EP1819273A1

EP1819273A1 - Textile device for electrophysiological measurements or electrostimulation

Info

Publication number: EP1819273A1
Application number: EP05812913A
Authority: EP
Inventors: Bernhard Bischoff; Hans-Jörg ZWEIFEL; Tünde Kirstein; Markus Weder; Dirk Hegemann; Thierry Keller
Original assignee: BISCHOFF TEXTIL AG
Current assignee: BISCHOFF TEXTIL AG
Priority date: 2004-12-09
Filing date: 2005-12-09
Publication date: 2007-08-22
Also published as: WO2006060934A1

Abstract

Disclosed is a textile device for electrophysiological measurements or electrostimulation, comprising a textile layer (4) which can be biased towards the body surface of an individual wearing said device. The side of the textile layer (4) that faces the body is provided with a group of electrodes which are designed to be in skin contact. Said group of electrodes encompasses at least one electrode (2) that has a minimum height of 1 mm and is embroidered onto the textile layer.

Description

Textile device for electrophysiological measurements or electrostimulation

Technical area

The invention relates to a textile device for electrophysiological measurements or electrostimulation according to the preamble of claim 1 and to a textile device for electrophysiological measurements according to the preamble of claim 15.

PRIOR ART The integration of measuring systems in textiles has recently become increasingly important. In particular, under the keyword "smart clothes" different garments are developed, which serve to capture or monitor vital signs especially in sick people or competitive athletes.

DE 100 47 533 A1 describes an intelligent item of clothing, in particular a tight-fitting shirt or undershirt, which has a sensor mounted in or on the tissue for measuring a condition and / or a bodily function of the individual carrying the item of clothing. Examples are the monitoring of respiration, pulse or blood pressure and the

Measurement of an electrocardiogram (hereinafter: "ECG") mentioned, but the specific design of the proposed sensors is not specified.

WO 03/059101 A1 describes a method and a device for integrating electronics in textiles. In this case, the device comprises a textile material which is designed, for example, as a ribbon fabric with electrically conductive warp and / or weft threads, and an electronic component. Furthermore, hard encapsulation - for example, a two-component or a high-melting hot melt adhesive - provided which cover, inter alia, the contact point of the electronic component and stabilize mechanically. In particular, the encapsulations should allow subject the textile material, despite the permanently installed electronic component, to a textile care. However, the hard-encapsulated construction inevitably has a rigidity, which has a detrimental effect on the comfort.

Another textile device for performing an ECG measurement is described in GB 2 350 193 A. This comprises a stretchable garment which can be prestressed against the body surface of an individual carrying the device and which comprises a textile layer knitted from electrically conductive and non-conductive threads. The conductive filaments form electrically interconnected inner and outer conductive loops. In this case, the inner loops on the body-facing side of the garment and form an intended for contacting with the skin of the individual electrode. The outer loops located on the side of the garment facing away from the body form an external electrical connection region, which serves for the derivation of the ECG signals detected via the electrode to an associated measuring device. Depending on the type of ECG measurement provided, at least two or more electrodes designed in the above manner form an electrode group. However, the knitted design of the device described limits the choice of thread material used to form the electrodes, since the electrodes formed by the inner loops are part of the textile layer itself. In particular, the requirements of good electrical conductivity on the one hand and the desired for a good contact high elasticity on the other hand can be opposed.

Another textile device for carrying out an ECG measurement is described in WO 2004/100784 A1. Also in this device, a knitted electrode is provided.

WO 2004/105863 A1 was published on December 9, 2004, which is not prior to the priority date of the present application. Darstellunq of the invention

The object of the invention is to improve a generic device and in particular to avoid their disadvantages.

This object is achieved according to the invention by the device defined in claim 1.

Due to the fact that according to the invention the electrode group comprises at least one electrode embroidered on the textile layer, there are various advantages in comparison with the prior art.

In particular, in the case of embroidered electrodes, the embroidery materials, i. the yarns used are largely embroidered or largely embroidered in the three-thread system (soutache), largely independent of the material of the textile layer. In particular, can be used as the embroidery floor, an elastic base material such as polyester mesh, while for the electrodes conductive yarns of a suitable metal such as copper, steel, titanium, silver or other precious metals are used, which as a rule a much lower elasticity than the Textile layer exhibit.

Thanks to the great flexibility of the available embroidery techniques, there is a great deal of freedom with regard to the selected configuration of the electrodes. In particular, different shapes as well as surface textures can be produced by different embroidery techniques. In machine embroidery, moreover, a very rapid change between different materials is possible, which increases freedom of design and manufacturing efficiency. In addition, there is a virtually unlimited choice with regard to the dimensioning and positioning of the embroidered electrodes on the textile layer, which is particularly advantageous in the production of electrodeposited garments. - A -

The device according to the invention can be used to carry out various electrophysiological measurements which require the attachment of electrodes to the body surface of an individual. These include, for example, the measurement of ECG or electroencephalograms (EEG), the performance of electromyography (EMG) and electrooculography (EOG) measurements as well as the measurement of heart rate or body fat percentage. Furthermore, the device according to the invention is also suitable for various types of electrical stimulation. In general, the device is preferably suitable for human patients or athletes, but it can in principle be designed for animals, especially for experimental animals.

Advantageous embodiments of the above device are defined in claims 2 to 14.

It has proven advantageous if the embroidered electrodes have an irregular embroidery pattern in which the individual stitches have a substantially random orientation with respect to the adjacent stitches.

Preferably, the embroidery electrodes are at least partially embroidered from a metal-coated thread, whereby at the same time good mechanical and electrical properties can be achieved. Due to the excellent electrical conductivity, silver would be a particularly advantageous coating material. However, silver can lead to skin intolerance. In addition, silver is relatively easily oxidizable, which is why the surface layers forming change the electrical conductivity and can therefore lead to measurement errors. Thus, a double metal-coated thread is preferably used, which has a non-metallic inner thread with a silver layer and an overlying thin layer of a skin-friendly metal. For example, outer titanium, palladium or platinum coatings are suitable for this purpose. Advantageously, the electrodes are embroidered from a plurality of layers which protrude in a knob-like manner on the body-facing side of the textile layer and thereby bring about improved contact with the surface of the skin. As a result, the elastic pre-tension of the textile layer required for the electrical contact is thus lower than it would be for flat electrodes.

Preferably, the electrodes are embroidered according to the single-thread, two-thread or else the three-thread system (soutache). For example, the so-called "Bean Stitch" or the "Vermicelles" embroidery type are used for this purpose, wherein advantageously different touring layers are embroidered on top of each other. If necessary, different materials can be used for the front thread, the back thread and, if necessary, the thread sewn in the three-thread system.

Both for electrophysiological measurements and for electrostimulation, each electrode must be provided with an electrical lead, which may be provided with an insulating and / or shielding layer. Advantageously, the feed line is formed by a line wire embroidered on the textile layer, this being preferably arranged in a serpentine manner to compensate for the distortion occurring in the case of an elastic textile layer. Alternatively, the electrical supply line may be formed by a conductive textile fabric. In particular, this may be a conductor track woven into the textile layer.

For certain applications, the electrical lead has a terminal area on the body-facing side of the textile layer for an associated component, for example for a transmitter to be worn under a garment. Advantageously, however, the electrical connection region is located on the side of the textile layer facing away from the body, where it can be connected to an externally supported, easily removable component. For this purpose, the connection area is designed, for example, as a plug element. Other components may also be electronic impedance converters, amplifiers, filters and the like.

Particularly in the case of nap-type electrodes, sufficient electrical contact with the skin surface is ensured for many applications, which is a significant advantage over conventional electrodes which are bonded to the skin surface as rubber or plastic electrodes with silver / silver chloride coating. Nevertheless, it may be advantageous for certain applications to cover the embroidered electrodes with a contacting medium, preferably an electrically conductive, physiologically harmless gel. In this case, a good absorption capacity of the contacting medium can be achieved by a suitable choice of the embroidery materials.

Advantageously, the textile layer is formed as part of a garment on which the electrode group is arranged according to the intended electrophysiological measurement or electrostimulation. Conveniently, the garment provides the necessary elastic bias to push the electrode group against the skin surface. As garments, bras, undershirts (T-shirts), jackets, boleros, and trousers are used. Also advantageous are appropriately designed elastic chest straps or wristbands or wristbands.

In particular, in the case of long-term or load measurements, it may temporarily lead to movement-related interruptions or reductions in the contact between the electrode and the skin. Advantageously, therefore, the electrode group comprises a plurality of electrodes, which exceeds the number of electrodes required for a given electrophysiological measurement. Furthermore, a selection control known per se is provided, by means of which a subgroup of electrodes can be selected continuously or at predetermined time intervals, which currently delivers best measuring signals with respect to a predefined criterion. The device according to the invention as claimed in claim 15 can be used for electrophysiological measurements which require the attachment of electrodes in the vicinity of the body surface of an individual. In this case there is no direct contact between the stick electrodes and the skin, since the former are arranged on the body-side of the textile layer. Rather, in this Anordnungsari: a capacitive coupling between the electrode and the skin accomplished, whereby temporally modulated signal components can be detected.

Preferred embodiments are defined in claims 16 to 24.

Brief description of the drawings

Exemplary embodiments of the invention will be described in greater detail below with reference to the drawings, in which:

Fig. 1 shows a first example of embroidered electrode, in plan view;

FIG. 2 shows the electrode of FIG. 2 on a textile layer, in a photographic plan view; FIG.

3 shows a double-coated embroidery thread, in cross-section;

4 shows a group of electrodes according to FIGS. 1 and 2, in a photographic plan view;

5 shows an electrode arrangement on a double textile layer with rear electrical connection, in a photographic view from the rear;

Fig. 6 shows a second example of embroidered electrode, in plan view; Fig. 7 shows a first type of electrode arrangement on a human

Torso, in schematic view from the back;

8 shows the electrode arrangement of FIG. 7, in a schematic plan view;

9 shows an electrocardiogram recorded with an electrode arrangement according to FIGS. 7 and 8;

10 shows a further type of electrode arrangement, in a schematic representation;

Fig. 11 shows another type of electrode with integrated chip, in a schematic cross-sectional view.

Ways to carry out the invention

The device shown in FIGS. 1 and 2 comprises an electrode 2, which is embroidered on a serving as embroidery bottom textile layer 4 made of elastic polyester tulle, and an electrical lead wire 6. As is apparent in particular from FIG. 2, the electrode is a knob-like elevation which, for example, has a nub diameter of 1.5 cm and a height of approximately 1 to 2 mm, but if desired also more.

The electrode shown was embroidered in the three-thread system with several superimposed touring layers in the so-called "Vermicelles system". As can be seen from FIGS. 1 and 2, an irregularly appearing embroidery pattern is thereby produced. As the upper thread as well as the lower thread, one copper thread each having a denier of 190 dtex (Bischoff Phfib 010) was used; By means of these copper threads, an insulated copper thread serving as supply line 6 was embroidered. To form the required contact between the feed line 6 and the electrode 2, the lead wire 6 is stripped in its terminal contacting region prior to embroidering. Instead of copper, other conductive materials Rials such as steel, titanium, silver or other precious metals are used. As an advantageous material for the electrical supply line 6, moreover Aracon ^® (DuPont) has been found, a substrate formed of metal-coated fibers of aromatic polyamide yarn. Furthermore, also carbon fibers come into consideration.

Silver is due to its high electrical conductivity of about 63x10 ⁶ S / m, a particularly advantageous electrical coating material. However, silver can lead to skin incompatibility and tends to form surface layers which may affect electrical conductivity and thereby lead to measurement errors. For this reason, it is advantageous to attach another metal layer over the silver layer. For this outer cover layer, a metal is to be selected that is skin-friendly and chemically inert. While the inner silver layer is provided for the electrical transmission in the longitudinal direction of the thread - ie over a comparatively long distance - only the layer thickness of the outer metal layer in the radial direction has to be traversed for the electrical transmission between the skin and the silver layer - ie a comparatively short distance. Therefore, it is acceptable that the metal of the outer layer has a lower electrical conductivity than silver. Particularly suitable metals for the outer layer are titanium, platinum and palladium. Titanium has a comparatively poor electrical conductivity of about 2.6x10 ⁶ S / m compared to platinum (9.4x10 ⁶ S / m) and palladium (10x10 ⁶ S / m), but is less expensive. Obviously, therefore, the optimal choice of the outer coating metal in each case depends on the intended application.

An example of a double-coated embroidery thread is shown in FIG. On an inner thread PES made of a polyester monofilament with a diameter of 0.08 mm diameter, a silver layer Ag with a layer thickness of 100 nm and above a titanium layer Ti of 100 nm is applied. In general, the two metal layers can be applied with a layer thickness of approximately 20 to approximately 200 nm, the two layers being th same or different thicknesses. As a method of attaching the metal layers, the plasma coating is particularly suitable. In another embodiment, the inner thread is formed from a twisted polyester multifilament.

As can be seen in FIG. 4, for example, three electrodes 2 a, 2 b, 2 c embroidered on the textile layer 4 form an electrode group. The arrangement of the electrodes, i. the positioning of the individual electrodes 2a, 2b and 2c on the carrier 4 is to be selected according to the intended application. Depending on a lead wire 6a, 6b and 6c extends from an associated electrode 2a, 2b and 2c to a connector element 8, which is provided for connection to electrical supply or discharge elements, not shown. The individual lead wires 6a, 6b and 6c are designed in a serpentine manner and fastened to the textile layer 4 by means of suitably positioned stapling stitches 10 (see FIG. The meandering course of the lead wires and the distance between the individual stitches 10 allow a largely unhindered stretching or deformation of the elastic textile layer 4, which contributes significantly to the wearing comfort of the device.

If necessary, the textile layer can be formed as shown in FIG. 5 as a double layer with an inner, body-facing layer 4a and an outer, body facing away layer 4b. This may be particularly expedient in order to achieve a good pressure behavior with the outer layer 4b, while the inner layer 4a is optimized with respect to its physiological compatibility, comfort or electrical insulation capability. Also shown in FIG. 5 is an electrical connection region 12 with a plug part 14 mounted on the side of the double layer 4a, 4b facing away from the body.

A further embodiment of the electrode is shown in FIG. 6, which shows an electrode 2d, which is made with the so-called "bean-stitch" embroidery type, with associated lead wire 6d. FIGS. 7 and 8 show an electrode arrangement for measuring ECG signals. In order to obtain a reliable, low-noise ECG signal, a certain contact pressure of the electrodes on the skin surface is required. Typically, this contact pressure should be about 5 Newtons (ie 5 kgms ^{' 2} ). For this reason, the elastic textile layer serving as a support for the electrode assembly is advantageously formed as part of a suitably shaped garment, wherein the electrodes are arranged on the body-facing side of the textile layer. Such a garment is shown in FIG. 7 in the form of a body-adjacent T-shirt 18. In each case, an embroidered electrode is located on the shoulder of the left arm LA, on the shoulder of the right arm RA and on the neck N. An ECG measured with this arrangement is shown in FIG. 9, wherein the voltage difference V as a function of time t is applied.

Instead of the electrode arrangement described above, for example, the Einthoven arrangement shown in Fig. 10 can be used, in which the ECG electrodes on the left arm LA, right arm RA and the right foot RF are mounted, the latter derivative serves as a grounding point GND.

FIG. 11 shows a further embroidery electrode 2e, which is embroidered on a piece of film 4c. The embroidery electrode is located on the body-facing side of the film piece 4c. The latter is welded or glued to a further, outer textile layer 18, wherein the corresponding welding or adhesive seam 20 is shown schematically. In general, the foil back 4c is made of a non-stretchable material; the necessary contact pressure of the embroidery electrode against the skin is accomplished by an elastic outer textile layer 18. Preferably, the seam 20 is executed circumferentially and thus surrounds a pocket located between the film piece 4c and the outer textile layer 18 with evaluation chip 22 arranged therein. The latter is in electrical connection with the embroidery electrode 2e via a feed line 6e. The evaluation chip 22 is equipped with a battery and can be used for about 3 years via a wireless Connection (eg ZigBee (wireless)) Transfer measurement data to an assigned data logger. The short supply line largely avoids or reduces faults and artifacts. In a further embodiment, the evaluation chip is assigned to a whole group of adjacent electrodes, for example embroidery electrodes with a diameter of 1 cm in a circle arrangement with a diameter of 4 cm. In this case, a corresponding number of electrical leads between the evaluation chip and each electrode should be provided. When connecting the individual embroidery electrodes to one another, it is thus also possible to implement conventional diagnostic electrode leads, in particular for ECG measurements.

Regardless of whether or not the film piece 4c serves to hold an integrated evaluation chip, it is advantageous for some applications if the film material has a high water vapor transmission resistance Ret, at least in the region of the embroidery electrode; preferably this should be at least 40 In ² PaW ¹ . This leads to the formation of condensation in the area of the electrode after a short period of contact with the electrode. This in turn leads to the improvement of the electrical contact between skin and electrode, which may be possible to dispense with the attachment of a contacting medium.

In a further textile device for electrophysiological measurements, not shown, the electrode group is mounted on the side of the textile layer facing away from the body. Accordingly, the stick electrodes are not in direct contact with the skin, but are only separated therefrom by the comparatively thin textile layer. Such an electrode arrangement is suitable for a capacitive measuring operation, ie for measuring AC voltage components of a physiological signal. The embroidered electrodes are preferably also made of a thread with double metal coating (eg inside Ag, outside Ti), which combines the advantages of good electrical conductivity and good skin compatibility in itself. LIST OF REFERENCES

2, 2a, 2b, 2c, 2d, 2e embroidery electrode

4, 4a, 4b, 4c textile layer

6, 6a, 6b, 6c, 6d, 6e electrical supply line

8 plug element

10 basting stitch

12 electrical connection area

14 plugs from 12

16 T-shirt

18 outer textile layer

20 welding or adhesive seam

22 evaluation chip

LA left arm

RA right arm

Right foot

N neck

V electrical voltage t time

PES polyester

Ag silver layer

Ti titanium layer

Claims

claims

A textile device for electrophysiological measurements or for electrostimulation, comprising a textile layer (4, 4a) which can be prestressed against the body surface of an individual carrying the device and which faces the body

2, 2a, 2b, 2c, 2d), characterized in that the electrode group comprises at least one embroidery electrode (2; 2a, 2b, 2c, 2d) embroidered on the textile layer, and that the embroidery electrode a height of at least 1 mm.

2. Device according to claim 1, characterized in that the embroidery electrode has an irregular embroidery pattern.

3. Apparatus according to claim 1 or 2, characterized in that the

Embroidery electrode is at least partially embroidered from a metal-coated thread.

4. The device according to claim 3, characterized in that the metal-coated thread has a silver layer and an overlying layer of a skin-friendly metal.

5. Device according to one of claims 1 to 4, characterized in that the embroidery electrode is embroidered from a plurality of layers.

6. Device according to one of claims 1 to 5, characterized in that the embroidery electrode (2; 2a, 2b, 2c; 2d) is embroidered after the single-thread, two-thread or after the three-thread system.

7. Device according to one of claims 1 to 6, characterized in that the embroidery electrode (2, 2a, 2b, 2c, 2d) with an electrical supply line (6; 6a, 6b, 6c; 6d), which is formed by an embroidered on the textile layer (4), preferably serpentine running wire.

8. Device according to one of claims 1 to 7, characterized in that the embroidery electrode is provided with an electrical supply line, which is formed by a conductive textile fabric.

9. Apparatus according to claim 7 or 8, characterized in that the electrical supply line on the body side facing away from the textile layer

(4; 4b) located electrical connection portion (12) for an associated component.

10. Device according to one of claims 1 to 6, characterized in that it on the body side facing away from the textile layer (4c) with a

Embroidery electrode (2e) electrically connected chip (22), which is capable of wireless transmission of measurement data to an evaluation unit.

11. Device according to one of claims 1 to 10, characterized in that the embroidery electrode (2, 2a, 2b, 2c, 2d, 2e) is occupied with a Kontaktierungsme- medium.

12. Device according to one of claims 1 to 11, characterized in that the textile layer (4) is formed as part of a garment (16) to which the electrode group (LA, RA, N) according to the intended electrophysiological measurement (ECG) or Electrostimulation is arranged.

13. Device according to one of claims 1 to 12, characterized in that the textile layer (4c) at least in the region of the embroidery electrode (2e) has a high water vapor transmission resistance (Ret).

14. Device according to one of claims 1 to 13, characterized in that the electrode group comprises a plurality of electrodes, which exceeds the number of electrodes required for a given electrophysiological measurement, wherein a selection control is present, by means of which a subset of electrodes is selectable which currently provides best measurement signals with respect to a predefined criterion.

15. textile device for electrophysiological measurements, with an against the body surface of an individual wearing the device vorspannba- ren, characterized in that the textile layer is provided on the body side facing away with a group of electrodes for capacitive measuring operation, which embroidered at least one on the textile layer Embroidery electrode comprises, wherein the embroidery electrode has a height of at least 1 mm.

16. The apparatus according to claim 15, characterized in that the embroidery electrode is at least partially embroidered from a metal-coated thread.

17. The device according to claim 16, characterized in that the metal-coated thread has a silver layer and an overlying titanium layer.

18. Device according to one of claims 15 to 17, characterized in that the embroidery electrode is embroidered after the single-thread, two-thread or after the three-thread system.

19. The device according to one of claims 15 to 17, characterized in that the embroidery electrode is provided with an electrical supply line, which is formed by an embroidered on the textile layer, preferably serpentine extending lead wire.

20. Device according to one of claims 15 to 18, characterized in that the embroidery electrode is provided with an electrical supply line, which is formed by a conductive textile fabric.

21. The apparatus of claim 19 or 20, characterized in that the electrical supply line has a located on the body side facing away from the textile layer electrical connection area for an associated component.

22. Device according to one of claims 15 to 18, characterized in that it comprises on the body side facing away from the textile layer has an electrically connected to the embroidery electrode chip, which is capable of wireless transmission of measurement data to an evaluation unit.

23. Device according to one of claims 15 to 22, characterized in that the textile layer is formed as part of a garment on which the electrode group is arranged according to the intended electrophysiological measurement.

24. Device according to one of claims 15 to 23, characterized in that the electrode group comprises a plurality of electrodes, which exceeds the number of electrodes required for a given electrophysiological measurement, wherein a selection control is present, by means of which a subset of electrodes is selectable which currently provides best measurement signals with respect to a predefined criterion.