Array type myoelectricity electrode patch

Abstract

The utility model discloses an array type myoelectricity electrode patch which comprises a substrate, a plurality of sensing electrodes fixed on the substrate and an electrode interface, a plurality of wires connected with the sensing electrodes are arranged on the substrate, and each sensing electrode is connected with the electrode interface through one wire; the conducting wire comprises a first conducting layer, a second conducting layer and a damping layer from inside to outside, the second conducting layer comprises a sensing area and a non-sensing area, the sensing area is connected with the bottom of the sensing electrode, and the damping layer is tightly attached to the outer side of the non-sensing area. According to the utility model, the outer side of the wire is provided with the damping layer which is tightly attached to the outer side of the wire, so that impact force generated by rapid movement or vibration can be absorbed and relieved, the arrangement of the damping layer is helpful for stabilizing an interface between sensing equipment and skin, and movement interference caused by muscle pulling can be reduced during signal acquisition, thereby reducing errors.

Description

Technical Field

[0001] The utility model belongs to the technical field of medical monitoring equipment, and in particular relates to an array type electromyography electrode sticker. Background Art

[0002] Bioelectric signals include electromyographic signals, electrocardiographic signals, and electroencephalographic signals, among which electromyographic signals are often used to study muscle diseases and muscle fatigue evaluation. As a tool for collecting electromyographic signals, electromyographic electrodes are divided into single-channel electrodes and array-type electromyographic electrode patches composed of multiple channels. Compared with single electrodes, array-type electrode patches are widely studied because they can obtain electromyographic signals from multiple channels covering muscle groups and extract more information about the activation and coordination of muscle groups. Among them, flexible and stretchable electromyographic array-type electrode patches have become an important development direction for electromyographic array-type electrode patches due to their good skin adhesion and anti-interference capabilities.

[0003] However, the existing electrode array uses an insulating flexible substrate material with poor air permeability and is prone to sweating, which leads to large motion artifacts. Sweating can also cause the adhesiveness of the pad to decrease, resulting in poor adhesion between the electrode and the skin and poor signal quality. Poor adhesion between the electrode and the skin will cause instability in the electrode-skin impedance, thus affecting the stability of the recorded signal.

[0004] Therefore, it is urgent to solve the problem of how to improve the fit between the electrode and the skin and reduce the movement interference during muscle pulling. Utility Model Content

[0005] The utility model aims to provide an array type myoelectric electrode patch to solve the problems in the prior art that the flexible electrode has a low degree of fit with the skin and is prone to motion interference.

[0006] An array type myoelectric electrode patch, comprising a substrate, a plurality of sensing electrodes fixed on the substrate, and an electrode interface; a plurality of wires connected to the sensing electrodes are arranged on the substrate, and each sensing electrode is connected to the electrode interface through a wire; the wire comprises a first conductive layer, a second conductive layer, and a damping layer from the inside to the outside; the damping layer is closely attached to the outside of the second conductive layer;

[0007] The array-type electromyography electrode patch is divided into a sensing area and a non-sensing area, the sensing area includes a sensing electrode, a second conductive layer and a damping layer, and the non-sensing area includes an area of ​​the first conductive layer that does not overlap with the second conductive layer.

[0008] Furthermore, the sensing electrode comprises an adhesive electrode and a conductive electrode which are connected in sequence, and the bottom surface of the conductive electrode is connected to the substrate; wherein the adhesive electrode is made of conductive hydrogel, and the conductive electrode is a silver-silver chloride electrode.

[0009] Furthermore, the adhesive electrode of the sensing electrode and the damping layer of the wire are made of conductive hydrogel.

[0010] Furthermore, the first conductive layer is made of silver.

[0011] Furthermore, the area ratio of the sensing area to the non-sensing area is 4-5:7-8.

[0012] Furthermore, the material of the sensing area is silver, and the material of the non-sensing area is silver and copper.

[0013] Furthermore, the material of the substrate is polydimethylsiloxane (PDMS).

[0014] Compared with the prior art, the beneficial effects of the utility model are:

[0015] The array-type electromyography electrode patch provided by the utility model has a tightly fitting damping layer arranged on the outside of the wire, which can absorb and alleviate the impact force caused by rapid movement or vibration. The setting of the damping layer helps to stabilize the interface between the sensor device and the skin, and can reduce the movement interference caused by muscle pulling when collecting signals, thereby reducing errors.

[0016] The damping layer is made of conductive hydrogel, which has high softness, elasticity and biocompatibility, and can serve as a channel for electronic conduction. This enables the array-type EMG electrode to form a good fit with the surface of the skin or other biological tissues when in use, reducing the relative displacement caused by movement, thereby reducing motion artifacts and achieving high-quality acquisition of multi-channel EMG signals. BRIEF DESCRIPTION OF THE DRAWINGS

[0017] Figure 1 This is a schematic diagram of the array-type electromyographic electrode patch of the utility model.

[0018] Figure 2 This is a schematic diagram of the assembly structure of the array-type electromyography electrode patch of the utility model.

[0019] Figure 3 To apply the myoelectric acquisition results of the utility model.

[0020] Markings in the figure: 1, substrate; 11, sensing area; 12, non-sensing area; 2, sensing electrode; 21, adhesion electrode; 22, conductive electrode; 3, electrode interface; 4, wire; 41, first conductive layer; 42, second conductive layer; 43, damping layer. DETAILED DESCRIPTION

[0021] The technical solutions in the embodiments of this specification will be described clearly and completely below in conjunction with the drawings in the embodiments of this specification. Obviously, the described embodiments are only part of the embodiments of this specification, rather than all the embodiments.

[0022] like Figure 1 and Figure 2 As shown, the utility model provides an array type electromyographic electrode patch, comprising a substrate 1, a plurality of sensing electrodes 2 fixed on the substrate 1, and an electrode interface 3; a plurality of wires 4 connected to the sensing electrodes 2 are arranged on the substrate 1, and each sensing electrode 2 is connected to the electrode interface 3 through a wire 4; the sensing electrode 2 comprises an adhesive electrode 21 and a conductive electrode 22 connected in sequence, the bottom surface of the conductive electrode 22 is connected to the substrate 1, and the conductive electrode 22 is a silver-silver chloride electrode;

[0023] The wire 4 includes a first conductive layer 41, a second conductive layer 42 and a damping layer 43 from the inside to the outside; the damping layer 43 is closely attached to the outside of the second conductive layer 42;

[0024] The array type electromyography electrode patch is divided into a sensing area 11 and a non-sensing area 12. The sensing area 11 includes an adhesive electrode 21, a conductive electrode 22, a second conductive layer 42 and a damping layer 43. The non-sensing area 12 includes an area of ​​the first conductive layer 41 that does not overlap with the second conductive layer 42.

[0025] In a preferred embodiment of the present invention, the area ratio of the sensing area to the non-sensing area is 5:7.

[0026] The material of the adhesion electrode 21 and the damping layer 43 is conductive hydrogel, specifically PEDOT:PSS; the material of the first conductive layer 41 is silver; the material of the sensing area 11 is silver, and the material of the non-sensing area 12 is silver or copper; the material of the substrate 1 is polydimethylsiloxane PDMS; the wire 4 is screen-printed on the substrate 1 with conductive paste.

[0027] In a preferred embodiment of the present invention, the array-type electromyographic electrode is 12-13.5 cm long and 4-4.5 cm wide; the number of the sensing electrodes 2 is 10, which are linearly distributed in double rows on the upper surface of the substrate 1, the diameter of the sensing electrodes 2 is 5 cm, and the spacing between adjacent sensing electrodes 2 is 1 cm.

[0028] When the utility model is used, the array-type electromyographic electrode is attached to the back of the forearm of the subject. Since the sensing electrode 2 is a conductive hydrogel electrode, it is sticky and can adhere to the skin surface. Then a commercial patch electrode is attached to the back of the hand as a reference electrode. The subject is asked to gradually clench his fist to the maximum force and then relax, and then rest for 5 seconds. This is repeated. The electromyographic amplitude increases with the increase of force and decreases with relaxation. The waveform is obvious, and the electromyographic collection is completed.

[0029] The collection results are as follows Figure 3 As shown, the utility model can reduce the motion interference during muscle pulling when measuring electromyographic signals, and the collected signals are of high quality.

[0030] The following is an exemplary description of the method for making the array-type myoelectric electrode patch of the utility model, including:

[0031] (1) Screen printing silver paste on PDMS and obtaining the first layer of silver paste after drying;

[0032] (2) Covering a portion of the first layer of silver paste area with silver chloride paste by screen printing as a sensing area, and covering the remaining first layer of silver paste area with silver paste and copper by screen printing as a non-sensing area, and obtaining a second layer of silver paste after drying;

[0033] (3) attaching the mold to the PDMS substrate, pouring the conductive hydrogel solution, and preparing the sensing electrode after cooling;

[0034] (4) The non-sensing area is subjected to electrochemical gelation and covered with a damping layer to obtain the array-type electromyographic electrode patch.

[0035] The above embodiments are only specific implementations of the present invention, which are used to illustrate the technical solution of the present invention rather than to limit it. The protection scope of the present invention is not limited thereto.

[0036] Although the present invention has been described in detail with reference to the aforementioned embodiments, ordinary technicians in the field should understand that any technician familiar with the technical field can still modify the technical solutions recorded in the aforementioned embodiments or easily conceive of changes within the technical scope disclosed in the present invention, or make equivalent replacements for some of the technical features therein within the technical scope disclosed in the present invention; and these modifications, changes or replacements do not make the essence of the corresponding technical solutions deviate from the scope of the technical solutions of the embodiments of the present invention, and should all be covered by the protection scope of the present invention.

Claims

1. An array type myoelectric electrode patch, comprising a substrate (1), a plurality of sensing electrodes (2) fixed on the substrate (1), and an electrode interface (3), characterized in that: A plurality of wires (4) connected to the sensing electrodes (2) are provided on the substrate (1); each sensing electrode (2) is connected to the electrode interface (3) via a wire (4); the wire (4) comprises, from the inside to the outside, a first conductive layer (41), a second conductive layer (42) and a damping layer (43); The array-type electromyography electrode patch is divided into a sensing area (11) and a non-sensing area (12), wherein the sensing area (11) comprises a sensing electrode (2), a second conductive layer (42) and a damping layer (43), and the non-sensing area (12) comprises an area of ​​the first conductive layer (41) that does not overlap with the second conductive layer (42).

2. The array type myoelectric electrode patch according to claim 1, characterized in that: The sensing electrode (2) comprises an adhesive electrode (21) and a conductive electrode (22) which are connected in sequence, and the bottom surface of the conductive electrode (22) is connected to the substrate (1).

3. The array type myoelectric electrode patch according to claim 2, characterized in that: The material of the adhesive electrode (21) is conductive hydrogel, and the conductive electrode (22) is a silver-silver chloride electrode.

4. The array type myoelectric electrode patch according to claim 1, characterized in that: The material of the damping layer (43) of the conductive wire (4) is conductive hydrogel.

5. The array type myoelectric electrode patch according to claim 1, characterized in that: The material of the first conductive layer (41) is silver.

6. The array type myoelectric electrode patch according to claim 1, characterized in that: The area ratio of the sensing area (11) to the non-sensing area (12) is 4-5:7-8.

7. The array type myoelectric electrode patch according to claim 1 or 5, characterized in that: The material of the sensing area (11) is silver, and the material of the non-sensing area (12) is silver and copper.

8. The array type myoelectric electrode patch according to claim 1, characterized in that: The material of the substrate (1) is polydimethylsiloxane.

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