Anti-sticky electrocardiogram electrode patch and its use method

Abstract

The present invention relates to a brain electrocardiogram electrode patch that prevents sticking and a method of using the patch, and relates to the field of medical detection equipment. The patch includes: a base film, a circuit layer formed on the base film, an elastic adhesive sheet arranged on the electrode area of ​​the base film, and a hydrogel annular diffusion mechanism. The circuit layer includes an electrode located on the electrode area and a connecting lead connected to the corresponding electrode; the elastic adhesive sheet has a through hole aligned with the electrode, and the space in the through hole is used to fill the hydrogel so that the electrode connected to the hydrogel can sense brain electrocardiogram signals or electrocardiogram signals; the hydrogel annular diffusion mechanism is arranged on the electrode and located in the through hole, and is used to divide the through hole from the center to the outside into a ring core glue contact area, a ring middle glue diffusion area, and a ring outer glue storage area. The present invention has the effect of preventing the hydrogel from locally agglomerating and overflowing to the adhesive surface when in use, and solves the problem of whether the brain electrocardiogram electrode patch is sticky when in use.

Description

Technical Field

[0001] The present invention relates to the technical field of brain electrocardiogram signal measurement, and in particular to a non-stick brain electrocardiogram electrode patch and a use method thereof. Background Art

[0002] The collection of brain ECG signals is an indicator used to determine whether a certain function of a person is healthy. Brain ECG measurement equipment uses brain ECG sensors as consumable interface devices that contact human skin. For a long time, the brain ECG electrode patches, which are the main components of brain ECG sensors, have had the problem of whether they stick to human skin. The reasons are analyzed as follows: when the pressure applied during patch sticking is too large or uneven, the hydrogel overflows and diffuses to the sticking surface, resulting in a decrease in adhesion. When the human body's sticking part rotates, moves, shakes, is pressed or sweats, gaps are generated at the patch sticking point, and the hydrogel further overflows, resulting in distortion of the collection of brain ECG signals. When it is found that the adhesion is insufficient, a new brain ECG electrode patch needs to be replaced, and the cost of consumables increases.

[0003] Invention patent application publication number CN101199418A discloses a brain electrical impedance detection circuit and a brain electrical detection device. The brain electrical impedance detection circuit includes an excitation unit and a detection unit. The excitation unit includes a constant current source and a grounding resistor. The current output by the constant current source forms a current loop after passing through the lead and the grounding resistor; the detection unit includes a bandpass filter circuit, a multi-way switch, a first amplifier circuit, a demodulation circuit and a controller. The bandpass filter circuit filters the brain electrical signal. The controller controls the multi-way switch to switch the brain electrical signals output by the bandpass filter circuit to the first amplifier circuit in turn according to the set timing. The filtered brain electrical signal is amplified by the first amplifier circuit and then output to the demodulation circuit. After demodulation, the brain electrical impedance value is output. This prior art patent discloses a circuit structure of a brain electrical signal measurement device.

[0004] Invention patent application publication number CN105193411A discloses an EEG electrode sensor, including a thin film PCB circuit layer, an adhesive layer, a stylus layer and a conductive hydrogel, one end of the thin film PCB circuit layer is a plug port, the other end of the thin film PCB circuit layer is provided with four electrode cores, the adhesive layer is arranged on the thin film PCB circuit layer, and four through holes are provided at the position where the adhesive layer is opposite to the electrode core, the size of the through holes matches the electrode core, the size of the stylus layer and the conductive hydrogel matches the through holes and are arranged on the electrode core from bottom to top in sequence. The size of the stylus layer and the conductive hydrogel matches the through holes and are arranged on the electrode core in sequence from bottom to top. Since the stylus design of the stylus layer will greatly increase the cost of consumable materials, the EEG electrode patches currently used in the prior art generally do not use a stylus structure. Under pressure attachment, the conductive hydrogel easily overflows to the adhesive surface of the adhesive layer in a specific direction, resulting in a decrease in the bonding force of the adhesive layer. In addition, in order to avoid the sticky or non-sticky phenomenon that causes poor conductive hydrogel connection, the thickness of the existing adhesion layer is about 0.2 cm, and the through-hole is deepened to increase the filling amount of conductive hydrogel to solve the early poor contact of the conductive hydrogel during use, which relatively increases the possibility of conductive hydrogel overflowing from the through-hole, and the sticky or non-sticky problem during use cannot be effectively solved. The increase in the use of conductive hydrogel exacerbates the slippage of the attachment surface relative to the contact part of the human body, and also increases the cost of the EEG electrode sensor as a consumable material.

[0005] Invention patent application publication number CN107638176A discloses an application of a hydrogel in the preparation of an electrode for detecting cerebral cortical electrograms, and a cerebral cortical electrogram acquisition technology using a gel with low conductivity as an electrode. The gel achieves conductivity through its free ions in the brain fluid environment, and the directional movement of the ions forms an electric current, achieving a detection effect comparable to that of highly conductive materials. The hydrogel is a biocompatible hydrogel with an elastic modulus of less than 100MPa. This prior art patent opens up the use of low-conductivity hydrogels in EEG electrode sensors. Whether it is a high-conductivity or low-conductivity hydrogel, it is in a colloidal state, and the various amorphous shapes of the electrodes of the EEG electrode patch in contact with the human body are easily squeezed and overflowed.

[0006] The applicant disclosed an EEG electrode patch and its preparation method and EEG sensor in the invention patent application publication number CN110859618A. The patch includes: an insulating film, a plurality of lead wires printed on the inner surface of the film, a plurality of contact electrodes printed on the outer surface of the film and an anti-interference film attached to the inner surface, the insulating film has a via, and the second contact area of ​​the insulating film is far away from the lead-out area relative to the first contact area; the inner electrodes of the lead wires are dispersed in the first contact area and the second contact area, and the lead-out electrodes of the lead wires are concentrated in the lead-out area; the contact electrodes are located in the first contact area and the second contact area, and are electrically connected to the corresponding inner electrodes through the vias; a signal shielding structure is provided on the anti-interference film, covering the line segment of the lead wire, for achieving multiple anti-interference effects. Hydrogel is still used between the contact electrode and the human body contact area. Summary of the invention

[0007] The main purpose of the present invention is to provide a brain electrocardiogram electrode patch, and the main improvement is to solve the problem of whether the brain electrocardiogram electrode patch is sticky when used.

[0008] The second main purpose of the present invention is to provide a brain electrocardiogram sensor including the brain electrocardiogram electrode patch, which is used to prevent the hydrogel from agglomerating and overflowing onto the local bonding surface, or / and to reduce the amount of hydrogel filling in the through-holes.

[0009] The third main purpose of the present invention is to provide a method for using a brain electrocardiogram electrode patch to reduce the shedding of the elastic adhesive sheet, so as to achieve accurate collection of brain electrocardiogram signals.

[0010] The main purpose of the present invention is achieved through the following technical solutions:

[0011] A brain electrocardiogram electrode patch is proposed, comprising:

[0012] A base film having a functional surface, wherein the functional surface includes a plurality of electrode areas, a first lead area, a second lead area and an external connection area, wherein the first lead area connects the electrode areas, and the second lead area connects one of the electrode areas and the external connection area;

[0013] A circuit layer is formed on the functional surface of the base film, the circuit layer includes a plurality of electrodes located on the electrode area and a plurality of connecting leads connected to the corresponding electrodes, the connecting leads are located on the first lead area and gathered in the second lead area;

[0014] An elastic adhesive sheet is disposed on the electrode area and is used to adhere to human skin. The elastic adhesive sheet has a through hole aligned with the electrode. The space in the through hole is used to fill with hydrogel so that the electrode connected to the hydrogel can sense brain signals or electrocardiogram signals.

[0015] The hydrogel annular dispersion mechanism is arranged on the electrode and located in the through hole, and is used to divide the through hole from the center to the outside into a ring core gel contact area, a ring middle gel dispersion area, and a ring outer gel storage area.

[0016] By adopting the above technical solution, the hydrogel annular dispersion mechanism is used to divide the through hole of the elastic adhesive sheet into a ring core glue contact area, a ring middle glue scattered area, and a ring outer glue containing area. The hydrogel predetermined to be filled in the through hole can be concentrated in the ring core glue contact area. When subjected to pressure and extrusion, the hydrogel is dispersed in the ring middle glue scattered area and will not overflow in a certain direction. The hydrogel can expand evenly in the ring outer glue containing area, and after the pressure is finished, it will evenly flow back to the ring core glue contact area through the ring middle glue scattered area in a circular manner. Therefore, the squeezed hydrogel will not overflow and diffuse to the adhesive surface of the elastic adhesive sheet, solving the problem of whether the brain ECG electrode patch is sticky in the prior art.

[0017] The present invention can be further configured as follows in a preferred example: the hydrogel annular diffusion mechanism comprises a circular ring sheet fixed to the electrode and a diffusion rod arranged on the annular surface of the circular ring sheet, wherein the diffusion rod specifically comprises a gripping rod with a barb and a contact rod with a straight upward contact end;

[0018] Preferably, the annular sheet, the grab bar and the touch bar are an integral part formed by injection molding;

[0019] Specifically, the annular sheet is adhered to the electrode in a manner that the hollow circle is aligned with the center point of the electrode.

[0020] By adopting the above preferred technical features and utilizing the specific structure of the hydrogel annular diffusion mechanism, the bottom surface of the annular sheet can be fixed to the electrode, and a plurality of diffusion rods can be set on the top surface of the annular sheet. The center of the annular sheet can be used for the hydrogel to pass through and conduct the center point of the electrode. The function of the diffusion rod is to disperse and divert the hydrogel that overflows from the contact area of ​​the annular core glue under pressure in the diffusion area in the ring, overflow to the outer glue area in a relatively uniform manner, and then expand evenly. In the preferred embodiment, the grabbing rod with a barb specifically included in the diffusion rod is also used to grasp the hydrogel adsorbent to prevent a large amount of hydrogel from being taken out when adjusting the sensing position, and the contact rod with a straight upper contact end specifically included in the diffusion rod is also used to contact the human body contact area under excessive pressure to prevent the depth of the through hole from being excessively squeezed. In the preferred embodiment, the one-piece formed by injection molding can greatly reduce the production cost of the hydrogel annular diffusion mechanism, and even if the hydrogel annular diffusion mechanism is non-conductive, it does not affect the conduction between the hydrogel and the electrode in the contact area of ​​the annular core glue. In the preferred embodiment, the hollow circle of the annular sheet is aligned with the center point of the electrode to fix the hydrogel annular diffusion mechanism, so that the outer gel-containing area of ​​the through hole has a consistent width after fixation, and the hydrogel that flows back from the outside of the ring to the center of the ring after being compressed also has a consistent filling amount.

[0021] In a preferred example, the present invention can be further configured as follows: the brain electrocardiogram electrode patch also includes: a hydrogel adsorbent, which is arranged in the through hole of the elastic adhesive sheet, and the grabbing rod and the feeling rod penetrate into the hydrogel adsorbent.

[0022] By adopting the above preferred technical features, using the hydrogel adsorbent in the through hole and the grabbing rod and the touch rod piercing the hydrogel adsorbent, it is avoided that a large amount of hydrogel is taken out and lost when adjusting the human brain electrocardiogram measurement position.

[0023] In a preferred example, the present invention can be further configured as follows: the height of the grab rod and the touch rod is below the adhesive surface of the elastic adhesive sheet; specifically, before the brain electrocardiogram electrode patch is used, the adhesive surface of the elastic adhesive sheet is covered with a sticker protective film.

[0024] By adopting the above preferred technical features, the height limit of the grab bar and the touch bar is utilized to effectively disperse the overflowed hydrogel, and most of the hydrogel is retained in the through hole and below the adhesive surface of the elastic adhesive sheet. In a specific solution, a sticker protective film is used to cover the adhesive surface of the patch before use to protect the adhesiveness of the adhesive surface from changing.

[0025] In a preferred example, the present invention can be further configured as follows: the conductive area of ​​the electrode is determined by the through hole of the elastic adhesive sheet, and the conductive area of ​​the electrode is divided into a central pad and an outer ring pad surrounding the central pad according to the area occupied by the hydrogel annular diffusion mechanism.

[0026] By adopting the above-mentioned preferred technical features and utilizing the area determination method of the electrode, the contact pad is determined by the elastic adhesive sheet and the hydrogel annular dispersion mechanism. The electrode has a central pad and an outer ring pad surrounding the central pad. Both the central pad and the outer ring pad can be used to conduct the hydrogel and collect brain and electrocardiogram signals to avoid the hydrogel's empty connection and disconnection. Usually, the bottom of the hydrogel has a priority conduction effect on the electrode at the central pad, and the top of the hydrogel has a priority conduction effect on the human body contact area above the outer ring pad.

[0027] The present invention can be further configured in a preferred example as follows: the outer contour of the elastic adhesive sheet is substantially the same as the outer contour of the corresponding electrode area, the elastic adhesive sheet also has a reinforcement portion extending to the first lead area connected to the corresponding electrode area; the elastic adhesive sheet includes a foam layer with a thickness of less than 0.1 cm, the basic shape of the through hole is circular, and a glue-containing notch is formed around the through hole;

[0028] Specifically, the thickness of the elastic adhesive sheet is between 0.03 and 0.1 cm, more specifically between 0.05 and 0.075 cm;

[0029] Preferably, the adhesive-containing notches are arranged symmetrically, and one of the adhesive-containing notches corresponding to each electrode region faces the first lead region connected to the corresponding electrode region.

[0030] By adopting the above-mentioned preferred technical features, the outer contour of the elastic adhesive sheet is substantially the same as the outer contour of the corresponding electrode area. When the patch is used, medical staff can easily distinguish the location where the electrode is pasted and press it by hand. The reinforcement part of the elastic adhesive sheet is used to prevent the connection between the electrode area and the corresponding first lead area from being bent to form a crease, and the connecting lead is not easy to break at this connection. By utilizing the specific form of the elastic adhesive sheet and the glue-containing gap formed around the through hole, the elastic adhesive sheet has elastic elasticity in the thickness direction, and the hydrogel filled in the through hole can be stored in the glue-containing gap before overflowing to the outside of the elastic adhesive sheet, thereby reducing the amount of hydrogel overflowing above the bonding surface. Generally, the side walls of the through hole and the glue-containing gap have no or only weak hydrogel adhesion compared to the electrode. In the specific scheme, the thickness range of the elastic adhesive sheet is defined, and the thickness of the elastic adhesive sheet is less than half of the thickness of the adhesive layer in the prior art, which is easier to deform, which is conducive to the shape change of the elastic adhesive sheet in the contact area with the human body, and the shape of the hydrogel also changes accordingly, and the filling amount of the hydrogel in the through hole can be relatively reduced, and the amount of hydrogel used can be reduced by less than half without the problem of insufficient hydrogel adhesion. In the preferred scheme, the symmetrical arrangement of the gel-containing gaps and one of the gel-containing gaps facing the corresponding first lead area are used to form a symmetrical expansion of the hydrogel under pressure in the gel-containing gap and symmetrical reflux to the center of the ring after being compressed. The gel-containing gap on one side faces the reinforcement part of the elastic adhesive sheet, which will not excessively change the structure of the elastic adhesive sheet, and the through hole is not easy to deform.

[0031] The present invention can be further configured as follows in a preferred example: the brain electrocardiogram electrode patch is specifically a brain electrocardiogram electrode patch, the electrodes include a positive electrode, a reference electrode and a negative electrode, the reference electrode is located between the positive electrode and the negative electrode, and is used to measure the impedance of the positive electrode and the negative electrode, and the positive electrode and the negative electrode are used to establish a signal path of human skin between the positive and negative electrodes to measure brain electrocardiogram signals;

[0032] Preferably, in the second lead area, the second connecting lead connected to the reference electrode is arranged between the first connecting lead connected to the positive electrode and the third connecting lead connected to the negative electrode to shield interference signals of the positive and negative electrodes;

[0033] Specifically, the line width of the second connecting lead is smaller than any line width of the first connecting lead and the third connecting lead.

[0034] By adopting the above-mentioned preferred technical features, using a specific EEG electrode patch, the reference electrode is located between the positive electrode and the negative electrode, and the impedance changes from the positive electrode and the negative electrode to the reference electrode are used to judge whether the positive electrode and the negative electrode are well attached. The second connecting lead connected to the reference electrode in the second lead area is arranged in the middle, and the interference signal between the positive and negative electrodes can also be shielded. In a specific scheme, the line width of the second connecting lead can be smaller, and the relatively wide first connecting lead and the third connecting lead can be arranged in the limited width of the second lead area. When the connecting lead for normal measurement of brain electrocardiogram signal transmission is wider, it can avoid bending and breaking, that is, the breakage of the second connecting lead does not affect the collection function of the actual brain electrocardiogram signal.

[0035] In a preferred example, the present invention can be further configured as follows: the second lead area is connected to one of the electrode areas, which is an electrode area provided with the reference electrode, and the extension direction of the second lead area is inclined toward the electrode area connected to the negative electrode, so that the second lead area and the two first lead areas form a Y-shaped wiring film.

[0036] By adopting the above-mentioned preferred technical features and utilizing a specific Y-shaped wiring film, the second lead area may be pulled obliquely away from the human body attachment site, and the cable connector connected to the brain and ECG signal measuring device is obliquely away from the human body attachment site. Even if the reference electrode is pulled by mistake, the detachment of the reference electrode will not affect the brain and ECG signal collection of the positive and negative electrodes, that is, the reference electrode as one of the human body attachment points has a buffering effect on the patch's resistance to pulling.

[0037] The second main purpose of the present invention is achieved through the following technical solutions:

[0038] A brain electrocardiogram sensor is proposed, comprising a brain electrocardiogram electrode patch according to any one of the above technical solutions or a feasible technical combination thereof, and a cable connector connected to the external connection area.

[0039] By adopting the above technical solution, the flat cable connector is detachably connected to the brain electrocardiogram signal measuring device, and the brain electrocardiogram sensor is a consumable device that comes into contact with the human body during the brain electrocardiogram signal measurement. The hydrogel annular dispersion mechanism in the through hole is used to prevent the hydrogel from clumping and overflowing onto the local bonding surface, or / and to reduce the amount of hydrogel filling in the through hole.

[0040] The third main purpose of the present invention is achieved through the following technical solutions:

[0041] A method for using a brain electrocardiogram electrode patch is proposed, and a brain electrocardiogram electrode patch is implemented based on any of the above technical solutions or a feasible technical combination thereof, including:

[0042] Filling the through holes of the elastic adhesive sheet with hydrogel, and connecting the hydrogel to the corresponding electrodes through the annular adhesive contact area;

[0043] The non-functional surface of the electrode area applies pressure so that the adhesive surface of the elastic adhesive sheet adheres to the human skin, and the hydrogel also contacts the human skin corresponding to the position of the through hole. Under the diffusion effect of the hydrogel annular diffusion mechanism, the hydrogel will not locally clump and overflow to the adhesive surface;

[0044] Brain electrocardiogram signals are detected and collected via the hydrogel, the electrodes and the connecting leads.

[0045] By adopting the above technical scheme, the adhesive surface of the elastic adhesive sheet is used as a mechanical fixation before the human body collects brain electrocardiogram signals, and the hydrogel surrounded by the through holes of the elastic adhesive sheet is the contact medium for the human body to collect brain electrocardiogram signals. Under the dispersion effect of the hydrogel annular dispersion mechanism, the hydrogel will not locally clump and overflow to the adhesive surface of the elastic adhesive sheet, thereby reducing the shedding of the elastic adhesive sheet, so as to realize the accurate collection of brain electrocardiogram signals for detection and collection.

[0046] In summary, the present invention includes at least one of the following technical effects that contribute to the prior art:

[0047] 1. The through hole of the elastic adhesive sheet is divided into a ring core adhesive contact area, a ring middle adhesive diffusion area, and a ring outer adhesive area by using a hydrogel annular diffusion mechanism, so as to prevent the hydrogel from agglomerating and locally overflowing to the adhesive surface of the elastic adhesive sheet, and the problem of whether it is sticky or not will not occur, and the detected EEG signal or ECG signal will be more stable;

[0048] 2. Since the problem of stickiness can be solved, the amount of hydrogel required per electrode can be reduced, and the thickness of the elastic adhesive sheet can be further reduced. Compared with the 0.2 cm of the adhesive layer in the prior art, the thickness of the elastic adhesive sheet can be reduced to 0.03-0.1 cm, specifically 0.05-0.075 cm;

[0049] 3. The use of the diffuser rod specifically includes a grab rod with a barb and a touch rod with a straight-up touch end, which can increase the number of repeated sticking of the brain ECG electrode patch at the electrode. When adjusting the human body attachment position or re-sticking, too much hydrogel will not be brought out from the through hole. BRIEF DESCRIPTION OF THE DRAWINGS

[0050] Figure 1 An exploded view of some preferred embodiments of the electrocardiogram electrode patch of the present invention is shown;

[0051] Figure 2 A three-dimensional assembly diagram of some preferred embodiments of the electrocardiogram electrode patch of the present invention is shown;

[0052] Figure 3Schematic diagrams of circuit layers of brain electrocardiogram electrode patches in some preferred embodiments of the present invention are shown;

[0053] Figure 4 A three-dimensional schematic diagram showing a hydrogel annular diffusion mechanism partially enlarged and displayed on an electrode under a basement membrane in some preferred embodiments of the present invention;

[0054] Figure 5 Schematic diagrams showing the cross-section of the electrocardiogram electrode patch at the electrode region in some preferred embodiments of the present invention;

[0055] Figure 6 Schematic diagrams showing electrode division of the brain electrocardiogram electrode patch in some preferred embodiments of the present invention are shown.

[0056] Attached figures: 10, base film; 11, electrode area; 12, first lead area; 13, second lead area; 14, external area; 20, circuit layer; 21, electrode; 21A, positive electrode; 21B, reference electrode; 21C, negative electrode; 211, center pad; 212, occupied area; 213, outer ring pad; 22, connecting lead; 22A, first connecting lead; 22B, second connecting lead; 22C, third connecting lead; 30, elastic adhesive sheet; 31, through hole; 32, adhesive surface; 33, reinforcement part; 34, adhesive notch; 40, hydrogel annular dispersion mechanism; 41, circular ring sheet; 42, dispersion rod; 42A, grab rod; 42B, touch rod; 50, hydrogel; 60, hydrogel adsorbent; 70, sticker protective film; 80, protective layer. DETAILED DESCRIPTION

[0057] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments for understanding the inventive concept of the present invention, and cannot represent all the embodiments, nor are they interpreted as the only embodiments. Based on the embodiments in the present invention, all other embodiments obtained by ordinary technicians in this field on the premise of understanding the inventive concept of the present invention are within the scope of protection of the present invention.

[0058] It should be noted that if there are directional indications (such as up, down, left, right, front, back...) involved in the embodiments of the present invention, the directional indication is only used to explain the relative position relationship, movement status, etc. between the components in a certain specific posture. If the specific posture changes, the directional indication will also change accordingly. In order to facilitate the understanding of the technical solution of the present invention, the anti-sticky brain-ECG electrode patch of the present invention and the method of use thereof are further described and explained in detail below, but are not limited to the scope of protection of the present invention. The "sticky or not" referred to in the embodiments means that after an object is adhered, it will not stick even if pressure is applied, and it is easy to fall off or shift, causing the detected EEG signal or ECG signal to lose accuracy. The "brain-ECG signal" referred to in the embodiments means any one of the EEG signal and the ECG signal, not including both the EEG signal and the ECG signal, and is preferably applicable to the EEG signal.

[0059] Figure 1 An exploded view of some preferred embodiments of the electrocardiogram electrode patch of the present invention is shown; Figure 2 Draw a three-dimensional combination diagram of the brain electrocardiogram electrode patch; Figure 3 Draw a schematic diagram of the circuit layer of the brain electrocardiogram electrode patch; Figure 4 A three-dimensional schematic diagram showing a partially enlarged hydrogel annular diffusion mechanism disposed on an electrode under a transparent basement membrane is shown; Figure 5 A schematic diagram showing the sectioning of the electrocardiogram electrode patch at the electrode area; Figure 6 A schematic diagram of the electrode division of the brain ECG electrode patch is shown. The attached figure only shows the common parts of multiple embodiments, and the parts with differences or distinctions are described in text or presented in comparison with the drawings. Therefore, based on the industrial characteristics and technical essence, technical personnel familiar with the field should correctly and reasonably understand and judge whether the individual technical features described below or any combination of them can be characterized in the same embodiment, or whether multiple technical features with mutually exclusive technical essences can only be characterized in different variations. The technical features described below may belong to one embodiment or to multiple embodiments.

[0060] Reference Figure 1 and Figure 2 Some embodiments of the present invention provide a brain electrocardiogram electrode patch, which mainly includes: a base film 10, a circuit layer 20, an elastic adhesive sheet 30, and a hydrogel annular diffusion mechanism 40. The base film 10 is used to carry the circuit layer 20, the circuit layer 20 is used to collect and transmit brain electrocardiogram signals, the elastic adhesive sheet 30 is used to adhere and fix the periphery of the contact part for measuring and collecting brain electrocardiogram signals of the human body, and the hydrogel annular diffusion mechanism 40 is used to disperse the overflow of the hydrogel in a certain specific direction after being compressed.

[0061] Reference Figure 1 and Figure 2The base film 10 has a functional surface, which serves as a circuit forming surface. The functional surface includes a plurality of electrode areas 11, a first lead area 12, a second lead area 13 and an external connection area 14. The first lead area 12 connects the electrode areas 11, and the second lead area 13 connects one of the electrode areas 11 and the external connection area 14. The base film 10 is specifically a PE insulating film (Polyethylene), which is usually opaque. The back of the base film 10 can be printed with numbers or symbols corresponding to the electrode numbers; non-limitingly, based on different requirements for properties such as ductility and dielectric properties, the base film 10 can also be other insulating films, such as PET (polyethylene terephthalate), PVC (Polyvinylchlorid), PU (Polyurethane), etc. In the example, the width of the electrode area 11 in the width direction of the lead area is greater than the unit width of the first lead area 12 and the second lead area 13, so the difference between the electrode area 11 and the lead area can be quickly distinguished by the appearance of the base film 10.

[0062] Reference Figure 1 and Figure 3 , the circuit layer 20 is formed on the functional surface of the base film 10, and the circuit layer 20 includes a plurality of electrodes 21 located on the electrode area 11 and a plurality of connecting leads 22 connected to the corresponding electrodes 21, and the connecting leads 22 are located on the first lead area 12 and converge at the second lead area 13. The circuit layer 20 is specifically a circuit formed by printing conductive silver paste, which has better softness and toughness, and is not easy to form creases after metal bending. It can also be a copper circuit or other metal circuit or a conductive circuit formed by solidifying other conductive particles other than silver powder. The electrode 21 specifically includes a positive electrode 21A, a reference electrode 21B and a negative electrode 21C. The shape of the electrode 21 can be specifically circular, but can be non-limited to be square or other shapes. The circular shape is to facilitate the determination of the center point of the electrode 21 and reduce the amount of ineffective corners of the electrode 21. After the circuit layer 20 is formed, Figure 1 As shown, the protective layer 80 can be used to cover the connecting leads 22 on the first lead area 12 and the second lead area 13. The protective layer 80 is a solder mask layer or an insulating film. In this example, it is made of a different material from the base film 10 and is formed in a different way, such as printing, but it is not limited to the same material and the same formation method. The connecting leads 22 are exposed as external terminals (such as Figure 2 As shown), for combined connection of cable connectors.

[0063] Reference Figure 1 and Figure 2The elastic adhesive sheet 30 is disposed on the electrode area 11 and is used to adhere to human skin. The elastic adhesive sheet 30 has a through hole 31 aligned with the electrode 21. The space in the through hole 31 is used to fill the hydrogel 50 so that the electrode 21 connected to the hydrogel 50 can sense brain signals or electrocardiogram signals. The material of the elastic adhesive sheet 30 can be foam or other elastic insulating materials. The elastic adhesive sheet 30 has an adhesive surface 32. In addition to being fixed to the body part to be measured with the adhesive surface 32, the elastic adhesive sheet 30 can also limit the dissipation of the hydrogel 50 with the through hole 31 (such as Figure 5 shown).

[0064] Reference Figure 1 and Figure 4 The hydrogel annular dispersion mechanism 40 is disposed on the electrode 21 and located in the through hole 31, so as to divide the through hole 31 from the center to the outside into a ring core gel contact area, a ring middle gel dispersion area, and a ring outer gel storage area. Figure 5 The hydrogel annular diffuser 40 generally has a hollow ring core extending from the top surface of the hydrogel directly to the corresponding electrode 21, corresponding to the position of the ring core gel contact area. Figure 5 and Figure 6 The ring core glue contact area of ​​the through hole 31 is located above the center pad 211 of the electrode 21, the ring center glue area of ​​the through hole 31 is located above the area 212 of the electrode 21 set by the hydrogel ring-shaped diffusion mechanism 40, and the ring outer glue holding area of ​​the through hole 31 is located above the ring outer pad of the electrode 21. The function of the ring center glue holding area is to break up the overflow of the hydrogel from the ring center to the outside of the ring with a specific direction, so that the ring outer glue holding area can evenly contain the overflowed hydrogel in a ring shape.

[0065] The basic principle of the above embodiment is: using the hydrogel annular dispersion mechanism 40 to divide the through hole 31 of the elastic adhesive sheet 30 into a ring core glue contact area, a ring middle glue scattered area, and a ring outer glue containing area, the hydrogel 50 to be filled in the through hole 31 can be concentrated in the ring core glue contact area, and when subjected to pressure and extrusion, the hydrogel 50 is dispersed in the ring middle glue scattered area, and will not overflow in a certain direction, and the hydrogel 50 can expand evenly in the ring outer glue containing area, and after the pressure is finished, it will flow back to the ring core glue contact area evenly through the ring middle glue scattered area in a circular manner. Therefore, the squeezed hydrogel 50 will not overflow and diffuse to the adhesive surface 32 of the elastic adhesive sheet 30, solving the problem of whether the brain ECG electrode patch is sticky in the prior art.

[0066] In a better example, refer to Figure 1 and Figure 4, the hydrogel annular diffusion mechanism 40 has a circular ring sheet 41 fixed to the electrode 21 and a diffusion rod 42 arranged on the ring surface of the circular ring sheet 41; by using the specific structure of the hydrogel annular diffusion mechanism 40, the bottom surface of the circular ring sheet 41 can be fixed to the electrode 21, and a plurality of diffusion rods 42 can be arranged on the top surface of the circular ring sheet 41, and the center of the circular ring sheet 41 can be used for the hydrogel 50 to pass through and connect to the center point of the electrode 21. The function of the diffusion rod 42 is to disperse and divert the hydrogel 50 that overflows from the ring core glue contact area under pressure in the glue diffusion area in the ring, overflow to the glue holding area outside the ring in a relatively uniform manner, and then expand uniformly. The length of the diffusion rod 42 is usually controlled to be between one-half and one times the depth of the through hole 31, specifically between 60% and 90% of the depth of the through hole. In addition to the diffusion rod structure, in the variation example, the hydrogel annular diffusion mechanism 40 can also be, for example, a vertical filter cartridge, a filter screen or other structural forms that can disperse the overflowed hydrogel.

[0067] Reference Figure 4 and Figure 5 The diffuser rod 42 specifically includes a gripping rod 42A with a barb and a contact rod 42B with a straight upward contact end. In the preferred embodiment, the gripping rod 42A with a barb specifically included in the diffuser rod 42 is also used to grip the hydrogel adsorbent 60 to prevent a large amount of hydrogel 50 from being brought out when adjusting the sensing position, and the contact rod 42B with a straight upward contact end specifically included in the diffuser rod 42 is also used to excessively press the lower contact area of ​​the human body to prevent the depth of the through hole 31 from being excessively squeezed.

[0068] Preferably, refer to Figure 4 and Figure 5 The annular sheet 41, the gripping rod 42A and the contact rod 42B are an integral part formed by injection molding; in this preferred embodiment, the integral part formed by injection molding can greatly reduce the manufacturing cost of the hydrogel annular diffuser 40, and even if the hydrogel annular diffuser 40 is non-conductive, it does not affect the connection between the hydrogel 50 and the electrode 21 in the annular core gel contact area. The hydrogel annular diffuser 40 is specifically a non-conductive plastic molding.

[0069] Specifically, refer to Figure 4 and Figure 5 , the annular sheet 41 is fixed to the electrode 21 in such a way that the hollow circle of the annular sheet 41 is aligned with the center point of the electrode 21. In this specific solution, the annular hydrogel diffusion mechanism 40 is fixed by aligning the hollow circle of the annular sheet 41 with the center point of the electrode 21, so that the outer gel-containing area of ​​the through hole 31 has a uniform width after being fixed as much as possible, and the hydrogel 50 that flows back from the outer part of the annular gel-containing area to the center of the annular ring after being compressed also has a uniform filling amount.

[0070] In a preferred example, refer to Figure 5The height of the grab bar 42A and the feeler bar 42B is below the adhesive surface 32 of the elastic adhesive sheet 30; the overflowing hydrogel is effectively dispersed by the height restriction of the grab bar 42A and the feeler bar 42B, and most of the hydrogel 50 is retained in the through hole 31 and below the adhesive surface 32 of the elastic adhesive sheet 30. For details, refer to Figure 1 Before the brain electrocardiogram electrode patch is used, the adhesive surface 32 of the elastic adhesive sheet 30 is covered with a sticker protective film 70; in this specific embodiment, the sticker protective film 70 is used to cover the adhesive surface 32 before the patch is used to protect the adhesiveness of the adhesive surface 32 from changing.

[0071] In a preferred example, refer to Figure 1 and Figure 5 The brain ECG electrode patch also includes: a hydrogel adsorbent 60, which is arranged in the through hole 31 of the elastic adhesive sheet 30, and the grab rod 42A and the touch rod 42B penetrate into the hydrogel adsorbent 60. By utilizing the hydrogel adsorbent 60 in the through hole 31 and the grab rod 42A and the touch rod 42B penetrating into the hydrogel adsorbent 60, a large amount of hydrogel 50 is prevented from being taken out and lost when adjusting the human brain ECG measurement position. The hydrogel adsorbent 60 is specifically but not limited to a low-density porous fluffy sponge for adsorbing the hydrogel 50 in the through hole 31 (such as Figure 5 shown).

[0072] In a preferred example, refer to Figure 1 and Figure 6 , the conducting area of ​​the electrode 21 is determined by the through hole 31 of the elastic adhesive sheet 30, and the conducting area of ​​the electrode 21 is divided into a central pad 211 and an outer pad 213 surrounding the central pad 211 by the area 212 occupied by the hydrogel annular diffusion mechanism 40. The electrode 21 is determined by the area of ​​the electrode 21, and becomes a contact pad determined by the elastic adhesive sheet 30 and the hydrogel annular diffusion mechanism 40. The electrode 21 has a central pad 211 and an outer pad 213 surrounding the central pad 211. Both the central pad 211 and the outer pad 213 can be used to conduct the hydrogel, and can collect brain and heart electrocardiogram signals to avoid the open circuit of the hydrogel 50. Usually, the bottom of the hydrogel 50 has a priority conducting effect on the electrode 21 at the central pad 211, and the top of the hydrogel 50 has a priority conducting effect on the human body contact area above the outer pad 213. Therefore, the assembly error of the elastic adhesive sheet 30 fixed on the electrode area 11 can be tolerated, and the subsequently assembled hydrogel annular diffusion mechanism 40 can be fixed on the electrode 21 by simply positioning it according to the center point of the through hole 31 of the elastic adhesive sheet 30 .

[0073] In a preferred example, refer to Figure 2 and Figure 6The outer contour of the elastic adhesive sheet 30 is substantially the same as the outer contour of the corresponding electrode area 11, and the elastic adhesive sheet 30 also has a reinforcement portion extending to the first lead area 12 connected to the corresponding electrode area 11; by making the outer contour of the elastic adhesive sheet 30 substantially the same as the outer contour of the corresponding electrode area 11, medical staff can easily distinguish the part where the electrode 21 is pasted when the patch is used, and perform hand-held pressing. By making use of the reinforcement portion of the elastic adhesive sheet 30, the connection between the electrode area 11 and the corresponding first lead area 12 is prevented from being bent to form a crease, and the connecting lead 22 is not easily broken at the connection.

[0074] Specifically, the elastic adhesive sheet 30 includes a foam layer with a thickness of less than 0.1 cm, the through hole 31 is basically circular in shape, and a gel-receiving notch 34 is formed around the through hole 31; by utilizing the specific form of the elastic adhesive sheet 30 and the gel-receiving notch 34 formed around the through hole 31, the elastic adhesive sheet 30 has elasticity in the thickness direction, and the hydrogel 50 filled in the through hole 31 can be stored in the gel-receiving notch 34 before overflowing to the outside of the elastic adhesive sheet 30, thereby reducing the amount of hydrogel overflow above the bonding surface. Generally, the side walls of the through hole 31 and the gel-receiving notch 34 have no or only weak hydrogel adhesion compared to the electrode 21.

[0075] More specifically, the thickness of the elastic adhesive sheet 30 is between 0.03 and 0.1 cm, and more specifically between 0.05 and 0.075 cm. In the specific embodiment, the thickness range of the elastic adhesive sheet 30 is defined, and the thickness of the elastic adhesive sheet 30 is less than half of the thickness of the adhesive layer in the prior art, which makes it easier to deform, and is conducive to the shape change of the elastic adhesive sheet 30 in conformity with the contact area of ​​the human body. The shape of the hydrogel also changes accordingly, and the filling amount of the hydrogel 50 in the through hole 31 can be relatively reduced, which can reduce the use of hydrogel by less than half without the problem of insufficient adhesion of the hydrogel.

[0076] Preferably, the gel-containing notches 34 are symmetrically arranged, and one of the gel-containing notches 34 corresponding to each electrode area 11 faces the first lead area 12 connected to the corresponding electrode area 11. In this preferred embodiment, the symmetrical arrangement of the gel-containing notches 34 and one of the gel-containing notches 34 facing the corresponding first lead area 12 are utilized to form a hydrogel 50 that symmetrically expands in the gel-containing notches 34 under pressure and symmetrically flows back to the center of the ring after being compressed, and the gel-containing notches 34 on one side face the reinforcement part of the elastic adhesive sheet 30, so that the structure of the elastic adhesive sheet 30 will not be excessively changed, and the through hole 31 is not easily deformed.

[0077] In a preferred example, refer to Figure 1 and Figure 3The electrocardiogram electrode patch is specifically an electrocardiogram electrode patch, the reference electrode 21B is located between the positive electrode 21A and the negative electrode 21C, and is used to measure the impedance of the positive electrode 21A and the negative electrode 21C. The positive electrode 21A and the negative electrode 21C are used to establish a signal path between the human skin and the positive electrode 21A and the negative electrode 21C to measure the electrocardiogram signal; the reference electrode 21B is located between the positive electrode 21A and the negative electrode 21C, and the impedance changes from the positive electrode 21A and the negative electrode 21C to the reference electrode 21B are used to judge whether the positive electrode 21A and the negative electrode 21C are well attached. When in use, the elastic adhesive sheet 30 corresponding to the positive electrode 21A is attached to the front of the human forehead, the elastic adhesive sheet 30 corresponding to the reference electrode 21B is attached to the side of the human forehead, and the elastic adhesive sheet 30 corresponding to the negative electrode 21C is attached to the ear bone behind the ear of the human head.

[0078] Preferably, in the second lead area 13, the second connecting lead 22B connected to the reference electrode 21B is arranged between the first connecting lead 22A connected to the positive electrode 21A and the third connecting lead 22C connected to the negative electrode 21C to shield the interference signal between the positive electrode 21A and the negative electrode 21C; by arranging the second connecting lead 22B connected to the reference electrode 21B in the second lead area 13 in the middle, the interference signal between the positive electrode 21A and the negative electrode 21C can also be shielded.

[0079] Specifically, the line width of the second connecting lead 22B is smaller than any line width of the first connecting lead 22A and the third connecting lead 22C. In a specific solution, the line width of the second connecting lead 22B can be smaller, and the first connecting lead 22A and the third connecting lead 22C, which are relatively wide, can be arranged in the limited width of the second lead area 13. When the connecting lead 22 is used to measure the transmission of the brain electrocardiogram signal normally, the wider it is, the more it can avoid being broken, that is, the breakage of the second connecting lead 22B does not affect the actual brain electrocardiogram signal collection function.

[0080] In a preferred example, the second lead area 13 is connected to one of the electrode areas 11, which is the electrode area 11 provided with the reference electrode 21B. The extension direction of the second lead area 13 is inclined toward the electrode area 11 connected to the negative electrode 21C, so that the second lead area 13 and the two first lead areas 12 form a Y-shaped wiring film. With a specific Y-shaped wiring film, the second lead area 13 may be pulled outward obliquely away from the human body attachment site, and the cable connector connected to the brain and electrocardiogram signal measurement device has an oblique distance relationship with the human body attachment site. Even if it is pulled to the reference electrode 21B by mistake, the detachment of the reference electrode 21B does not affect the brain and electrocardiogram signal collection between the positive electrode 21A and the negative electrode 21C, that is, the reference electrode 21B, as one of the human body attachment points, has a buffering effect of resisting the pulling of the patch.

[0081] For details, please refer to Figure 1 and Figure 3 The bending sections of the first connecting lead 22A and the third connecting lead 22C are also located in the middle electrode area 11 where the reference electrode 21B is provided, so that there will be no scattered line branches in the middle part of the electrode patch. The first connecting lead 22A is L-shaped on both sides of the middle electrode area 11, and the third connecting lead 22C is U-shaped on one side of the middle electrode area 11, and then the lines are gathered in the second lead area 13. Since the middle electrode area 11 of the reference electrode 21B is also attached to the human body contact part when in use

[0082] In other embodiments of the present invention, a brain electrocardiogram sensor is also proposed, comprising a brain electrocardiogram electrode patch according to any of the above-mentioned technical solutions or a feasible technical combination thereof, and a cable connector (not shown) connected to the external connection area 14 (located at the extended end of the second lead area 13).

[0083] The basic principle of the above embodiments is that the cable connector in the external connection area 14 can be detachably connected to the brain electrocardiogram signal measuring device, and the brain electrocardiogram sensor is a consumable device that comes into contact with the human body during the brain electrocardiogram signal measurement, and utilizes the hydrogel annular diffusion mechanism 40 in the through hole 31 to prevent the hydrogel 50 from clumping and overflowing onto the local bonding surface, or / and to reduce the through hole filling amount of the hydrogel 50.

[0084] In addition, an embodiment of the present invention further proposes a method for using a brain-ECG electrode patch, which is implemented based on any of the above technical solutions or feasible technical combinations thereof, including:

[0085] Step S1: Fill the through hole 31 of the elastic adhesive sheet 30 with the hydrogel 50, and the hydrogel 50 is connected to the corresponding electrode 21 through the annular adhesive contact area;

[0086] Step S2: applying pressure from the non-functional surface of the electrode area 11 so that the adhesive surface 32 of the elastic adhesive sheet 30 adheres to the human skin, and the hydrogel 50 also contacts the human skin corresponding to the position of the through hole 31. Under the diffusion effect of the hydrogel annular diffusion mechanism 40, the hydrogel 50 will not locally clump and overflow to the adhesive surface 32;

[0087] Step S3: Detect and collect brain electrocardiogram signals via the hydrogel 50, the electrode 21 and the connecting lead 22. In a specific application, the impedance from the reference electrode 21B to the positive electrode 21A and the impedance from the reference electrode 21B to the negative electrode 21C can be used to determine whether the positive electrode 21A and the negative electrode 21C are well attached, and the brain electrocardiogram signals of the human body can be collected from the positive electrode 21 to the negative electrode 21C.

[0088] The basic implementation principle of the above embodiment is: the adhesive surface 32 of the elastic adhesive sheet 30 is used as a mechanical fixation before the human body collects brain electrocardiogram signals, and the hydrogel 50 surrounded by the through hole 31 of the elastic adhesive sheet 30 is the contact medium for the human body to collect brain electrocardiogram signals. Under the dispersion effect of the hydrogel annular dispersion mechanism 40, the hydrogel 50 will not locally clump and overflow to the adhesive surface 32 of the elastic adhesive sheet 30, thereby reducing the shedding of the elastic adhesive sheet 30, so as to realize the accurate collection of brain electrocardiogram signals for detection and collection.

[0089] The embodiments of this specific implementation method are all preferred embodiments for facilitating the understanding or implementation of the technical solutions of the present invention, and are not intended to limit the protection scope of the present invention. All equivalent changes made based on the structure, shape, and principle of the present invention should be included in the protection scope of the present invention.

Claims

1. A brain electrocardiogram electrode patch, characterized in that: include: A base film having a functional surface, wherein the functional surface includes a plurality of electrode areas, a first lead area, a second lead area and an external connection area, wherein the first lead area connects the electrode areas, and the second lead area connects one of the electrode areas and the external connection area; A circuit layer is formed on the functional surface of the base film, the circuit layer includes a plurality of electrodes located on the electrode area and a plurality of connecting leads connected to the corresponding electrodes, the connecting leads are located on the first lead area and gathered in the second lead area; An elastic adhesive sheet is disposed on the electrode area and is used to adhere to human skin. The elastic adhesive sheet has a through hole aligned with the electrode. The space in the through hole is used to fill with hydrogel so that the electrode connected to the hydrogel can sense brain signals or electrocardiogram signals. A hydrogel annular dispersion mechanism is arranged on the electrode and located in the through hole, and is used to divide the through hole from the center to the outside into a ring core gel contact area, a ring middle gel dispersion area, and a ring outer gel storage area; The hydrogel annular dispersion mechanism comprises a circular ring sheet fixed to the electrode and a plurality of dispersion rods arranged on the annular surface of the circular ring sheet, wherein the dispersion rod comprises a grabbing rod with a barb and a contact rod with a straight-up contact end, and the heights of the grabbing rod and the contact rod are below the adhesive surface of the elastic adhesive sheet, and the dispersion rod is configured to disperse and divert the hydrogel that overflows from the pressurized contact area of ​​the ring core glue in the dispersed glue area in the ring, and overflow to the outer glue containing area of ​​the ring in a relatively uniform manner to achieve uniform expansion; Among them, the outer contour of the elastic adhesive sheet is substantially the same as the outer contour of the corresponding electrode area, and the elastic adhesive sheet also has a reinforcement portion extending to the first lead area connected to the corresponding electrode area; the elastic adhesive sheet includes a foam layer with a thickness of less than 0.1 cm, the basic shape of the through hole is circular, and a glue-containing gap is formed around the through hole; the thickness of the elastic adhesive sheet is between 0.03 and 0.1 cm.

2. The brain electrocardiogram electrode patch according to claim 1, characterized in that: The annular sheet, the grab bar and the feeler bar are an integral part formed by injection molding.

3. The brain electrocardiogram electrode patch according to claim 1, characterized in that: The annular sheet is adhered to the electrode in a manner that the hollow circle of the annular sheet is aligned with the center point of the electrode.

4. The brain electrocardiogram electrode patch according to claim 1, characterized in that: Also includes: The hydrogel adsorbent is arranged in the through hole of the elastic adhesive sheet, and the grabbing rod and the touching rod penetrate into the hydrogel adsorbent.

5. The brain electrocardiogram electrode patch according to claim 1, characterized in that: Before the brain electrocardiogram electrode patch is used, the adhesive surface of the elastic adhesive sheet is covered with a sticker protective film.

6. The brain electrocardiogram electrode patch according to claim 1, characterized in that: The conductive area of ​​the electrode is determined by the through hole of the elastic adhesive sheet, and the conductive area of ​​the electrode is divided into a central pad and an outer ring pad surrounding the central pad according to the area occupied by the hydrogel annular diffusion mechanism.

7. The brain electrocardiogram electrode patch according to claim 1, characterized in that: The thickness of the elastic adhesive sheet is between 0.05 and 0.075 cm. The adhesive notches are symmetrically arranged, and one of the adhesive notches corresponding to each electrode area faces the first lead area connected to the corresponding electrode area.

8. The brain electrocardiogram electrode patch according to any one of claims 1 to 7, characterized in that: The brain-ECG electrode patch is specifically an EEG electrode patch, and the electrodes include a positive electrode, a reference electrode and a negative electrode. The reference electrode is located between the positive electrode and the negative electrode to measure the impedance of the positive electrode and the negative electrode. The positive electrode and the negative electrode are used to establish a signal path between the positive and negative electrodes of human skin to measure brain-ECG signals; in the second lead area, the second connecting lead connected to the reference electrode is arranged between the first connecting lead connected to the positive electrode and the third connecting lead connected to the negative electrode to shield the interference signals of the positive and negative electrodes.

9. The brain electrocardiogram electrode patch according to claim 8, characterized in that: The line width of the second connection lead is smaller than any line width of the first connection lead and the third connection lead.

10. The brain electrocardiogram electrode patch according to claim 9, characterized in that: The second lead area is connected to one of the electrode areas, which is the electrode area provided with the reference electrode. The extension direction of the second lead area is inclined toward the electrode area connected to the negative electrode, so that the second lead area and the two first lead areas form a Y-shaped wiring film.

11. A brain electrocardiogram sensor, characterized in that: It comprises a brain electrocardiogram electrode patch as described in any one of claims 1-10 and a cable connector connected to the external connection area.

12. A method for using a brain electrocardiogram electrode patch, characterized in that: Based on the implementation of a brain electrocardiogram electrode patch according to any one of claims 1 to 10, the method of use includes: Filling the through holes of the elastic adhesive sheet with hydrogel, and connecting the hydrogel to the corresponding electrodes through the annular adhesive contact area; The non-functional surface of the electrode area applies pressure so that the adhesive surface of the elastic adhesive sheet adheres to the human skin, and the hydrogel also contacts the human skin corresponding to the position of the through hole. Under the diffusion effect of the hydrogel annular diffusion mechanism, the hydrogel will not locally clump and overflow to the adhesive surface; Brain electrocardiogram signals are detected and collected via the hydrogel, the electrodes and the connecting leads.

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