WO2020056925A1

WO2020056925A1 - Skin dry electrode

Info

Publication number: WO2020056925A1
Application number: PCT/CN2018/118867
Authority: WO
Inventors: 都展宏; 王立平
Original assignee: 深圳先进技术研究院
Priority date: 2018-09-20
Filing date: 2018-12-03
Publication date: 2020-03-26
Also published as: CN110916651A

Abstract

A skin dry electrode comprising a recording electrode (120), a grounding electrode (110) and a reference electrode (130). A first end of the grounding electrode (110) is configured to be connected to a first position (A) of an object to be tested, a first end of the recording electrode (120) is configured to be connected to a second position (B) of the object to be tested, and a first end of the reference electrode (130) is configured to be connected to a third position (C) of the object to be tested. A second end of the grounding electrode (110) is connected to a signal acquisition device by means of a first external interface (111), a second end of the recording electrode (120) is connected to the signal acquisition device by means of a second external interface (121), and a second end of the reference electrode (130) is connected to the signal acquisition device by means of a third external interface (131). The recording electrode (120), the grounding electrode (110) and the reference electrode (130) comprise an electrically conductive fabric, an elastic support and an electrically conductive connection part, the electrically conductive fabric being attached to the elastic support.

Description

Skin dry electrode

This disclosure claims the priority of a Chinese patent application with a filing date of September 20, 2018 and an application number of 201811100543.5, the entire contents of which are incorporated herein by reference.

Technical field

The present disclosure relates to the technical field of biomedical engineering, for example, to a skin dry electrode.

Background technique

Skin electrodes are used clinically to measure bioelectrical signals to detect the state of disease, or to detect the attention, relaxation, and sleep status of medical and civilian test subjects. Among them, bioelectrical signals include ECG signals, brain Electrical signals and myoelectric signals. Common skin electrodes are wet electrodes, dry electrodes, and capacitor electrodes.

Wet electrodes are mostly silver-silver chloride electrodes or other pure metal electrodes. Using this wet electrode to provide bioelectrical signals such as EEG signals can provide lower contact impedance, but skin preparation and electrode surface preparation are required before use. The application of conductive paste requires the guidance of professionals in professional institutions. The conductive paste is easy to dry, and the collection effect is poor after the conductive paste is dry. It is also easy to stick to the skin or hair, and it is difficult to clean. It is not only a long-term acquisition of EEG signals. Bottlenecks, it also takes a lot of time and energy to debug and maintain this wet electrode.

The use of dry electrodes and capacitor electrodes can avoid conductive paste, but because dry electrodes usually use contact electrodes and conductive parts use metal conductors, it is easy to cause damage to the human body in motion, and the change in contact area will also reduce the quality of the signal. , Not suitable for long-term use. The capacitor electrode is a layer of capacitor dielectric plated on a stainless steel substrate. Although it can solve part of the problem, the manufacturing process is complicated, the processes are numerous, the cost is high, and the signal to noise is high. There are also some electrode structures in which the impedance is reduced by using springs, but the manufacturing process is relatively complicated and the cost is high, and if the contact area is small, excessive pressure will cause local skin swelling and even inflammation, causing discomfort.

Summary of the Invention

The present disclosure provides a dry skin electrode that can be used for a long time without the use of a viscous material such as a conductive paste and without the guidance of a professional. It is simple to make and low in cost, and can effectively prevent changes in contact resistance caused by exercise.

A dry skin electrode includes a recording electrode, a ground electrode, and a reference electrode. A first end of the ground electrode is provided to be connected to a first position of an object to be tested, and a first end of the recording electrode is provided to be connected to the object to be tested. The second end of the reference electrode is connected to the third position of the object to be tested; the second end of the ground electrode is connected to the signal acquisition device through a first external interface; The second end is connected to the signal acquisition device through a second external interface, and the second end of the reference electrode is connected to the signal acquisition device through a third external interface. The recording electrode, the ground electrode, and the reference electrode each include a conductive fabric, An elastic support and a conductive connection portion, the conductive fabric is attached to the elastic support, the conductive fabric in the recording electrode provides an electrical signal to the signal acquisition device through a second external interface, and the ground electrode The conductive fabric provides a ground signal to the signal acquisition device through a first external interface, and the conductive fabric in the reference electrode passes through Three external interface provides the reference signal to the signal acquisition device.

In one embodiment, the conductive fabric is woven from a mixed wire of metal and non-metal. The composition of the metal includes at least one of nickel, zinc, silver, lead, copper and platinum. The composition of the non-metal includes nylon, silk protein. At least one of polyimide, polyimide, and polyurethane.

In one embodiment, the elastic support is a sponge or an elastic silicone rubber.

In an embodiment, the sponge is one of a polyurethane sponge, a polyethylene sponge, and a polystyrene sponge, and the composition of the elastic silicone rubber includes at least one of silicon, oxygen, carbon, and sulfur. element.

In an embodiment, the conductive connection portion in the recording electrode is connected to the second external interface through a wire, the conductive connection portion in the ground electrode is connected to the first external interface through a wire, and the conductive connection in the reference electrode is The part is connected to the third external interface through a wire.

In one embodiment, the wire is one of a tail wire, a single-strand wire, a multi-strand wire, and a ribbon wire.

In an embodiment, the conductive connection portion includes a metal sheet, solder, and conductive adhesive, the conductive fabric is connected to the metal sheet through the solder, and the metal sheet is connected to the wire through the conductive adhesive.

In an embodiment, the skin dry electrode further includes an elastic non-conductive cloth, and two ends of the elastic non-wire cloth are provided with adhesive patches, and the recording electrode, the ground electrode, and the reference electrode are disposed on the Elastic non-conductive cloth.

In one embodiment, the number of the recording electrodes is at least one.

The skin dry electrode provided by the present disclosure can be used for a long period of time without the help of viscous materials such as conductive paste and without the guidance of professionals. It is simple to manufacture and low in cost, and can effectively prevent changes in contact resistance caused by exercise.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a structural diagram of a skin dry electrode according to an embodiment; FIG.

FIG. 2 is a schematic diagram of a skin dry electrode placement position according to an embodiment; FIG.

3 is a schematic diagram of a recording electrode according to an embodiment;

4 is a schematic diagram of a medical EEG machine interface provided by an embodiment;

5 is a schematic diagram of an electronic pin external interface provided by an embodiment;

6 is a schematic diagram of a miniature neural external interface according to an embodiment;

FIG. 7 is a schematic diagram of an elastic non-conductive cloth according to an embodiment.

detailed description

The disclosure is described below with reference to the drawings and embodiments.

This embodiment provides a skin stem electrode that can be used to collect bioelectrical signals such as EEG signals and / or ECG signals to complete detection of a disease or behavior state. FIG. 1 is a structural diagram of a skin dry electrode provided in this embodiment. The skin dry electrode includes a recording electrode 120, a ground electrode 110, and a reference electrode 130. A first end of the ground electrode 110 is disposed to be connected to a test object. The first position A is connected, the first end of the recording electrode 120 is set to be connected to the second position B of the object to be tested, and the first end of the reference electrode 130 is set to be connected to the third position C of the object to be tested. The first position A of the test object and the third position C of the test object may be the same position, the second position B of the test object and the first position A of the test object or the third position C of the test object For different positions. The second end of the ground electrode 110 is connected to the signal acquisition device 140 through a first external interface 111, and the second end of the recording electrode 120 is connected to the signal acquisition device 140 through a second external interface 121. The second end is connected to the signal acquisition device 140 through a third external interface 131.

The recording electrode 120, the ground electrode 110, and the reference electrode 130 each include a conductive fabric, an elastic support, and a conductive connection portion. The conductive fabric is attached to the elastic support. The fabric provides an electrical signal to the signal acquisition device 140 through a second external interface 121, and the conductive fabric in the ground electrode 110 provides a ground signal to the signal acquisition device 140 through a first external interface 111. The conductive fabric provides a reference signal to the signal acquisition device 140 through the third external interface 131.

In one embodiment, the skin dry electrode is a device that can collect bioelectrical signals such as EEG signals and ECG signals. The skin dry electrode includes a recording electrode 120, a ground electrode 110, and a reference electrode 130. The recording electrode 120 is provided. In order to collect bioelectric signals such as EEG signals or ECG signals, the recording electrode 120 may be placed on a bare skin position, such as the forehead, to reduce the interference of hair on bioelectric signals such as EEG signals or ECG signals, and to increase the EEG signal. The accuracy of the acquisition is also convenient for the adhesion of the recording electrode 120 to the skin. In the embodiment, the EEG signal is taken as an example. The ground electrode 110 is configured to collect a ground signal to reduce the interference of other electrical signals on the EEG signal. The ground electrode 110 may be placed in the middle of the forehead or behind the earlobe. The reference electrode 130 is set to collect a reference signal, and the signal acquisition device 140 performs a difference operation between the collected reference signal and the electrical signal, and reflects the fluctuation of the collected EEG signal or the change in the state of the test subject through the difference signal. Among them, the reference electrode 130 can be placed on the forehead or behind the earlobe. The placement of the reference electrode 130 can reduce the ECG signal mixed in the EEG signal and improve the accuracy of the EEG signal. Exemplarily, referring to FIG. 2, FIG. 2 is a schematic diagram of a skin dry electrode placement position. In one embodiment, the ground electrode 110 is placed in the middle of the forehead, the recording electrode 120 is placed on the left side of the ground electrode 110, and the reference electrode 130 is placed on the right side of the ground electrode 110.

Among them, the outer shape of the recording electrode 120, the ground electrode 110, and the reference electrode 130 may be a square or a circle. Making the outer shape of the recording electrode 120, the ground electrode 110, and the reference electrode 130 into a circle may prevent the tip effect. The electric field is not uniform, and the outer shape of the recording electrode 120, the ground electrode 110, and the reference electrode 130 is made into a square shape to facilitate processing. In this embodiment, the outer shapes of the recording electrode 120, the ground electrode 110, and the reference electrode 130 are not limited. In order to ensure the accuracy of the test, the outer shapes of the recording electrode 120, the ground electrode 110, and the reference electrode 130 are consistent.

In an embodiment, the first end of the recording electrode 120, the first end of the ground electrode 110 and the first end of the reference electrode 130 are connected, and the second end of the ground electrode 110 is connected to the signal acquisition device 140 through the first external interface 111. The second end of the recording electrode 120 is connected to the signal acquisition device 140 through a second external interface 121, and the second end of the reference electrode 130 is connected to the signal acquisition device 140 through a third external interface 131. Therefore, the recording electrode 120 and the ground electrode 110 are connected. The reference electrode 130 and the signal acquisition device 140 form a loop. When the recording electrode 120, the ground electrode 110, and the reference electrode 130 are in contact with the skin, the EEG signal, ground signal, and reference signal can be transmitted to the signal through the corresponding external interfaces. The acquisition device 140 completes the detection. In order to accurately reflect the change of the status of the person under test, in this embodiment, the recording electrode 120, the ground electrode 110, and the reference electrode 130 are set to the same design, that is, the recording electrode 120, the ground electrode 110, and the reference electrode 130 all include a conductive fabric 310, The elastic support body 320 and the conductive connection portion 330 have the same structure of each part. Referring to FIG. 3, FIG. 3 is a schematic diagram of a recording electrode provided in this embodiment.

Taking the recording electrode 120 as an example, each partial structure will be described. The conductive fabric 310 is configured to collect EEG signals. The conductive fabric 310 may be a metal conductive cloth or a conductive cloth made of a mixture of a metal conductive cloth and a non-metal conductive cloth. In actual applications, it can be selected according to requirements. The elastic support body 320 is provided to ensure that the recording electrode 120 is in an expanded state, and at the same time to avoid damage to the human body caused by the conductive fabric 310 due to the movement of the test person. In one embodiment, the elastic support body 320 with different mechanical properties can achieve different purposes. For example, the relatively soft elastic support body 320 can increase the comfort of the test person, which is beneficial to long-term use. The relatively hard elastic support body 320 The conductive fabric 310 can be better supported, the conductive performance can be improved, and the contact resistance with the skin can be reduced. The actual elastic support 320 can be selected according to needs. In one embodiment, the conductive fabric 310 is attached to the elastic support 320. When the recording electrode 120 is in contact with the skin, the sweat wets the elastic support 320 and the conductive fabric 310, so that the EEG current passes through the skull, causing the conductive fabric 310. The change in local potential causes the conductive fabric 310 to collect EEG signals. The conductive connection portion 330 is configured to provide the EEG signals collected by the conductive fabric 310 to the signal acquisition device 140 through the second external interface 121, where the second external interface 121 can also be referred to as an electrode interface, and is configured to connect the signal acquisition device 140, The EEG signals are transmitted to a signal acquisition device 140.

In order to ensure stable contact between the second external interface 121 and the signal acquisition device 140, the diameter or length of the second external interface 121 can be appropriately increased if the signal acquisition device 140 allows, for example, a medical EEG machine interface can be used. FIG. 4 is a schematic diagram of a medical EEG machine interface provided by this embodiment. The second external interface 121 may also use a high-density electrode interface, such as an electronic pin external interface or a micro-neural external interface, to implement multi-channel signal transmission. Refer to FIGS. 5 to 6, where FIG. 5 is provided in this embodiment. A schematic diagram of an external interface of an electronic pin. FIG. 6 is a schematic diagram of a miniature nerve external interface provided by this embodiment.

This embodiment provides a dry skin electrode that can be used for a long period of time without the use of viscous materials such as conductive paste and without the guidance of professionals. It is simple to make and low in cost, and can effectively prevent changes in contact resistance caused by exercise.

Based on the above embodiment, the conductive fabric 310 is woven from a metal and non-metal mixed wire, and the metal component includes at least one of nickel, zinc, silver, lead, copper, and platinum, and the non-metal component includes nylon. At least one of silk protein, silk protein, polyimide, and polyurethane.

In one embodiment, the components of the conductive fabric 310 include metals and non-metals. On the one hand, electrical signals can be collected through metal, and on the other hand, the flexibility, comfort, and durability of the conductive fabric 310 can be increased through non-metals to reduce noise. Among them, the non-metallic component may be an organic component. The composition of the metal may be one or more of nickel, zinc, silver, lead, copper, and platinum. The content of nickel is 0% to 35%, and the content of zinc is 0% to 25%. The content of silver is 0% -90%, the content of lead is 0% -5%, the content of copper is 0% -95%, and the content of platinum is 0% -70%. The non-metallic component may be one or more of nylon, silk protein, polyimide, and polyurethane, wherein the content of nylon is 0% -20%, and the content of the silk protein is 0% -10%. The content of the polyimide is 0% -50%, and the content of the polyurethane is 0% -30%. The sum of the metal content and the non-metal content in the conductive fabric 310 is 100%.

Based on the above embodiments, the elastic support body 320 is a sponge or an elastic silicone rubber, or may be other elastic support bodies, such as a combination of a spring and a plastic. Among them, the Shore hardness of the sponge or elastic silicone rubber is D20-D65, D indicates that the hardness is relatively high, and 20 indicates that the Shore hardness value of the sponge or elastic silicone rubber is 20. Optionally, the outer edge of the elastic support body 320 may extend from the outer edge of the conductive fabric 310 to prevent the outer edge of the conductive fabric 310 from damaging the test subject.

Based on the above embodiments, the sponge is one of polyurethane sponge, polyethylene sponge, and polystyrene sponge, and the composition of the elastic silicone rubber includes at least one of silicon, oxygen, carbon, and sulfur. An element.

Based on the above embodiment, the conductive connection portion of the recording electrode 120 is connected to the second external interface 121 through a wire, and the conductive connection portion of the ground electrode 110 is connected to the first external interface 111 through a wire. The conductive connection portion in the electrode 130 is connected to the third external interface 131 through a wire.

In one embodiment, taking the recording electrode 120 as an example, referring to FIG. 3, the conductive connection portion 330 is connected to the external interface 340 through a lead 350. After the conductive fabric 310 collects the EEG signal, it can be transmitted to the conductive connection portion 330 and the lead 350 to The external interface 340 is further transmitted to the signal acquisition device 140 by the external interface 340. In order to ensure a stable connection between the conductive connection portion 330 and the conductive wire 350, the conductive fabric 310, the conductive connection portion 330, and the conductive wire 350 can be fully contacted by a conductive adhesive or the like.

Based on the above embodiment, the wire 350 is one of a tail wire, a single-strand wire, a multi-strand wire, and a row wire. The selection of the lead 350 is to consider the impedance and anti-buckling performance. The low-impedance and good anti-bend performance of the lead 350 can ensure the stability of the EEG signal and improve the accuracy of the state judgment of the testee. For example, a tail wire, a single-stranded wire, a multi-stranded wire, or a ribbon wire can be selected, which can not only achieve sufficient contact with the conductive connection portion 330, but also avoid the effect of solder on the wire 350.

On the basis of the above embodiment, the conductive connection portion 330 includes a metal sheet, solder, and conductive adhesive, the conductive fabric 310 is connected to the metal sheet through the solder, and the metal sheet is connected to the metal sheet through the conductive adhesive. The wire 350 is connected. In order to make the metal sheet and the conductive fabric 310 contact stably, the metal sheet is fixed. In the embodiment, solder is used to connect the conductive fabric 310 to the metal sheet. At the same time, in order to avoid damage to the wire 350 by the solder, the conductive sheet is used to realize the metal sheet and the wire 350 Connection.

On the basis of the above embodiment, the skin dry electrode further includes an elastic non-conductive cloth 710, and two ends of the elastic non-wire cloth 710 are provided with adhesive sheets 720, the recording electrode 120, the ground electrode 110, and The reference electrode 130 is disposed on the elastic non-conductive cloth 710. Referring to FIG. 7, FIG. 7 is a schematic diagram of an elastic non-conductive cloth provided in this embodiment. The elastic non-conductive cloth 710, the recording electrode 120, the ground electrode 110 and the reference electrode 130 form a whole. The cloth 710 is in contact with the skin, and the adhesive sheets 720 at both ends of the elastic non-conductive cloth 710 can be adhered to the skin, which is simple, convenient, and easy to operate.

Based on the above embodiment, the number of the recording electrodes 120 is at least one. This setting allows testing of multiple locations on the skin.

Claims

A dry skin electrode includes a recording electrode, a ground electrode, and a reference electrode. A first end of the ground electrode is provided to be connected to a first position of an object to be tested, and a first end of the recording electrode is provided to be connected to the object to be tested. The second end of the reference electrode is connected to the third position of the object to be tested; the second end of the ground electrode is connected to the signal acquisition device through a first external interface; The second end is connected to the signal acquisition device through a second external interface, and the second end of the reference electrode is connected to the signal acquisition device through a third external interface.

The recording electrode, the ground electrode, and the reference electrode respectively include a conductive fabric, an elastic support, and a conductive connection portion. The conductive fabric is attached to the elastic support, and the conductive electrode in the recording electrode is conductive. The fabric provides an electrical signal to the signal acquisition device through the second external interface, and the conductive fabric in the ground electrode provides the ground signal to the signal acquisition device through the first external interface. The conductive fabric provides a reference signal to the signal acquisition device through the third external interface.
The dry skin electrode according to claim 1, wherein the conductive fabric is woven by a metal and non-metal mixed wire, and the composition of the metal includes at least one of nickel, zinc, silver, lead, copper and platinum, and the non-metal The composition includes at least one of nylon, silk protein, polyimide, and polyurethane.
The skin dry electrode according to claim 1, wherein the elastic support is a sponge or an elastic silicone rubber.
The dry skin electrode according to claim 3, wherein the sponge is one of polyurethane sponge, polyethylene sponge, and polystyrene sponge, and the components of the elastic silicone rubber include silicon element, oxygen element, carbon element and At least one element of sulfur.
The dry skin electrode according to claim 1, wherein the conductive connection portion in the recording electrode is connected to the second external interface through a wire, and the conductive connection portion in the ground electrode is connected to the first external interface through a wire, so The conductive connection portion in the reference electrode is connected to the third external interface through a wire.
The dry skin electrode according to claim 5, wherein the wire is one of a tail wire, a single-strand wire, a multi-strand wire, and a ribbon wire.
The dry skin electrode according to claim 5, wherein the conductive connection portion includes a metal sheet, solder, and conductive glue, the conductive fabric is connected to the metal sheet through the solder, and the metal sheet is connected through the conductive The glue is connected to the wire.
The dry skin electrode according to claim 1, further comprising an elastic non-conductive cloth, and two ends of the elastic non-conductive cloth are provided with adhesive patches, and the recording electrode, the ground electrode, and the reference electrode are provided on the Elastic non-conductive cloth.
The skin dry electrode according to any one of claims 1 to 8, wherein the number of the recording electrodes is at least one.