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WO2018133522A1 - Électrode en tissu et moniteur d'électrocardiogramme - Google Patents

Électrode en tissu et moniteur d'électrocardiogramme Download PDF

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Publication number
WO2018133522A1
WO2018133522A1 PCT/CN2017/112400 CN2017112400W WO2018133522A1 WO 2018133522 A1 WO2018133522 A1 WO 2018133522A1 CN 2017112400 W CN2017112400 W CN 2017112400W WO 2018133522 A1 WO2018133522 A1 WO 2018133522A1
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WO
WIPO (PCT)
Prior art keywords
fabric
substrate
conductive
electrode
fabric electrode
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/CN2017/112400
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English (en)
Chinese (zh)
Inventor
包磊
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Shenzhen Benevolence Medical Sci & Tech Co Ltd
Original Assignee
Shenzhen Benevolence Medical Sci & Tech Co Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Shenzhen Benevolence Medical Sci & Tech Co Ltd filed Critical Shenzhen Benevolence Medical Sci & Tech Co Ltd
Publication of WO2018133522A1 publication Critical patent/WO2018133522A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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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
    • 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
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • 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
    • A61B5/6802—Sensor mounted on worn items

Definitions

  • the invention belongs to the technical field of medical device/medical device auxiliary device, and particularly relates to a fabric electrode and an electrocardiograph.
  • cardiovascular and cerebrovascular diseases have become the most important health threat to the elderly in recent years, second only to cancer.
  • Effective prevention of sudden death caused by cardiovascular and cerebrovascular diseases is effective monitoring of the cardiovascular and cerebrovascular system of chronic diseases, especially long-term monitoring at night, which will increase the probability of catching disease changes, such as premature ventricular contractions. Monitoring requires 6 hours of monitoring to be reliably obtained.
  • the acquisition structure of the physiological electrical signal is called an electrode.
  • Conductive electrode is a common accessory on health care equipment. It can be used to evenly transmit current signals on the human body. It can also be used to collect electrical signals from human body electrical signals.
  • the electrodes are divided into various types.
  • the silica electrode is divided into water-absorbing electrodes according to its application. , heating electrodes and conductive electrodes, etc.
  • the characteristics of the conductive electrode are as follows: first, it has far-infrared rays; second, it has anti-fouling, deodorizing, absorbing toxins, and inhibiting bacteria; third is good in conductivity; fourth is electrode use. Soft and elastic, it can be applied to any part of the body.
  • the conductive electrode is made up of eucalyptus oil, medical amide and a variety of strong adhesion chemical raw materials and non-woven fibers; it is soft, comfortable, safe and hygienic, has no irritation to the skin, has no side effects, and relies on its high electrical conductivity. It can be used in all kinds of medium and low frequency physiotherapy devices as well as in medical and beauty industries.
  • fabric electrodes have been shown to better capture physiological electrical signals in the resting state of the human body, mainly due to the fact that the conductive fibers in the fabric are very close to the heart when worn (the ECG signal is strong).
  • the disadvantages of the fabric dry electrode are manifested, that is, a slight slip between the skin and the skin may cause a baseline shift of the signal; or a large impedance between the skin and the fabric electrode causes a large noise, Will affect the system's judgment of human physiological signals. Therefore, the existing electrodes of the wearable device can not solve the problem of physiological signal acquisition stability under the dynamic condition of the human body.
  • the existing electrode structure of physiological electrical signal acquisition mainly has the following problems:
  • the impedance between the existing flexible fabric of the fabric and the skin is relatively large, resulting in large signal noise and instability;
  • the object of the present invention is to overcome the above deficiencies of the prior art and to provide a fabric electrode for solving It is a technical problem that the existing fabric electrode has poor signal stability and is uncomfortable.
  • Another object of the present invention is to provide an electrocardiograph to solve the problem of signal distortion caused by poor signal stability and uncomfortable defects of the existing electrocardiograph due to the presence of electrodes, and the technical problem of limited use.
  • a fabric electrode comprises a substrate and a conductive fabric, the conductive fabric is fixedly coupled to the substrate, and a cavity is formed between the conductive fabric and the substrate, and the cavity is filled with an elastic support body, at least
  • the conductive fabric of the opposite surface region of the substrate has a honeycomb structure, and the honeycomb opening of the honeycomb structure is away from the substrate, and the conductive rubber is filled in the nest.
  • an electrocardiograph comprises an electrode and the electrode is a fabric electrode of the invention.
  • the fabric electrode of the present invention has a honeycomb structure at least in contact with the conductive fabric of the human body, and the composite structure formed by the conductive fabric and the conductive adhesive can effectively improve the gas permeability of the fabric electrode and enhance the gas permeability.
  • Comfort on the other hand, it enhances the stability of the fabric electrode structure, enhances the stability of the contact between the fabric electrode and the skin, effectively avoids the displacement of the fabric electrode, and reduces the contact resistance between the conductive fabric and the skin, and improves The resolution, sensitivity and stability of fabric electrode physiological signal monitoring.
  • the electrode of the electrocardiograph of the invention adopts the fabric electrode of the invention, thereby effectively improving the bonding force between the electrode and the skin, avoiding the relative displacement of the electrode, and reducing the impedance between the electrode and the skin, thereby improving the heart.
  • the resolution and sensitivity of the physiological signal monitoring of the electric tester is the resolution and sensitivity of the physiological signal monitoring of the electric tester.
  • FIG. 1 is a schematic structural view of a fabric electrode according to an embodiment of the present invention.
  • FIG. 2 is a schematic view showing the honeycomb structure of the conductive fabric contained in the fabric electrode according to the embodiment of the present invention
  • Figure 3 is a partial front elevational view showing the honeycomb structure of the conductive fabric contained in the fabric electrode of the embodiment of the present invention
  • FIG. 4 is a schematic view showing the structure of a substrate included in a fabric electrode according to an embodiment of the present invention.
  • inventions of the present invention provide a fabric electrode.
  • the fabric electrode structure is shown in Figures 1-4 and includes a substrate 1 and a conductive fabric 2.
  • the conductive fabric 2 is fixedly coupled to the substrate 1 , and a cavity is formed between the conductive fabric 2 and the substrate 1 , and the cavity is filled with an elastic support 3 .
  • the substrate 1 contained in the above fabric electrode provides a carrier for bonding structural members such as the conductive fabric 2.
  • the shape and size of the substrate 1 substantially determines the shape and size of the fabric electrode of the embodiment of the present invention, and the specific shape and size may be determined according to the practical application requirements of the fabric electrode.
  • the shape of the substrate 1 may be circular or square.
  • the circular diameter or square side length may be from 3 cm to 5 cm.
  • the thickness of the substrate 1 can be flexibly selected according to the material. In one embodiment, the thickness is controlled to be 1 to 5 mm.
  • the material of the substrate 1 may be selected from metals, and specifically may be stainless steel, aluminum alloy or the like. Of course, the material of the substrate 1 can also be plastic, regardless of the metal or plastic, to ensure that the conductive fabric 2 is electrically connected to the signal collection system.
  • the bonding of the substrate 1 and the conductive fabric 2 can be performed by using an adhesive, such as a conductive adhesive.
  • a pinhole structure 11 is formed on the periphery of the substrate 1. The pinhole structure is used for the passage of the sewing thread, and the two substrates 1 of the conductive fabric 2 are sewn and fixedly connected, thereby improving the stability of the connection between the two, that is, improving the stability of the fabric electrode structure.
  • the above substrate 1 is a mesh structure 12, and a pinhole structure 11 is evenly distributed at the edges thereof, as shown in FIG.
  • This structure can effectively reduce the weight of the substrate 1, that is, reduce the weight of the entire electrode and improve its gas permeability.
  • the conductive fabric 2 contained in the above fabric electrode has electrical conductivity and can effectively capture electrical signals.
  • a honeycomb structure is provided at least in the region of the conductive fabric 2 opposite to the substrate 1.
  • the entire conductive fabric 2 can also be provided in a honeycomb structure.
  • the structure of the honeycomb is shown in Figures 2 and 3.
  • the nest opening of the honeycomb structure is facing away from the substrate, that is, the opening of the nest is oriented toward a contact surface such as skin.
  • the conductive fabric 2 in the region opposite to the substrate is directly in contact with the surface to be inspected, such as the skin, when the fabric electrode is specifically operated, at least the conductive fabric 2 of the region is disposed or woven into a honeycomb structure.
  • the air permeability of the fabric is effectively improved; on the other hand, the contact surface with the conductive adhesive 4 filled in the nest is increased, thereby enhancing the bonding force between the conductive adhesive 4 and the conductive fabric 2, and the fabric electrode is improved.
  • the honeycomb structure can also provide a buffering space, and enhance the squeezing buffer space between the fabric electrode and the contact surface such as the skin, so that the fabric electrode is in close contact with the skin surface, and the gas permeability is ensured. .
  • the nest of the honeycomb structure presents a pyramid shape with the spire facing the substrate 1.
  • the nest is arranged in a pyramid shape, and when the electrode is pressed, the cushioning function of the honeycomb structure is further improved, and the fabric electrode is further improved to ensure close contact with the skin surface under the action of the pressing force, and the gas permeability is ensured.
  • the surface resistance of the conductive fabric 2 in each of the above embodiments is controlled to be not more than 10 ⁇ /m 2 .
  • the conductive fabric 2 has a thickness of 2 to 10 mm
  • the honeycomb structure has a thickness of 2 to 10 mm.
  • the conductive fabric 2, particularly the honeycomb structure region has a warp and weft density of 15 to 30/cm 2 , the warp and weft yarn density of 20 to 80, and the honeycomb structure has a cell size of 12*12. Warp and weft, 18*18 warp and weft or 24*24.
  • the honeycomb structure is formed by weaving conductive fibers according to the design of the honeycomb structure using various types of looms (swords, jets, and the like) according to the existing process.
  • the fiber material of the conductive fabric 2 is any one of silver-plated nylon filament, high-strength stainless steel filament, and polymer conductive fiber, or two or more blended fibers.
  • the conductive adhesive 4 is filled in the honeycomb structure of the above-mentioned conductive fabric 2, which on the one hand improves the bonding force between the above-mentioned fabric electrode and the contact surface such as the skin, and at the same time, assists the conductive fabric 2 to capture the electrical signal, and improves the conductive fabric 2 Sensitivity.
  • the conductive paste 4 is filled in the nest of the honeycomb structure and overflows the nest appropriately, for example, a conductive adhesive layer can be formed outside the honeycomb structure.
  • the conductive paste 4 has a bulk resistance of not more than 10 3 ⁇ cm.
  • the conductive adhesive 4 may be a conductive latex, such as a conductive material (such as graphene oxide or metal micro-nano particles, content ⁇ 10 wt%) added to the nipple material to form a bulk resistance of less than 10 3 ⁇ . Cm silica gel with a certain adhesion.
  • a conductive latex such as a conductive material (such as graphene oxide or metal micro-nano particles, content ⁇ 10 wt%) added to the nipple material to form a bulk resistance of less than 10 3 ⁇ . Cm silica gel with a certain adhesion.
  • the elastic support body 3 contained in the fabric electrode can serve as a cushioning function, and the fabric electrode can be ensured to adhere to the skin surface under the action of the pressing force, and the gas permeability is ensured.
  • the fabric electrode when used in a wearable device, the elasticity of the wearable device in contact with human skin can be flexibly adjusted, and the flexibility of wearing can be improved.
  • the thickness of the elastic support body 3 is controlled to be 5 to 10 mm.
  • the elastic support body 3 is made of any one of a sponge, a high elastic spacer fabric, and a rubber.
  • the sponge may be, but not limited to, a polyurethane foam sponge, a polyester sponge, a polyether sponge, a polyvinyl alcohol sponge, or the like.
  • the material has high elasticity and good gas permeability, thereby improving the gas permeability and the buffering ability of the above-mentioned fabric electrode, further ensuring that the fabric electrode is in close contact with the skin surface, and the gas permeability is ensured.
  • the elastic support 3 may be coated with the above-mentioned conductive fabric 2, and then the conductive fabric may be bonded to the substrate 1, such as by adhesive bonding or/and suture stitching.
  • the surface of the substrate 1 opposite to the bonding surface of the conductive fabric 2 is also fixedly coupled with a connecting member 5 for connecting the fabric electrode to the fabric electrode carrier.
  • the connection of the connecting member 5 to the fabric electrode carrier is preferably a detachable connection, of course, it may also be a fixed connection, preferably a detachable connection, such as the connecting piece 5 being a Velcro, a buckle with the female snap, and a pin. Connect any one.
  • the fixed connection can be a sewn connection.
  • the above fabric electrode not only has excellent gas permeability, enhances comfort, but also has excellent structural stability, enhances stability in contact with the skin, effectively avoids the displacement of the fabric electrode, and the skin
  • the low contact resistance between the two increases the resolution, sensitivity and stability of the physiological signal monitoring of the fabric electrode.
  • the embodiment of the invention also provides an electrocardiogram Tester.
  • the device may be a conventional electrocardiograph, or may be a wearable electrocardiograph, preferably a wearable ECG tester, the electrocardiograph contains an electrode, and the electrode is implemented by the invention described above. Example fabric electrode.
  • the bonding force between the electrode and the skin is effectively improved, the relative displacement of the electrode is avoided, and the impedance between the electrode and the skin is reduced, thereby improving the resolution and sensitivity of the physiological signal monitoring of the electrocardiograph.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Veterinary Medicine (AREA)
  • Physics & Mathematics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Cardiology (AREA)
  • Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)

Abstract

L'invention concerne une électrode en tissu et un moniteur d'électrocardiogramme. L'électrode en tissu comprend un substrat (1) et un tissu conducteur (2). Le tissu conducteur (2) est fixé au substrat (1). Une chambre est formée entre le tissu conducteur (2) et le substrat (1). La chambre renferme un élément de support élastique (3). Le tissu conducteur (2) situé en regard du substrat (1) est un tissu à structure en nid d'abeilles présentant une ouverture en nid d'abeilles orientée à l'opposé du substrat (1). Le nid d'abeilles renferme une résine conductrice (4). Le moniteur d'électrocardiogramme comprend l'électrode en tissu. L'électrode en tissu présente une respirabilité favorable et une structure relativement stable, assure un contact stable avec la peau en vue d'empêcher efficacement l'électrode en tissu de se déplacer, et réduit une résistance de contact entre l'électrode en tissu (2) et la peau. Le moniteur d'électrocardiogramme permet d'obtenir une résolution, une sensibilité et une stabilité supérieures d'un signal physiologique détecté.
PCT/CN2017/112400 2017-01-18 2017-11-22 Électrode en tissu et moniteur d'électrocardiogramme Ceased WO2018133522A1 (fr)

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CN201710040399.XA CN106551693A (zh) 2017-01-18 2017-01-18 织物电极和心电测试仪
CN201710040399.X 2017-01-18

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WO2018133522A1 true WO2018133522A1 (fr) 2018-07-26

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CN111657930A (zh) * 2020-05-21 2020-09-15 无锡驰枫信息技术有限公司 织物电极及智能心电衣
CN114934336A (zh) * 2022-05-10 2022-08-23 陕西锦澜科技有限公司 导电混纺纱线、阻燃导电织物及柔性智能可穿戴设备

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EP3632304A4 (fr) * 2017-05-29 2021-03-03 Toyobo Co., Ltd. Vêtement de mesure d'informations biométriques
CN107198519B (zh) 2017-06-30 2023-12-12 华南理工大学 一种新型吸汗织物电极
CN107411735A (zh) * 2017-08-30 2017-12-01 华南理工大学 一种生物电信号柔性干式电极及其制备方法
CN107495961A (zh) * 2017-09-25 2017-12-22 北京海思瑞格科技有限公司 心电电极及其制备方法
DE102017126463A1 (de) * 2017-11-10 2019-05-16 Ottobock Se & Co. Kgaa Orthopädietechnische Einrichtung
CN110916651A (zh) * 2018-09-20 2020-03-27 深圳先进技术研究院 一种皮肤干电极
CN110063724B (zh) * 2019-04-26 2022-03-18 清华大学 柔性生物电极及其制备方法
CN110353662A (zh) * 2019-07-30 2019-10-22 军事科学院系统工程研究院军需工程技术研究所 一种复合织物电极及其制备方法
CN113768508A (zh) * 2021-09-03 2021-12-10 厦门柯迪森科技有限公司 一种基于柔性金属纤维织物干电极的心电监测系统
CN116269407B (zh) * 2023-03-24 2025-07-08 南通大学 一种双通道织物电极
CN116671923A (zh) * 2023-06-20 2023-09-01 中北大学 一种心电电极及其制备方法

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CN111657930A (zh) * 2020-05-21 2020-09-15 无锡驰枫信息技术有限公司 织物电极及智能心电衣
CN114934336A (zh) * 2022-05-10 2022-08-23 陕西锦澜科技有限公司 导电混纺纱线、阻燃导电织物及柔性智能可穿戴设备

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