Self-adhering electrodes with low skin contact impedance and uses thereof

Abstract

The application discloses a self-adhesive electrode with low skin contact impedance and application thereof, wherein the self-adhesive electrode comprises an electrode containing Ag / AgCl material, a conductive layer and a substrate. The conductive layer changes the contact characteristics of the hydrogel and the skin by adding nano-clay in the ion-conducting hydrogel system, so that the conductive layer and the skin are tightly coupled, thereby realizing the effects of long-time stable and low contact impedance and anti-interference. In addition, the conductive layer has good tensile strength and viscoelasticity, so that a wet electrode which realizes adhesion only by the conductive layer can be obtained without using common electrode auxiliary materials such as foam, non-woven fabric and pressure-sensitive adhesive. The electrode overcomes the defect that the contact impedance of the common electrode cannot be kept stable for a long time, and simplifies the fixing mode of the electrode, and can be used for continuous acquisition of physiological signals such as electroencephalogram, electrocardiogram and electromyogram, and has the advantages of stable contact impedance, simple structure, good water retention and good biocompatibility.

Description

TECHNICAL FIELD

[0001] The application belongs to the technical field of biological electrodes, and particularly relates to a self-adhesive electrode with low skin contact impedance and application thereof. BACKGROUND

[0002] Biological electrical signals are generated along with life activities in a biological body, such as electrocardiogram signals, electroencephalogram signals, electromyogram signals and the like. A biological electrode is a sensor for measuring biological electrical signals, and is widely applied in the fields of medical treatment, physiological research, neuroscience, human-computer interaction and the like. The biological electrical signals are very weak (mv, μV level), and the current biological electrode cannot guarantee the stability of the contact impedance between the electrode and the skin for a long time in use, thereby seriously affecting the signal quality.

[0003] The biological electrode uses Ag / AgCl electrodes and Cl - to generate electrochemical redox reactions to complete signal acquisition. The conductive paste can infiltrate the skin to ensure stable contact between the electrode and the skin. In addition, the Ag / AgCl electrode has a very stable half-cell potential, which together makes the electrode contact impedance low and stable. The Ag / AgCl electrochemical system is the most effective "gold standard" way to collect physiological electrical signals. However, the conductive paste has the disadvantages of being difficult to clean and inconvenient to use, so dry electrodes and gel wet electrodes are attracting more and more attention. Dry electrodes are composed of conductive materials such as metals and do not use conductive paste. They rely on capacitive coupling to collect electrical signals on the skin surface. Such electrodes have poor flexibility, are not tightly connected to the skin, and have unstable contact surfaces, resulting in high and unstable contact impedance. In order to reduce the contact impedance, dry electrodes increase the pressure to strengthen the tightness of the contact with the skin, such as using a bandage to wrap and fix, which is not comfortable for patients. Later, dry electrodes based on conductive flexible materials greatly improved the comfort and contact problems. For example, the patent with the patent number CN202080072889.8 discloses an application of a physiological electrode made of conductive substances PEDOT: PSS and water-based polyurethane. However, this electrode still uses the capacitive coupling collection method of dry electrodes, and the contact impedance is unstable and high. The commonly used patch-type gel wet electrode is composed of Ag / AgCl electrodes, ion-conducting hydrogel and pressure-sensitive adhesive. Due to the low strength and poor adhesion of the gel, the coupling between the hydrogel and the skin cannot be guaranteed, and the contact impedance is unstable. In addition, due to the low tensile strength and poor viscoelasticity of the gel, the electrode cannot be independently fixed on the skin, so a large area of pressure-sensitive adhesive needs to be added around the electrode to assist in fixing the electrode, which results in a larger electrode.

[0004] The self-adhesive electrode with low contact impedance is designed, which overcomes the defect that the contact impedance of the common electrode cannot be kept stable for a long time, simplifies the fixing mode of the electrode, and has the advantages of stable contact impedance, simple structure, good water retention, good biocompatibility and the like. SUMMARY

[0005] The first object of the present application is to provide a self-adhesive electrode with low skin contact impedance, which overcomes the defects of the prior art. The electrode is tightly coupled with the skin through the conductive layer, the contact impedance is stable and low for a long time, the signal is stable and not easy to be disturbed, and the pressure-sensitive adhesive does not need to be used for fixing.

[0006] The self-adhesive electrode with low skin contact impedance comprises an electrode containing Ag / AgCl material, a conductive layer and a substrate; one end of the conductive layer is connected with one end of the electrode containing Ag / AgCl material, and the other end is used for being tightly coupled with the skin; the other end of the electrode containing Ag / AgCl material is connected with one end of the substrate.

[0007] The solvent, monomer, crosslinking agent, nanoclay and sodium chloride are mixed uniformly and then refrigerated, and then the initiator and catalyst are added and stirred uniformly to prepare a prepolymer solution; the prepolymer solution is poured into a mold for polymerization molding to prepare the nanoclay hydrogel; wherein the monomer is acrylamide (AM), and the solvent is a mixed solution of deionized water and glycerol.

[0008] Preferably, the crosslinking agent is N,N'-methylene bisacrylamide (BIS), the nanoclay is Laponite XLS, the initiator is ammonium persulfate (APS), and the catalyst is N,N,N',N'-tetramethyl ethylenediamine (TEMED).

[0009] Preferably, the mass-volume ratio of the monomer, sodium chloride and crosslinking agent is (15-20) mg: 3 mg: 3 μL.

[0010] Preferably, the mass of the nanoclay accounts for 0.1-0.5% of the total mass of the prepolymer solution, and more preferably 0.5%.

[0011] Preferably, the refrigeration time is 25-35 min.

[0012] Preferably, the refrigeration temperature is 8-10°C.

[0013] Preferably, the volume ratio of the initiator, catalyst and crosslinking agent is (1-1.5): 1: 6.

[0014] Preferably, the polymerization molding time is 8-10 h.

[0015] As preferred, the temperature of polymerization molding is 35-45 DEG C.

[0016] As preferred, the substrate comprises an electrode male buckle, a non-woven fabric and a PET film, the non-woven fabric and the PET film are provided with a through hole in the center; the electrode comprising the Ag / AgCl material comprises a sheet-shaped assembly and a columnar assembly which are integrally formed and coated with Ag / AgCl material on the surface; one end of the columnar assembly is connected with one side of the sheet-shaped assembly, and the other end of the columnar assembly passes through the through hole of the non-woven fabric and the PET film and is embedded with the electrode male buckle; the sheet-shaped assembly is embedded in the conductive layer, and the non-woven fabric and the PET film are arranged on one side of the conductive layer; the non-woven fabric is in contact with the conductive layer, and the PET film is in contact with the electrode male buckle; the PET film is a polyethylene terephthalate film.

[0017] The second object of the present application is to provide the use of the above-mentioned self-adhesive electrode with low skin contact impedance in collecting bioelectric signals.

[0018] As preferred, the bioelectric signals comprise electrocardiogram and electroencephalogram.

[0019] Compared with the prior art, the present application has the following beneficial effects:

[0020] (1) The electrode of the present application can realize long-time stable and low contact impedance and anti-interference effect; the present application adds nano-clay in the conductive layer, changes the contact characteristics of the hydrogel and the skin, and improves the mechanical properties of the conductive layer, so that it can be firmly and closely attached to the skin, thereby realizing the close coupling with the skin, and still maintaining the original contact state of the conductive layer and the skin under the interference of shaking, moving and the like, so that the impedance value of the electrode can be stably kept at a low level for a long time, and therefore the electrode can also collect physiological electrical signals stably under certain motion conditions, without being disturbed like the electrode fixed by pressure-sensitive adhesive.

[0021] (2) The electrode of the present application has self-adhesion performance, and the conductive layer has good tensile strength and viscoelasticity, so that the electrode can be firmly adhered to the skin only by relying on the conductive layer, and therefore it is not necessary to use common electrode auxiliary materials such as foam, non-woven fabric and pressure-sensitive adhesive, thereby avoiding the skin inflammation caused by the use of pressure-sensitive adhesive, the negative effect of large-area skin occupation, and the damage to the skin after peeling, and improving the use comfort and biocompatibility.

[0022] (3) The electrode of the present application is assembled and embedded with non-woven fabric, PET film, electrode male buckle and electrode containing Ag / AgCl material, then put into the mold, then pour the prepolymer liquid into the self-made mold, the prepolymer liquid contacts the electrode containing Ag / AgCl material and non-woven fabric at the same time, then infiltrates the non-woven fabric, and the conductive layer and the non-woven fabric are combined tightly after polymerization, so as to prevent the two from separating and affecting the signal quality.

[0023] (4) The electrode of the present application has good water retention performance. On the one hand, the hydrogel and the nanoclay improve the mechanical strength and improve the water retention capacity; on the other hand, the addition of glycerol further improves the water retention capacity.

[0024] (5) The electrode of the present application adopts the principle of wet electrode collection, the hydrogel is used as the connecting medium of the electrode containing Ag / AgCl material and the skin, and the charge is transmitted through the oxidation-reduction reaction of the salt in the hydrogel and Ag / AgCl. BRIEF DESCRIPTION OF DRAWINGS

[0025] Figure 1 It is a structure diagram of a self-adhesive electrode with low skin contact impedance.

[0026] Figure 2 It is a forming mold diagram of a self-adhesive electrode with low skin contact impedance.

[0027] Figure 3 It is a tensile test result diagram of the nanoclay hydrogel prepared in Example 1.

[0028] Figure 4 It is a comparison of the tensile properties of the self-adhesive electrode with low skin contact impedance under different nanoclay contents.

[0029] Figure 5 It is a viscosity test result diagram of the nanoclay hydrogel prepared in Example 1.

[0030] Figure 6 It is a comparison of the adhesion properties of the self-adhesive electrode with low skin contact impedance under different nanoclay contents.

[0031] Figure 7 It is a nanoclay hydrogel electrode impedance test result diagram.

[0032] Figure 8 It is a comparison of the adhesion properties of the self-adhesive electrode with low skin contact impedance under different nanoclay contents.

[0033] Figure 9 It is a signal diagram of the self-adhesive electrode with low skin contact impedance collecting brain electricity.

[0034] Figure 10Power spectrum of electroencephalogram collected by self-adhesive electrode with low skin contact impedance.

[0035] Figure 11 Comparison of results of electrocardiogram collected by self-adhesive electrode with low skin contact impedance and comparative electrode under motion interference, wherein (a) is the result of envelope processing of electrocardiogram signal obtained by using electrode of the present application, and (b) is the result of envelope processing of electrocardiogram signal obtained by using comparative electrode.

[0036] Embodiment

[0037] The present application will be described in detail below in conjunction with the accompanying drawings and embodiments.

[0038] As described above, in view of the deficiencies of the prior art, the present inventors have long studied and practiced a lot and proposed the technical solution of the present application, which is mainly based on at least comprising:

[0039] The present application discloses a self-adhesive electrode with low skin contact impedance, which can realize stable and low contact impedance for a long time. The present application adds nano-clay in the conductive layer to improve the mechanical properties of the conductive layer, so that it can maintain the original contact state even if it is deformed under the condition of firm and close adhesion with the skin, thereby realizing the close coupling with the skin, so that the impedance value of the electrode can be stably kept at a low level for a long time, thereby realizing the anti-interference effect. At the same time, the electrode of the present application has self-adhesive performance, and does not need common auxiliary fixing methods such as pressure-sensitive adhesive, thereby improving the use comfort and biocompatibility.

[0040] The present application discloses a self-adhesive electrode with low skin contact impedance, which comprises an electrode 1 containing Ag / AgCl material, a conductive layer 2 and a substrate 3. One end of the conductive layer 2 is connected with one end of the electrode 1 containing Ag / AgCl material, and the other end is used for close coupling with the skin. The other end of the electrode 1 containing Ag / AgCl material is connected with one end of the substrate 3. The substrate 3 comprises an electrode male buckle, a non-woven fabric and a PET film, and the non-woven fabric and the PET film are provided with through holes in the center. The electrode containing Ag / AgCl material comprises an integrally formed sheet-shaped component and a columnar component, and the surface is coated with Ag / AgCl material. One end of the columnar component is connected with one side of the sheet-shaped component, and the other end of the columnar component passes through the through holes of the non-woven fabric and the PET film and is embedded with the electrode male buckle. The sheet-shaped component is embedded in the conductive layer 2, and the non-woven fabric and the PET film are arranged on one side of the conductive layer 2. The non-woven fabric is in contact with the conductive layer 2, and the PET film is in contact with the electrode male buckle.

[0041] The material of the conductive layer 2 is nano-clay hydrogel, which is prepared by the following steps:

[0042] The solvent, acrylamide AM, N,N'-methylene bisacrylamide BIS, nanoclay Laponite XLS and sodium chloride are mixed uniformly, and then refrigerated at 8-10 DEG C for 25-35 min, and then ammonium persulfate APS and catalyst N,N,N',N'-tetramethyl diethylamine TEMED are added and stirred uniformly to prepare a prepolymer solution; the mass-volume ratio of AM, sodium chloride and BIS is (15-20) mg:3 mg:3 μL, the volume ratio of APS, TEMED and BIS is (1-1.5):1:6, and the mass of the nanoclay is 1-5 mg; the prepolymer solution is poured into a mold and polymerized at 35-45 DEG C for 8-10 h to prepare the nanoclay hydrogel; wherein the solvent is a mixed solution of ionized water and glycerol.

[0043] The electrode provided by the application is used by directly sticking one end of the conductive layer not in contact with the Ag / AgCl electrode to the skin, and then fixing the GND electrode and the Ref electrode at corresponding positions to start collecting signals; during use, the electrode of the application relies on the close coupling of the conductive layer and the skin, and can stably collect signals without using pressure-sensitive adhesive, and can maintain stable low skin contact impedance for a long time.

[0044] Hereinafter, only certain exemplary embodiments are simply described. As those skilled in the art can recognize, the described embodiments can be modified in various different ways without departing from the spirit or scope of the embodiments of the application. Therefore, the drawings and the description are considered to be exemplary in nature rather than limiting.

[0045] Acrylamide (AM) was purchased from Shanghai McLean Biotech Co., Ltd., N,N'-methylene bisacrylamide (BIS) was purchased from Aladdin Reagent (Shanghai) Co., Ltd., deionized water, ammonium persulfate (APS) and tetramethyl ethylenediamine (TEMED) were purchased from Sigma-Aldrich (Shanghai) Trading Co., Ltd., sodium chloride was purchased from Jiangsu Qiangsheng Functional Chemical Co., Ltd., glycerol (glycerol) was purchased from National Pharmaceutical Group Chemical Reagent Co., Ltd., nanoclay (Laponite XLS) was purchased from Byk Chemical (Shanghai) Co., Ltd.; the contrast electrode was purchased from Shanghai LiTu Medical Instrument Co., Ltd.

[0046] The embodiments of the application will be described in detail below with reference to the accompanying drawings.

[0047] Example 1: Preparation of nanoclay hydrogel

[0048] Into a centrifuge tube were added 200 mg acrylamide, 30 mg sodium chloride, 5 mg nanoclay, 370 μL deionized water and 450 μL glycerol and stirred well to dissolve; then 30 μL N,N'-methylenebisacrylamide was added for crosslinking, and the solution was cooled in a refrigerator (8°C) for 30 minutes. Finally, 5 μL N,N,N',N'-tetramethyl ethylenediamine was added as a catalyst, and 5 μL ammonium persulfate in deionized water at a concentration of 4% was added as an initiator to prepare a nanoclay hydrogel pre-polymer solution; the pre-polymer solution was then quickly poured into the prepared mold, and the mold was placed in a sealed bag and allowed to stand at 40°C for 8 hours to obtain a nanoclay hydrogel.

[0049] Test 1: Test the mechanical properties of the nanoclay hydrogel

[0050] Test the tensile properties of the nanoclay hydrogel: The mechanical properties of the hydrogel were tested using a high modulus fiber strength tester model XS(08)XG from Shanghai Xusai Instrument Co., Ltd. The nanoclay hydrogel (10 mm x 7 mm x 1 mm) was placed in the tensile clamp and tested for tensile properties at a speed of 10 mm / min. The results are shown in Figure 3 , which show that the maximum tensile strength is about 93 kPa and the elongation at break is more than 1300%.

[0051] Test the shear properties of the nanoclay hydrogel: The nanoclay hydrogel (16 mm x 12 mm x 1 mm) was loaded on a glass substrate at a speed of 10 mm / min until the lap shear sample separated using a tensile testing machine by lap shear method. The maximum shear force was 17 kPa.

[0052] Test the tackiness of the nanoclay hydrogel: The results are shown in Figure 5 .

[0053] Test 2: Test the impedance of the electrode pair

[0054] (1) The nanoclay hydrogel pre-polymer solution in Example 1 was used to make a nanoclay hydrogel with a diameter of 16 mm and a thickness of 1.5 mm.

[0055] (2) Two nanoclay hydrogel electrodes from Test 1 were used to form an electrode pair by gluing the electrodes together. The working electrode was connected to the male buckle of one electrode, and the reference electrode was connected to the female buckle of the other electrode. The impedance of the electrode pair was measured using a two-electrode system.

[0056] Figure 7 is the test result, which shows that the impedance at 10 Hz is 116 Ω (less than 250 Ω), meeting the low impedance requirement.

[0057] Test 3: Test the electrode-skin impedance:

[0058] (1) The gel of the contrast electrode was removed to obtain the contrast electrode substrate as a mold, and the nanoclay hydrogel prepolymer solution in Example 1 was added, and after gelation, a nanoclay hydrogel electrode was prepared as a working electrode; the contrast electrode was used as a reference electrode and a counter electrode; the three electrodes were sequentially attached to the arm, and the impedance value at 10 Hz was tested. Continuous measurement for 6 hours, once every hour, and the electrode was not removed during the measurement.

[0059] (2) The contrast electrode was used as a working electrode, reference electrode and counter electrode, and the test was carried out in the same way.

[0060] This method perfectly restores the use scene of the contrast electrode gel and is very suitable for comparison. Figure 8 The results are shown in the table below, it can be seen that the impedance value of the electrode using nanoclay hydrogel is lower than that of the contrast electrode, and the impedance remains stable within 6 hours.

[0061] Application Example 1

[0062] Step one, preparation of a self-adhesive electrode with low skin contact impedance

[0063] (1) Electrode substrate preparation: a non-woven fabric and a PET film with a central hole were cut by a laser cutting machine, the release paper on one side of the non-woven fabric was torn off, and was attached to the PET film. The cylindrical assembly containing the Ag / AgCl material electrode was inserted through the central hole between the non-woven fabric and the PET film, and was embedded with a male buckle.

[0064] (2) The substrate combined with the electrode containing the Ag / AgCl material was placed in a mold as shown in Figure 2 , the sheet-shaped assembly containing the Ag / AgCl material was on the upper side, the nanoclay hydrogel prepolymer solution prepared in Example 1 was added, and was placed in a sealed bag. After waiting for 8-10 hours, the self-adhesive electrode with low skin contact impedance was completed, and the structure is shown in Figure 1 .

[0065] Step two, use of the above self-adhesive electrode with low skin contact impedance to collect and process electroencephalogram

[0066] According to the 10-20 international standard lead system, the self-adhesive electrode with low skin contact impedance was attached to the FP1 position, and the Ref electrode and the GND electrode were placed behind the ear. The collection process is divided into two parts, open eyes and closed eyes. The collection device is Olympic CFM6000, and the collected electroencephalogram signal is preprocessed as shown in Figure 9 , D1 is the electroencephalogram when the eyes are open, and D2 is the electroencephalogram when the eyes are closed. Signal preprocessing is to process the data using MATLAB, including removing the baseline and band-pass filtering (0.5 Hz-45 Hz). The signal change of blinking and closing the eyes can be clearly seen. Figure 10is the power spectrum of the signal in the two processes of eyes open and eyes closed, and it can be seen that there is a peak at 10 Hz during eyes closed, which represents the alpha wave (the frequency range of the alpha wave is 8-13 Hz) in the brain electricity.

[0067] Electrophysiological signals mainly include electroencephalogram, electrocardiogram and electromyogram. Among them, the electroencephalogram has the lowest amplitude (μV level) and is most susceptible to noise interference, and the electrocardiogram and electromyogram (mv level) are relatively easy to obtain compared with the electroencephalogram.

[0068] Application Example 2

[0069] Step one, preparation of self-adhesive electrode with low skin contact impedance

[0070] (1) Preparation of electrode substrate: the non-woven fabric and PET film with a central through hole are cut by a laser cutting machine, the release paper on one side of the non-woven fabric is torn off, and the non-woven fabric is pasted on the PET film. The cylindrical assembly containing the Ag / AgCl material electrode is inserted through the central hole between the non-woven fabric and the PET film, and is embedded with the male buckle.

[0071] (2) Place the substrate combined with the electrode containing the Ag / AgCl material in the mold as shown in Figure 2 , with the electrode sheet assembly containing the Ag / AgCl material on the upper side, add the nanoclay hydrogel prepolymer solution prepared in Example 1, put it into a sealed bag, and wait for 8-10 hours. The self-adhesive electrode with low skin contact impedance is completed, and the structure is as shown in Figure 1 .

[0072] Step two, collection of electrocardiogram using the above self-adhesive electrode with low skin contact impedance

[0073] The self-adhesive electrode with low skin contact impedance is pasted on the inside of the right wrist, and the GND electrode and the Ref electrode are placed on the back of the left wrist and the back of the hand, respectively, using a contrast electrode. The subject operates according to the command: keeps still (T1 stage), bends the arm at 0.1 Hz (T2 stage), keeps still (T3 stage), and bends the arm at 0.2 Hz (T4 stage). Bending the arm means that the left arm is placed flat on the table, and the right arm is bent 90° according to the direction of the subject, then put it down, and the left arm is always stationary. Bending and putting down is one cycle. The obtained electrocardiogram signal is envelope processed, and the obtained result is as shown in Figure 11 (a). It can be seen that the signal amplitude obtained using the self-adhesive electrode with low skin contact impedance remains stable in the four stages and is not easily disturbed by movement.

[0074] Step three, collection of electrocardiogram using a contrast electrode

[0075] The contrast electrode is used instead of the self-adhesive electrode with low skin contact impedance, and the remaining steps remain the same as Step two. The obtained result is as shown in Figure 11(b) As shown, the amplitude difference is very large in the stage of static and bending arm, so the disturbance caused by motion is very serious.

[0076] Comparative Example 1

[0077] The content of nanoclay in Example 1 was set to 0, 0.2%, 0.4%, 0.5%, 0.6%, 0.8% and 1.0% respectively, and the rest of the conditions were unchanged, to prepare electrodes with different nanoclay contents. The elongation at break and tensile strength were tested, and the results are shown in Figure 4

[0078] Comparative Example 2

[0079] The content of nanoclay in Example 1 was set to 0, 0.1%, 0.2%, 0.5%, 0.6% and 1.0% respectively, and the rest of the conditions were unchanged, to prepare electrodes with different nanoclay contents. The maximum adhesion was tested, and the results are shown in Figure 6 .​

Claims

1. A self-adhesive electrode with low skin contact resistance, the self-adhesive electrode with low skin contact resistance comprising an electrode containing Ag / AgCl material, a conductive layer, and a substrate; one end of the conductive layer is connected to one end of the electrode containing Ag / AgCl material, and the other end is used for tight coupling with the skin; the other end of the electrode containing Ag / AgCl material is connected to one end of the substrate; Its features are, The conductive layer is made of nano-clay hydrogel, which is prepared using the following steps: The monomer, solvent, crosslinking agent, nanoclay, and sodium chloride were mixed evenly and refrigerated. Then, an initiator and catalyst were added and stirred evenly to obtain a prepolymer solution. The prepolymer solution was poured into a mold and polymerized to obtain the nanoclay hydrogel. The monomer was acrylamide AM, the solvent was a mixed solution of deionized water and glycerol, the crosslinking agent was N,N'-methylenebisacrylamide BIS, the nanoclay was Laponite XLS, the initiator was ammonium persulfate APS, and the catalyst was N,N,N',N'-tetramethyldiethylamine TEMED.

2. The self-adhesive electrode with low skin contact resistance according to claim 1, characterized in that, The mass-volume ratio of the monomer, sodium chloride, and crosslinking agent is (15-20) mg: 3 mg: 3 μL.

3. The self-adhesive electrode with low skin contact resistance according to claim 1, characterized in that, The nano-clay is 0.1% to 0.5% of the mass ratio.

4. The self-adhesive electrode with low skin contact resistance according to claim 1, characterized in that, The volume ratio of initiator, catalyst and crosslinking agent is (1-1.5):1:

6.

5. The self-adhesive electrode with low skin contact resistance according to claim 1, characterized in that, The refrigeration time is 25–35 minutes, and the refrigeration temperature is 8–10℃.

6. The self-adhesive electrode with low skin contact resistance according to claim 1, characterized in that, The polymerization time is 8-10 hours, and the polymerization temperature is 35-45℃.

7. The self-adhesive electrode with low skin contact resistance according to claim 1, characterized in that, The substrate includes an electrode male fastener, a nonwoven fabric, and a PET film, with through holes in the center of the nonwoven fabric and PET film. The electrode containing Ag / AgCl material includes an integrally formed sheet component and a columnar component, with Ag / AgCl material covering the surface. One end of the columnar component is connected to one side of the sheet component, and the other end of the columnar component passes through the through hole in the nonwoven fabric and PET film and engages with the electrode male fastener. The sheet component is embedded in the conductive layer, and the nonwoven fabric and PET film are disposed on one side of the conductive layer. The nonwoven fabric is in contact with the conductive layer, and the PET film is in contact with the electrode male fastener.

8. The application of the self-adhesive electrode with low skin contact resistance as described in any one of claims 1-7 as an EEG electrode.

9. The application of the self-adhesive electrode with low skin contact resistance as described in any one of claims 1-7 as an electrocardiogram electrode.

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