DE202018100556U1 - Textile bioelectric monitoring electrode - Google Patents

Abstract

Textile bioelectrical monitoring electrode, comprising a textile substrate and an external coupling unit, characterized in that the textile substrate is provided on the surface or in the interior with a mechanically non-detachable, integrally formed conductor with the textile substrate; the external coupling unit is connected on the one hand to the electrical conductor in terms of communication technology and on the other hand to a bioelectrical detection circuit.

Description

Technical area

The present utility model relates to the areas of portable devices and intelligent textiles, in particular relates to a textile monitoring electrode for monitoring the bioelectrical signals on the body surface.

State of the art

The term "bioelectricity" refers to changes in potential and changes in polarity that occur in the course of the life activities of bodily organs, tissues and cells. This is a type of physical, physico-chemical change during life activities that signals normal physiological activity and is also a underlying marker for living bodily tissues.

With technological advances and medical advances, the attention of society as a whole to human health is increasingly increasing. By monitoring and evaluating human bio-electricity, one obtains the information as well as rules about human health, states of motion, etc., to provide a lasting, underlying, scientific guidance.

One example is ECG monitoring, where the long-term real-time monitoring of electrocardiological signals has gradually become a technical measure for the efficient assessment of cardiovascular function. In order to realize the long-term monitoring of the electrocardiological signals on condition that the human daily life is not to be influenced, it requires in addition to the presence of lazy monitoring devices also designed for long-term efficacy Elektrokardio electrode as one of the essential conditions.

The hitherto clinically applicable electrocardioid electrode is the Ag / AgC1 electroconductive gel electrode which, however, causes the following problems after prolonged use: (1) Due to the fact that the electrode material has no air and moisture permeability, it may cause discomfort to the skin after long-term use come; (2) By gradually drying out the electroconductive gel upon prolonged use, the contact resistance between the electrodes and the skin is rapidly changed to impair the accuracy and stability of the electrocardiological signals; (3) The presence of the electrically conductive gel may also be one of the incentives for causing the discomfort of the skin such as skin allergy and so on; (4) Such electrode is not reusable, that is, it can not be reused many times.

In the heretofore commercially available heart rate band, the electrode is generally made of elastomers or silicone rubber, which dispenses with the application of the electrically conductive gel, but has the large-area rigid electrode plates without air permeability, resulting from the extreme contact with the skin during long-term Sluggishness would always lead to discomfort for the person being monitored. In order to achieve the long-term monitoring of the electrocardiological signals, the carrying capacity of the ideal electrocardioid electrode should approximate the existing textiles used in the manufacture of the garment, i.e. not only the softness like textiles, but also good air and moisture permeability. Thus, the development of the textile bioelectrical monitoring electrode can overcome the above-mentioned disadvantages and also meet the demand of modern society for long-term monitoring of the electrocardiological signals.

In another way, the sensors are applied to the field of motion and fitness for electromyographic (EMG) monitoring. In recent years, with the recognition of fitness and bodybuilding has taken part in more and more exercise and fitness. The electromagg electromaggic sensors provide real-time monitoring and display of the fitness effect, real-time data acquisition, and minor physical changes, resulting in results that are much more sensitive than traditional fitness-device-based sensor units. However, this places higher demands on the sensors. Given the peculiarity of exercise and fitness, that is, that you are always in constant motion, the sensor that can be supported by the human body must necessarily have a sufficiently good degree of adhesion and last but not least be sufficiently light and thin that there is no foreign body sensation for the skin cause to monitor person and also do not lead to heavy sweating, ie can not cause discomfort to the person being monitored. Then one can speak of the true distribution. However, the sensor having such an effect is not available in the previous market.

Content of the present utility model

Based on the technical background, this utility model necessarily provides one for monitoring the bioelectrical signals on the body surface prepared textile bioelectrical monitoring electrode ready, which has higher comfort and is often reusable.

The above object is achieved by a technical concept as follows:

A textile bioelectrical monitoring electrode, comprising a textile substrate and an external coupling unit, wherein the textile substrate is provided on the surface or in the inner space with an integrally formed with the textile substrate, integrally formed electrical conductor; wherein the external coupling unit on the one hand communicatively connected to the electrical conductor and on the other hand is linked to a bioelectric detection circuit.

The electrical conductor is an electrically conductive composite layer created by applying the electrically conductive pastes to one or two surfaces of the textile substrate by printing, applying, or spraying; or, the electrical conductor is an electrically conductive composite body formed thereby to penetrate the electrically conductive pastes in the deposition process into the textile substrate; or, the conductor is formed so as to weave the electrically conductive yarn formed by the electrically conductive pastes applied to the surface of the fiber or yarn through the weaving work into the textile substrate.

Preferably, the electrically conductive composite comprises the conductor base material and the electrically conductive particulate material distributed in the conductor base material, and the conductor base material comprises silicone rubber, polyurethane or other high molecular weight elastomers and the electrically conductive particulate material comprises carbon fiber, carbon nanotubes , Graphite particles, graphene, carbon black or metal powder.

When the electrical conductor is produced by the weaving through the electrically conductive yarn woven into the textile substrate, the textile substrate is formed as the electrically non-conductive yarn from the one-piece structure resulting from interweaving the electrically conductive yarn with the electrically non-conductive yarn and the electrical conductor then formed as the electrically conductive yarn.

More concretely, the weaving process may comprise the following steps: first, the electrically conductive gel may be applied to the fiber or yarn surface, after which the electrically conductive yarn and the electrically non-conductive yarn are woven together to form the textile with one electrically conductive side and another electrically insulated side or produce both electrically conductive sides. It should be pointed out that, if more than two types of yarns are used in the weaving industry, one type of yarn will float on the textile surface from the state of the art of the textile industry and will not appear on the back.

Preferably, the external coupling unit is designed as the electrically conductive yarn arranged stationarily on the textile substrate, as the electrically conductive snap fastener fastened to the surface of the electrical conductor, or as the extensible electrically conductive signal wire retained on the surface of the electrical conductor by printing technology.

If the external coupling unit is formed as the yarn laid out fixedly on the textile substrate, the electrical conductor is connected to the electrically conductive yarn by welding, gluing, sewing, hot stamping or embroidering.

Preferably, the electrical conductor has a shape adapted to the textile substrate or is formed as a cavity structure, or the hollow part has a round, square or other arbitrary shape, that is, the electrical conductor can be shaped in a pattern. The hollow part can have an air-permeable effect without impairing the functionality of the electrical conductor.

The electrical conductor has good electrical conductivity to meet the demand for electrocardiological signal acquisition; while achieving a good adhesion property to the textile substrate so as to protect the stable, persistent physical integrity and, more particularly, to adjust the impedance and stiffness particularly in water washing provided that the comfort, air and moisture permeability of the fabrics are maintained.

Preferably that the textile substrate is formed as a nonwoven, non-stretchable but soft tissue or braid.

In summary, the present invention proposes a combination of the electrical conductor with the textile substrate to form the textile bioelectrical monitoring electrode, which not only has a simple thin structure, but is also easy and quick to produce, due to the direct contact with the skin of monitoring object for the permanent detection of bioelectric (eg electrocardiological, electromyographic) signals is suitable and can accurately capture the bioelectric signal in different movement models, at the same time also has the excellent comfort and air permeability. This textile bioelectrical monitoring electrode can be seamlessly integrated into the other textiles, and can also adapt to different applications by designing and controlling the thickness, hardness and shape of the electrical conductor. When the electrical conductor of two or more than two unconnected textile bioelectrical monitoring electrodes is brought into contact with the human skin, the electrocardiological real-time signals can be detected or the heart rate values can be read out. Usually, the lower the impedance of the electrode is, and the greater the contact pressure, contact area, and humidity, the better quality the detected electrocardiological signals will have.

• 1. Die erfindungsgemäß hergestellte textile bioelektrische Überwachungselektrode hat geringe Impedanz und gute Weichheit, und auch besitzt gute Luft- und Feuchtigkeitsdurchlässigkeit;
• 2. Die Elektrode ist mit Dünnheit, ohne geschichtes Berührungsgefühl und nicht zuletzt hautfreundlich und glatt ausgebildet, sodass sie dazu verwendet wird, die bioelektrische (z.B. elektrokardiologischen, elektromyographischen) Signale langfristig zu überwachen, ohne dass es zur Hautreizung oder Hautallergie kommt;
• 3. Unter Nutzung der Verfahren wie Bedrucken, Applizieren, Aufspritzen, Abscheiden, Weben usw. werden der elektrische Leiter und das Textilsubstrat zu einer unlösbaren Einheit verarbeitet, wobei der Verfahrensprozeß einfach, schnell und effizient ist und die Leitfähigkeit, Dicke, Härte sowie Ausformung des elektrischen Leiters allesamt einstellbar sind;
• 4. Es ist wasserbeständig (bis 80 Male) und kann gut in die bei der Bekleidung eingesetzten Textilen integriert werden; es kann bei vielfältigen trägbaren Elektronik-Systemen und intelligenten Textilen einschließlich Herzfrequenz-Bändern, elektrokardiologischen Westen, Herzfrequenz-Kleidungen, elektromyographischen Kleidungen, intelligenten Unterbekleidungen usw. Anwendung finden;
• 5. Infolgedessen, dass die Dicke des Fertigprodukts so niedrig wie 0,5 mm sein kann, und dass sich die Luftdurchlässigkeit durch Einstellung des Musters, der Lochanzahl, der Apertur der Durchlöcher verändern und die Weichheit dem in der Bekleidung eingesetzten Polyester-Baumwoll-Mischgewebe annähern kann, trifft kein Fremdkörpergefühl auf.

Compared with the prior art, the present utility model has the following advantages:

• 1. The textile bioelectrical monitoring electrode made according to the invention has low impedance and good softness, and also has good air and moisture permeability;
• 2. The electrode is designed with thinness, no touch of touch and not least skin-friendly and smooth, so that it is used to monitor the long-term bioelectric (eg electrocardiologic, electromyographic) signals without causing skin irritation or skin allergy;
• 3. Using the methods such as printing, application, spraying, deposition, weaving, etc., the electrical conductor and the textile substrate are processed into a non-detachable unit, wherein the process process is simple, fast and efficient and the conductivity, thickness, hardness and shape of the electrical conductor are all adjustable;
• 4. It is water resistant (up to 80 times) and can be well integrated into garments used in clothing; it can be applied to a variety of portable electronic systems and smart textiles including heart rate bands, electrocardiological vests, heart rate clothing, electromyographic apparel, smart underwear, etc.
• 5. As a result, the thickness of the finished product may be as low as 0.5 mm, and the air permeability is changed by adjustment of the pattern, the number of holes, the aperture of the holes and the softness of the polyester-cotton blend used in the garment can approach, meets no foreign body feeling.

Brief description of the drawings

1 schematically shows the basic structure of the first embodiment

of the present utility model;

2 schematically shows the basic structure of the second embodiment of the present utility model;

3 shows the electrocardiogram during sitting activity for the mentioned in the technical background disposable gel electrode;

4 shows the electrocardiogram during the sitting operation for the textile electrode in the first embodiment of the present utility model;

5 shows the electrocardiogram during the sitting operation for the textile electrode in the second embodiment of the present utility model.

Detailed embodiments

The present utility model and its advantageousness will be described in more detail with reference to concrete embodiments. However, these embodiments are not to be construed as limiting.

Embodiment 1.

How out 1 can be seen, this embodiment proposes a textile bioelectrical monitoring electrode, comprising the electrical conductor 1 , the textile substrate 3 as well as the external coupling unit 2 , The electrical conductor 1 completely covers the underlying textile substrate 3 , The electrical conductor 1 is made of graphite / silicone rubber composite; the underlying textile substrate 3 consists of polyester nonwoven; the external coupling unit 2 is called the on the surface of the electrical conductor 1 fixedly mounted metallic copper-nickel snap fastener selected.

The processing steps for the bioelectric monitoring biological electrode of the present embodiment include:
First, the electrically conductive graphite / silicone rubber gel becomes evenly on the surface of the underlying textile substrate material by the screen printing 3 applied; The fact that the silicone rubber hardens after heating, the electrical conductor 1 Curing of the silicone rubber is one such process in which the small molecules of the silicone rubber crosslink to large molecules and, as the macroscopic finding, the silicone rubber is converted from liquid to solid elastomer; at the edge of the main body of the textile substrate 3 and the electrical conductor 1 comprehensive textile bioelectrical monitoring electrode round holes are provided; the spike of the snap closure and the pinout are pressed in place of the through holes to the external coupling unit 2 to build.

Embodiment 2.

How out 2 As can be seen, this embodiment proposes a textile bioelectrical monitoring electrode comprising the electrical conductor 10 , the textile substrate 30 as well as the external coupling unit 20 , The electrical conductor 10 uses a mold, which partially through the textile substrate 30 is covered. The electrical conductor 10 is made of graphite / silicone rubber composite; the underlying textile substrate 30 consists of polyester nonwoven; the external coupling unit 20 is called that on the electrical conductor 10 sewn, silver plated and electrically conductive yarn formed, at which point the silicone rubber layer is applied for packaging and protection.

The processing steps for the bioelectric monitoring biological electrode of the present embodiment include:
Design of the mold of the sieve plate;
First, the electrically conductive carbon black / silicone rubber gel is uniformly screen printed on the underlying textile Subtratmaterial 30 applied; The fact that the silicone rubber hardens after heating, the electrical conductor 10 generated, wherein the electrical conductor 10 together with the textile substrate 30 forming the main body of the textile bioelectrical monitoring electrode;
At the edge of this main body, the silver-plated electrically conductive yarn is sewn to the external coupling unit 20 train. In place of the silver-plated electrically conductive yarn, the silicone rubber acting as packaging and protection is applied.

In the two embodiments mentioned above, the electrical conductor and the textile substrate of the textile bioelectrical monitoring electrode are also formed as one piece. Whether the screen printing process, or the coating process, can also connect the electrical conductor to the textile substrate in a mechanically insoluble uncoated manner. By selecting the appropriate material for the textile substrate, the thin, soft, skin-friendly, air-permeable and reusable finished product can be realized.

When comparing between 3 and 4 . 5 It can be seen that for the created using the 1st and 2nd embodiments electrocardiogram Although no other effect than that of using the conventional once-usable gel electrode (namely AgAgCl electrode) created electrocardiogram is achieved, but the textile electrode of present utility model obviously has a simpler, thinner structure and is formed with washability, softness and better skin friendliness.

The above embodiments are merely illustrative of the technical concepts and features of the present invention so that those skilled in the art can already understand and practice the contents of the present invention without limiting the claimed scope. All equivalent modifications and variations, which are made according to the spirit of the present invention, all fall within the claimed scope of the present utility model.

Claims (8)

Textile bioelectrical monitoring electrode, comprising a textile substrate and an external coupling unit, characterized in that the textile substrate is provided on the surface or in the interior with a mechanically non-detachable, integrally formed conductor with the textile substrate; the external coupling unit is connected on the one hand to the electrical conductor in terms of communication technology and on the other hand to a bioelectrical detection circuit. A bioelectric monitoring bioelectronic electrode according to claim 1, characterized in that the electrical conductor is a conductive composite layer formed by applying the conductive pastes to one or two surfaces of the textile substrate by printing, applying or spraying; or that the electrical conductor is an electrically conductive composite body produced thereby by penetrating the electrically conductive pastes into the textile substrate during the deposition process; or that the electrical conductor is produced in such a way as to weave the conductive yarn which forms by means of the conductive pastes applied to the surface of the fiber or yarn through the weaving work into the textile substrate. A bioelectric monitoring bioelectronic electrode according to claim 2, characterized in that the electrically conductive composite constituting the composite electrically conductive layer and the composite conductive body, the conductor base material and the electrically conductive particulate material distributed in the conductor base material, and that the conductor base material is silicone rubber, polyurethane or other high molecular weight elastomers and the electrically conductive particulate material is carbon fiber, carbon nanotubes, graphite particles, graphene, carbon black or metal powder , Textile bioelectrical monitoring electrode according to claim 3, characterized in that when the electrical conductor is produced by the weaving through the woven into the textile substrate electrically conductive yarn, namely the textile substrate as the electrically non-conductive yarn of the interleaving of the electrically conductive yarn with the electrically non-conductive yarn formed one-piece structure is formed and the electrical conductor is the electrically conductive yarn. Textile bioelectrical monitoring electrode according to claim 1, characterized in that the external coupling unit as the stationary on the textile substrate arranged electrically conductive yarn, as the held with the surface of the electrical conductor electrically conductive snap fastener or as the pressure technically held on the surface of the electrical conductor stretchable electrically conductive signal wire is formed. Textile bioelectrical monitoring electrode according to claim 5, characterized in that, when the external coupling unit is formed as the yarn held on the textile substrate, the electrical conductor is connected to the electrically conductive yarn by welding, gluing, sewing, hot stamping or embroidering. Textile bioelectric monitoring electrode according to one of claims 1 to 6, characterized in that the electrical conductor has a shape adapted to the textile substrate, or that the electrical conductor is formed according to a pattern. Textile bioelectric monitoring electrode according to one of claims 1 to 6, characterized in that the textile substrate is formed as a nonwoven, non-stretchable yet soft tissue or mesh.

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