EP1819273A1 - Dispositif textile destine a des mesures electrophysiologiques ou a l'electrostimulation - Google Patents

Dispositif textile destine a des mesures electrophysiologiques ou a l'electrostimulation

Info

Publication number
EP1819273A1
EP1819273A1 EP05812913A EP05812913A EP1819273A1 EP 1819273 A1 EP1819273 A1 EP 1819273A1 EP 05812913 A EP05812913 A EP 05812913A EP 05812913 A EP05812913 A EP 05812913A EP 1819273 A1 EP1819273 A1 EP 1819273A1
Authority
EP
European Patent Office
Prior art keywords
electrode
embroidery
textile layer
embroidered
electrodes
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.)
Withdrawn
Application number
EP05812913A
Other languages
German (de)
English (en)
Inventor
Bernhard Bischoff
Hans-Jörg ZWEIFEL
Tünde Kirstein
Markus Weder
Dirk Hegemann
Thierry Keller
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.)
BISCHOFF TEXTIL AG
Original Assignee
BISCHOFF TEXTIL AG
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 BISCHOFF TEXTIL AG filed Critical BISCHOFF TEXTIL AG
Publication of EP1819273A1 publication Critical patent/EP1819273A1/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • 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
    • A61B5/6804—Garments; Clothes
    • 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
    • A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
    • A61B5/282—Holders for multiple electrodes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/0404—Electrodes for external use
    • A61N1/0472—Structure-related aspects
    • A61N1/0484—Garment electrodes worn by the patient

Definitions

  • 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.
  • 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
  • ECG electrocardiogram
  • WO 03/059101 A1 describes a method and a device for integrating electronics in textiles.
  • 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.
  • 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.
  • the encapsulations should allow subject the textile material, despite the permanently installed electronic component, to a textile care.
  • 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.
  • 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.
  • at least two or more electrodes designed in the above manner form an electrode group.
  • 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.
  • 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.
  • the object of the invention is to improve a generic device and in particular to avoid their disadvantages.
  • the electrode group comprises at least one electrode embroidered on the textile layer, there are various advantages in comparison with the prior art.
  • 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.
  • an elastic base material such as polyester mesh
  • 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.
  • 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.
  • the embroidered electrodes have an irregular embroidery pattern in which the individual stitches have a substantially random orientation with respect to the adjacent stitches.
  • 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.
  • silver would be a particularly advantageous coating material.
  • silver can lead to skin intolerance.
  • silver is relatively easily oxidizable, which is why the surface layers forming change the electrical conductivity and can therefore lead to measurement errors.
  • 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.
  • outer titanium, palladium or platinum coatings are suitable for this purpose.
  • 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.
  • the elastic pre-tension of the textile layer required for the electrical contact is thus lower than it would be for flat electrodes.
  • the electrodes are embroidered according to the single-thread, two-thread or else the three-thread system (soutache).
  • 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.
  • different materials can be used for the front thread, the back thread and, if necessary, the thread sewn in the three-thread system.
  • each electrode must be provided with an electrical lead, which may be provided with an insulating and / or shielding layer.
  • 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.
  • 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.
  • 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.
  • 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.
  • the connection area is designed, for example, as a plug element.
  • Other components may also be electronic impedance converters, amplifiers, filters and the like.
  • a good absorption capacity of the contacting medium can be achieved by a suitable choice of the embroidery materials.
  • 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.
  • the garment provides the necessary elastic bias to push the electrode group against the skin surface.
  • bras, undershirts (T-shirts), jackets, boleros, and trousers are used.
  • elastic chest straps or wristbands or wristbands are also advantageous.
  • the electrode group comprises a plurality of electrodes, which exceeds the number of electrodes required for a given electrophysiological measurement.
  • 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.
  • 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
  • FIGS. 1 and 2 shows a group of electrodes according to FIGS. 1 and 2, in a photographic plan view
  • FIG. 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
  • FIG. 8 shows the electrode arrangement of FIG. 7, in a schematic plan view
  • FIGS. 7 and 8 show an electrocardiogram recorded with an electrode arrangement according to FIGS. 7 and 8;
  • Fig. 11 shows another type of electrode with integrated chip, in a schematic cross-sectional view.
  • 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.
  • 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.
  • Rials such as steel, titanium, silver or other precious metals are used.
  • Aracon ® DuPont
  • Silver is due to its high electrical conductivity of about 63x10 6 S / m, a particularly advantageous electrical coating material.
  • silver can lead to skin incompatibility and tends to form surface layers which may affect electrical conductivity and thereby lead to measurement errors.
  • 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.
  • 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.
  • FIG. 1 An example of a double-coated embroidery thread is shown in FIG.
  • a silver layer Ag with a layer thickness of 100 nm and above a titanium layer Ti of 100 nm is applied on an inner thread PES made of a polyester monofilament with a diameter of 0.08 mm diameter.
  • 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.
  • the plasma coating is particularly suitable.
  • the inner thread is formed from a twisted polyester multifilament.
  • 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.
  • 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.
  • 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.
  • FIG. 6 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.
  • a certain contact pressure of the electrodes on the skin surface is required.
  • this contact pressure should be about 5 Newtons (ie 5 kgms ' 2 ).
  • 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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

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

Abstract

L'invention concerne un dispositif textile destiné à des mesures électrophysiologiques ou à l'électrostimulation, présentant une couche textile (4) pouvant être comprimée contre la surface du corps d'un individu portant le dispositif selon l'invention, pourvue sur son côté orienté vers le corps, d'un groupe d'électrodes conçu pour entrer en contact avec la peau. Ledit groupe d'électrodes comporte au moins une électrode (2) cousue sur la couche textile, présentant une hauteur d'au moins 1 mm.
EP05812913A 2004-12-09 2005-12-09 Dispositif textile destine a des mesures electrophysiologiques ou a l'electrostimulation Withdrawn EP1819273A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
CH20392004 2004-12-09
PCT/CH2005/000739 WO2006060934A1 (fr) 2004-12-09 2005-12-09 Dispositif textile destine a des mesures electrophysiologiques ou a l'electrostimulation

Publications (1)

Publication Number Publication Date
EP1819273A1 true EP1819273A1 (fr) 2007-08-22

Family

ID=35709348

Family Applications (1)

Application Number Title Priority Date Filing Date
EP05812913A Withdrawn EP1819273A1 (fr) 2004-12-09 2005-12-09 Dispositif textile destine a des mesures electrophysiologiques ou a l'electrostimulation

Country Status (2)

Country Link
EP (1) EP1819273A1 (fr)
WO (1) WO2006060934A1 (fr)

Families Citing this family (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB0519836D0 (en) * 2005-09-29 2005-11-09 Smartlife Technology Ltd Contact sensors
WO2008022482A1 (fr) * 2006-08-25 2008-02-28 Bischoff Textil Ag dispositif textile à électrodeS, en particulier pour l'électrostimulation multicanaL ou des mesures électrophysiologiques, et procédé pour sa fabrication
EP2072009A1 (fr) * 2007-12-21 2009-06-24 Brian Keith Russell Capteur d'électrocardiogramme
EP2252242B1 (fr) 2008-02-05 2016-04-13 Compex Medical S.A. Orthèse de stimulation
WO2011131233A1 (fr) * 2010-04-20 2011-10-27 Wearable Information Technologies, S.L. (Weartech) Appareil de capteur
US9272139B2 (en) 2010-07-01 2016-03-01 Marilyn J. Hamilton Universal closed-loop electrical stimulation system
WO2012145865A1 (fr) * 2011-04-29 2012-11-01 Yang Chang-Ming Procédé d'électronisation de tissu et son produit
GB2499406A (en) * 2012-02-15 2013-08-21 Michael Corbett Fabric electrode modules
ES2715386T3 (es) 2014-07-15 2019-06-04 Comftech S R L Sensor para medir señales eléctricas fisiológicas
WO2018124995A1 (fr) * 2016-12-30 2018-07-05 Inovent Fikri Mulkiyet Haklari Yonetim Ticaret Ve Yatirim Anonim Sirketi Dispositif tens portable pour la prisen en charge de la douleur chronique
DE102018133335A1 (de) * 2018-12-21 2020-06-25 Otto Bock Healthcare Products Gmbh Textilelektrode

Family Cites Families (9)

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Publication number Priority date Publication date Assignee Title
US4417581A (en) * 1979-05-23 1983-11-29 The University Of Florida Corneal electrode for electroretinography
GB2350193B (en) 1999-03-15 2003-04-09 Alan Remy Magill Health monitoring garment
AU5530900A (en) * 1999-07-01 2001-01-22 N.V. Bekaert S.A. Garment comprising electrode
DE10047533A1 (de) 2000-09-21 2002-04-11 Deutsche Telekom Ag Intelligente Kleidung
DE10202123A1 (de) 2002-01-21 2003-07-31 Infineon Technologies Ag Verfahren und Vorrichtung zur Integration von Elektronik in Textilien
US7444177B2 (en) * 2003-03-04 2008-10-28 Alireza Nazeri EKG recording accessory system (EKG RAS)
ITMI20030649A1 (it) * 2003-04-01 2004-10-02 Fond Don Carlo Gnocchi Onlu S Struttura integrata per il rilevamento di segnali
GB0311320D0 (en) 2003-05-19 2003-06-25 Univ Manchester Knitted transducer devices
GB0312517D0 (en) 2003-05-31 2003-07-09 Koninkl Philips Electronics Nv Embroidered electrode

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See references of WO2006060934A1 *

Also Published As

Publication number Publication date
WO2006060934A1 (fr) 2006-06-15

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