt-0.1-wt% by mass respectively.
Preferably, the silver flake/gallium-based alloy conductive particles 3-9 are micron-sized, wherein the mass ratio of the silver flake to the gallium-based alloy is 0.2-1, the silver flake/gallium-based alloy conductive particles 3-9 are synthesized into microspheres through ultrasonic vibration, preferably, the amide monomer comprises acrylamide and/or an acrylamide derivative, the substitution degree of quaternary ammonium salt chitosan-phenylboronic acid functional molecule (QCS-PBA) 3-6 is more than 90%, the initiator is any one or more of alpha-ketoglutaric acid, irgacure2959, irgacure1173, ammonium persulfate and potassium persulfate, and the cross-linking agent is any one or more of N, N' -methylenebisacrylamide, PEGDA and the like.
As shown in fig. 5 and 6, in some preferred embodiments, the electrode set includes a stimulation electrode and a recording electrode;
the back-end wireless core main control module comprises a core processor module 6-1, an electric stimulation module 6-8, an electromyographic signal acquisition module and a wireless transmitting module;
the stimulating electrode is connected with the electric stimulating module 6-8 and induces nerves to generate action potential through pulse voltage signals applied by the electric stimulating module 6-8, the electromyogram signal acquisition module is connected with the recording electrode to realize real-time acquisition of electromyogram data, and the core processor module 6-1 is respectively connected with the electric stimulating module 6-8 and the electromyogram signal acquisition module and is used for inducing the electric stimulating module 6-8 to operate, store and process the electromyogram signal data and transmit the electromyogram signal data to an external terminal through the Wifi transmitting module 6-7.
In some preferred embodiments, the back-end wireless core main control module 6 further includes a lithium battery power supply module 6-3 and a voltage stabilizing module 6-2, where the lithium battery power supply module 6-3 and the voltage stabilizing module 6-2 are used to implement constant voltage supply of the back-end wireless core main control module 6.
In some preferred embodiments, the wireless core master control module 6 also includes an external terminal, which may be selected as a PC upper computer terminal 6-6.
Preferably, the back-end wireless core main control module 6 further comprises an hour hand crystal oscillator module 6-4 and a program downloading module 6-5, and the hour hand crystal oscillator module 6-4 and the program downloading module 6-5 are respectively connected with the core processor module 6-1.
In some preferred embodiments, the core processor module 6-1 selects an STM32F103 main control chip, the electromyographic signal acquisition module is an ADS1299 chip 6-9, the voltage stabilizing module 6-2 is a TPS61070DDCR voltage stabilizing module, and the wireless transmitting module is a Wifi transmitting module 6-7.
In some preferred embodiments, the stimulating electrodes include an electro-stimulating electrode anode 3-2 and an electro-stimulating electrode cathode 3-1, which are respectively connected to the electro-stimulating modules 6-8, and the recording electrode includes a collecting electrode 3-3, a reference electrode 3-4, and a ground electrode 3-5, which are respectively connected to the myoelectric signal collecting modules. The electric stimulation electrode anode 3-2 and the electric stimulation electrode cathode 3-1 are attached to the skin of a patient to be detected, pulse voltage signals are applied through the electric stimulation module 6-8 to induce nerves to generate action potentials, the collecting electrode 3-3, the reference electrode 3-4 and the ground electrode 3-5 are attached to corresponding nerve parts to be detected, the electromyogram collecting module is connected, real-time collection of the electromyogram is achieved, the core processor module 6-1 stores and analyzes collected signal data and then transmits the collected signal data to the Wifi transmitting module 6-7, the collected signal data are wirelessly transmitted to an external terminal, and various index data of the electromyogram are displayed in real time, so that on-line diagnosis of the electromyogram is achieved.
Preferably, the flexible substrate layer 4, the flexible packaging layer 2, the stretchable conducting layer 3 and the hydrogel interface layer 1 form a flexible collection front end, and the flexible collection front end is connected with the rear end wireless core main control module 6 through the flexible flat cable jack 5.
As shown in fig. 2, the epidermal hydrogel hybrid electronic system was prepared by the following method:
1) Preparing PDMS prepolymer 7 by mixing PDMS prepolymer and curing agent in a mass ratio of 10:1, spin-coating the PDMS prepolymer on a PMMA layer 8, and curing the PDMS prepolymer at 90 ℃ for one hour to obtain a flexible substrate layer 4;
2) Attaching a PVC mask layer 9 on the obtained flexible substrate layer 4 to realize electrode patterning, and configuring the mass ratio of ethanol to benzophenone to be 95:5, then dropwise adding the benzophenone solution 10 into the flexible substrate layer 4 for 5-20min;
3) Dissolving 10-15 mmol of quaternary ammonium salt chitosan in 60-100 ml of MES solution with pH of 5-6, degassing, fully mixing to obtain a uniform mixed solution, adding 1-5mmol of 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride and 1-5mmol of N-hydroxy thiosuccinimide, magnetically stirring, mixing and degassing, slowly dissolving 1-10mmol of 4-carboxyphenylboronic acid in the solution, sealing and fully stirring for 12 hours, dialyzing, freeze-drying to obtain quaternary ammonium salt chitosan-phenylboronic acid functional molecules (QCS-PBA) 3-6, dissolving silver flake/gallium-cause alloy conductive particles 3-9, PEDOT: PSS 3-7, amide monomers and the synthetic quaternary ammonium salt chitosan-phenylboronic acid functional molecules (QCS-PBA) 3-6, an initiator and a cross-linking agent in deionized water, stirring uniformly and degassing to obtain conductive slurry (SLM/APB conductive slurry); the conductive slurry is used as SLM/APB ink to be printed on the flexible substrate layer 4 in a patterning way, and is heated to 70 ℃ to be cured for 2 hours, so that a fully polymerized stretchable conductive layer 3 is obtained;
4) Spin-coating PDMS pre-polymer solution on the stretchable conducting layer 3, and curing for 1h at 90 ℃ to obtain a flexible packaging layer 2;
5) Dissolving polyvinyl alcohol chain (PVA) 1-1, alginate-catechol functional molecule (Alg-DA) 1-2, a polyamide monomer, ammonium chloride salt cationic monomer, an initiator and a cross-linking agent in deionized water, magnetically stirring until the initiator and the cross-linking agent are completely dissolved, and injecting the mixture into a circular electrode die for ultraviolet curing for 1h after degassing to obtain a hydrogel interface layer 1;
6) Diphenyl iodized chloride/phosphate buffer (DPI/PBS) 11 is dripped on the electrode group of the stretchable conducting layer 3, and the hydrogel interface layer is laminated for 10.5-1h, so that boric acid ester bonds are formed between phenylboric acid, polyvinyl alcohol and catechol groups to realize two-layer bonding.
In some preferred embodiments, the materials of the flexible substrate layer and the flexible packaging layer are Polydimethylsiloxane (PDMS), and the mass ratio of the prepolymer and the curing agent in the flexible substrate layer and the flexible packaging layer is 10:1, the curing temperature is 90 ℃ and the curing time is 1h. The diphenyl ketone solution is a mixed solution of ethanol and diphenyl ketone, wherein the mass ratio of the ethanol to the diphenyl ketone is 95:5.
preferably, the pH value of the Phosphate Buffer (PBS) in diphenyl iodized salt/phosphate buffer (DPI/PBS) is 7.5-10, and the mass fraction of the diphenyl iodized salt is 2-5 wt%.
As shown in fig. 7, the epidermal hydrogel hybrid electronic system monitors the patient median nerve motor branch electromyogram 22 of the median nerve and the normal person median nerve motor branch electromyogram 23, and diagnosis and monitoring of electromyogram are realized by comparing electromyogram related knowledge of latency, conduction speed, amplitude and the like.
The foregoing description of the preferred embodiments of the invention is not intended to limit the invention to the precise form disclosed, and any such modifications, equivalents, and alternatives falling within the spirit and scope of the invention are intended to be included within the scope of the invention.
Claims (10)
1. The skin hydrogel hybrid electronic system for electromyography monitoring is characterized by comprising a flexible frame main body, a stretchable conducting layer (3), a hydrogel interface layer (1) and a rear-end wireless core main control module (6), wherein the flexible frame main body is formed by jointly constructing a flexible substrate layer (4) and a flexible packaging layer (2), the stretchable conducting layer (3) is integrated with a wire and an electrode group, the stretchable conducting layer (3) is arranged in the flexible frame main body, the electrode group extends out of the flexible main body frame through a window on the flexible packaging layer (2), and the hydrogel interface layer (1) is arranged on the flexible packaging layer (2) and adhered to the electrode group for adhering to skin tissues; wherein,
the components of the hydrogel interface layer (1) comprise a polyvinyl alcohol chain (1-1), an alginate-catechol functional molecule (1-2), an amide monomer, an ammonium chloride salt cationic monomer, an initiator and a cross-linking agent, and the components are polymerized by ultraviolet initiation to form the hydrogel interface layer (1); the material of the stretchable conducting layer (3) contains quaternary ammonium salt chitosan-phenylboronic acid functional molecules (3-6), and diphenyl iodized salt/phosphate buffer solution (11) is dropwise added to the surface of the electrode group;
the electrode group is connected with the rear-end wireless core main control module (6) and is used for inducing nerves to generate action potential through pulse voltage signals applied by the rear-end wireless core main control module (6) and measuring electromyographic signals, and the rear-end wireless core main control module (6) receives data of the electrode group, analyzes and processes the received data and then wirelessly transmits the data to an external terminal.
2. The skin hydrogel mixed electronic system for electromyography monitoring according to claim 1, wherein in the hydrogel interface layer (1), polyvinyl alcohol chains (1-1), alginate-catechol functional molecules (1-2), amide monomers, ammonium chloride salt cationic monomers, initiators and crosslinking agents account for 5-wt-10 wt%, 2-wt-8 wt%, 15-wt-30 wt%, 10 wt-15 wt%, 0.01-wt-0.05 wt%, 0.02-wt-0.1 wt% respectively, and the balance being water.
3. The epidermal hydrogel mixed electronic system for electromyography monitoring according to claim 2, wherein the molecular weight of the polyvinyl alcohol chain (1-1) is 10000-750000, the molecular weight of alginate in the alginate-catechol (1-2) functional molecule is 7000-350000, the amide monomer is any one or more of acrylamide and acrylamide derivatives, the ammonium chloride salt cation monomer is acryloyloxyethyl trimethyl ammonium chloride or methacryloyloxyethyl trimethyl ammonium chloride, the initiator is one or two of ammonium persulfate or potassium persulfate, and the crosslinking agent is one or two of N, N' -methylenebisacrylamide or PEGDA and the like.
4. The epidermal hydrogel mixed electronic system for electromyography monitoring according to claim 1, wherein the stretchable conductive layer (3) is made of a conductive paste which is stretchable after curing and comprises silver flake/gallium alloy conductive particles (3-9), PEDOT: PSS conductive polymer (3-7), amide monomer, quaternary ammonium salt chitosan-phenylboronic acid functional molecule (3-6), initiator and cross-linking agent.
5. The skin hydrogel hybrid electronic system for electromyography monitoring according to claim 4, wherein the mass fractions of silver flake/gallium alloy conductive particles (3-9), PEDOT: PSS conductive polymer (3-7), amide monomer, quaternary ammonium salt chitosan-phenylboronic acid functional molecule (3-6), initiator and cross-linking agent in the conductive slurry are respectively 10 wt% -15 wt%, 2wt% -8 wt%, 20 wt% -30 wt%, 5wt% -15 wt%, 0.01 wt% -0.05 wt% and 0.02 wt% -0.1 wt%.
6. The skin hydrogel hybrid electronic system for electromyography monitoring of claim 5, wherein said silver flake/gallium-based alloy conductive particles (3-9) are of micron order, wherein the mass ratio of silver flake to gallium-based alloy is 0.2-1.
7. The epidermal hydrogel mixed electronic system for electromyography monitoring of any one of claims 1-6, wherein the electrode set comprises a stimulating electrode and a recording electrode;
the rear-end wireless core main control module (6) comprises a core processor module (6-1), an electric stimulation module (6-8), an electromyographic signal acquisition module and a wireless transmitting module;
the stimulating electrode is connected with the electric stimulating module (6-8) and induces nerve to generate action potential through pulse voltage signals applied by the electric stimulating module (6-8), the electromyographic signal acquisition module is connected with the recording electrode to realize real-time acquisition of electromyographic data, and the core processor module (6-1) is respectively connected with the electric stimulating module (6-8) and the electromyographic signal acquisition module and is used for inducing the electric stimulating module (6-8) to operate, store and process the electromyographic signal data and transmit the electromyographic signal data to an external terminal through the Wifi transmitting module (6-7).
8. The skin hydrogel hybrid electronic system for electromyography monitoring of claim 7, wherein the back-end wireless core main control module (6) further comprises a lithium battery power supply module (6-3) and a voltage stabilizing module (6-2), and the lithium battery power supply module (6-3) and the voltage stabilizing module (6-2) are used for realizing constant voltage supply of the back-end wireless core main control module (6).
9. The epidermal hydrogel mixed electronic system for electromyography monitoring of claim 7, wherein said epidermal hydrogel mixed electronic system is prepared by the following method:
s1, dissolving 10-15 mmol of quaternary ammonium salt chitosan in MES solution with the pH of 5-6, then degassing, fully mixing to obtain a uniform mixed solution, adding 1-5mmol of 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride and 1-5mmol of N-hydroxy thiosuccinimide, magnetically stirring, mixing and degassing;
s2, slowly dissolving 1-10mmol of 4-carboxyphenylboronic acid in the solution, sealing and fully stirring for 10-24 hours, dialyzing and freeze-drying to obtain a quaternary ammonium salt chitosan-phenylboronic acid functional molecule (3-6);
s3, dissolving silver flake/gallium alloy conductive particles (3-9), PEDOT: PSS conductive polymer (3-7), amide monomer, the quaternary ammonium salt chitosan-phenylboronic acid functional molecule (3-6), initiator and cross-linking agent in deionized water, uniformly stirring, and degassing to obtain conductive slurry;
s4, dropwise adding the benzophenone solution into the flexible substrate layer (4) for 5-20min, then patterning and printing the conductive slurry on the flexible substrate layer (4), heating and curing to obtain a fully polymerized stretchable conductive layer (3), and bonding a flexible packaging layer (2) on the stretchable conductive layer (3);
s5, dissolving a polyvinyl alcohol chain (1-1), an alginate-catechol functional molecule (1-2), a polyamide monomer, an ammonium chloride salt cationic monomer, an initiator and a crosslinking agent in deionized water, magnetically stirring until the polyvinyl alcohol chain is completely dissolved, and injecting the mixture into a circular electrode die for ultraviolet curing after the magnetic stirring is performed, so as to obtain a hydrogel interface layer (1);
s6, dropwise adding diphenyl iodized chloride/phosphate buffer solution onto the stretchable conductive layer (3), and laminating the hydrogel interface layer (1) for 0.5-1h to promote the formation of boric acid ester bonds between phenylboric acid, polyvinyl alcohol and catechol groups to realize two-layer bonding.
10. The epidermal hydrogel mixed electronic system for electromyography monitoring of any one of claims 1-6, wherein the pH of the diphenyl iodized salt/phosphate buffer is 7.5-10 and the mass fraction of diphenyl iodized salt is 2-5 wt%.
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| CN202311653181.3A CN117338306B (en) | 2023-12-05 | 2023-12-05 | Epidermal hydrogel hybrid electronic system for electromyography monitoring |
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| CN202311653181.3A CN117338306B (en) | 2023-12-05 | 2023-12-05 | Epidermal hydrogel hybrid electronic system for electromyography monitoring |
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Citations (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5800685A (en) * | 1996-10-28 | 1998-09-01 | Cardiotronics Systems, Inc. | Electrically conductive adhesive hydrogels |
| CN1376187A (en) * | 1999-07-30 | 2002-10-23 | 匹兹堡玻璃板工业俄亥俄股份有限公司 | Coating compositions having improved scratch resistance, coated substrates and methods related thereto |
| CN1377392A (en) * | 1999-07-30 | 2002-10-30 | 匹兹堡玻璃板工业俄亥俄股份有限公司 | Flexible coating compositions having improved scratch resistance, coated substrates and methods related thereto |
| JP2004271807A (en) * | 2003-03-07 | 2004-09-30 | Konica Minolta Holdings Inc | Photosensitive composition and planographic printing plate material, and method for processing planographic printing plate material and image forming method |
| US20060057191A1 (en) * | 2004-08-30 | 2006-03-16 | Southwest Research Institute | Biocidal fibrous and film materials utilizing silver ion |
| CN112515681A (en) * | 2020-12-11 | 2021-03-19 | 安徽医科大学 | Preparation method of ion-conductive hydrogel electrode and wearable electrocardio sensor using same |
| CN113057637A (en) * | 2021-03-08 | 2021-07-02 | 电子科技大学 | Hydrogel-based flexible bioelectrode array and manufacturing method thereof |
| CN115662680A (en) * | 2022-10-27 | 2023-01-31 | 华中科技大学 | Hydrogel for electric control viscosity electric stimulation electrode and preparation method and application thereof |
| CN116195991A (en) * | 2023-02-10 | 2023-06-02 | 华中科技大学 | Surface type movement state monitoring hybrid electronic system with interface viscosity light-controlled adjustable |
| CN116837639A (en) * | 2023-07-01 | 2023-10-03 | 中国人民解放军军事科学院防化研究院 | Strippable decontamination composite film capable of being rapidly solidified under sunlight and preparation method |
-
2023
- 2023-12-05 CN CN202311653181.3A patent/CN117338306B/en active Active
Patent Citations (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5800685A (en) * | 1996-10-28 | 1998-09-01 | Cardiotronics Systems, Inc. | Electrically conductive adhesive hydrogels |
| CN1376187A (en) * | 1999-07-30 | 2002-10-23 | 匹兹堡玻璃板工业俄亥俄股份有限公司 | Coating compositions having improved scratch resistance, coated substrates and methods related thereto |
| CN1377392A (en) * | 1999-07-30 | 2002-10-30 | 匹兹堡玻璃板工业俄亥俄股份有限公司 | Flexible coating compositions having improved scratch resistance, coated substrates and methods related thereto |
| JP2004271807A (en) * | 2003-03-07 | 2004-09-30 | Konica Minolta Holdings Inc | Photosensitive composition and planographic printing plate material, and method for processing planographic printing plate material and image forming method |
| US20060057191A1 (en) * | 2004-08-30 | 2006-03-16 | Southwest Research Institute | Biocidal fibrous and film materials utilizing silver ion |
| CN112515681A (en) * | 2020-12-11 | 2021-03-19 | 安徽医科大学 | Preparation method of ion-conductive hydrogel electrode and wearable electrocardio sensor using same |
| CN113057637A (en) * | 2021-03-08 | 2021-07-02 | 电子科技大学 | Hydrogel-based flexible bioelectrode array and manufacturing method thereof |
| CN115662680A (en) * | 2022-10-27 | 2023-01-31 | 华中科技大学 | Hydrogel for electric control viscosity electric stimulation electrode and preparation method and application thereof |
| CN116195991A (en) * | 2023-02-10 | 2023-06-02 | 华中科技大学 | Surface type movement state monitoring hybrid electronic system with interface viscosity light-controlled adjustable |
| CN116837639A (en) * | 2023-07-01 | 2023-10-03 | 中国人民解放军军事科学院防化研究院 | Strippable decontamination composite film capable of being rapidly solidified under sunlight and preparation method |
Non-Patent Citations (3)
| Title |
|---|
| CUI, NING，等: "A Tough Polysaccharide-Based Hydrogel with an On-Demand Dissolution Feature for Chronic Wound Care through Light-Induced Ultrafast Degradation", 《ACS APPLIED BIO MATERIALS》, vol. 3, no. 12, pages 8338 - 8343 * |
| YUCHEN ZHOU，等: "Biocompatible polysaccharide ionic hydrogel as ultra-stretchable and multifunctional wearable sensor", 《ELECTRONIC MATERIALS》, vol. 57, pages 16367 * |
| ZHANG, HD，等: "Dual-network polyacrylamide/carboxymethyl chitosan-grafted-polyaniline conductive hydrogels for wearable strain sensors", 《CARBOHYDRATE POLYMERS》, no. 1, pages 1 - 10 * |
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