WO2020056925A1 - 皮肤干电极 - Google Patents

皮肤干电极 Download PDF

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Publication number
WO2020056925A1
WO2020056925A1 PCT/CN2018/118867 CN2018118867W WO2020056925A1 WO 2020056925 A1 WO2020056925 A1 WO 2020056925A1 CN 2018118867 W CN2018118867 W CN 2018118867W WO 2020056925 A1 WO2020056925 A1 WO 2020056925A1
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Prior art keywords
electrode
conductive
external interface
wire
acquisition device
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English (en)
French (fr)
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都展宏
王立平
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Shenzhen Institute of Advanced Technology of CAS
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Shenzhen Institute of Advanced Technology of CAS
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
    • A61B5/291—Bioelectric electrodes therefor specially adapted for particular uses for electroencephalography [EEG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/263—Bioelectric electrodes therefor characterised by the electrode materials
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/263—Bioelectric electrodes therefor characterised by the electrode materials
    • A61B5/27—Conductive fabrics or textiles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
    • A61B5/296—Bioelectric electrodes therefor specially adapted for particular uses for electromyography [EMG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/683—Means for maintaining contact with the body
    • A61B5/6832—Means for maintaining contact with the body using adhesives
    • A61B5/6833—Adhesive patches

Definitions

  • the present disclosure relates to the technical field of biomedical engineering, for example, to a skin dry electrode.
  • 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.
  • 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.
  • 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.
  • 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.
  • the elastic support is a sponge or an elastic silicone rubber.
  • the sponge is one of a polyurethane sponge, a polyethylene sponge, and a polystyrene sponge
  • the composition of the elastic silicone rubber includes at least one of silicon, oxygen, carbon, and sulfur. element.
  • 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
  • the conductive connection in the reference electrode is The part is connected to the third external interface through a wire.
  • the wire is one of a tail wire, a single-strand wire, a multi-strand wire, and a ribbon wire.
  • 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.
  • 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.
  • 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.
  • FIG. 1 is a structural diagram of a skin dry electrode according to an embodiment
  • 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
  • FIG. 4 is a schematic diagram of a medical EEG machine interface provided by an embodiment
  • FIG. 5 is a schematic diagram of an electronic pin external interface provided by an embodiment
  • FIG. 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • FIG. 2 is a schematic diagram of a skin dry electrode placement position.
  • 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
  • the reference electrode 130 is placed on the right side of the ground electrode 110.
  • 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.
  • 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.
  • 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.
  • the acquisition device 140 completes the detection.
  • 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.
  • FIG. 3 is a schematic diagram of a recording electrode provided in this embodiment.
  • 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.
  • the elastic support body 320 with different mechanical properties can achieve different purposes.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • the components of the conductive fabric 310 include metals and non-metals.
  • 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.
  • 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%.
  • 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.
  • the Shore hardness of the sponge or elastic silicone rubber is D20-D65
  • D indicates that the hardness is relatively high
  • 20 indicates that the Shore hardness value of the sponge or elastic silicone rubber is 20.
  • 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.
  • the sponge is one of polyurethane sponge, polyethylene sponge, and polystyrene sponge
  • the composition of the elastic silicone rubber includes at least one of silicon, oxygen, carbon, and sulfur. An element.
  • 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.
  • the conductive connection portion 330 is connected to the external interface 340 through a lead 350.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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
  • the metal sheet is connected to the metal sheet through the conductive adhesive.
  • the wire 350 is connected.
  • solder is used to connect the conductive fabric 310 to the metal sheet.
  • the conductive sheet is used to realize the metal sheet and the wire 350 Connection.
  • 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.
  • 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.
  • the number of the recording electrodes 120 is at least one. This setting allows testing of multiple locations on the skin.

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Abstract

一种皮肤干电极，包括记录电极（120）、接地电极（110）和参考电极（130）。接地电极（110）的第一端设置为与待测试对象的第一位置（A）相连，记录电极（120）的第一端设置为与待测试对象的第二位置（B）相连，参考电极（130）的第一端设置为与待测试对象的第三位置（C）相连，接地电极（110）的第二端通过第一外接接口（111）和信号采集设备连接，记录电极（120）的第二端通过第二外接接口（121）和信号采集设备连接，参考电极（130）的第二端通过第三外接接口（131）和信号采集设备连接。记录电极（120）、接地电极（110）和参考电极（130）包括导电织物、弹性支撑体和导电连接部，导电织物贴覆在弹性支撑体上。

Description

皮肤干电极
本公开要求申请日为2018年9月20日、申请号为201811100543.5的中国专利申请的优先权，该申请的全部内容通过引用结合在本公开中。
技术领域
本公开涉及生物医学工程技术领域，例如涉及一种皮肤干电极。
背景技术
皮肤电极在临床上应用于生物电信号的测量，以检测疾病的状态，或者检测医用和民用上被测试人员的注意力、放松程度和睡眠状态等，其中，生物电信号包括心电信号、脑电信号及肌电信号等。常见的皮肤电极有湿电极、干电极和电容电极。
湿电极多采用银-氯化银电极或其他纯金属电极，利用这种湿电极采集脑电信号等生物电信号时可以提供较低的接触阻抗，但在使用前需要进行皮肤准备且在电极表面涂抹导电膏，需要有专业机构专业人士指导，而导电膏很容易变干，且导电膏变干后采集效果较差，还容易粘在皮肤或毛发上，难以清洗，不仅成为脑电信号长期采集的瓶颈，还需要花费大量的时间精力对这种湿电极进行调试和维护。
干电极和电容电极的使用可以避免导电膏，但由于干电极通常采用接触式电极，导电部分采用金属导体，在运动状态下容易对人体带来损伤，并且接触面积的改变也会降低信号的质量，不适用于长期使用。电容电极是在不锈钢基底上镀一层电容电介质，尽管可以解决一部分问题，但制作工艺复杂，工序繁 多，成本高，而且信噪比较高。也有一些电极结构中通过采用弹簧来降低阻抗，但制作工艺相对复杂，成本较高，而且如果接触面积较小，会因压强过大带来局部皮肤红肿甚至发炎，引起不适。
发明内容
本公开提供一种皮肤干电极，可以长期使用，无需借助导电膏等粘性材料，无需专业人士指导使用，且制作简单、成本低，可以有效防止运动导致的接触阻抗变化。
一种皮肤干电极，包括记录电极、接地电极和参考电极，所述接地电极的第一端设置为与待测试对象的第一位置相连，所述记录电极的第一端设置为与待测试对象的第二位置相连，所述参考电极的第一端设置为与待测试对象的第三位置相连；所述接地电极的第二端通过第一外接接口和信号采集设备连接，所述记录电极的第二端通过第二外接接口和信号采集设备连接，所述参考电极的第二端通过第三外接接口和信号采集设备连接，其中，所述记录电极、接地电极和参考电极分别包括导电织物、弹性支撑体和导电连接部，所述导电织物贴覆在所述弹性支撑体上，所述记录电极中的导电织物通过第二外接接口向所述信号采集设备提供电信号，所述接地电极中的导电织物通过第一外接接口向所述信号采集设备提供接地信号，所述参考电极中的导电织物通过第三外接接口向所述信号采集设备提供参考信号。
在一实施例中，所述导电织物通过金属和非金属混合线材织成，金属的成分包括镍、锌、银、铅、铜和铂中的至少一种，非金属的成分包括尼龙、蚕丝蛋白、聚酰亚胺和聚氨酯中的至少一种。
在一实施例中，所述弹性支撑体为海绵或弹性硅橡胶。
在一实施例中，所述海绵为聚氨酯海绵、聚乙烯海绵和聚苯乙烯海绵中的一种，所述弹性硅橡胶的成分包括硅元素、氧元素、碳元素和硫元素中的至少一种元素。
在一实施例中，所述记录电极中的导电连接部通过导线与第二外接接口连接，所述接地电极中的导电连接部通过导线与第一外接接口连接，所述参考电极中的导电连接部通过导线与第三外接接口连接。
在一实施例中，所述导线为尾巴线、单股导线、多股导线和排线中的一种。
在一实施例中，所述导电连接部包括金属片、焊锡和导电胶，所述导电织物通过所述焊锡与所述金属片连接，所述金属片通过所述导电胶与所述导线连接。
在一实施例中，所述皮肤干电极还包括弹性非导电布，所述弹性非导线布的两端设置有粘贴片，所述记录电极、所述接地电极和所述参考电极设置在所述弹性非导电布上。
在一实施例中，所述记录电极的数量至少为一个。
本公开提供的皮肤干电极，可以长期使用，无需借助导电膏等粘性材料，无需专业人士指导，且制作简单、成本低，可以有效防止运动导致的接触阻抗变化。
附图说明
图1为一实施例提供的一种皮肤干电极的结构图；
图2为一实施例提供的一种皮肤干电极放置位置的示意图；
图3为一实施例提供的一种记录电极的示意图；
图4为一实施例提供的一种医用脑电图机接口的示意图；
图5为一实施例提供的一种电子插针外接接口的示意图；
图6为一实施例提供的一种微型神经外接接口的示意图；
图7为一实施例提供的一种弹性非导电布的示意图。
具体实施方式
下面结合附图和实施例对本公开进行说明。
本实施例提供一种皮肤干电极，可用于采集脑电信号和/或心电信号等生物电信号，完成疾病或行为状态的检测。图1为本实施例提供的一种皮肤干电极的结构图，该皮肤干电极包括记录电极120、接地电极110和参考电极130，所述接地电极110的第一端设置为与待测试对象的第一位置A相连，所述记录电极120的第一端设置为与待测试对象的第二位置B相连，所述参考电极130的第一端设置为与待测试对象的第三位置C相连。其中，待测试对象的第一位置A与待测试对象的第三位置C可以为同一位置，待测试对象的第二位置B与待测试对象的第一位置A或者待测试对象的第三位置C为不同位置。所述接地电极110的第二端通过第一外接接口111和信号采集设备140连接，所述记录电极120的第二端通过第二外接接口121和信号采集设备140连接，所述参考电极130的第二端通过第三外接接口131和信号采集设备140连接。
其中，所述记录电极120、接地电极110和参考电极130分别包括导电织物、弹性支撑体和导电连接部，所述导电织物贴覆在所述弹性支撑体上，所述记录电极120中的导电织物通过第二外接接口121向所述信号采集设备140提供电信号，所述接地电极110中的导电织物通过第一外接接口111向所述信号采集设备140提供接地信号，所述参考电极130中的导电织物通过第三外接接口131向所述信号采集设备140提供参考信号。
在一实施例中，皮肤干电极是一种可以采集脑电信号、心电信号等生物电信号的装置，皮肤干电极包括记录电极120、接地电极110和参考电极130，其中，记录电极120设置为采集脑电信号或心电信号等生物电信号，记录电极120可以放置于皮肤裸露的位置，例如前额，以减少毛发对脑电信号或心电信号等生物电信号的干扰，提高脑电信号采集的精度，同时也便于记录电极120与皮肤的贴合，实施例中以采集脑电信号为例。接地电极110设置为采集接地信号，以降低其他电信号对脑电信号的干扰，接地电极110可以放置于前额的中部，也可以放在耳垂后面。参考电极130设置为采集参考信号，信号采集设备140将采集的参考信号和电信号进行差值运算，通过差值信号反映采集的脑电信号的波动或被测试人员状态的变化，其中，参考电极130可以放置在前额，也可以放置在耳垂后面，参考电极130这样放置可以减少脑电信号中混入的心电信号，提高脑电信号的准确度。示例性的，参考图2，图2为一种皮肤干电极放置位置的示意图。在一实施例中，接地电极110放置在前额的中部，记录电极120放置在接地电极110的左侧，参考电极130放置在接地电极110的右侧。
其中，记录电极120、接地电极110和参考电极130的外形形状可以是方形，也可以是圆形，记录电极120、接地电极110和参考电极130的外形形状制作成圆形可以预防尖端效应造成的电场不均匀，记录电极120、接地电极110和参考电极130的外形形状制作成方形可以使加工方便。本实施例中对记录电极120、接地电极110和参考电极130的外形形状不作限定，为了保证测试的准确性，记录电极120、接地电极110和参考电极130的外形形状一致。
在一实施例中，记录电极120的第一端、接地电极110的第一端和参考电极130的第一端相连，接地电极110的第二端通过第一外接接口111和信号采集设备140连接，记录电极120的第二端通过第二外接接口121和信号140采 集设备连接，参考电极130的第二端通过第三外接接口131和信号采集设备140连接，因此使得记录电极120、接地电极110、参考电极130和信号采集设备140构成一个回路，当记录电极120、接地电极110和参考电极130与皮肤接触时，可以分别将脑电信号、接地信号和参考信号通过对应的外接接口传输给信号采集设备140，完成检测。为了准确反映被测试人员状态的变化，本实施例中设定记录电极120、接地电极110和参考电极130采用相同的设计，即记录电极120、接地电极110和参考电极130都包括导电织物310、弹性支撑体320和导电连接部330，且每个部分结构均相同，参考图3，图3为本实施例提供的一种记录电极的示意图。
以记录电极120为例，对每个部分结构进行说明。其中，导电织物310设置为采集脑电信号，导电织物310可以是金属导电布，也可以是金属导电布和非金属导电布混合而成的导电布，实际应用中可以根据需要选择。弹性支撑体320设置为保证记录电极120处于膨胀状态，同时避免由于被测试人员的运动导致导电织物310对人体带来损伤。在一实施例中，不同机械性能的弹性支撑体320可以实现不同的目的，例如相对较软的弹性支撑体320可以增加被测试人员的舒适度，利于长期使用，相对较硬的弹性支撑体320可以更好的支撑导电织物310，改善导电性能，降低与皮肤的接触阻抗，实际采用的弹性支撑体320可以根据需要选择。在一实施例中，导电织物310贴覆在弹性支撑体320上，当记录电极120与皮肤接触时，汗液湿润弹性支撑体320和导电织物310，使脑电电流穿过颅骨，引起导电织物310局部电位的变化，进而使导电织物310采集到脑电信号。导电连接部330设置为将导电织物310采集的脑电信号通过第二外接接口121提供给信号采集设备140，其中第二外接接口121也可以记为电极接口，设置为连接信号采集设备140，将脑电信号传输给信号采集设备140。
为了保证第二外接接口121和信号采集设备140稳定接触，在信号采集设备140允许的情况下，可以适当增大第二外接接口121的直径或长度，例如可以采用医用脑电图机接口，参考图4，图4为本实施例提供的一种医用脑电图机接口的示意图。第二外接接口121也可以采用高密度电极接口，如电子插针外接接口或微型神经外接接口，以实现多通道的信号传输，参考图5-图6，其中，图5为本实施例提供的一种电子插针外接接口的示意图，图6为本实施例提供的一种微型神经外接接口的示意图。
本实施例提供一种皮肤干电极，，可以长期使用，无需借助导电膏等粘性材料，无需专业人士指导，且制作简单、成本低，可以有效防止运动导致的接触阻抗变化。
在上述实施例的基础上，所述导电织物310通过金属和非金属混合线材织成，金属的成分包括镍、锌、银、铅、铜和铂中的至少一种，非金属的成分包括尼龙、蚕丝蛋白、聚酰亚胺和聚氨酯中的至少一种。
在一实施例中，导电织物310的成分包括金属和非金属，一方面可以通过金属采集电信号，另一方面又可以通过非金属增加导电织物310的柔韧性、舒适度和耐用度，降低噪音，其中，非金属的成分可以是有机成分。金属的成分可以是镍、锌、银、铅、铜和铂中的一种，也可以是多种，其中，镍的含量为0％-35％，所述锌的含量为0％-25％，所述银的含量为0％-90％，所述铅的含量为0％-5％，所述铜的含量为0％-95％，所述铂的含量为0％-70％。非金属的成分可以是尼龙、蚕丝蛋白、聚酰亚胺和聚氨酯中的一种或多种，其中，尼龙的含量为0％-20％，所述蚕丝蛋白的含量为0％-10％，所述聚酰亚胺的含量为0％-50％，所述聚氨酯的含量为0％-30％。导电织物310中金属的含量和非金属的含量之和为100％。
在上述实施例的基础上，所述弹性支撑体320为海绵或弹性硅橡胶，也可以是其他弹性支撑体，如弹簧和塑料的结合物。其中，海绵或弹性硅橡胶的邵氏硬度为D20-D65，D表示硬度相对较高，20表示海绵或弹性硅橡胶的邵氏硬度值为20。可选的，弹性支撑体320的外边缘可以延伸出导电织物310的外边缘，以避免导电织物310的外边缘对被测试人员造成损伤。
在上述实施例的基础上，所述海绵为聚氨酯海绵、聚乙烯海绵和聚苯乙烯海绵中的一种，所述弹性硅橡胶的成分包括硅元素、氧元素、碳元素和硫元素中的至少一种元素。
在上述实施例的基础上，所述记录电极120中的导电连接部通过导线与第二外接接口121连接，所述接地电极110的导电连接部通过导线与第一外接接口111连接，所述参考电极130中的导电连接部通过导线与第三外接接口131连接。
在一实施例中，以记录电极120为例，参考图3，导电连接部330通过导线350与外接接口340连接，当导电织物310采集脑电信号后可以通过导电连接部330和导线350传输到外接接口340，进而由外接接口340传输给信号采集设备140。为了保证导电连接部330和导线350的稳定连接，可以通过导电胶等材料使导电织物310、导电连接部330和导线350充分接触。
在上述实施例的基础上，所述导线350为尾巴线、单股导线、多股导线和排线中的一种。导线350的选择是考虑阻抗和抗弯折性能，阻抗低、抗弯折性能好的导线350可以保证脑电信号的稳定，提高被测试人员状态判断的准确性。例如可以选择尾巴线、单股导线、多股导线或排线，既可以实现和导电连接部330的充分接触，也可以避免焊锡对导线350的影响。
在上述实施例的基础上，所述导电连接部330包括金属片、焊锡和导电胶， 所述导电织物310通过所述焊锡与所述金属片连接，所述金属片通过所述导电胶与所述导线350连接。为了使金属片和导电织物310稳定接触，将金属片固定，实施例中采用焊锡将导电织物310与金属片连接，同时，为了避免焊锡对导线350的损坏，采用导电胶实现金属片和导线350的连接。
在上述实施例的基础上，所述皮肤干电极还包括弹性非导电布710，所述弹性非导线布710的两端设置有粘贴片720，所述记录电极120、所述接地电极110和所述参考电极130设置在所述弹性非导电布710上。参考图7，图7为本实施例提供的一种弹性非导电布的示意图，弹性非导电布710、记录电极120、接地电极110和参考电极130构成一个整体，测试时只需将弹性非导电布710与皮肤接触，并将弹性非导电布710两端的粘贴片720粘在皮肤上即可，简单方便，容易操作。
在上述实施例的基础上，所述记录电极120的数量至少为一个。这样设置可以实现对皮肤多个位置的测试。

Claims (9)

  1. 一种皮肤干电极，包括记录电极、接地电极和参考电极，所述接地电极的第一端设置为与待测试对象的第一位置相连，所述记录电极的第一端设置为与待测试对象的第二位置相连，所述参考电极的第一端设置为与待测试对象的第三位置相连；所述接地电极的第二端通过第一外接接口和信号采集设备连接，所述记录电极的第二端通过第二外接接口和信号采集设备连接，所述参考电极的第二端通过第三外接接口和信号采集设备连接，其中，
    所述记录电极、所述接地电极和所述参考电极分别包括导电织物、弹性支撑体和导电连接部，所述导电织物贴覆在所述弹性支撑体上，所述记录电极中的所述导电织物通过所述第二外接接口向所述信号采集设备提供电信号，所述接地电极中的所述导电织物通过所述第一外接接口向所述信号采集设备提供接地信号，所述参考电极中的所述导电织物通过所述第三外接接口向所述信号采集设备提供参考信号。
  2. 根据权利要求1所述的皮肤干电极，其中，所述导电织物通过金属和非金属混合线材织成，金属的成分包括镍、锌、银、铅、铜和铂中的至少一种，非金属的成分包括尼龙、蚕丝蛋白、聚酰亚胺和聚氨酯中的至少一种。
  3. 根据权利要求1所述的皮肤干电极，其中，所述弹性支撑体为海绵或弹性硅橡胶。
  4. 根据权利要求3所述的皮肤干电极，其中，所述海绵为聚氨酯海绵、聚乙烯海绵和聚苯乙烯海绵中的一种，所述弹性硅橡胶的成分包括硅元素、氧元素、碳元素和硫元素中的至少一种元素。
  5. 根据权利要求1所述的皮肤干电极，其中，所述记录电极中的导电连接部通过导线与第二外接接口连接，所述接地电极中的导电连接部通过导线与第一外接接口连接，所述参考电极中的导电连接部通过导线与第三外接接口连接。
  6. 根据权利要求5所述的皮肤干电极，其中，所述导线为尾巴线、单股导线、多股导线和排线中的一种。
  7. 根据权利要求5所述的皮肤干电极，其中，所述导电连接部包括金属片、焊锡和导电胶，所述导电织物通过所述焊锡与所述金属片连接，所述金属片通过所述导电胶与所述导线连接。
  8. 根据权利要求1所述的皮肤干电极，还包括弹性非导电布，所述弹性非导电布的两端设置有粘贴片，所述记录电极、所述接地电极和所述参考电极设置在所述弹性非导电布上。
  9. 根据权利要求1-8任一所述的皮肤干电极，其中，所述记录电极的数量至少为一个。
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