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WO2008152588A2 - Materiaux pour capteurs capacitifs - Google Patents

Materiaux pour capteurs capacitifs Download PDF

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Publication number
WO2008152588A2
WO2008152588A2 PCT/IB2008/052298 IB2008052298W WO2008152588A2 WO 2008152588 A2 WO2008152588 A2 WO 2008152588A2 IB 2008052298 W IB2008052298 W IB 2008052298W WO 2008152588 A2 WO2008152588 A2 WO 2008152588A2
Authority
WO
WIPO (PCT)
Prior art keywords
capacitive sensor
insulating separation
skin
separation material
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/IB2008/052298
Other languages
English (en)
Other versions
WO2008152588A3 (fr
Inventor
Bastiaan Feddes
Lena Gourmelon
Gerardus Rudolph Langereis
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.)
Koninklijke Philips NV
Original Assignee
Koninklijke Philips Electronics NV
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 Koninklijke Philips Electronics NV filed Critical Koninklijke Philips Electronics NV
Publication of WO2008152588A2 publication Critical patent/WO2008152588A2/fr
Publication of WO2008152588A3 publication Critical patent/WO2008152588A3/fr
Anticipated expiration legal-status Critical
Ceased 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
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A61B5/7207—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts
    • 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
    • A61B5/30—Input circuits 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
    • A61B5/30—Input circuits therefor
    • A61B5/302—Input circuits therefor for capacitive or ionised electrodes, e.g. metal-oxide-semiconductor field-effect transistors [MOSFET]
    • 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
    • A61B5/30—Input circuits therefor
    • A61B5/305—Common mode rejection

Definitions

  • the subject matter relates to capacitive sensors for sensing body electrical fields present at a location on the surface of the body and more specifically to the materials used for the capacitive sensors.
  • US patent document 20050177038 discloses a bio-electrode for detecting heart signals comprising a dry electrode surface having an elevated resistivity to reduce the effect of polarization noise.
  • Such types of bio-electrodes are susceptible to motion artefacts. These motions generate static charges that can affect proper functioning of the bio -electrodes.
  • the method comprises substantially matching the tribo-electric property of the insulating separation material or the material used for the housing with that of the skin of the body and selecting the material based on the outcome of the matching is disclosed.
  • Fig. 4a and Fig. 4b schematically shows results of five measurements of the differential voltages obtained using a pair of exemplary contact less Electro-myogram (EMG) capacitive sensors;
  • EMG Electro-myogram
  • Fig. 5 schematically shows an embodiment of the capacitive sensor comprising a conductive coating on the insulating layer
  • Fig. 8 schematically shows an embodiment of the capacitive sensor implemented using tribo-electric materials.
  • the word sensor in this document refers to the capacitive sensor comprising the whole sensing element, consisting of an electrode (e.g. conductive plate) and a surrounding package. It is further noted here that often electrophysiological measurements are made using a pair of sensors.
  • EMG and Electro-cardiograph (ECG) sensors are commonly used in a bipolar setup which means that two sensors are used in combination with a third one (reference or local ground) to limit common mode signals.
  • the bipolar capacitive sensor configuration comprises: 1. sensor
  • analog filtering/anti-aliasing circuits 4. an analog to digital converter
  • C-dV/dt describes the desired behavior: the translation of a surface potential to an electrode current.
  • V-dC/dt describes the origin of the motion artefact because dC/dt is not equal to zero because C changes in time.
  • the impedance converters (the small triangles in Fig. 1) have a resistor at their input of typically IOOGO to drain (static) charge on the electrode to ground. This trick does not drain away charge from the sensor surfaces, for example the packaging of the electrode, as there is no galvanic contact between electrode and sens or surface. Therefore, it would be advantageous to have a method to avoid static charge on the non conductive parts.
  • a capacitive sensor (200) for sensing electrical fields of a body comprising an electrode, a shield, an insulating separation material, wherein the electrode and the shield are separated by an insulating separation material and a housing including associated electronic circuits, wherein the tribo-electric property of the insulating separation material or the material used for the housing (206) substantially matches with that of the skin of the body thereby reducing the generation of static charge on the capacitive sensor is disclosed.
  • the housing containing the associated electronics may form a part of the capacitive sensor or may be present outside (i.e. external) the capacitive sensor connected by wires.
  • Fig. 2b shows the layout of the capacitive sensor 200 with all layers. The housing for the electronics is not shown.
  • 202 is the electrode and 204 is the shield (guard) that is shielding the electrode from picking up noise from the outside.
  • the electrode 202 and the shield 204 are separated with insulating separation material (while the electrode 202 and the shield 204 are also electrically separated from one another).
  • the insulating separation material and all the packaging material used for the housing 206 are implemented in a tribo-electric safe material (i.e. the materials are tribo -electrically well chosen).
  • the copper electrode is surrounded by a polyimide polymer or other insulating layer, making it a capacitive sensor as no conductive (galvanic) contact between skin and electrode plate is possible using this device.
  • the inventors have found that the choice to use polyimide from a tribo-electric point is bad.
  • the human skin is on the extreme positive charge generating side of the tribo-electric series (see appendix A) while polyimide is on the negative side.
  • Fig. 4a and Fig. 4b an experiment was carried out to prove that the assumption of static charge induced motion artefacts is valid.
  • the vertical axis is the differential voltage and the horizontal axis is the time in seconds.
  • Fig. 4a and Fig. 4b differ only in the vertical scaling of the graphs (1Ox).
  • a sensor consisting of a copper electrode in a polyimide package was used. The sensor was tested with:
  • the capacitive sensor comprises a conducting coating disposed substantially around the insulating separation material such that the conducting coating is substantially close to the skin of the body so as to facilitate quick discharge of the static charges generated in the capacitive sensor-to-skin interface.
  • insulating separation material such that the conducting coating is substantially close to the skin of the body so as to facilitate quick discharge of the static charges generated in the capacitive sensor-to-skin interface.
  • this coating can even be in the form of textile that is fixed to the insulating material because as soon as it is fixed (glued for example) no relative movement will occur and no static charges will be generated).
  • discharging can be promoted by applying a metal or other conductive coating on top of the capacitive sensor.
  • This metal layer is not in galvanic contact with the capacitive plate (electrode) meant for picking up the body electrical fields.
  • the capacitive plate electrode
  • this idea appears counter intuitive, especially because the contact less sensors were mentioned to no longer need a conductive/galvanic contact between skin and sensor.
  • the electrical contact to the skin can be of low quality, different than in case of real galvanic measurements where a stable interface is needed.
  • 602 relates to the voltage measurements of the polyimide electrode mounted on the skin and 604 relates to the voltage measurements of the polyimide electrode covered by an aluminum mounted on the skin.
  • the DC component represented by 604 (aluminum covered electrode) is about 0, because no net static charges are present (they were dissipated very efficiently) and upon shaking the human arm almost no effect could be seen in the sensor output.
  • 602 show big effects due to static charge.
  • the conductive polymers applied on the insulating material as wires, mesh or solid material might serve the purpose of promoting rapid discharge of static charges, thereby stimulating proper functioning of the sensor and correct measurement of body electrophysiological signals.
  • the wires should be in the material in such a way that they cannot touch the electrode.
  • the case for clean room clothing is different that the conducting parts around the capacitive sensors should not be grounded, as electrical noise will be picked up which becomes visible on the capacitive electrode as a noise signal.
  • a metal contact will also do, because during movements there will always be a small part of the conducting coating/wires in contact with the skin, serving the purpose of a rapid discharge.
  • the tribo-electric property of the insulating separation material used for the insulating- to-skin interface is substantially close to the tribo- electric property of the skin of the body.
  • a material with poor tribo-electric properties relative to the skin e.g. polyimide
  • a material with better tribo-electric properties relative to the skin e.g. polyimide
  • a material with better tribo- electric properties e.g. polyimide
  • a material is chosen that has better tribo- electric properties.
  • the layer of the sensor that is in direct contact to the skin is to be chosen carefully as the static charges that develop between sensor surface and skin cause the problems. It is noted that those parts touching the body need to be of a suitable material, especially the sensor surface touching the skin. Hence, having trbio -electrically matched materials can reduce the generation of static charges.
  • Glass is the best material with respect to the tribo-electric series, but is at first sight the least practical to assemble into a comfortable wearable sensor. However, a very thin layer of glass, for example applied by spin coating, might not decrease comfort while significantly improving performance of a capacitive sensor. Further, the above-mentioned materials are relatively close in tribo- electric properties to the human skin, at least much closer than polymeric materials that are commonly used.
  • the textiles have, besides the advantage of suitable tribo-electric properties, the added advantage of comfort and easy integration in garments.
  • the insulating separation material and the housing are woven or knitted by interlacing strands of a fabric selected from the group consisting of nylon, wool, silk and cotton.
  • a fabric selected from the group consisting of nylon, wool, silk and cotton.
  • the insulating separation material and the housing are laminated on a textile substrate by combining thin layers of textile material.
  • the advantage of laminating is that it can be applied after the apparel is finalized. In this way, the textile production process is decoupled from the sensor realization process. This has a logistic advantage in the industry.
  • the insulating separation material and the housing are embroidered or sewn or embedded on a textile substrate using a thread.
  • the advantage of sewing is that it is an application method which is easily done in difficult places on finalized apparel, for example next to a stitch, button or joint
  • advantage of integration into textile is that textiles are already on the human body and the measurement system is to be merged with the natural surroundings for unobtrusive measurements. All textile application methods (weaving, embroidery and lamination) are known in the textile industry and appear quite common to the user.
  • the wiring of the capacitive sensor preferably should have good tribo -electric properties. Choosing sensor wiring with a suitable coating might help reduce static charging problems.
  • the disclosed capacitive sensor is useful in all applications where motions are present during measurement of electrophysiological signals from the body.
  • Some applications are ECG, EMG, wearables for repetitive strain injury prevention, heart-rate straps, ECG, EMG sensors in chairs or beds.
  • the presence of human hair in such measurement also necessitates the ideas disclosed in the present patent application: avoiding charge formation and facilitating efficient charge dissipation. This is advantageous in performing capacitive EEG measurements on the hair covered environment of the head.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Molecular Biology (AREA)
  • Animal Behavior & Ethology (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Veterinary Medicine (AREA)
  • Surgery (AREA)
  • Physics & Mathematics (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Microelectronics & Electronic Packaging (AREA)
  • Signal Processing (AREA)
  • Artificial Intelligence (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Physiology (AREA)
  • Psychiatry (AREA)
  • Investigating Or Analyzing Materials By The Use Of Electric Means (AREA)
  • Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)

Abstract

L'invention concerne un capteur capacitif (200) servant à détecter les champs électriques d'un corps. Ce capteur comprend une électrode, un blindage, un matériau de séparation isolant séparant l'électrode du blindage, ainsi qu'un logement contenant des circuits électroniques associés, la propriété triboélectrique du matériau de séparation isolant ou du matériau utilisé pour le logement (206) correspondant sensiblement à celle de la peau, ce qui réduit la production de charge statique sur le capteur capacitif. Ledit capteur est utile dans toutes les applications où des mouvements sont effectués pendant la mesure de signaux électrophysiologiques provenant du corps, telles que l'électrocardiogramme (ECG), l'électromyogramme (EMG), des dispositifs destinés à être portés pour la prévention des lésions par microtraumatismes répétés, des sangles de contrôle de fréquence cardiaque, des capteurs ECG et EMG placés sur des sièges ou des lits.
PCT/IB2008/052298 2007-06-15 2008-06-11 Materiaux pour capteurs capacitifs Ceased WO2008152588A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP07301113.2 2007-06-15
EP07301113 2007-06-15

Publications (2)

Publication Number Publication Date
WO2008152588A2 true WO2008152588A2 (fr) 2008-12-18
WO2008152588A3 WO2008152588A3 (fr) 2009-06-18

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Cited By (27)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2010140106A1 (fr) 2009-06-05 2010-12-09 Koninklijke Philips Electronics N.V. Systeme de detection capacitif
WO2011094606A3 (fr) * 2010-02-01 2011-10-20 Proteus Biomedical, Inc. Système de rassemblement de données
US20120199755A1 (en) * 2011-02-03 2012-08-09 Space Admi. Electric Field Quantitative Measurement System and Method
CN102973261A (zh) * 2011-09-02 2013-03-20 中国科学院电子学研究所 一种用于动态心电监测的电容耦合式电场传感器
US20130165813A1 (en) * 2011-12-23 2013-06-27 Industrial Technology Research Institute Sensor for acquiring muscle parameters
US20140125358A1 (en) * 2012-07-13 2014-05-08 Rescon Ltd Reducing movement and electrostatic interference in a non-resistive contact sensor assembly
WO2014033234A3 (fr) * 2012-08-31 2014-05-30 Rescon Limited Stabilisation de signal dans un ensemble capteur de contact non résistif
JP2014212971A (ja) * 2013-04-25 2014-11-17 株式会社デンソー 心電波形計測装置
US8937554B2 (en) 2011-09-28 2015-01-20 Silverplus, Inc. Low power location-tracking device with combined short-range and wide-area wireless and location capabilities
US9008761B2 (en) 2010-02-01 2015-04-14 Proteus Digital Health, Inc. Two-wrist data gathering system
WO2015094378A1 (fr) * 2013-12-20 2015-06-25 Apple Inc. Détecteur de proximité cutanée et d'effet de déséquilibre
EP2774535A4 (fr) * 2011-11-02 2015-07-08 Nipro Corp Électrocardiographe et bioélectrode
US9084566B2 (en) 2006-07-07 2015-07-21 Proteus Digital Health, Inc. Smart parenteral administration system
US9125979B2 (en) 2007-10-25 2015-09-08 Proteus Digital Health, Inc. Fluid transfer port information system
EP2465427A3 (fr) * 2010-12-17 2015-09-23 Polar Electro Oy Circuit d'atténuation d'interférence pour mesures biométriques
CN105942678A (zh) * 2016-07-18 2016-09-21 广东乐源数字技术有限公司 一种手环离手判断的方法
EP2747637B1 (fr) * 2011-08-24 2017-03-08 T&W Engineering A/S Moniteur d'eeg à électrodes capacitives
US9603542B2 (en) 2009-07-13 2017-03-28 Koninklijke Philips N.V. Electro-physiological measurement with reduced motion artifacts
US9804199B2 (en) 2013-11-19 2017-10-31 The United States of America as Represented by NASA Ephemeral electric potential and electric field sensor
US10024900B2 (en) 2016-06-09 2018-07-17 United States Of America As Represented By The Administrator Of Nasa. Solid state ephemeral electric potential and electric field sensor
EP3459449A1 (fr) * 2017-09-26 2019-03-27 Nokia Technologies Oy Appareil de détection de biosignaux
US10281430B2 (en) 2016-07-15 2019-05-07 The United States of America as represented by the Administratior of NASA Identification and characterization of remote objects by electric charge tunneling, injection, and induction, and an erasable organic molecular memory
GB2570535A (en) * 2017-09-05 2019-07-31 B Secur Ltd Non-contact authentication device
US10620252B2 (en) 2017-01-19 2020-04-14 United States Of America As Represented By The Administrator Of Nasa Electric field imaging system
US10712378B2 (en) 2016-07-01 2020-07-14 United States Of America As Represented By The Administrator Of Nasa Dynamic multidimensional electric potential and electric field quantitative measurement system and method
US10900930B2 (en) 2016-07-15 2021-01-26 United States Of America As Represented By The Administrator Of Nasa Method for phonon assisted creation and annihilation of subsurface electric dipoles
US20230000413A1 (en) * 2021-06-30 2023-01-05 Siemens Healthcare Gmbh Integrated differential voltage measuring system

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2002065904A1 (fr) * 2001-02-23 2002-08-29 Cordless Antistatic Research Inc. Bioelectrode de detection perfectionnee

Cited By (41)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9084566B2 (en) 2006-07-07 2015-07-21 Proteus Digital Health, Inc. Smart parenteral administration system
US9125979B2 (en) 2007-10-25 2015-09-08 Proteus Digital Health, Inc. Fluid transfer port information system
CN102458239B (zh) * 2009-06-05 2015-03-25 皇家飞利浦电子股份有限公司 电容式感测系统
CN102458239A (zh) * 2009-06-05 2012-05-16 皇家飞利浦电子股份有限公司 电容式感测系统
WO2010140106A1 (fr) 2009-06-05 2010-12-09 Koninklijke Philips Electronics N.V. Systeme de detection capacitif
US8847613B2 (en) 2009-06-05 2014-09-30 Koninklijke Philips N.V. Capacitive sensing system
US9603542B2 (en) 2009-07-13 2017-03-28 Koninklijke Philips N.V. Electro-physiological measurement with reduced motion artifacts
WO2011094606A3 (fr) * 2010-02-01 2011-10-20 Proteus Biomedical, Inc. Système de rassemblement de données
US10376218B2 (en) 2010-02-01 2019-08-13 Proteus Digital Health, Inc. Data gathering system
US9014779B2 (en) 2010-02-01 2015-04-21 Proteus Digital Health, Inc. Data gathering system
US9008761B2 (en) 2010-02-01 2015-04-14 Proteus Digital Health, Inc. Two-wrist data gathering system
EP2465427A3 (fr) * 2010-12-17 2015-09-23 Polar Electro Oy Circuit d'atténuation d'interférence pour mesures biométriques
US9279719B2 (en) * 2011-02-03 2016-03-08 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Electric field quantitative measurement system and method
US20120199755A1 (en) * 2011-02-03 2012-08-09 Space Admi. Electric Field Quantitative Measurement System and Method
EP2747637B1 (fr) * 2011-08-24 2017-03-08 T&W Engineering A/S Moniteur d'eeg à électrodes capacitives
CN102973261A (zh) * 2011-09-02 2013-03-20 中国科学院电子学研究所 一种用于动态心电监测的电容耦合式电场传感器
CN102973261B (zh) * 2011-09-02 2014-05-14 中国科学院电子学研究所 一种用于动态心电监测的电容耦合式电场传感器
US8937554B2 (en) 2011-09-28 2015-01-20 Silverplus, Inc. Low power location-tracking device with combined short-range and wide-area wireless and location capabilities
US10080505B2 (en) 2011-11-02 2018-09-25 Nipro Corporation Electrocardiograph and bioelectrode pad
EP2774535A4 (fr) * 2011-11-02 2015-07-08 Nipro Corp Électrocardiographe et bioélectrode
US20130165813A1 (en) * 2011-12-23 2013-06-27 Industrial Technology Research Institute Sensor for acquiring muscle parameters
US20140125358A1 (en) * 2012-07-13 2014-05-08 Rescon Ltd Reducing movement and electrostatic interference in a non-resistive contact sensor assembly
US20140152319A1 (en) * 2012-07-13 2014-06-05 Rescon Ltd Reducing movement and electrostatic interference in a non-resistive contact sensor assembly
US9157946B2 (en) * 2012-07-13 2015-10-13 Rescon Ltd Reducing movement and electrostatic interference in a non-resistive contact sensor assembly
WO2014033234A3 (fr) * 2012-08-31 2014-05-30 Rescon Limited Stabilisation de signal dans un ensemble capteur de contact non résistif
JP2014212971A (ja) * 2013-04-25 2014-11-17 株式会社デンソー 心電波形計測装置
US9804199B2 (en) 2013-11-19 2017-10-31 The United States of America as Represented by NASA Ephemeral electric potential and electric field sensor
WO2015094378A1 (fr) * 2013-12-20 2015-06-25 Apple Inc. Détecteur de proximité cutanée et d'effet de déséquilibre
US10024900B2 (en) 2016-06-09 2018-07-17 United States Of America As Represented By The Administrator Of Nasa. Solid state ephemeral electric potential and electric field sensor
US10712378B2 (en) 2016-07-01 2020-07-14 United States Of America As Represented By The Administrator Of Nasa Dynamic multidimensional electric potential and electric field quantitative measurement system and method
US11293964B2 (en) 2016-07-01 2022-04-05 United States Of America As Represented By The Administrator Of Nasa Dynamic multidimensional electric potential and electric field quantitative measurement system and method
US11360048B2 (en) 2016-07-15 2022-06-14 United States Of America As Represented By The Administrator Of Nasa Method for phonon assisted creation and annihilation of subsurface electric dipoles
US10281430B2 (en) 2016-07-15 2019-05-07 The United States of America as represented by the Administratior of NASA Identification and characterization of remote objects by electric charge tunneling, injection, and induction, and an erasable organic molecular memory
US10900930B2 (en) 2016-07-15 2021-01-26 United States Of America As Represented By The Administrator Of Nasa Method for phonon assisted creation and annihilation of subsurface electric dipoles
CN105942678A (zh) * 2016-07-18 2016-09-21 广东乐源数字技术有限公司 一种手环离手判断的方法
US10620252B2 (en) 2017-01-19 2020-04-14 United States Of America As Represented By The Administrator Of Nasa Electric field imaging system
GB2570535A (en) * 2017-09-05 2019-07-31 B Secur Ltd Non-contact authentication device
WO2019063874A1 (fr) * 2017-09-26 2019-04-04 Nokia Technologies Oy Appareil de détection de signaux biologiques
EP3459449A1 (fr) * 2017-09-26 2019-03-27 Nokia Technologies Oy Appareil de détection de biosignaux
US11497426B2 (en) 2017-09-26 2022-11-15 Nokia Technologies Oy Apparatus and electronic circuitry for sensing biosignals
US20230000413A1 (en) * 2021-06-30 2023-01-05 Siemens Healthcare Gmbh Integrated differential voltage measuring system

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