WO2013075388A1 - 一种侦测心跳或电极接触良好与否的物品、方法及系统 - Google Patents

一种侦测心跳或电极接触良好与否的物品、方法及系统 Download PDF

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Publication number
WO2013075388A1
WO2013075388A1 PCT/CN2012/000417 CN2012000417W WO2013075388A1 WO 2013075388 A1 WO2013075388 A1 WO 2013075388A1 CN 2012000417 W CN2012000417 W CN 2012000417W WO 2013075388 A1 WO2013075388 A1 WO 2013075388A1
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WO
WIPO (PCT)
Prior art keywords
electrode
electrodes
fabric
human body
article
Prior art date
Application number
PCT/CN2012/000417
Other languages
English (en)
French (fr)
Inventor
杨章民
杨子琳
杨皓
杨景雯
Original Assignee
Yang Chang-Ming
Yang Tzu-Lin
Yang Ho
Yang Ching-Wen
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 Yang Chang-Ming, Yang Tzu-Lin, Yang Ho, Yang Ching-Wen filed Critical Yang Chang-Ming
Priority to KR1020167024323A priority Critical patent/KR101854230B1/ko
Priority to EP12851285.2A priority patent/EP2783725A4/en
Priority to CN201280058101.3A priority patent/CN104302351B/zh
Priority to KR20147017093A priority patent/KR20140098809A/ko
Priority to KR1020167024326A priority patent/KR101854244B1/ko
Priority to JP2014542681A priority patent/JP6169592B2/ja
Publication of WO2013075388A1 publication Critical patent/WO2013075388A1/zh
Priority to US14/288,259 priority patent/US11253203B2/en

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/024—Measuring pulse rate or heart rate
    • A61B5/0245—Measuring pulse rate or heart rate by using sensing means generating electric signals, i.e. ECG signals
    • 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
    • A61B5/7221—Determining signal validity, reliability or quality
    • 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
    • A61B5/251—Means for maintaining electrode contact with the body
    • A61B5/252—Means for maintaining electrode contact with the body by suction
    • 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
    • A61B5/276—Protection against electrode failure
    • 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]
    • 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
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/339—Displays specially adapted therefor
    • A61B5/341—Vectorcardiography [VCG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/369—Electroencephalography [EEG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/389—Electromyography [EMG]
    • 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
    • A61B5/6805—Vests, e.g. shirts or gowns
    • 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
    • A61B5/6843—Monitoring or controlling sensor contact pressure
    • 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 an article, a method and a system for detecting good heartbeat or electrode contact, in particular to a form of a fabric worn on the body, capable of capturing an electrocardiogram signal, an electromyogram signal or an electroencephalogram signal
  • a patient lying on a hospital bed a healthy person in daily activities, a professional or amateur athlete, or a person engaged in high-risk work, such as a firefighter, they need to be uninterrupted, unwired, and not Prevent physical monitoring of normal activities to know their physiological condition and facilitate appropriate measures when necessary. For example, a first aid is given to a patient with myocardial infarction. Implementing physiological monitoring functions on everyday fabrics is one of the most common solutions.
  • U.S. Patent Application Serial No. 12/209,288 uses a patch to attach a plurality of electrodes to the body. This eliminates the need for clothing and ensures that the electrodes are in good contact with the body. However, such a patch can only be placed on the chest, and a complete three-limb electrocardiogram cannot be obtained, and it is uncomfortable for the user to directly attach the electrode to the body through the patch.
  • the electrode of U.S. Patent No. 7,474,910 is provided on a cloth by means of a float yarn, wherein the electrode itself can also be elastic and can be stretched.
  • this method of arranging the electrodes does not take into account the effect that the friction between the electrodes and the cloth or the human body can produce, and is not a three-dimensional space design, so it can only be used in a tight-fitting design, otherwise the user will move with the electrode as soon as it moves.
  • the skin has a relative movement.
  • the fabrics with physiological monitoring functions provided by the prior art have not yet obtained an ECG i sopotent ia l surface ma p using an electrocardiographic signal to obtain a better signal. Or avoid sweat interference, and use a separate electrode structure to reduce the body Dynamic interference, and can also detect whether the electrode is in contact with a good fabric. Summary of the invention
  • the factors related to the amplitude of the ECG signal collected by the body surface are as follows:
  • the amplitude of the ECG signal is proportional to the number of myocardial cells (myocardial thickness);
  • the amplitude of the ECG signal is inversely proportional to the position of the physiological electrode and the distance between the cardiomyocytes. The larger the angle of the clip is, the smaller the projection of the ECG signal on the lead is, and the weaker the potential is. .
  • the electrocardiogram P, Q is drawn by computer simulation (" Simulat ion s tudies of the electrocardiogram. I. the normal heart” , by WT Mi Her and DB Geselowit tz, Circ. Res. 1978: 43).
  • R, S, T is an equipotential line diagram of each wave, wherein the equipotential lines of the R wave are as shown in FIG. 1(a), which shows the electrode, control box and wire of the daylight of the preferred embodiment of the present invention.
  • FIG. 1(a) shows the electrode, control box and wire of the daylight of the preferred embodiment of the present invention.
  • the present invention proposes a new separate electrode structure and the position and area of the electrode for reducing body motion interference. , transmission line layout. Accordingly, the object of the present invention is to overcome the existing defects of the above-mentioned existing physiological monitoring function fabric, and to provide a new article, method and system for detecting good heartbeat or electrode contact, and the technology to be solved
  • the problem is that it can accurately and continuously extract the ECG signal by using a fabric that is washable on the body, and can accurately measure the ECG signal while satisfying the wearing comfort and the appearance. It is not easily interfered by body movements and sweat, and is very suitable for practical use.
  • Another object of the present invention is to provide a new article, method and system for detecting good heartbeat or electrode contact.
  • the technical problem to be solved is that it can be changed by environmental conditions, and selected by dry electrode or capacitor.
  • the coupled electrode captures the ECG signal, and the processor can select the two electrodes with the best ECG signal from the accompanying noise in the ECG signal or the impedance of the electrode, or activate different circuits, firmware or software to Save power consumption and make it more suitable for practical use.
  • Mental state and can be interpreted by the ECG waveform, mental state, gait, Or posture, which is more suitable for practical use.
  • An article, method and system for detecting good heartbeat or electrode contact according to the present invention comprising at least two electrodes, and a control box, wherein the electrodes are selected according to an equipotential line diagram and have a separate structure It is not fixed on the clothes to reduce the interference caused by body movements.
  • a processor in the control box a microcontroller is provided, and the firmware is provided in the microcontroller, which can not only calculate the heart rate, but also can be impedance or electrocardiogram of the electrodes.
  • the noise accompanying the signal identifies whether the electrode is in good contact with the human body and can be used to detect posture, mental state, and mental state.
  • the firmware of the microcontroller of the present invention is provided with automatic gain control, which automatically adjusts the linear range of its signal and uses the linear range of the signal to estimate motion interference. And it can detect whether the contact between the electrode and the human body is good by measuring noise, body surface impedance, muscle impedance, etc.
  • the electrode can be fixed by magnetic force to reduce body motion interference.
  • the article proposed by the invention can be provided with an elastic container inside the electrode, the container is provided with a hole for gas or liquid to enter and exit, can store gas or liquid, and can generate negative pressure to allow the electrode to be adsorbed on the skin, and can be used
  • the conductive liquid is slowly released due to capillary phenomenon or being squeezed to solve the problem that the electrode is not in contact with the body or the conductivity is poor.
  • the article proposed by the invention can be provided with a gas sputum or a liquid sac between the electrode and the fabric to solve the problem that the electrode is not attached to the body.
  • the system proposed by the present invention first detects the impedance between the two electrodes in the behavioral action when the device is used immediately, for example, in the first ten seconds, if the impedance is stable and within the set range, the control box starts detecting Measure the ECG signal, otherwise the control box will improve the signal quality by informing the user to tighten the belt, add conductive liquid, add a third electrode or activate the active electrode.
  • this method can also be applied to electromyography, electroencephalography, impedance pneumography, transcutaneous electrical nerve stimulation (TENS), electric shock, and the like.
  • the present invention has significant advantages and advantageous effects over the prior art.
  • the article, method and system for detecting good heartbeat or electrode contact have at least the following advantages and benefits:
  • the invention comprises: a piece of fabric, the fabric is provided with at least two electrodes, the electrode is covered with a conductor, the inner body contains an elastic body so that it can be attached to the human body comfortably, and the electrode is connected to the connector by a transmission line, and the connection
  • the other end of the device is connected to the control box, and the processor in the control box is provided with an analog circuit (also can be made on the fabric) for pre-processing the physiological signals obtained by the electrodes, and a processor is also provided in the processor, which can physiologically
  • the signal is converted into a digital signal, and the physiological signal is transmitted to other communication devices via a wireless module such as Bluetooth.
  • the fabric can obtain a variety of information, and then analyze the information to form a system.
  • the common problem is that when the electrode is in poor contact with the body, the signal cannot be correctly obtained.
  • the present invention adopts eleven methods to detect whether the electrode is in contact with the skin. Good.
  • the present invention infers the wearer's posture and action by the contact of the electrode with the body to promptly alert the wearer and detect his or her activity and mental state.
  • the above method can also be applied to electrodes for electroencephalography, electromyography, transcutaneous electrical stimulation therapy, electroporation treatment, and whether the electrodes are in good contact.
  • the wearable electrode is likely to be in poor contact with the skin when the fabric is loose.
  • the present invention can also add air sputum or liquid helium to the electrode, and if necessary, pressurize to press the electrode against the human body.
  • the present invention can selectively add a water-impermeable film layer inside the wearable electrode, and leave the conductive water inside the electrode when washing, and the moisture may be caused by capillary phenomenon when worn or used. It is squeezed and slowly released to the electrodes and skin.
  • the present invention selectively adds a flexible conductor between the conductive cloth of the electrode and the elastomer, such as a conductor woven from stainless steel fibers.
  • the present invention proposes seven novel electrode structures to reduce body motion interference.
  • the present invention proposes two methods for determining whether a transmission line is open.
  • the present invention relates to an article, method and system for detecting good heartbeat or electrode contact.
  • the present invention is to provide a plurality of fabric electrodes on a fabric, using an equipotential diagram of the electrocardiogram, and considering The interference caused by human motion, innovative design of the separation electrode structure, electrode position, area, and wire layout to detect the heartbeat; and the selection of the dry electrode or capacitively coupled electrode with the change of environmental conditions
  • the electrical signal; and the measurement of noise, body surface impedance, muscle impedance, etc. can detect whether the contact between the electrode and the human body is good; in addition, the posture and motion of the human body can be estimated by the waveform and noise of the ECG signal.
  • the invention has significant advances in technology and has obvious positive effects, and is a novel, progressive and practical new design.
  • the fabric referred to in the present invention can be used for clothing, underwear, jackets, sheets, pillows, socks, shoes, scarves, headscarves, gloves, aprons, belts, toilet seats, carpets, hats and cushions, steering wheel covers, watches Etc. BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1(a) is a view showing the positional relationship between the structure of the electrode, the control box and the wire of the daylight and the isoelectric line of the electrocardiographic signal according to the preferred embodiment of the present invention.
  • Figure 1 (b) is an enlarged schematic view of the control box of Figure 1 (a).
  • Figure 1 (c) is a schematic view of the position of the electrode determined by the relative movement distance of the skin during exercise in the present invention. Figure.
  • Figure 1 (d) is a schematic view of the left side of Figure 1 (c).
  • Fig. 2 (a) is a cross-sectional view showing an electrode having a chuck type structure in the present invention.
  • Fig. 2 (b) is a cross-sectional view showing a container provided in the electrode in the present invention.
  • Fig. 2 (c) is a cross-sectional view showing the inside of the electrode in which the bag is formed of a film which is not easily permeable to water or gas.
  • Fig. 2 (d) is a cross-sectional view showing the fibers of the conductive cloth having the suction cup structure in the present invention.
  • Fig. 3 (a) is a side view of an electrode containing a conductive fiber of the present invention.
  • Figure 3 (b) is a side view of the electrode containing the conductive strip of the present invention.
  • Figure 4 (a) is a side view of the solitary electrode of the present invention slid onto the fabric.
  • Fig. 4 (b) is a side view showing the spiral electrode of the present invention using a spiral transmission line having an increasing radius.
  • Figure 4 (c) is a side view of the electrode of the present invention secured by two suspension strips.
  • Figure 4 (d) is a schematic view of the electrode of the present invention with a webbing as a hanging strip sewn to the fabric.
  • Fig. 5 (a) is a side view showing the arrangement of the electrodes in the electrode so that the electrodes can slide along the transmission line.
  • Fig. 5 (b) is a schematic view showing a channel provided on the side of the electrode in the present invention.
  • Fig. 5 (c) is a schematic view showing the passage of the fabric on which the electrode is placed in the present invention.
  • Fig. 5 (d) is a schematic view showing the side of the electrode and the passage on the fabric in the present invention.
  • Fig. 6 (a) is a schematic view showing the fabric in which the electrode is placed in the present invention with openings to allow the connecting wires to pass through.
  • Fig. 6 (b) is a schematic view showing the electrode provided with an opening in the present invention to allow the connecting wire to pass through.
  • Fig. 6 (c) is a schematic view showing that the electrode and the fabric are provided with openings in the present invention to allow the connecting wires to pass through.
  • Figure 6 (d) is a schematic view of the opening of the connecting wire looped through the fabric in the present invention.
  • Figure 7 (a) is a schematic view showing a first preferred embodiment of the electrode disposed on the slide table in the present invention.
  • Figure 7 (b) is a schematic view showing a second preferred embodiment of the electrode disposed on the slide table in the present invention.
  • Figure 7 (c) is a schematic view showing a third preferred embodiment of the electrode disposed on the slide table in the present invention.
  • Fig. 8 (a) is a waveform diagram of R waves obtained by using the webbing as a suspension strip on the side of the electrode when standing still.
  • Fig. 8 (b) is a waveform diagram of the R wave obtained by the side of the electrode with the webbing as a hanging strip in the walking of the present invention.
  • Fig. 8 (c) is a waveform diagram of R waves obtained by using the webbing as a hanging strip on the side of the electrode when standing in the sitting position of the present invention.
  • Fig. 8 (d) is a waveform diagram of R waves obtained by using the webbing as a hanging strip on the side of the electrode in the in-situ high leg raising of the present invention.
  • Fig. 9 (a) is a schematic view showing a first preferred embodiment of the double-layered separated structure electrode of the present invention joined by a connecting wire.
  • Fig. 9 (b) is a schematic view showing a second preferred embodiment of the double-layered separated structure electrode of the present invention in which the webbing is bonded.
  • Fig. 9 (c) is a schematic view showing a third preferred embodiment of the double-layered separated structure electrode of the present invention in which the webbing is bonded.
  • Fig. 9(d) is a waveform diagram of the R wave obtained by the double-layered separation structure electrode of the present invention.
  • Fig. 10 (a) is a schematic view showing the equipotential lines and electrode positions of the front side R wave in the present invention.
  • Fig. 10 (b) is a schematic view showing the equipotential lines and electrode positions of the R wave on the left side in the present invention.
  • Fig. 10 (c) is a view showing the equipotential lines and electrode positions of the R wave on the back surface in the present invention.
  • Fig. 11 (a) is a diagram showing the heart signal of the present invention measured by electrodes disposed at A and B of Fig. 10 (a).
  • Figure 11 (b) is a diagram of the heart signal of the present invention measured by electrodes disposed at A and C of Figure 10 (a).
  • Figure 11 (c) is a diagram of the heart signal of the present invention measured by electrodes disposed at B and H of Figure 10(a).
  • Figure 11 (d) is a diagram of the heart signal of the present invention measured by electrodes disposed at D and E of Figure 10(c).
  • Fig. 11(e) is a diagram showing the heart signal of the present invention measured by electrodes disposed at F and G of Fig. 10(c).
  • Fig. 11(f) is a diagram showing the heart signal of the present invention measured by electrodes disposed at I and J of Fig. 10(b).
  • Figure 12 (a) is an electrocardiogram of the present invention measured by an electrode having an area of 6 * 3 cm 2 .
  • Figure 12 (b) is an electrocardiogram of the present invention measured by an electrode having an area of 6 * 6 cm 2 .
  • Figure 12 (c) is an electrocardiogram of the present invention measured by an electrode having an area of 6 * 9 cm 2 .
  • Fig. 13 (a) is a waveform diagram of the R wave measured by Z and B of Fig. 10 (c) and Fig. 10 (a) of the present invention.
  • Fig. 13 (b) is a waveform diagram of the R wave measured by the ⁇ and I of Fig. 10 (c) and Fig. 100) of the present invention.
  • Fig. 13 (c) is a waveform diagram of the R wave measured by the parallel connection of B and I of Figs. 10(a) and 10(b) and Z of Fig. 10(c).
  • Fig. 13 (d) is a waveform diagram of the R wave measured by the parallel connection of B and I of Figs. 10(a) and 10(b) and Z of Fig. 10(c) while walking.
  • Figure 14 is a side view showing the separation electrode provided in the elastic conductive cloth in the present invention.
  • Fig. 15 (a) is an electrocardiogram obtained when the right arm of the present invention is in front of the rear left arm.
  • Fig. 15 (b) is an electrocardiogram obtained when the arms of the present invention are in front.
  • Fig. 15 (c) is an electrocardiogram obtained when the arms of the present invention are in the back.
  • Fig. 15 (d) is an electrocardiogram obtained when the right arm of the present invention is at the rear of the front left arm.
  • Fig. 16 (a) is a waveform diagram of the R wave obtained when the electrode impedance is 15 M Ohms.
  • Figure 16 (b) is a waveform diagram of the R wave obtained when the electrode impedance is 30 M Ohms.
  • Fig. 16 (c) is a waveform diagram of R waves obtained when the electrodes are separated from the human body in a stationary state.
  • Fig. 17 (a) is a waveform diagram of the R wave obtained when the electrode impedance is 10 M Ohms.
  • Fig. 17 (b) is a waveform diagram of the R wave obtained when the electrode impedance is 10 M Ohms.
  • Figure 17 (c) is a waveform diagram of the R wave obtained by lifting the leg in situ when the electrode impedance is 10 M Ohms.
  • Fig. 17 (d) is a waveform diagram of the R wave obtained when the electrode impedance is 0.8 M Ohms.
  • Fig. 17 (e) is a waveform diagram of the R wave obtained when the electrode impedance is 0.8 M Ohms.
  • Fig. 17 (f) is a waveform diagram of R waves obtained by lifting the legs in situ when the electrode impedance is 0.8 M Ohms.
  • Figure 18 (a) is a schematic view showing the first form in which the two electrodes of the present invention are used in combination.
  • Figure 18 (b) is a schematic view showing a second formula in which two electrodes of the present invention are used in combination.
  • Figure 18 (c) is a schematic view showing a third form in which the two electrodes of the present invention are used in combination.
  • Figure 18 (d) is a schematic view of a fourth form in which the two electrodes of the present invention are used in combination.
  • Figure 18 (e) is a schematic view showing a fifth form in which the two electrodes of the present invention are used in combination.
  • Figure 18 (f) is a schematic view of a sixth form in which the two electrodes of the present invention are used in combination.
  • Figure 18 (g) is a schematic view of a seventh form in which the two electrodes of the present invention are used in combination.
  • Figure 18 (h) is a schematic view of an eighth form in which the two electrodes of the present invention are used in combination.
  • Figure 18 (i) is a schematic view of a ninth form in which the two electrodes of the present invention are used in combination.
  • Figure 19 is a schematic diagram of a circuit in which a capacitively coupled electrode and a dry electrode of the present invention share a circuit.
  • Figure 20 is a side view of an electrode containing a gas sputum or sac in the present invention.
  • Fig. 21 (a) is a side view showing the gas or liquid helium contained in the two electrodes connected to each other and assisted each other in the present invention.
  • Fig. 21 (b) is a side view showing the gas or liquid helium contained in the two electrodes connected to each other and mutually repelled in the present invention.
  • Figure 22 (a) is a schematic view of the present invention in which a magnet is attached to each of the fabric and the electrode.
  • Fig. 22 (b) is a schematic view showing the use of a ring type permanent magnetic substance in the present invention.
  • Fig. 22 (c) is a schematic view showing the arrangement of permanent magnetic substances on both sides of the electrode on the clothes of the present invention.
  • Fig. 23 is a view showing whether or not the pulse wave detecting electrode is in poor contact with the present invention.
  • Fig. 24 (a) is a waveform diagram of the R wave measured when the body surface capacitance of the present invention is 2. 7 nF.
  • Fig. 24 (b) is a waveform diagram of the R wave measured when the body surface capacitance of the present invention is 21. 7 nF.
  • Fig. 25 (a) is a schematic view showing the two electrodes in different shapes but electrically connected in the present invention.
  • Figure 25 (b) is a signal generation diagram of two electrodes of different shapes but electrically connected in the present invention.
  • Figure 26 is a schematic illustration of four electrodes connecting different electronic components in the present invention.
  • Fig. 27 is a view showing whether or not the sine wave measuring electrode is in poor contact in the present invention.
  • Fig. 28 is a schematic view showing a fifth method for judging whether or not the electrode is in poor contact with the skin according to the present invention.
  • Fig. 29 is a schematic view showing the sixth method for judging whether or not the electrode is in poor contact with the skin according to the present invention.
  • Fig. 30 is a schematic view showing the seventh method for judging whether or not the electrode is in poor contact with the skin according to the present invention.
  • Fig. 31 is a schematic view showing the eighth method for judging whether or not the electrode is in poor contact with the skin according to the present invention.
  • 32 is a schematic diagram of the present invention for determining whether a transmission line is poorly connected.
  • Permanent magnetic substance 10 snap button
  • Stop slider 85
  • FIG. 1(a) is a schematic diagram showing the positional relationship between the structure of the electrode, the control box and the transmission line of the daylight and the equipotential line of the electrocardiographic signal according to the preferred embodiment of the present invention.
  • the architecture of the present invention is to place two electrodes 40 respectively under the left and right sides of the day. Wherein, the electrode 40 of the left underarm is disposed in the region of the highest potential (+1. 4); however, in order to avoid respiratory interference and avoid the position where the female user happens to be wearing the underwear, the other electrode 40 is not set at the lowest position.
  • the present invention can optionally further add a third electrode as a negative feedback current input to the body electrode to reduce noise, or work with the above two electrodes to obtain a three-conductor Connect the ECG, or use the stray capacitance between the control box and the human body as the negative feedback current input electrode.
  • the snap button 10 is a connector for transmitting an electrocardiographic signal to the control box 50, as shown in Fig. 1 (b), and Fig. 1 (b) is an enlarged schematic view of the control box of Fig.
  • the snap button 10 described above can also be replaced by a conductive devil felt. Can get the same effect.
  • the snap 10 or the devil's felt is provided with a water absorbing material (such as a sponge), and a waterproof layer such as a hot melt adhesive film, a nylon cloth, a hydrophobic material or a plastic wrap is provided at the bottom to prevent the sweat from affecting the signal. Transmission.
  • the diaper can be constructed by splicing the upper and lower parts or the upper, middle and lower parts, each part of which is made of different materials, for example, a part of the electrode is made of a strong elastic Lycra cloth. manufacturing, fixed to the electrodes on the body, while the other part is used for producing fabrics easily extended, thus easily pull Lycra fabric portion ⁇
  • the control box 50 of the present invention is electrically connected to the electrodes via the snap button 10 as a connector to sense the electrocardiographic signal.
  • the control box 50 can be equipped with an instrumentation amplifier, a bandpass filter, a microcontroller, and a wireless communication module to wirelessly transmit signals to other communication devices so that the user is not bound by wires.
  • the present invention firstly measures the relative movement distance of the body movement to the muscle and the skin when the position of the electrode is selected.
  • Fig. 1 (c) is a schematic view of the electrode position determined by the relative movement distance of the skin during exercise
  • Fig. 1 (d) is the left side of Fig. 1 (c)
  • the relative movement distances of positions 2 and 3 on the left side of the human body and position 2 on the right side in Fig. 1 (d) are the same as those on the third side. From Table 1, the relative movement distance The smallest is position 9, followed by set 1 and position 3 again. However, the potentials of position 9 and position 3 are lower: while position 10 is not conducive to contact with the electrodes because it is at the concave surface of the human body. In view of the R-wave equipotential map of the human body and the relative movement distance of the skin, it is preferable to set the electrodes at positions 3 and 3.
  • the first and second steps of the electrode are at the potential of 1. 4 and -1. 0.
  • the area can detect two locations of the largest R wave.
  • the cuff of the daywear of the present invention should be 2 to 4 cm larger than that of the general shirt to avoid movement of the electrode caused by the movement of the arms to cause motion interference.
  • the electrodes on the left and right sides can be moved down 3 to 5 cm.
  • the present embodiment proposes seven methods for placing the electrodes on the fabric, so as to prevent the electrodes from moving relative to the skin during exercise, and it is further desirable to achieve that the electrodes do not move relative to the clothes. . Therefore, when the invention is first used, the impedance between the two electrodes 40 in the behavioral action is first detected.
  • the control box 50 starts the detection.
  • the ECG signal is measured, otherwise the control box 50 will inform the user to tighten the belt, add conductive liquid, add a third electrode or activate the active electrode to activate the active electrode (refer to Merri t et al.) Fabr ic- Based on Act ive Electrode Des ign and Fabricat ion for Heal th Moni tor ing Clothing" , IEEE TRANSACTIONS ON INFORMATION TECHNOLOGY IN BI0MEDICINE, VOL. 13, NO. 2, 2009), etc., to improve signal quality.
  • the specific seven methods are as follows: The first method: suction cup structure
  • the first type of suction cup structure is provided with a suction cup structure on a plane where the electrodes are in contact with the human body.
  • the suction cup structure is made of a material which is hydrophilic and gas-impermeable, and the suction cup structure is connected to a container which is elastic and can be restored to its original shape after being pressed, and the container is provided with a small hole for liquid or gas to enter and exit.
  • the container When washing the fabric, the container can contain an electrically conductive liquid (for example, water for washing the fabric); and after the fabric itself is dried or dried, the liquid remains in the container; when the person wears the fabric, the liquid in the container It can ooze out according to the capillary phenomenon, or the liquid in the container is squeezed onto the electrode when the container is squeezed; when the liquid in the container flows out and the container becomes air-containing, the elasticity of the container can be affected After squeezing, the inside of the container is under negative pressure to suck the human skin, so that the electrode does not move relative to the human body, and at the same time, a conductive liquid (such as water) on the skin can be sucked on the electrode to facilitate conduction, as shown in FIG. 2 (a) is a cross-sectional view of an electrode having a chuck structure in the present invention.
  • an electrically conductive liquid for example, water for washing the fabric
  • a valve or plug can be added to the small hole of the container.
  • the valve or plug can be opened to allow liquid to enter during washing, and closed to preserve when drying or drying the fabric.
  • the liquid in the container can also set an automatic closed opening on the small hole of the container. Close or valve, when the user inserts the switch or valve into the tube, the liquid can be filled into the container, and when the user pulls the tube out of the switch or the valve, the switch or the valve is automatically closed to save the liquid in the container.
  • Fig. 2(b) is a cross-sectional view showing a container provided in the electrode of the present invention.
  • Fig. 2 (c) is a cross-sectional view showing the inside of the electrode in which the bag is formed of a film which is not easily permeable to water or gas.
  • the outer layer of the electrode shown in Fig. 2(b) is a conductive cloth, and a container having elasticity and being able to be opened after being pressed is provided inside, and the container is provided with a small hole for liquid or gas to enter and exit. It functions as the first type of suction cup type structure described above.
  • an elastic material e.g., a sponge having pores and absorbing water is provided between the conductive cloth of the electrode and the container, and the elastic material can also store a liquid to facilitate conduction.
  • the electrode shown in Fig. 2(c) is a bag formed of a film which is not easily permeable to water or gas permeable in the conductive cloth, and an elastic material (e.g., a sponge) having pores and absorbing water is provided in the bag.
  • the bag is opened to accommodate a liquid or gas, and a small hole is provided in the bag for liquid or gas to enter and exit. The negative pressure generated by these two structures is not completely used to suck the human body, but is slowly decompressed.
  • the human body When the human body moves, it can press the container or the bag to generate a new negative pressure, and at the same time, the liquid stored in the container or the bag. Slowly translated.
  • the container and bag shown in Fig. 2(b) and Fig. 2(c) can provide a conductive liquid, and the conductive liquid is slowly released to the electrode and the skin during use.
  • the container and bag shown in Figure 2 (b) and Figure 2 (c) can also be used directly as a suction cup, and the electrode is attached to the human body.
  • the second type of suction cup structure is provided with a tiny suction cup structure on the fibers of the conductive cloth of the electrode, so that the electrode is squeezed out by the air squeezed by the human body, and the elasticity of the suction cup material can make the inside of the suction cup Negative pressure and suction of the human body, as shown in Fig. 2(d), Fig. 2(d) is a cross-sectional view of the fiber of the conductive cloth having the suction cup structure in the present invention.
  • This structure can make the friction between the conductive cloth of the outer layer of the electrode and the human body greater than the friction between the fabric and the human body, thereby reducing body motion interference.
  • a generally non-conducting fiber can be used to first contact the human body.
  • the above-mentioned suction cup type structure can also be disposed separately from the fabric by the electrode, and the electrode of the suction cup type structure is connected to the fabric by a transmission line disposed on the electrode, and the length of the transmission line (not shown) is L.
  • the purpose of the electrode is not to move relative to the human body. At this point, the electrodes are able to counteract the interference generated by the body motion and transmit the ECG signal to the processor in the control box.
  • FIG. 3 ( a) is a side view of an electrode comprising a conductive fiber of the present invention.
  • the present invention can form two or three flexible and conductive strips made of a conductive material, such as silver fiber, on the electrode. a strip of cloth, a conductive silicone strip, or a polymer conductive strip, which is formed by the above-mentioned bristle-type crusting composed of conductive fibers, and is placed on the periphery of the electrode to increase the friction between the electrode and the skin.
  • 3 (a) shows the same effect of the brush-type structure, and at the same time, it is not easy to cause adverse reactions of the skin, as shown in Fig. 3 (b), and Fig. 3 (b) is a side view of the electrode containing the conductive strip of the present invention.
  • the two electrodes shown in Figure 3 (a) and Figure 3 (b) above may also be provided with an elastic body, and the electrode may be provided with a transmission line of length L (generally about 0.2 to 3 cm) and passed through the transmission line. Connected to the fabric, the electrodes can be separated from the fabric (hereinafter referred to as a separate structure) to achieve the purpose that the electrodes do not move relative to the human body, and thereby reduce body motion.
  • L generally about 0.2 to 3 cm
  • the friction between the electrode and the human body is much greater than the friction between the electrode and the garment, so that the electrode does not move relative to the skin during exercise.
  • the electrodes in the method can also be disposed on the clothes in a separate structure to further achieve the purpose that the electrodes do not move with the clothes, and the effect is the same as the above method.
  • the electrodes are arc-shaped as shown in Figs. 4(a) to 4(d), and may be flat-bottom type or other type, and the transmission line 80 is connected to the fabric 85 in contact with the human body.
  • the transmission line 80 may have elasticity.
  • the transmission line 80 is woven on an elastic band or other woven tape.
  • the transmission line 80 has a suspended length of L (generally about 0.5 to 0.3 cm) for the relative movement of the electrode and the fabric 85.
  • the surface of the electrode is a conductive cloth 65 having a large frictional force, such as a conductive cloth of a pile structure.
  • At least one side of the contact surface of the electrode and the fabric 85 is made of a smooth material 82 having a low frictional force, such as a lining cloth, a waterproof smooth cloth, an iron sheet, a copper sheet, a stainless steel sheet, a glass material or a Teflon-coated fabric. Etc., in order to facilitate the sliding of the electrode.
  • the inside of the electrode is provided with an elastomer, a conductive silicone, or a general fabric.
  • the outer edge of the electrode may optionally be provided with a stop strip 83 to increase the coefficient of friction between the electrode and the human body, and the surface of the electrode in contact with the fabric 85 may be made of a smooth material 82.
  • the transmission line between the electrode and the fabric 85 may be a spiral transmission line having a fixed radius as shown in FIG. 4(a), or a spiral transmission line having a gradually increasing radius as shown in FIG. 4(b) or a folded shape. (As shown in Figure 4 (d), the webbing is folded in three times) transmission line for telescopic purposes. When the spiral or folded transmission line is stretched, it will automatically retract without occupying space.
  • 4(a) is a side view of the curved electrode of the present invention slid on the fabric.
  • Fig. 4 (b) is a side view showing the spiral electrode of the present invention using a spiral transmission line having an increasing radius.
  • Figure 4 (c) is a side elevational view of the electrode of the present invention secured by two suspension strips.
  • Figure 4 (d) is a schematic view of the electrode of the present invention with a webbing as a hanging strip sewn to the fabric.
  • the electrode can also be a flat-bottom type, so that at least two suspension strips of length L are used to connect the electrodes to the fabric, for example, a suspension strip woven from a smooth wire such as a nylon thread or an elastic yarn, as shown in Fig. 4 ( c) As shown, one of the suspension strips may be a transmission line.
  • the suspension strip containing the transmission line may be covered with an insulating layer, such as a covered copper wire; or an insulating layer, such as silver fiber; or the entire suspension strip is made of a conductive material, such as a stainless steel conductive strip, and the suspension strip itself may also be As an electrode, it can pick up physiological electrical signals when it comes into contact with the human body, so as to increase the chance of sensing the ECG signal, and also reduce another transmission line.
  • the anti-sliding strip can be silica gel, latex, fluff, or devil felt, etc., and it can also be a conductive material itself, which can be used as an electrode.
  • the suspension strip can also be made of a woven tape having a movable length L on the electrode, as shown in Fig. 4 (d), wherein the webbing can be combined with the fabric to leave a space of length L (0.2: to 3 cm).
  • the electrode is free to move.
  • the electrode can move freely with the skin in a three-dimensional space with a range of 0. 2 to 3 cm, without moving relative to the skin, and further achieve the purpose that the electrode does not move with the fabric.
  • the anti-slip strip 83 is directly sewn on the fabric 85 with a slip-resistant fabric to achieve an effect that the electrode does not move relative to the human body and reduces body motion interference.
  • the frictional force of the fabric with respect to the skin when the fabric is moved by an external force is much larger than the tensile force of the fabric relative to the slip-resistant fabric.
  • the structure of the slip-resistant fabric on the fabric can also be applied to other structures in the present invention, wherein the slip-resistant fabric can be silicone, latex, fluff, devil felt or high-tension elastic cloth, such as stockings.
  • the webbing itself may contain a transmission line 80 or be a conductive material itself, or it may be used as an electrode at the same time, thereby reducing the applied transmission line 80.
  • the electrode has a channel therein for sliding the transmission line 80 in the channel, and the transmission line has an excess length L on the fabric 85 for the electrode to slide.
  • FIG. 5(a) shows that the electrode is provided with a channel in the electrode to slide the electrode along the transmission line.
  • Side view Another example is shown in FIG. 5(b).
  • FIG. 5(b) is a schematic view showing a channel provided on the side of the electrode in the present invention, wherein the electrode has a planar structure and each channel is provided on each side of the electrode, and each channel is provided.
  • Each has a connecting line to secure the electrodes to the fabric.
  • the above connecting wires may be nylon wires, elastic yarns, wirings, cloth strips, metal wires, plastic wires, plastic strips, conductive wires or conductive strips, etc., and are preferably elastic and smooth.
  • the channel can also be arranged on the fabric, and a connecting line is arranged in each channel on the fabric, and the two ends of the connecting wire are fixed on the electrode, as shown in Fig. 5 (c),
  • Fig. 5 (c) is a schematic view of the fabric on which the electrode is placed in the present invention; or a channel may be provided on both the electrode and the fabric, and the passages of the two are connected by a connecting wire, as shown in Fig. 5(d) 5(d) is a schematic view showing the side of the electrode and the passage on the fabric in the present invention.
  • the excess length of the connecting cable is L (0.5 to 3 cm)
  • the two surfaces of the electrode in contact with the clothing are made of a smooth material (such as a lining cloth, a waterproof smooth cloth, an iron piece, a copper piece, a stainless steel piece, a glass material or a fluoride).
  • a smooth material such as a lining cloth, a waterproof smooth cloth, an iron piece, a copper piece, a stainless steel piece, a glass material or a fluoride.
  • Dragon-covered fabric, etc. Manufactured to reduce friction, the electrode edge can be optionally fitted with a stop strip (not shown) or a slip-resistant fabric on the fabric to increase friction. Therefore, when the human body moves, the range in which the electrodes can move is
  • the electrode can move freely with the skin without moving relative to the skin, and further achieve the purpose that the electrode does not move with the fabric.
  • the conductive material may be disposed in the channel, and the conductive material may be coated with an insulating layer or an insulating layer.
  • the connecting wire is, for example, a transmission line, and can be made of a conductive material, such as a conductive cloth and covered with an insulating layer or an insulating layer. When the conductive cloth is not covered with an insulating layer, it can also serve as an electrode, and the physiological electric signal can be picked up when contacting the human body. If the channel and the connecting line are not conductive, a transmission line must be added to connect the electrodes to receive the signal.
  • the material of the connecting wire is as described above, preferably a material having elasticity and smoothness.
  • Fig. 6(a) is a schematic view showing the fabric in which the electrode is placed in the present invention with openings to allow the connecting wires to pass through.
  • Fig. 6(b) is a view showing the electrode provided with an opening in the present invention to allow the connecting line to pass through.
  • Fig. 6 (c) is a schematic view showing the electrode and the fabric of the present invention provided with openings to allow the connecting wires to pass through.
  • Fig. 6 (d) is a schematic view showing the opening of the connecting wire looped through the fabric in the present invention.
  • the electrode and/or the fabric is provided with an opening, the opening is for the connecting line to pass through, the contact surface of the electrode and the clothing is made of a smooth material to reduce the friction, and the electrode edge can be selectively installed with the sliding strip .
  • the opening is not shown on the fabric as shown in Figure 6 (a); it can also be placed on the electrode itself, as shown in Figure 6 (b); or the electrode and the fabric are provided with openings, as shown in Figure 6 (c ) shown.
  • the opening may be a circular hole as shown in Figs. 6(a) to 6(c), or may be an elongated hole as shown in Fig. 6(d) for passing the web as a connecting line.
  • the webbing passing through the opening may be fixed at both ends to the electrode, on the woven fabric, or in a loop shape.
  • the electrical conductivity of the sliding strips, the openings and the connecting wires is as described in the third and fourth methods above, and the length L of the connecting wires for sliding is about 0.2 to 3 cm to ensure effective reduction of body motion interference.
  • the connecting wire itself can also be a conductive material, if not, an additional transmission line is required.
  • the material of the connecting wire is as described in the fourth method described above.
  • a wireless transmission system can be disposed in the electrode to transmit the signal acquired by the electrode.
  • the electrode 40 is not fixed on the fabric, but is fixed on the slider of the slide table, as shown in Fig. 7 (a), Fig. 7 (a) is the first preferred embodiment of the electrode disposed on the slide table in the present invention.
  • a schematic view of the embodiment; or the electrode is fixed on the sliding table, and the slider is provided on the fabric, as shown in FIG. 7(b), and FIG. 7(b) is the second electrode disposed on the sliding table in the invention.
  • the schematic diagram of the preferred embodiment allows the electrode to be arbitrarily slid in the two-dimensional direction by the slider, and the movable range of the slider is L, so that the electrode 40 can follow the human body, and the electrode and the skin have no relative motion. .
  • Fig. 7 (c) shows an example in which an opening is provided in the fabric 85, and the electrode 40 and the slider are respectively disposed above and below the opening to realize three-dimensional movement. 2 ⁇
  • the electrode 40 is movable in the range of L, L is about 0. 2 to 3 cm.
  • a transmission line must be connected to the electrode to transmit the signal.
  • a conductive material may be provided at the opening of the fabric 85 to connect it to the conductive material of the electrode or the slider itself to transmit a signal.
  • the present invention performs the same operation in the same temperature and humidity environment on the same day, and the same user first uses the physiological electrode patch to squat down (see FIG. 1) as a control group.
  • Detection of postures and movements Among them, the four postures and movements are standing still, walking, standing up from sitting position and raising legs in place.
  • an outer sleeve is attached to the experimental underwear to obtain the R wave.
  • the R-wave is obtained by the separation electrode of FIG. 4(d), and the obtained result is as shown in FIG. 8(a) to FIG.
  • 8(d) and the DC resistance is 0.6 M ohm ( Ohms), wherein, 8(a) is a waveform diagram of R waves obtained by using the webbing as a suspension strip on the side of the electrode when standing still, and FIG. 8(b) is an R wave obtained by using the webbing as a suspension strip on the side of the electrode when walking in the present invention.
  • FIG. 8(c) is a waveform diagram of R waves obtained by using the webbing as a hanging strip on the side of the electrode when standing in the sitting position of the present invention, and FIG. 8(d) is the side of the electrode when the in-situ high leg is raised in the present invention.
  • the webbing is a waveform diagram of the R wave obtained by the suspension strip.
  • Fig. 9(a) is a schematic view showing a first preferred embodiment of the layered structure electrode of the present invention joined by a connecting wire.
  • the electrode is connected with a large rough fabric by a connecting line, the rough fabric is laminated with another smooth material, and the contact surface of the electrode and the rough fabric is provided with a smooth material with low friction, so that the electrode and the rough fabric are easily opposed. Sliding so that the electrode does not move relative to the skin when the body is active; the rough fabric is combined with the fabric by a connecting line, and at least one side of the contact surface of the fabric and the rough fabric is a smooth material with low friction to reduce fabric and fabric. Friction between.
  • the webbing can be replaced by a webbing in Fig. 9(a), and the webbing is passed through a rough fabric and a smooth material under the electrode to form a ring shape, as shown in Fig. 9(b), wherein Fig. 9(b) is the present invention.
  • FIG. 9(c) A schematic view of a second preferred embodiment of the two-layer split structure electrode in the form of a webbing combination.
  • the direction of the inner ribbon of the electrode Rough fabrics are parallel.
  • Another way is to make the direction of the inner ribbon of the electrode perpendicular to the rough fabric, forming a ring on the outer side of the rough fabric, bypassing the rough fabric, as shown in FIG. 9(c), wherein FIG. 9(c) is the invention
  • FIG. 9(c) A schematic view of a third preferred embodiment of a two-layer split structure electrode in combination with a webbing. The effect is shown in Fig. 9(d), and Fig. 9(d) is a waveform diagram of the R wave obtained by the user while walking, which is obtained by the electrode of the layered structure.
  • the two-layer separated structure may adopt any two of the foregoing first to sixth methods, and the upper and lower two separate structures may be implemented by the same or different structures. Furthermore, the present invention may further add one or more layers to the above-mentioned two-layer separated structure to form a multilayer separated structure; the double-layer or multi-layer separated structure is also applicable to a capacitively coupled electrode, and the specific content thereof Please refer to the description of the third embodiment for details.
  • the material of the connecting line in the two-layer separated structure is as described in the fourth method.
  • the anti-slip strip or the anti-slip fabric may be selectively attached to the electrode or the fabric to reduce the friction between the electrode and the fabric or the relative movement between the electrode and the skin.
  • the articles connecting the electrode and the fabric described in the above first to seventh methods may also be connected via a snap button or a conductive velcro (Velcro) to facilitate the electrode to be detached and Replace, see Table 2.
  • a snap button or a conductive velcro (Velcro) to facilitate the electrode to be detached and Replace, see Table 2.
  • the sponge is used as an elastomer, its water storage characteristics can be utilized to help the electrode conduct electricity.
  • the upper and lower sides of the elastic body are provided with a waterproof rubber film, and a smooth fabric is arranged outside.
  • the smooth fabric and the waterproof film itself are not easy to permeate, so the upper smooth fabric and the waterproof film are needle-punched with several small holes so that the sponge absorbs water during washing, and the water is slowly released to the human body during use.
  • Conductive cloth Even when the fabric is completely dry and does not contain water when the fabric is worn, the above-mentioned waterproof film can prevent the sweat from evaporating after being worn, and leave the sweat on the conductive cloth and the sponge to help the electrode to conduct electricity.
  • the conductive cloth of the foregoing electrode may also have an elastic body, such as a sponge, a silica gel, a spring or the like. As shown in Fig. 9a, a smooth material is also provided between the two to reduce the friction between the electrode and the elastic body. At the same time, the electrode area is larger than the elastomer by 0.4 square centimeter or more, so that the conductive cloth can move and deform at the same time when the skin moves and deforms, for example, from a square to a diamond, without being restricted by the elastic body. That is, there is a smooth material to wrap the elastomer or to separate from the elastomer by the above method instead of directly stitching or pasting on the elastomer.
  • an elastic body such as a sponge, a silica gel, a spring or the like.
  • a smooth material is also provided between the two to reduce the friction between the electrode and the elastic body.
  • the electrode area is larger than the elastomer by 0.4 square cent
  • each of the electrodes used in the present invention is a flexible conductive cloth or a conductive sheet (e.g., silver fiber, stainless steel sheet), and a conductor-containing elastomer may be disposed inside.
  • the conductor is used to increase the conductivity of the electrode, and when the electrode is damaged by water washing or wearing, the electrode can still have the sensing capability and increase the service life of the electrode.
  • the conductor of the surface of the electrode in contact with the human body in the present invention may preferably be a material having a large frictional force, such as a wool or a stop strip, or may increase the friction by increasing the electrode area.
  • the elastomer added to the inside of the electrode may be a sponge which is elastic and absorbent, silica gel or the like, or the elastomer may be made of, for example, a spring or the like, and the water retaining water can be added inside.
  • Agent The water retaining agent is insoluble in water, but can absorb water equivalent to one hundred times its own weight, and can effectively inhibit evaporation of water.
  • Water-retaining agents are divided into two major categories, one is acrylamide-acrylate copolymer cross-linking (polyacrylamide, sodium polyacrylate, potassium polyacrylate, ammonium polyacrylate, etc.); the other is starch grafted acrylate copolymerization Crosslinker (starch grafted acrylate).
  • acrylamide-acrylate copolymer cross-linking polyacrylamide, sodium polyacrylate, potassium polyacrylate, ammonium polyacrylate, etc.
  • starch grafted acrylate copolymerization Crosslinker starch grafted acrylate
  • Commonly used water retaining agents are amorphous particles, powders, fine powders, flakes and fibers.
  • the elastomer itself is a conductive material, that is, an electrode, because it can retain moisture and has anti-vibration and filtering functions, so it can increase and stabilize its conductivity.
  • the present invention can selectively add a thin layer that is not easily permeable to water, a semi-permeable layer or a needle-punched impervious fabric, and a water-impermeable printing outside the elastic and water-absorbing material that can be selected for the elastomer.
  • Glue coating, waterproof fabric, waterproof strip to block moisture, making it difficult to penetrate.
  • the elastomer itself has a semi-permeable function, so that the water remains in the elastomer and slowly oozes out.
  • the body compresses the elastomer, allowing the liquid stored in the elastomer to be slowly released to the electrodes and the skin.
  • the liquid contained in the elastic body is replaced by air, once the elastic body is squeezed, the inside thereof is under a negative pressure, which can suck the human skin, and at the same time, can suck the conductive liquid (such as water) on the skin into the electrode. Conducive to electrical conduction.
  • the present invention can selectively add a conductor between the conductive cloth of the electrode and the elastomer, for example, a conductor woven from stainless steel fibers.
  • the control box can also pass current through the heating element to raise the temperature of the electrode or the fabric in the vicinity thereof, or heat the electrode or the fabric nearby to increase the temperature of the human body or the surface of the electrode and increase the amount of sweat to reduce the impedance between the electrode and the human body.
  • the functional warming fabric can be made into a detachable type, which is taken off in the hot weather, as described in Table 2.
  • Table 2 The preliminary result of our experiment is that in the environment of low temperature and low humidity (temperature 16 ⁇ , relative humidity 55%), the impedance of the electrode is 40 M Ohms just after wearing, and can be gradually reduced to 20 M Ohms after 30 minutes, and then maintained. Stable, you can get a heartbeat.
  • the experimental results of the same reason show that the temperature of the skin, the impedance of the electrode and the quality of the electrocardiographic signal have a high correlation.
  • the present invention can provide a thermistor in the electrode to measure the temperature of the electrode, and then Implement appropriate countermeasures. See Table 2 for details.
  • the temperature and humidity of the human body surface are not exactly the same, but the isotherm or equal wet line can be used to draw the distribution of temperature and humidity on the surface of the human body, similar to the electrocardiogram.
  • the isotherm diagram or the contour of the wet surface of the human body will change with the temperature and humidity of the environment, and the summer and winter will be different.
  • the invention can integrate the electrocardiogram and the isotope diagram to select a better electrode position. For example, when the weather is hot, the electrical conductivity of the whole body skin is good. At this time, only the electrocardiogram and other bit line diagrams can be used to determine the electrode position, as shown in Figure 1 (a); in cold weather, the chest temperature is highest in the heart socket.
  • the electrodes When the electrodes are respectively placed at the right side of the right chest as shown in Fig. 10 (a), the front part of the chest (-0. 3 equipotential line) and the left side of the lower chest of the front chest (1. 4 equipotential line).
  • the measured electrocardiogram is as shown in Fig. 11 (a), wherein the amplitude of the R wave is about 1. 8 mV;
  • Fig. 11 (b) is the electrode is placed at A and C of Fig. 10 (a), respectively.
  • the measured electrocardiogram (between 0.3 and 0.5 equipotential lines), wherein the amplitude of the R wave is about 0.7 mV, which is consistent with the results simulated in the aforementioned literature, thereby determining the positions at A and B.
  • FIG. 11 (c) is an electrocardiogram measured by placing the electrodes at B (1.4 bit line) and H (-1.0 bit line) of Fig. 10 (a), where the amplitude of the R wave is about It is 2. 2mV, the largest, but it is susceptible to respiratory interference, and the equipotential line is dense, the potential changes greatly, the electrode is easily displaced, and even reaches the positive potential region across the zero equipotential line, so that not only the amplitude is reduced. It is very likely that the direction of the peak is reversed and it is difficult to identify; in addition, it is also vulnerable to the female bra, so it is chosen to set the electrodes at A and B, instead of setting the electrode at H (-1.
  • the principle of selecting the position of the electrode of the present invention is such that one electrode is located in the positive potential region and the other electrode is located in the negative potential region, bounded by zero equipotential lines and does not cross the zero equipotential line. .
  • the R wave can be obtained by placing the electrode on the back of the human body.
  • Figure 11 (d) is an electrocardiogram measured by placing electrodes at D (0.3 bit line) and E (-0. 3 bit line) of the back of the human body of Figure 10 (c), wherein The amplitude of the R wave is about 0.6 mV;
  • Fig. 11 (e) shows that the electrodes of the present invention are respectively disposed at F (between 0.3 and 0 equipotential lines) and G (-0) of Fig. 10 (c). Between the 3 and 0 equipotential lines, the measured electrocardiogram, wherein the amplitude of the R wave is about 0. 45 mV, that is, the smaller the amplitude of the R wave obtained by setting the back electrode to the inner side, the smaller The results simulated by the aforementioned documents are consistent.
  • R waves can be obtained by placing the electrodes on the left and right sides of the human body.
  • Figure 11 (f) shows the electrodes measured at I (0. 3 and 0.5 equipotential lines) and J (zero equipotential lines) on the left side of the human body in Figure 10 (b).
  • the sizes are different.
  • the T waves of 11 (a) and 11 (b) are larger than the T waves of 11 (c), and 11 (d)
  • the T wave of 11 (e) is larger than the T wave of 11 (f), and the ratio of the amplitude of the T wave to the R wave is different in each figure. This is because T wave, R wave, Q wave, S wave and The isoline diagram of the P wave is different.
  • the amplitude difference of the R wave obtained by D and E is only 0.15 mV, where R wave and T wave
  • the ratio is also different from Fig. 11 (a), Fig. 11 (b), and Fig. 11 (c).
  • an electrode extending in the lower right or lower left direction that is, an equipotential line that is zero from the center, and is oriented toward a higher or lower equipotential line. Greater amplitude.
  • the present invention can estimate the position of the electrocardiogram by the waveform structure of each wave of the electrocardiogram.
  • the influence of the size of the electrode area on the electrocardiographic signal can also be inferred from Fig. 10(a) to Fig. 10(c). Since the electrode used in the present invention is a piece, not a small point, the potential of its output should be the average of the potentials of its covered area. For the electrode located at D or E, the potential of the output is still relatively sparse, and the potential of the output is still close to 0.3 or -0.3.
  • a small-area electrode in the bit line has an output potential of 1.4, but an electrode located at a large area may be exposed to a region other than the equi-line 1 to lower the potential of the output. It is about 1 mV or less.
  • the present invention can provide a large-area electrode in a region where the equipotential linear density is low, which will not cause amplitude attenuation and increase the friction of the electrode.
  • the R waves measured by the electrodes of different areas are set at A and B of Fig. 10 (a), wherein the electrodes corresponding to Fig. 12 (a) are 6 * 3 square centimeters; Figure 12 (b) corresponds to the electrode is 6 * 6 square centimeters; Figure 12 (c) corresponds to the electrode is 6 * 9 square centimeters.
  • the anti-slip strip is sewn; placed on the electrode or the anti-slip surface # is sewn on the fabric to achieve no significant displacement of the electrode relative to the fabric. This mode is further reduced to 2*2 cm2 in the electrode area.
  • a stable ECG signal can also be read.
  • Electrodes There are two advantages to increasing the electrode area: First, it is less likely to cause poor contact, and second, it can increase the friction with the skin and reduce body motion interference.
  • the above-mentioned electrodes are used for adult sizes, and for children or infants, the ratio of commercially available adult and infant electrodes can be reduced.
  • the transmission line between the electrode 40 and the control box 50 may be a wire with an insulating layer or a tree line without an insulating layer. If the insulating layer fails or the line is used, there may be two effects, one is susceptible to perspiration. Or the impact of rain, the second is affected by static electricity. However, static interference can be handled by circuits or firmware, so its effect is not significant. When the insulation layer fails or the line touches the sweat or rain on the skin or clothing, it is possible to form an unintended electrode, so that the electrocardiographic signal at the place is transmitted to the control box 50 together, causing non- Expected interference. If the potential is between 0.
  • the amplitude is at least ⁇ 0.3 m.
  • the area of the region between 0. 3 and -0.3 is set to be in the range of 0.3 to 0.3.
  • the insulator in addition to the transmission line with its own insulating layer, can also be installed with a water-impermeable fabric or a water-impermeable glue coating between the human body and the transmission line or a waterproof fabric and a waterproof sticker to wrap the line to the cable. On the fabric to block moisture infiltration.
  • the ECG signal in the zone is controlled by ⁇ 5.
  • the position set by the control box 50 should preferably avoid the highest or lowest equipotential line area of 1.4 or -1, and the area with the potential of 0 (see Figure 1 (a)
  • the vicinity of the point is such that even if one of the input terminals forms an electrode due to sweat or rain, at least the terminal picks up an electrical signal close to zero, and another has not
  • the amplitude of the 0. 5mV is obtained by the input of the electrocardiographic signal of the electrode of the electrode of the bit line of the Figure 1.
  • the equipotential line is not extended by zero symmetry, that is, the positive end can reach +1. 4mV, and the negative end is only - 1.
  • OmV even if the control box is located at W of Fig.
  • the input terminal of the control box 50 receiving the negative terminal signal may have a potential of +0.5. 5 ⁇
  • the area of the control box 50 is set to the area of the R wave equipotential line 0 to 0.5.
  • the control box 50 If the two terminals of the control box 50 are located near the zero equipotential line of the chest, because the equipotential line is dense (that is, the potential changes drastically), and because of the ductility of the fabric, in the case of sweat, the control box The terminal of 50 is likely to hit an area where the potential is not zero but rather high or low. Therefore, even in a wet condition, the processor of the control box 50 can read a R wave having a relatively large amplitude. Setting the control box 50 here also shortens the length of the transmission line.
  • the present invention sets two input terminals of the control box 50 and the transmission line respectively on the upper and lower sides of the outer casing of the control box 50, so as to prevent the two terminals from being wet with rain or sweat at the same time, causing electrocardiogram
  • the signal is shorted to zero potential, causing the processor within control box 50 to receive no signal.
  • the two terminals on the control box 50 of the present invention can detect significant R waves as long as one of the terminals is not affected by moisture and both terminals are at the same potential. In the same way, the same design can also get obvious P, Q, S, T wave signals.
  • this embodiment proposes a "complementary electrode group" to reduce body motion interference, as shown in FIG. 10(a) to FIG. 10(c), at B, An electrode is provided at each of I, Z, and the electrodes at B and I are connected to the positive input terminal of the control box 50, and the first electrode is connected to the negative input terminal of the control box 50.
  • the reason why the electrode at Z is selected in the middle of the body and is zero-zero is that the interference between the left and right arms is minimized in the middle of the body, and the zero-equal line can make the Z electrode match the high-order line (for example, B + 1.
  • the R wave is measured by an electrode of the equipotential line and the electrode of the equipotential line (for example, 0.3 bit line at I).
  • the amplitude of the R wave measured by the electrode at Z and the electrode at B alone is 1.2 mV; as shown in Fig. 13 (b), the electrode at Z and the electrode at I alone The amplitude of the R wave is 0. 6 mV; as shown in Fig.
  • the amplitude of the R wave measured by the electrode at Z and the parallel B and the electrode at I is 0.6 m V; (d), when the left arm is forward, the left side of the top is stretched forward so that the pressure between the electrode at B and the human body is lowered, but at the same time the pressure between the electrode and the human body at I increases; otherwise, when left When the arm is backward, the left side of the top is stretched backwards, so that the pressure between the electrode at B and the human body is increased, but at the same time, the pressure between the electrode at the I and the human body is lowered.
  • the electrode at the B and the electrode at the I are A complementary pair of electrodes, whether the left hand is in front or behind, at least one electrode has sufficient pressure on the body to pick up the R wave. If the amplitude of the R wave is measured, by Figure 13 (a) to Figure 13 ( d), you can estimate the position of the arm. If it is close to 1.2 mV, it means that the arm is backward and the electrode at I is bad. If it is close to 0.3 mV, it means that the arm is forward. Poor electrode contact; if nearly 0. 6mV, said arm B causes the two electrodes at the intermediate I there are good when the contact arm is moved forward or backward, will produce some noise will.
  • the above-mentioned electrode at the zero potential can be similarly set by the Z at the back, or at the front M as shown in Fig. 1(a).
  • the complementary electrode can also be disposed between an elastic conductive cloth and the human body by using a separate electrode as shown in FIG. In this embodiment, a large-area elastic conductive cloth is used as the electrode at B, and a separate electrode is used as the electrode at the I.
  • two electrodes can also be arranged on the right side of the body, one of which is located at the front chest-0.77 equipotential line, and the other electrode is located at the back--0. 3 equipotential line. Know the posture state of the right hand.
  • the present invention can introduce the above-mentioned separate electrode, which is disposed under an elastic conductive cloth and a human body, and can also reduce body motion interference.
  • the elastic conductive cloth can also be used as an electrode, as shown in FIG.
  • one electrode is placed on the front and rear sides of the left and right sides, and the two electrodes on each side are connected in parallel to the processor of the control box.
  • the sleeve will pull the underarm garment forward, so that the electrode placed behind the underarm is close to the body, and the electrode placed in front of the underarm is away from the body.
  • the electrode placed behind the squat is away from the body, and the electrode placed in front of the squat is close to the body.
  • FIG. 15 (a) is an electrocardiogram obtained when the right arm of the present invention is in front of the rear left arm
  • FIG. 15(b) is an electrocardiogram obtained when both arms are in front of the present invention
  • FIG. 15(c) is a double of the present invention.
  • Fig. 15 (d) is the electrocardiogram obtained when the right arm of the present invention is behind the front left arm
  • electrodes of different areas or different positions such as electrodes located at the cuff, chest, and hind arm, etc., the ratio of P, Q, R, S, and T waves of the electrocardiogram obtained therefrom, To identify the posture of the body.
  • the posture is obtained by the waveform analysis
  • the motion is obtained by the noise analysis. Complement each other.
  • the ECG signals obtained from different locations have different ratios of Q, R, S, and T waves. These two principles can also be applied to determine the wearer's sleeping position.
  • two electrodes are respectively disposed on the front chest, the back, the left side, and the right side. When the wearer is lying on his back, the electrode placed on the back is pressed by the body and has good electrical conductivity. Although the other electrodes are in contact with the body but have poor conductivity, they have little effect on the ECG waveform.
  • the ECG signal is also provided by different electrode sets when the wearer is in other sleeping positions. Comparing the ECG, you can tell the wearer's sleeping position. This embodiment can read the R wave during body movement during the day and read the complete electrocardiogram at night when it is still.
  • the electrode of the present invention is a dry electrode made of fabric, instead of a physiological electrode patch commonly used in hospitals. Due to the large and unstable impedance between the dry electrode and the human body, it may not be possible to obtain a good quality ECG signal under certain circumstances (such as low temperature and low humidity), such as being susceptible to body motion, or when the body is stationary. There is still electromagnetic interference caused by the power supply. Therefore, the present embodiment proposes countermeasures against this subject in order to make the present invention more practical.
  • FIG. 16 (a) is a waveform diagram of the R wave obtained when the electrode impedance is 15 M Ohms
  • Figure 16 (b) is when the electrode impedance is 30 M. Waveform of the R wave obtained at rest in Ohms. At this time, the impedance of the skin and the electrode is too high, and it is difficult to conduct the ECG signal.
  • the R wave can be recognized in various actions such as lifting the leg in place, as shown in Figure 8 (a) to Figure 8 (d).
  • Figure 8 (a) to Figure 8 (d) 16(a) to Fig. 16(c) and 17(a) to Fig. 17(f)
  • the law is as follows: The lower the DC impedance, the more the noise Low; the greater the body motion interference, the higher the DC impedance; if the noise is large at rest, the noise is greater during motion. The aforementioned rules, and vice versa.
  • the electrode impedance can be continuously detected for a period of time (for example, 10), and the user can still read the ECG signal under what kind of motion condition. If the impedance is low enough : Take the ECG signal; if the impedance is too high, the processor in the control box takes appropriate countermeasures to optimize the whole system, and then starts to extract the ECG signal. For example, the equivalent DC resistance is 10 M. In Ohms, it can be seen that the R wave can still be read while still, but the R wave cannot be read in the motion state. If the impedance at that time is too high to satisfy the user's demand, for example, the demand is to recognize the R wave during walking, the countermeasures proposed in the present embodiment are as follows.
  • the preliminary result of our experiment is that when the electrode impedance is less than 1 M Ohms, the heartbeat can be measured with the control box shown in Figure 1 (a), and the interference caused by body movement is relatively low, even if the above is not used.
  • the separate electrode structure can still read the R wave during walking, and the capacitance between the two electrodes is about 10 nF.
  • the electrode impedance is between 1 M and 2 M Ohms, the R-wave during walking can be measured with a separate electrode structure, and the capacitance between the two electrodes is about 5 nF.
  • the electrode impedance is between 20 M and 30 M Ohms (the capacitance between the two electrodes is between 0.33 and 0.5 nF)
  • the active electrode circuit is activated (setting the preamplifier circuit to the near electrode) can reduce the noise to identify the static heartbeat; if the electrode impedance is between 30 M and 40 M Ohms (the capacitance between the two electrodes at this time) The value is approximately 0.25 to 0.33 nF), then the negative feedback circuit and the active electrode must be activated. Road, just enough to reduce the noise to identify the static heartbeat.
  • the processor can guide the user to tighten the belt, add clothing, and maintain functional warmth through the communication device.
  • the material, the position of the electrode is replaced, or the conductive liquid is added to the electrode so that the impedance is less than 40 M Ohms before the heartbeat is detected. Otherwise, the heartbeat is not detected, only the noise is detected and the power is wasted, but the noise can be measured. Get the body's action state. If the electrode impedance has dropped below 40 M Ohms and the noise is still too large to measure the heartbeat, the control box can activate the aforementioned unstarted circuit or activate the capacitively coupled electrode circuit (see Example 3 for details).
  • the above resistance value is only an example for explanation. In a large number of applications, the above resistance value should be adjusted according to the actual environment. In this embodiment, the resistance value in various conditions is stored in a database as a reference for judgment.
  • the above method can also be applied to electrodes for electroencephalography, electrogram, transcutaneous electrical nerve stimulation (TENS) or electric shock.
  • the temperature, resistance and capacitance of the electrodes listed in Table 2 are stable when the electrode is firmly attached to the body, and vice versa. It may be caused by the electrode not being close to the body or the user's strenuous exercise.
  • the ECG signal cannot be obtained at this time. Therefore, the temperature, resistance and capacitance of the electrode can be regarded as an indicator of whether or not the electrocardiographic signal can be obtained.
  • the sampling rate can be low and easy to identify, and is not as difficult to identify as the sampling rate of the electrocardiographic signal is complicated.
  • the temperature, resistance, and capacitance of the electrodes are not only suitable for the processor to provide appropriate countermeasures, but can also be sent to the remote monitoring center via the communication device to activate the appropriate circuitry, firmware, software or instructions from the remote end.
  • the electrode impedance cannot be reduced to obtain an ECG signal with a noise of 4 ,.
  • the processor can output a specific code without outputting the noise of the unrecognizable ECG type. Save on power consumption.
  • the above countermeasures can also be implemented in reverse.
  • the processor can select a bandpass with a wider band. Filter (0. 1 ⁇ 40 Hz) to capture the complete ECG, the processor can also recommend the user to relax the belt for comfort.
  • the processor can select a narrow bandpass filter (10 ⁇ 30 Hz) to capture the R wave while dropping 4 ⁇ dry ⁇ ⁇ , or Hi lber t- Huang transform to find the heart rate. Therefore, the present invention can be maintained in terms of power saving, comfort, and signal quality according to actual conditions. Optimization. This method is also applicable to electrodes for electroencephalography, electromyography, transcutaneous electrical nerve stimulation (TENS) or electric shock.
  • a certain threshold for example, 2 M Ohms
  • TESS transcutaneous electrical nerve stimulation
  • the first method of the sixth embodiment can simultaneously measure the capacitance value between the fabric electrodes, and if the capacitance value is still not small (for example, 10 nF) and the resistance value is large (for example, 10 M Ohms), the representative electrode Still on the body, just the skin is too dry and not easy to conduct. If the capacitance value is small and the resistance value is large, it is likely that the electrode is disconnected or the transmission line is faulty. At this time, the present invention can guide the user to check or troubleshoot through the communication device.
  • the capacitance value is still not small (for example, 10 nF) and the resistance value is large (for example, 10 M Ohms)
  • the representative electrode Still on the body, just the skin is too dry and not easy to conduct. If the capacitance value is small and the resistance value is large, it is likely that the electrode is disconnected or the transmission line is faulty.
  • the present invention can guide the user to check or troubleshoot through the communication device.
  • the resistance of the electrode is 5. 7 M Ohms, the capacitance is 5. 7 M Ohms, the capacitance is 2, the resistance of the electrode is 2. 2 M Ohms, the resistance is 5. 7 M Ohms, the capacitance is 2 2 nF ⁇ The resistance is 9. 3 M Ohms, the capacitance is 1. 2 nF. This is because the electrodes are not in close contact with the human body due to body movement, causing the resistance to rise and the capacitance to drop, while other causes (such as ambient temperature and humidity or sweat caused by non-motion) do not easily cause such rapid changes in electrode impedance. . Using this feature, we can estimate the state of human motion from changes in electrode impedance, ie, the greater the magnitude of the change, the more intense the motion.
  • the processor can selectively read the signals of the accelerometer, gyroscope, camera or other sensor that can sense the movement of the human body to confirm the movement of the human body.
  • the capacitor in the filter circuit can be connected in parallel with an electronic switch (consisting of a field effect transistor), which is controlled by the microcontroller and connected to the ground of the circuit.
  • an electronic switch consisting of a field effect transistor
  • the microcontroller turns on the electronic switch, causing the capacitor's charge to leak to the ground, and the signal is quickly pulled back to the middle by the saturation region, thus shortening the transient response time of the filter circuit, and more time is available. Identify the R wave.
  • one more electrode is added, and then two of the three electrodes are selected. That is, the ECG signal can be obtained.
  • This third electrode is disposed in the vicinity of the 0-bit line, and a better effect can be obtained.
  • one electrode is located at B (1.4 bit line), and the other electrode is located at -0.3 bit line.
  • the two electrodes can obtain a lead ECG signal, amplitude. For the case of 1.7 «iV, if one electrode is located at the 0-bit line, three lead-type ECG signals are obtained, and the amplitudes are 1.
  • the equipotential line is not extended by zero symmetry.
  • the position of the third electrode is preferably from 0 to +0.5.
  • the area between the bit lines is preferably, for example, the position of the third electrode is at +0.5.
  • the electrocardiographic signal having an amplitude of 1. 7 mV, 0.9 mV and 0.8 mV is obtained. If second The electrodes are located at the -1. 0 equipotential line, and the effect is better.
  • an electrode can be disposed on each of the left arm, the right arm, and the left leg of the diaper, which not only generates
  • Lead I, Lead II, Lead III limbs can also produce a reference potential for measuring the chest lead, and in the region between the thoracic-1 equipotential line to the +1. 4 equipotential line, ie the chest lead VI to V6 Position, set one or more electrodes with an area of 2*2 cm. Due to the elasticity of the fabric, it is likely to inadvertently move within this area, and the processor can collect the ECG signals from VI to V6.
  • the reference potential can be obtained by connecting the clothes and pants, or even a hat or glove, in addition to being taken by the limb. Second Embodiment Estimating human motion from noise
  • the first method Estimating human motion from the number of times the noise is misjudged as R waves
  • the noise when the noise is to be estimated to estimate the motion of the human body, if the noise is not suppressed by the filter firmware, a lot of noise is erroneously judged as an R wave. Since the interval between noises is much smaller than the interval between normal heartbeats, and under normal circumstances, it is impossible for a heartbeat to jump to extreme fierce in 72 minutes (R wave interval is 0. 833 seconds) under normal activity within one minute. 200 times under motion (R wave interval is 0.3 seconds), so the t controller in the control box can easily identify the presence or absence of noise.
  • the rules for identification are as follows: take the heart rate with the most number of times in one minute, and set the R wave.
  • the interval is 1, and a part of the R wave interval less than 1 (for example, one-half or two-thirds) is regarded as noise.
  • a part of the R wave interval less than 1 for example, one-half or two-thirds
  • noise By accumulating the number of noise intervals in the statistical graph, it can be regarded as a pointer of the noise level, that is, the magnitude of the motion amount.
  • the amount of exercise for a period of time (for example, seven hours of sleep) is plotted as a graph of sleep activity, thereby understanding the quality of sleep of the user.
  • the sleep activity map in which the noise number is accumulated as an activity index, the horizontal axis is time, and the vertical axis is the accumulation of noise times as the activity amount.
  • the noise level can also be expressed by the noise amplitude on the horizontal axis of the ECG. The larger the amplitude, the larger the amount of motion.
  • the noise is regular, for example, if there is a large amount of noise every 0.5 seconds, for three minutes, it can be inferred that the user is performing regular movements, such as walking; if occasionally a large amount of noise occurs, it may be caused by anxiety. Or the wearer is emotionally stressed, and there will be a lot of EMG signals interfering with the ECG.
  • the resulting activity map can be used for the elderly who are caring for the home. The caregiver can judge the behavior of the elderly and intervene in due course.
  • the second method estimates body motion from peak amplitude
  • the microcontroller can still recognize the R wave, but it will also get noise.
  • the amplitude of these noises may vary greatly and irregularly. However, normal The amplitude of the R wave is quite stable, and there is no rule.
  • the processor can record the maximum value (ie, the amplitude of the peak) for each small period of time. The time is plotted on the horizontal axis and the amplitude is plotted on the vertical axis. This figure represents the degree of body motion interference. When there is no body motion, the graph will show an approximate straight line, and the more intense the body motion, the greater the line undulation.
  • the third method estimates the body movement from the proportion of time taken up and down.
  • the ECG signal When the body is too intense, the ECG signal can easily drift to the upper saturation zone or the lower saturation zone. For the signal reaching the saturation region, the R wave cannot be interpreted. However, the ratio of reaching the saturation region to the total time represents the degree of motion interference. In a certain period of time, the longer the time to reach the saturation zone, the stronger the motion disturbance.
  • the fourth method is to estimate human motion from a linear range.
  • Figure 13 (d) shows the signal in motion
  • the firmware will automatically reduce its gain value, expand the linear range, so that the entire signal is not saturated in the linear range; relatively speaking, if the user is at rest, signal there will be a dramatic change, then the firmware will automatically increase its gain, narrow linear range, in order to obtain good resolution, namely existing conventional automatic gain control function (Auto Ga in control) 0
  • the degree of body motion can also be estimated by the change of the gain value or the magnitude of the linear range, that is, the gain value is large (the linear range is small), that is, the body motion is gentle, and vice versa.
  • the fifth method is to estimate human motion by the number of normal R waves per unit time.
  • Fig. 17 (a) to Fig. 17 (f) and the fourth method it is known that when the signal is disturbed by the body motion and drifts to the upper saturation region or the lower saturation region, the R wave cannot be interpreted. On the other hand, under normal conditions, the R waves are stably presented at reasonable intervals. Therefore, in this embodiment, the number of normal R waves in a unit time can be taken as an index, and the lower the number of R waves, the more intense the human body is.
  • an attitude sensor such as an accelerometer, a gyroscope, a geomagnetic meter, or an inclinometer can be selectively added to the control box or the fabric, and the signal such as the acceleration is used as a pointer for action or noise.
  • the conductance between the dry electrode and the skin becomes very low, which is not conducive to the extraction of the ECG signal, leaving only the capacitive.
  • a capacitively coupled electrode and circuit can be used, that is, there is no direct current conductance between the electrode and the skin, but capacitive coupling is used to transmit the ECG signal.
  • the physiological monitoring suit is preferably capable of combining both the dry electrode and the capacitively coupled electrode to respond to the environment. The change.
  • the insulating layer of the above-mentioned capacitively coupled electrode is a dielectric material, and a material having a relatively high dielectric constant and a low conductivity is preferable, such as nylon (Nylon, relative dielectric constant 2), silicon dioxide ( The relative dielectric constant is 3. 9), polyvinyl chloride (PVC, relative dielectric constant 3), copper calcium titanate (CCT0, relative dielectric constant is about 10000) and the like.
  • the dielectric shield can be attached to the fabric in addition to being attached to the conductor as a whole. The following examples are given.
  • the dielectric is mixed with a solvent or an adhesive, and then immersed in a cotton yarn, the cotton yarn is adhered to a dielectric shield, woven into a cloth, or woven into a cloth with other fibers, and then formed into a cloth.
  • the cotton yarn in the above example is replaced by a conductive fiber, and the woven fabric is a capacitively coupled electrode.
  • the dielectric material can be physically or chemically removed, and the conductive fiber can be exposed. Connect to other conductors.
  • the conductor and the dry electrode of the capacitively coupled electrode can be placed on the fabric in different ways, for example:
  • the non-conductive fiber and the conductive fiber are jointly woven by a text process, which is kni tt ing, weaving, tat t ing , embroidering or other suitable process;
  • non-conductive fibers may be, for example, but not limited to, cotton, hemp, nylon, etc.
  • the conductive fibers may be, but not limited to, multi-molecular conductive fibers or conductive metal fibers, or may be blended with stainless steel fibers and non-conductive fibers, or It is formed by coating or infiltrating a conductive material on the insulating fiber, and the ratio of the conductive material to the conductive region may be 1% to 100%.
  • the above-mentioned dry electrode and capacitor-bonded electrode are mounted on the fabric, and the combined type of the two electrodes is as follows:
  • Fig. 18 (a) is the first type of the two electrodes of the present invention.
  • the conductor 75 is covered with an insulating layer, disposed between the fabric 85 and the human body, and is located beside the dry electrode 40, as shown in FIG. 18(b), and FIG. 18(b) is a combination of the two electrodes of the present invention.
  • Fig. 18(c) is a schematic view showing a third form of the two electrodes of the present invention.
  • FIG. 18(d) is a schematic view showing a fourth form of the two electrodes of the present invention.
  • the conductor 75 is covered with an insulating layer, disposed between the fabric 85 and the human body, and placed on the dry electrode 40, as shown in FIG. 18(e), and FIG. 18(e) is a combination of the two electrodes of the present invention.
  • Fig. 18(f) is a schematic view of a sixth form in which the two electrodes of the present invention are used together;
  • Fig. 18(g) is a schematic view of the seventh form in which the two electrodes of the present invention are used together;
  • the conductor 75 is disposed as an electrode in the fabric 85.
  • the conductor 75 itself can be a dry electrode or a capacitively coupled electrode.
  • the microcontroller in the control box can switch the circuit using the capacitively coupled electrode to extract the ECG signal.
  • the microcontroller can switch the circuit using the dry electrode.
  • the ECG signal is taken (as shown in Fig. 19, wherein the visible noise level selectively uses a negative feedback electrode, and an insulating layer can be selectively added as a dielectric shield under the electrode to increase its capacitance, as shown in Fig. 18 (h) is shown in Figure 18 (h) is a schematic view of an eighth form of the two electrodes of the present invention.
  • the elastic conductor 75 is disposed on the inner surface of the fabric 85 and on the dry electrode 40, and another insulating layer dielectric is attached to the dry electrode 40, as shown in Fig. 18(i), and the dry electrode 40 is further
  • the elastic band (not shown in Fig. 18(i)) is attached to be attached to the fabric 85, and Fig. 18(i) is a schematic view of the ninth form in which the two electrodes of the present invention are used together.
  • the position of the capacitively coupled electrode with the preamplifier circuit should be as close as possible to the electrode, which is the "active electrode”.
  • the dry electrode shares a transmission line with the capacitively coupled electrode, as shown in FIG. 19, which is a schematic diagram of a circuit in which the capacitively coupled electrode of the present invention shares a circuit with the dry electrode.
  • FIG. 19 is a schematic diagram of a circuit in which the capacitively coupled electrode of the present invention shares a circuit with the dry electrode.
  • both shielding and protection can be used.
  • Conductive cloth such as silver fiber cloth or steel cloth
  • Conductive cloth used in the original copper foil, conductive film and other techniques used in general circuits, used on fabrics, or replaced with other conductive cloth or conductive materials to achieve shielding and protection purposes.
  • the gas or liquid helium may be disposed under the conductive cloth.
  • a gas or liquid helium (containing air such as air, water or oil) is disposed inside the electrode, when the body is only pressed to a certain side, The fluid in the gas or liquid helium will flow to the other side to bring the conductive cloth on the other side closer to the body, which increases the conductivity.
  • Elastomers such as sponges, silicones or springs can also be optionally added to the gas or liquid helium to absorb water. Sexual materials are preferred for buffering purposes.
  • the above gas or liquid helium can also be applied to electrodes at different positions, for example, one electrode is disposed under the right jaw and one electrode is disposed at the right waist.
  • the right lower arm and the right side of the waist should be pressed by the body, but due to the curve of the body or the uneven shape of the bed, it is possible that only one of the electrodes is completely depressed, and the other contact is not
  • a set of (two) gas or liquid helium is connected as a connecting tube as shown in Fig. 21 (a)
  • the other side electrode can be brought closer to the body. Increase conductivity.
  • a group of gas or liquid helium connected by a connecting pipe can also be used to prevent another electrode from accidentally touching the human body.
  • the sleep position is determined by the ECG signal waveform.
  • the right side should only be pressed to the right lower arm and the right side, but the front chest electrode will also be Being oppressed by the hand and touching the body.
  • gas or liquid helium may be disposed at the right lower jaw and the front chest electrode, and the two are connected by the communication tube, but the gas or liquid helium is not between the conductive cloth and the clothing, but is electrically conductive.
  • the air sputum or liquid helium in the right armpit will be pressed, so that the air sputum or liquid helium in the chest will expand, and it will not be easily touched by the hand and touch the body.
  • the above-mentioned electrodes are dry electrodes, which are in contact with the human body, but are equally applicable to capacitor-fitted electrodes.
  • a small piece or strip of material having a high relative dielectric constant may be added to the electrode, such as nylon (Nylon, relative dielectric constant of 3.2), and silicon dioxide (relative dielectric constant of 3.).
  • nylon nylon, relative dielectric constant of 3.2
  • silicon dioxide relative dielectric constant of 3.
  • a material such as polyvinyl chloride (PVC, relative dielectric constant 3) and copper calcium titanate (CCT0, relative dielectric constant: 10000), as described in the third embodiment, to increase the capacitance.
  • liquid helium filled with water it can be used in an elastic structure that can be opened when it is not pressed, and it is slightly leaky, that is, it is not completely sealed, so that it can absorb water during washing, and is used during use. At the pressure, a small amount of moisture can be exuded to the electrode to increase conductivity. If the liquid helium has the above-mentioned elastomer, the moisture contained in the liquid can be prevented from oozing out too quickly. When the liquid helium becomes contained in the liquid, the elasticity of the liquid helium can be negatively pressed inside the squeezed liquid to suck the human skin, and at the same time, the liquid (for example, water) on the skin can be sucked on the electrode. Conducive to electrical conduction.
  • an air compressor controls a pump to push air, oil or water
  • the pump is connected via a closed tube to a gas or liquid helium fixed between the electrode and the fabric.
  • the microcontroller can turn on the pump to inflate the gas or liquid helium to force the electrode against the skin by the pressure of the gas or liquid helium.
  • an oil or water storage tank may be provided in the control box.
  • the first method of this embodiment is to provide a permanent magnetic substance 5 on the outside or beside the electrode, such as AlNiCo, Ferrite, SmCo and NdFeB. And a magnetic conductive material such as silicon steel or permanent magnetic material 5 is disposed on the corresponding side of the body, but opposite to the polarity of the permanent magnetic shield, the attraction of the electrode 40 can be induced by the principle of heteropolar attraction.
  • the force of attaching to the body is greater, so that body motion interference can be reduced, as shown in Fig. 22 (a), and Fig. 22 (a) is a schematic view of the present invention in which a magnet is attached to the fabric and the electrode. .
  • the magnetic substance 5 is disposed outside or beside the electrode, and the permanent magnetic substance is disposed on the corresponding side of the body, which has the same effect.
  • the electrode itself may be a permanent magnetic substance 5 or a magnetic conductive substance, for example, stainless steel and silicon steel may be magnetically and electrically conductive, and thus may also serve as an electrode; aluminum-nickel-cobalt, samarium-cobalt and neodymium-iron-boron may also be electrically conductive, It can be used as the electrode 40; the permanent magnetic substance 5 or the magnetic conductive substance (such as ferrite) can be drawn into the wire, or placed in the hollow fiber, combined with other materials to form a wire, or coated by dyeing or electroplating. Outside the yarn, it is combined with a conductor (such as silver fiber) in a twisted or blended manner to form a conductive cloth, which is electrically conductive and magnetically conductive.
  • a conductor such as silver fiber
  • the second method of this embodiment utilizes the principle of the same pole repulsive to push the electrode 40 toward the body.
  • a permanent magnetic substance 5 is disposed on the outer side of the underarm electrode, and a permanent magnetic substance 5 is also disposed on the inner side of the upper arm so that the same poles of the two permanent magnetic substances 5 oppose each other, causing the underarm electrode 40 to be pushed toward the body. , you can reduce body motion interference.
  • a permanent magnetic substance 5 may be placed on an object close to the body (e.g., a bed, a chair, etc.) so as to be opposite to the pole, and the electrode 40 may be pushed toward the human body.
  • a permanent magnetic substance 5 is placed on the outer garment or the bra, and an electrode and a permanent magnetic substance 5 are placed on the underwear; a permanent magnetic substance 5 is placed on the outer pants and the shoes, and an electrode and a permanent magnetic substance 5 are placed on the sock to make the same
  • the poles are relatively repulsive to push the electrodes toward the body.
  • a permanent magnetic substance which is repelled by the same pole is provided in each of the electrode 40 and the fabric 85, that is, the electrode 40 is pushed toward the human body; similarly, in Fig. 4(a) to Fig. 4 ( d)
  • the separated electrode 40 and the fabric 85 may also be provided with a permanent magnetic substance 5 which is repelled by the same pole, that is, the electrode 40 is pushed toward the human body; similarly, as shown in FIG. 21(b)
  • the gas or liquid helium and the conductive cloth may each be provided with a permanent magnetic substance 5 which is repelled by the same pole, that is, the electrode 40 is pushed toward the human body.
  • a permanent magnetic substance 5 repelling the same polarity may be selectively disposed on the slider and the fabric shown in FIG. 7(a), that is, the electrode 40 may be pushed toward the human body; or in FIG. 7(b)
  • the electrode 40 and the slider are respectively provided with a permanent magnetic substance 5 which is repelled by the same pole, that is, the electrode 40 is pushed toward the human body; or, on the electrode 40 and the fabric 85 shown in FIG. 7(c)
  • the ring type permanent magnetic substance 5 can be used to increase the stability of the mutual repulsive magnetic force, as shown in Fig. 22 (b), and Fig. 22 (b) is a schematic view showing the use of the ring type permanent magnetic substance in the present invention.
  • the repulsive force of the permanent magnetic substance around the ring-shaped permanent magnetic substance 5 and the electrode 40 makes the electrode 40 within the ring type and is not easily moved outside.
  • the permanent magnetic substance 5 can be placed on both sides of the electrode 40 to attract the magnetic force to bring the electrode close to the human body, as shown in Fig. 22 (c), and Fig. 22 (c) is a schematic view showing the permanent magnetic substance on both sides of the electrode on the clothes of the present invention.
  • the magnetic material 5 is long, and the electrode 40 is brought close to the human body.
  • the permanent magnetic substance 5 is composed of a plurality of small blocks, which are composed of a plurality of small pieces, so that the south pole and the north pole are connected to each other.
  • the permanent magnetic substance 5 groups can be bent with the change of the body shape, and the magnetic effect is better. Users are also more comfortable. Sixth embodiment. Poor contact of the detecting electrode
  • the present invention provides eight methods for detecting whether the electrode is in poor contact with the skin:
  • Fig. 23 is a schematic view showing whether or not the pulse wave detecting electrode is in poor contact in the present invention. It is generated by a microcontroller or an oscillator (such as LM555), which is connected to an electrode via a current limiting resistor and an analog switch (ana log swi tch). The analog switch 1 and the analog switch 2 are digital. Output control to select the electrode connection pulse to detect poor electrode contact, or connect to the instrumentation amplifier to obtain the ECG signal.
  • a microcontroller or an oscillator such as LM555
  • an analog switch ana log swi tch
  • the analog switch 1 and the analog switch 2 select electrodes to connect the pulse wave
  • one electrode is connected to the analog input end of the microcontroller, and the amplitude or frequency or the effective period thereof is measured, that is, the impedance between the two electrodes is known.
  • the method of measuring the capacitance of the universal meter is to detect the impedance between the electrode and the skin layer of the human body, and the conductivity of the human skin is generally based on the capacitance, so the capacitance is obtained by the method.
  • a method of measuring a capacitor using a multimeter can be used, and the result is shown in Table 2. If the impedance is greater than a certain critical value, it is determined that the contact is poor. As shown in Fig. 24 (a) to Fig.
  • a change in capacitance a method in which a circuit emits a signal and expresses the impedance change as a function of frequency, voltage, or current.
  • This method can be used not only to determine if the electrode is in poor contact, but also to read breathing, posture, or gait analysis.
  • the electrode is directly in contact with the human body.
  • the oscillator When the person lies down, the oscillator generates a pulse wave frequency of 170 kHz, and when standing, it is 120 kHz when sitting down. It is 80 kHz when sitting down. This is because the gravity direction and posture change the chest circumference and the abdominal circumference. The pulse frequency changes accordingly.
  • the breathing can make the pulse wave frequency change up and down.
  • the breath can be measured at this time, it means that the electrode is in good contact with the human body.
  • this method can also be applied to a capacitively coupled electrode.
  • the electrode can not directly touch the human body. Because the circuit emits a pulse wave instead of a direct current, the capacitance value of the electrode can still be measured. At the same time, the electrodes can also be in direct contact with the clothes without the clothes.
  • Fig. 25(a) is a schematic view of two electrodes of different shapes but electrically connected in the present invention.
  • Two of the electrodes that are electrically connected but of different shapes, sizes, or materials have different impedance changes during the process of contact with the skin from loose to tight (as shown in A and B of Figure 25 (b)).
  • the impedance is different even in a completely close condition, whereby the method can infer that the electrode is in contact with the human body, thereby inferring the position of the electrode, thereby inferring its posture.
  • FIG. 26 is a schematic illustration of four electrodes of the present invention that connect different electronic components.
  • Two electrodes that are electrically connected but connected in series or in parallel with different electronic components will react differently when receiving the pulse input, and their modes, phases, impedances, and resonance frequencies will change.
  • the waveform will be an exponential function that charges and discharges, and is no longer the original pulse.
  • the microcontroller can discern these changes, so it can be inferred that the electrode is in contact with the human body, so that the electrode in contact with the human body can be used to receive the ECG signal.
  • the posture is inferred. For example, when the electrodes on the left and right sides are in contact with the human body, it can be inferred that the left and right arms are close to the body or not, and vice versa.
  • the microcontroller does not get the normal interval of R wave, Q wave or S wave for a period of time (for example, one minute) (the normal interval is about 1. 5 seconds to 0.3 seconds), thereby judging that the resulting signal is noise.
  • the following conditions may occur: 1.
  • the electrode is in poor contact with the skin or the skin is too dry and difficult to conduct electricity. 2.
  • the interference caused by body movement is too large, the signal is saturated up or down, and the R wave cannot be interpreted. 3.
  • the outside world The electromagnetic interference is too large.
  • the third method is a schematic view of whether or not the sine wave measuring electrode of the present invention is in poor contact.
  • a current limiting resistor about 10 K Ohms
  • a high-pass filter composed of passive components
  • a high-frequency signal generator such as a sine wave generator
  • a low-pass filter to the front end of the instrumentation amplifier to allow the low-frequency ECG signal (below 40 Hz) to be transmitted to the instrumentation amplifier, and prevent the sine wave from entering to avoid interfering with the ECG signal, so that the ECG signal can be simultaneously acquired.
  • the sine wave can detect whether the electrode is in poor contact.
  • Figure 27 can be placed on the active electrode circuit to reduce external electromagnetic interference and to help determine noise.
  • the fourth method is implemented by the conventional impedance pneumogram technique. If the respiratory rate can be read from the spirogram, the electrode is Stick to the body. Conversely, if a large number of high frequency components appear in the spirogram, it can be inferred that this high frequency must be noise because the frequency of normal breathing is very low (less than 1 Hz). Noise is a sign of poor contact.
  • the fifth method does not output any signal to the electrode, so that the electrode potential is close to floating, and then the signal obtained by the single electrode is taken.
  • the impedance at the input of the op amp is its own internal resistance (indicated by Rinl, Rin2).
  • an operational amplifier with an input impedance greater than 100 M Ohms should be used.
  • the electrode is in good contact with the human body, the human body forms a good conductor, which is easily capacitively or inductively coupled with a 50 or 60 Hz power source.
  • a single electrode will obtain a relatively strong 50 or 60 Hz. Disturbance source.
  • a single electrode is not easily coupled to a 50 or 60 Hz source of interference from the power supply because of the long transmission line, resulting in a relatively weak and white noise (whi te noi se) irregular background noise.
  • the sixth method the circuit on the fabric and the processor, is shown in Figure 29, which outputs a pulse to the electrode and records the voltage change during its charge and discharge. If the electrode is in good contact with the human body, a capacitance is formed between the human body and the electrode. The closer the contact is, the higher the capacitance value is, and the longer the charging and discharging time is.
  • the processor is charged and discharged via the electrode, and the current is returned to the processor in the control box through the stray capacitance between the processor and the human body.
  • the capacitance value is very low, and there is almost no charge and discharge time.
  • the processor can measure the charge and discharge time of a single time, or continuously charge and discharge with an oscillating circuit (for example, LM555) and measure the oscillation frequency. As described in the fifth embodiment, it can be judged whether the electrode and the skin are in poor contact.
  • an oscillating circuit for example, LM555
  • a small piece or a strip of high relative dielectric constant material may be selectively applied to the electrode, such as nylon (Nylon, relative dielectric constant of 3.2), silicon dioxide. (relative dielectric constant is 3.9), polyvinyl chloride (PVC relative dielectric constant is 3), copper calcium titanate (CCT0, relative dielectric constant is about 10000), etc., the above method can also be realized by sine wave .
  • the seventh method the internal structure of the processor is shown in Figure 30, an electrode itself has two transmission lines connecting the electrodes and the processor, and the microcontroller emits a sine wave or a pulse wave connected to the electrode via another transmission line.
  • Rou 11 and Rou 12 take 10M Ohms or more resistors to match the stray capacitance and inductance.
  • the fifth method is used for analysis. If the electrode is in good contact with the human body, the human body forms a good conductor. A 50 or 60 Hz power supply produces a capacitive or inductive coupling. Analog input 1 and analog input 3 can cause 50 or 60 Hz interference; conversely, 50 or 60 Hz interference is not easily obtained. Therefore, it can be judged whether the electrode is in poor contact with the skin, and if the input signal has no sine wave or pulse wave, the transmission line or the electrode may be damaged and the circuit is broken.
  • the dry electrode measures the surface surface DC resistance to evaluate whether the electrode is in good contact by adding an analog switch at the input end of the processor, as shown in FIG. 31, by a resistor and a Zener diode or A similar reference voltage source produces a DC power supply with a voltage of approximately 1 Volt to measure DC resistance. The lower voltage is taken to avoid polarization and electrolysis of water at the electrode end.
  • the purpose of using direct current is that the direct current cannot pass through the outermost stratum corneum of the skin. Only a small part can enter the body by the sweat gland. Most of the direct current will flow through the sweat on the surface of the skin, from one electrode to the other. The more dry the skin is, the less it will be. It is easy to conduct physiological electrical signals to the electrodes, that is, the electrodes are not in good contact with the human body.
  • the processor can measure whether the electrode is in good contact.
  • the processor can suspend the ECG signal from the dry electrode, and the ECG signal is obtained by the capacitor-coupled electrode. , or by the communication device to remind the user to wear more clothes to keep warm, can increase the sweat on the skin surface to improve the quality of ECG signals, as shown in Table 2.
  • Measure the DC resistance of the skin surface and also detect whether the electrode is attached to the skin. If it is, its value should be stable. Otherwise, the electrode contact is unstable. If the resistance value is large, it means that one electrode is not attached to the human body.
  • the ninth method is to provide a fabric-based sensor near the electrode to detect whether the electrode is in close contact with the human body, and whether the human body has a moving crepe sensor or the sensor can be used by the applicant's previously proposed US Patent 7,750,790.
  • the pressure and tension sensors themselves can also be considered as part of the electrode.
  • Figure 1 (a) to detect whether the left and right lower jaw electrodes are in good contact, the above fabric sensor can be installed on the clothes between the two poles.
  • the clothing fabric Elasticity creates a pulling force that puts pressure on the body and the fabric sensor detects the tension or pressure. Conversely, if it is too loose, the clothing does not have enough pressure or tension to allow the electrode to have good contact with the skin. On the other hand, if the tension or pressure detected by the fabric sensor is maintained at a certain value without a large change, that is, the user does not move, then there is no body motion disturbance; on the contrary, if the tension or pressure changes, it means The user is in motion and there is physical disturbance at this time.
  • the tenth method is to form a capacitive pressure or tension sensor by sandwiching an insulator between two conductive cloths, and the insulator may be an elastomer or a material containing a high dielectric constant. Under external pressure or tension, the capacitance value also changes.
  • the processor can measure the capacitance value using the circuit described in the first method of the fifth embodiment.
  • the capacitive pressure or tension sensor can be placed between the clothing and the human body. When the posture of the person changes, the capacitance value also changes.
  • the processor can set a threshold value, that is, under a certain degree of pressure, the physiological signal is accepted, for example, the pressure is greater than a critical value to start the electrocardiogram detection. If the capacitance value changes greatly, it means that there is body motion interference.
  • one of the two conductive cloths close to the human body can be used as a resistance (dry) electrocardiogram electrode at the same time, and the other can be used as a capacitively coupled electrocardiogram electrode at the same time, so that two conductive cloths form a capacitor as a switch, and at the same time
  • the conductive cloth can also be used as an electrode, so that poor contact is also detected at the same time.
  • the method for estimating physical activity by noise is disclosed in the present invention.
  • the embodiment can also estimate the physical activity by detecting the impedance of the electrode, for example, an electrode is located under the armpit. When it is in poor contact, it means that the arm is not in close contact with the body.
  • the present embodiment can also be applied to electrodes for electroencephalography, electromyography, transcutaneous electrical stimulation treatment, and electroshock treatment, and whether the electrodes are in good contact.
  • the eleventh method is to determine whether the electrode is close to the body by other physiological signal sensors.
  • other physiological signal sensors such as a stethoscope (which must be in full contact with the body but do not have to wait for its transient response to measure the heart and lungs), ultrasonic probes, Thermometer (need to wait for its transient response for about 3 minutes, if the sudden change in body temperature means the sensor is not close to the body), oximeter (need to wait for its instantaneous response for about 20 seconds), sphygmomanometer (if the blood pressure is unstable, it means people)
  • the electrocardiographic electrodes can be placed beside these sensors.
  • This embodiment can also provide other physiological sensors, such as an electromyography sensor, an oximeter, a thermometer, a cardiopulmonary sensor, or an ultrasonic blood flow meter, in the vicinity of the electrodes, by analyzing signals or noise of other physiological sensors. , to estimate the body motion of the site. For example, when the EMG sensor obtains a large signal, it means that the muscle activity is more intense, that is, there is body motion interference; similarly, when the oximeter only obtains violent sloshing noise without stable pulse wave At the time, it indicates that there is physical disturbance.
  • the processor can measure the impedance of each electrode, select the two electrodes with the lowest impedance, or select the electrodes by other methods to pick up the ECG signal, and obtain the best signal quality.
  • the output value used to determine whether the electrode is in good contact with the human body changes due to body motion.
  • the amplitude of these output values represents the degree of body movement. The more intense the motion, the greater the amplitude. If the body is at rest or the electrodes are in good contact with the human body, the output value is stable. Therefore, from the amplitude of these output values, the degree and state of body motion can be determined.
  • the electrode is in good contact with the human body, but a long-term and stable heartbeat signal cannot be obtained, which may result in poor contact of the electrode or the transmission line.
  • inspection and maintenance can be carried out in accordance with the method shown in the seventh embodiment, as described below. Seventh embodiment. Judging whether the transmission line or the electrode is poorly connected
  • the invention is capable of withstanding the general washing. If the force of the crucible is too large, the transmission line or the electrode may be damaged, and the ECG signal cannot be transmitted to the control box.
  • This embodiment proposes two methods: The first method allows the processor to determine whether the transmission line is poorly connected, as shown in FIG. Taking the dry electrodes on the left and right sides as an example, in addition to each of the transmission lines connected to the processor, a transmission line is connected to the two electrodes, which is connected in series with a push button (push but ton swi tch) or a toggle switch (toggle) Swi tch), disposed on the fabric of the present invention. When the button switch is not pressed, it will not conduct, and it will be turned on when pressed.
  • a push button push but ton swi tch
  • a toggle switch toggle
  • the signal output will present a horizontal line close to zero. If the transmission line or electrode is damaged, the signal output will be chaotic. The noise. In both cases, the signal output is greatly different.
  • the user's naked eye or the program built in the control box can determine whether the transmission line or the electrode is poorly connected by the amplitude of the noise.
  • the second method, on the fabric, is the same as the first method, that is, another transmission line is connected to the two electrodes, and the transmission line is connected in series with a push button switch or a switch, except that the processor is as shown in FIG. 29 or In the architecture of FIG. 30, the processor outputs a pulse wave or a sine wave as a carrier for testing via an output resistor, an electrode, and a transmission line, and then passes through another transmission line connecting the two electrodes and a push button switch or a switch thereof in series. And the other electrode and its transmission line, if the wire or electrode of the path is not damaged, the wave is returned to the control box, and the transmission line can be judged to be damaged by this method.
  • comparing the amplitudes of the output wave and the return wave if there is a large drop, it means that the conductivity is not good, the system is faulty, and should be sent for repair and should not be used.
  • the spectrum of the carrier and the signal-to-noise ratio (S/N) near its main band, and then analyze the S/N near the main band of the return wave spectrum.
  • the difference between the two is the quantization of external noise interference. pointer. If the transmission line and the electrode conduction condition are good, the difference between the two should be extremely small, and vice versa.
  • the present invention can set the quantization pointer (the noise amplitude of the first method, the difference between the carrier of the second method and the S/N near the main frequency band of the return wave) for each of the transmission lines and the electrodes.
  • the threshold for example, the threshold of the first method is 50% of the factory value.
  • the maintenance method is for a poorly conducting electrode or a transmission line, and a suture is added to the joint of the conductor to strengthen the conductivity, or a plurality of conductive wires are sewn, or a piece of conductive cloth is sewn.

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Abstract

公开了一种侦测心跳或电极接触良好与否的物品、方法及系统。该系统是在织品上设置多个织品电极，利用心电图的等位线图，并考虑人体运动所造成的干扰，设置为分离式电极结构。该系统可以根据电极位置、面积以及导线布局来侦测心跳，并可随环境状态的改变选择由干电池或电容耦合式电极撷取心电信号。该系统还可以通过测量噪声、体表阻抗、肌肉阻抗来侦测电极与人体的接触是否良好，还可以由心电信号波形及噪声来推测人体姿势与动作。

Description

一种侦测心跳或电极接触良好与否的物品、 方法及系统 技术领域
本发明涉及一种侦测心跳或电极接触良好与否的物品、 方法及系统，特 别是涉及一种以穿着于身体上的织品的形式， 能够撷取心电信号、 肌电信 号或脑电信号， 同时侦测姿势、 行为模式、 或精神状态的物品、 方法及系 统。 背景技术
无论是躺在病床上的病患， 还是日常活动中健康的人、 职业或业余运 动员、 以及从事高风险工作的人员， 如消防队员，都需要连续不间断的、 不 受电线束缚的、 且不妨碍正常活动的生理监视， 以得知其生理状况， 方便 在必要时采取适当措施。 例如对于心肌梗塞患者施予急救。 将生理监视功 能实现在日常穿着的织品上， 是目前常见的解决方案之一。
例如美国专利第 6, 198, 394 号， 在织品上设有传感器（电极）， 并通过 传输线连接到电路。 其缺点在于有些传输线是悬吊在织品之外， 既会妨碍 穿戴者的行动也不舒适。
美国专利第 6, 080, 690号修正了上述的缺点， 它的实现方式是将外面 包有绝缘层的传输线和一般织品的纤维编织（woven) 在一起， 来连接传感 器（电极）和电路。但是其仍然存在缺点，即在织品上要布局走线（rout ing) , 当要布设多条传输线时就会变得十分困难， 因为要在织入织品的传输线上 设立连接点（junct ion) , 以连接传感器或其他电子元件， 这需要十分复杂 的力口工流程。
美国专利申请案第 12/209288号是利用一贴片将多个电极贴在身体上。 这样就可不使用衣物并可确保电极与身体接触良好。 然而这种贴片只能设 置在胸前， 不能取得完整的三个肢导心电图， 而且将电极通过贴片直接贴 在身体上对于使用者而言也很不舒服。
美国专利第 US7474910 号中的电极是利用浮纱（Float yarn)设置在布 料上，其中电极本身也可具有弹性而能够伸缩。 但是这种设置电极的方法没 有考虑到电极与布料或人体之间的摩擦力所能够产生的效果，而且不是三 维空间的设计，故只能采用紧身设计，否则只要使用者一走动电极就会与皮 肤有相对移动。
综合以上所述， 目前现有技术所提供的具有生理监视功能的织品， 还 未有利用心电信号在人体表面呈现的等位线图（ECG i sopotent ia l surface ma p)来获得较佳信号或避开汗水干扰， 以及采用分离式电极结构以降低体 动干扰， 并且也能够侦测电极是否接触良好的织品。 发明内容
由目前心脏医学可知， 与由体表采集到的心电信号振幅有关的因素有 以下几项：
1、 心电信号的振幅与心肌细胞数量（心肌厚度）成正比关系；
2、 心电信号的振幅与生理电极设置的位置和心肌细胞之间的距离成反 比关系； 有关， 所夹角度愈大， 心电信号位于导程上的投影就愈小， 电位也就愈弱。
根据上述原 理 ， 有文献 （ " Simulat ion s tudies of the electrocardiogram. I. the normal heart " ， by WT Mi Her and DB Geselowi tz, Circ. Res. 1978: 43) 以计算机仿真绘制出了心电图 P， Q， R， S, T各波的等位线图， 其中 R波的等位线如图 1 (a)所示， 其显示了本发明 较佳实施例的日衣的电极、 控制盒与导线的架构与心电信号等位线的位置 关系。其中数值代表该处的电位， R波的振幅大小为两电极所在处的电位差。
利用此等位线图， 并考虑人体呼吸及运动所造成的干扰， 以及服装设 计上的可行性， 本发明针对降低体动干扰提出出了一种新的分离式电极架 构及电极的位置、 面积、 传输线布局。 藉此， 本发明的目的在于， 克服上 述现有的具有生理监视功能的织品现存的缺陷， 而提供一种新的侦测心跳 或电极接触良好与否的物品、 方法及系统，所要解决的技术问题是使其通过 采用一穿着于身体上可耐洗涤的织品， 能够长期且连续的撷取心电信号，并 且在满足穿着舒适和外型美观的前提下， 能够准确测得心电信号， 而不易 受到身体运动和汗水等干扰， 非常适于实用。
本发明的另一目的在于， 提供一种新的侦测心跳或电极接触良好与否 的物品、 方法及系统， 所要解决的技术问题是使其可随环境状态改变， 而 选择由干电极或电容耦合式电极撷取心电信号， 并且其处理器可由心电信 号中伴随的噪声或电极的阻抗， 来选出心电信号最佳的两个电极， 或启动 不同的电路、 固件或软件， 以节省电力消耗,从而更加适于实用。
本发明的再一目的在于， 提供一种新的侦测心跳或电极接触良好与否 的物品、 方法及系统， 所要解决的技术问题是使其可由侦测电极的阻抗或 噪声判别电极是否贴身， 从而能够克服环境或身体姿势的限制， 连续的撷 取心电信号， 从而更加适于实用。
本发明的还一目的在于， 提供一种新的侦测心跳或电极接触良好与否 的物品、 方法及系统， 所要解决的技术问题是使其可利用噪声侦测人体活 动、 姿势、 精神状态及心理状态； 并可由心电图波型判读精神状态、 步态、 或姿势， 从而更加适于实用。
本发明的目的及解决其技术问题是采用以下技术方案来实现的。 依据 本发明提出的的侦测心跳或电极接触良好与否的物品、 方法及系统， 包含 至少两个电极， 和一控制盒， 其中电极是依等位线图来选取位置， 并具有 分离式结构而不固定在衣物上， 以降低身体运动造成的干扰， 控制盒内有 处理器， 设置有微控制器， 微控制器内设有固件， 其不仅可以计算心率，并 且可由电极的阻抗或心电信号伴随的噪声， 来辨识电极与人体接触是否良 好， 并可用来侦测姿势、 精神状态及心理状态。
本发明微控制器的固件设有自动增益控制， 可自动调整其信号线性范 围， 并利用信号线性范围推估运动干扰。 并且可以由量测噪声、 体表阻抗、 肌肉阻抗等方式， 侦测电极与人体的接触是否良好
本发明提出的物品， 可利用磁力固定电极以减少体动干扰。
本发明提出的物品， 其电极内部可设有一具有弹性的容器， 该容器设 有一孔道供气体或液体进出， 可储存气体或液体， 并可产生负压让电极吸 附于皮肤上， 又可在使用时因毛细现象或受挤压而緩慢释出可导电液体，以 解决电极未与身体贴合或导电性不佳的困扰。
本发明提出的物品， 可设置气嚢或液囊于电极与织品之间， 以解决电 极未与身体贴合的困扰。
本发明提出的系统， 在刚间始使用时， 会先侦测在行为动作中两电极 间的阻抗， 例如在前十秒钟时，若阻抗稳定且在设定范围内，则控制盒启动 侦测心电信号， 否则控制盒会以告知使用者束紧衣带、 增加导电液体、 增 加第三个电极或启动主动电极等方式，来改善信号品质。 同理， 此方法也可 以适用于肌电图、 脑电图、 阻抗式呼吸计（impedance pneumography) , 经 皮神经电刺激 (TENS) 、 电击等。
本发明与现有技术相比具有明显的优点和有益效果。 借由上述技术方 案，本发明一种侦测心跳或电极接触良好与否的物品、 方法及系统至少具有 下列优点及有益效果：
本发明包含： 一件织品，织品上设有至少两个电极，电极外覆有导体，内 含有弹性体使其能够舒适地贴附于人体上， 电极以传输线连接至连接器 (connector) , 连接器的另一端连接控制盒， 控制盒内的处理器设有模拟电 路（也可做在织品上）对电极取得的生理信号进行前处理， 处理器内还设有 微控制器， 其可以将生理信号转换成数字信号，再经由蓝芽等无线模块将生 理信号传送至其他的通信设备。 经由信号处理的方法， 由此织品能够获得 多种信息，再对这些信息进行分析后形成一系统。
对于穿戴式电极而言， 常遇到的困扰是在电极与身体接触不良时，就无 法正确求得信号。 本发明采取了十一种方法来侦测电极与皮肤是否接触不 良。
本发明由电极与身体的接触情形可推知穿戴者的姿势和行动， 以适时 提醒穿戴者， 并可侦测其活动及精神状态。 上述的方法也可应用于脑电图、 肌电图、 经皮电刺激治疗、 电击治疗的电极， 测试其电极是否接触良好。
穿戴式电极在织品宽松时很可能与皮肤接触不良， 为解决此困扰，本发 明还可在电极上面增加气嚢或液嚢， 必要时加压以压迫电极紧贴人体。 此 外， 为了增加导电性， 本发明可选 ·ίΗ生地在穿戴式电极内部增加一不易透 水的薄膜层， 趁水洗时将导电水分留在电极内部， 在穿戴使用时，水份可因 毛细现象或受挤压而緩慢释出至电极与皮肤上。 此外， 当薄膜层内变成容 纳空气时, 薄膜层的弹性可在受挤压后使内部呈负压， 以吸住人体皮肤， 同 时又可将皮肤上可导电的液体（例如水）吸在电极上以利于导电。 此外， 为 了增加导电性 , 本发明可选择性地在电极的导电布和弹性体之间再增加可 曲挠的导体， 例如由不锈钢纤维织成的导体。
本发明提出了七种新型的电极架构， 以降低体动干扰。
本发明提出了两种方法， 用于判断传输线是否断路。
综上所述， 本发明是有关于一种侦测心跳或电极接触良好与否的物品、 方法及系统， 本发明是在织品上设置多个织品电极， 利用心电图的等位线 图， 并考虑人体运动所造成的干扰， 创新的设计出分离式电极结构、 电极 的位置、 面积、 以及导线布局，以侦测心跳； 并可随环境状态的改变选择由 干电极或电容耦合式电极撷取心电信号； 并且可以由量测噪声、体表阻抗、 肌肉阻抗等方式， 侦测电极与人体的接触是否良好； 此外， 可由心电信号 波型及噪声， 推测人体姿势与动作。 本发明在技术上有显著的进步， 并具 有明显的积极效果，诚为一新颖、 进步、 实用的新设计。
上述说明仅是本发明技术方案的概述， 为了能够更清楚了解本发明的 技术手段， 而可依照说明书的内容予以实施， 并且为了让本发明的上述和 其他目的、 特征和优点能够更明显易懂， 以下特举较佳实施例， 并配合附 图，详细说明如下。
本发明所称的织品，可为衣物、 内衣裤、 外套、 床单、 枕头、 袜子、 鞋 子、 围巾、 头巾、 手套、 围裙、 腰带、 马桶座垫、 地毯、 帽子和座垫、 方 向盘套、 腕表等形式。 附图的简要说明
图 1 (a)是本发明较佳实施例的日衣的电极、 控制盒与导线的架构与心 电信号等位线的位置关系的示意图。
图 1 (b)是图 1 (a)中控制盒的放大示意图。
图 1 (c)是本发明由运动时皮肤的相对移动距离决定电极位置的示意 图。
图 1 (d)是图 1 (c)左侧的示意图。
图 2 (a)是本发明中有吸盘型结构的电极的剖面图。
图 2 (b) 是本发明中电极内设有容器的剖面图。
图 2 (c)是本发明中电极内设有以不易透水或气的胶膜形成的袋子的剖 面图。
图 2 (d)是本发明中有吸盘结构的导电布的纤维的剖面图。
图 3 (a)是本发明含导电纤维的电极的侧视图。
图 3 (b)是本发明含导电条的电极的侧视图。
图 4 (a)是本发明孤形电极滑动于织品上的侧视图。
图 4 (b)是本发明弧形电极采用半径渐增的螺旋形传输线的侧视图。 , 图 4 (c)是本发明电极采用两悬挂条固定的侧视图。
图 4 (d)是本发明电极以织带作为悬挂条缝在织品上的示意图。
图 5 (a)是本发明中电极内设有通道使电极可沿传输线滑动的侧视图。 图 5 (b)是本发明中电极的側边设有通道的示意图。
图 5 (c)是本发明中电极所处的织品上设有通道的示意图。
图 5 (d)是本发明中电极的侧边与织品上皆设有通道的示意图。
图 6 (a)是本发明中电极所处的织品设有开孔以容许连接线穿过的示意 图。
图 6 (b)是本发明中电极设有开孔以容许连接线穿过的示意图。
图 6 (c)是本发明中电极与织品皆设有开孔以容许连接线穿过的示意 图。
图 6 (d) 是本发明中连接线成环型穿过织品上的开孔的示意图。
图 7 ( a )是本发明中电极设置于滑台上的第一较佳实施形式的示意图。 图 7 (b)是本发明中电极设置于滑台上的第二较佳实施形式的示意图。 图 7 (c)是本发明中电极设置于滑台上的第三较佳实施形式的示意图。 图 8 (a)是本发明在站立静止时电极侧面以织带为悬挂条所取得的 R波 的波形图。
图 8 (b)是本发明在走动时电极侧面以织带为悬挂条所取得的 R波的波 形图。
图 8 (c)是本发明由坐姿站起时电极侧面以织带为悬挂条所取得的 R波 的波形图。
图 8 (d)是本发明原地高抬腿时电极侧面以织带为悬挂条所取得的 R波 的波形图。
图 9 (a)是本发明的双层分离式结构电极以连接线结合的第一较佳实施 形式的示意图。 图 9(b)是本发明的双层分离式结构电极以织带结合的第二较佳实施形 式的示意图。
图 9(c)是本发明的双层分离式结构电极以织带结合的第三较佳实施形 式的示意图。
图 9(d) 是本发明的双层分离式结构电极所获得走动的 R波的波形图。 图 10 (a)是本发明中正面的 R波的等位线及电极位置的示意图。
图 10(b)是本发明中左侧的 R波的等位线及电极位置的示意图。
图 10 (c)是本发明中背面的 R波的等位线及电极位置的示意图。
图 11(a) 是本发明由电极设置在图 10(a)的 A与 B处所测得的心电信 号图。
图 11(b) 是本发明由电极设置在图 10(a)的 A与 C处所测得的心电信 号图。
图 11(c) 是本发明由电极设置在图 10(a)的 B与 H处所测得的心电信 号图。
图 11(d) 是本发明由电极设置在图 10(c)的 D与 E处所测得的心电信 号图。
图 11(e) 是本发明由电极设置在图 10(c)的 F与 G处所测得的心电信 号图。
图 11(f) 是本发明由电极设置在图 10(b)的 I与 J处所测得的心电信 号图。
图 12(a) 是本发明由面积 6*3平方厘米的电极所测得的心电图。
图 12(b) 是本发明由面积 6*6平方厘米的电极所测得的心电图。
图 12(c) 是本发明由面积 6*9平方厘米的电极所测得的心电图。
图 13(a)是本发明由图 10(c)和图 10 (a)的 Z与 B处所测得的 R波的波 形图。
图 13(b)是本发明由图 10(c)和图 100))的∑与 I处所测得的 R波的波 形图。
图 13(c)是本发明由图 10(a)和图 10(b)的 B、 I处并联与图 10(c)的 Z 处所测得的 R波的波形图。
图 13(d)是本发明由图 10(a)和图 10(b)的 B、 I处并联与图 10(c)的 Z 处在行走时所测得的 R波的波形图。
图 14是本发明中分离式电极设置于弹性导电布的侧视图。
图 15 (a)是本发明右臂在后左臂在前时取得的心电图。
图 15(b)是本发明双臂在前时取得的心电图。
图 15(c)是本发明双臂在后时取得的心电图。
图 15(d)是本发明右臂在前左臂在后时取得的心电图。 图 16 (a)是当电极阻抗为 15 M Ohms时静止所得的 R波的波形图。
图 16 (b)是当电极阻抗为 30 M Ohms时静止所得的 R波的波形图。
图 16 (c)是电极脱离人体在静止状态下所得的 R波的波形图。
图 17 (a)是当电极阻抗为 10 M Ohms时静止所得的 R波的波形图。
图 17 (b)是当电极阻抗为 10 M Ohms时行走所得的 R波的波形图。
图 17 (c)是当电极阻抗为 10 M Ohms时原地抬腿所得的 R波的波形图。 图 17 (d)是当电极阻抗为 0. 8 M Ohms时静止所得的 R波的波形图。 图 17 (e)是当电极阻抗为 0. 8 M Ohms时行走所得的 R波的波形图。 图 17 (f)是当电极阻抗为 0. 8 M Ohms时原地抬腿所得的 R波的波形图。 图 18 (a)是本发明两种电极并用的第一种形式的示意图。
图 18 (b)是本发明两种电极并用的第二种式的示意图。
图 18 (c)是本发明两种电极并用的第三种形式的示意图。
图 18 (d)是本发明两种电极并用的第四种形式的示意图。
图 18 (e)是本发明两种电极并用的第五种形式的示意图。
图 18 (f)是本发明两种电极并用的第六种形式的示意图。
图 18 (g)是本发明两种电极并用的第七种形式的示意图。
图 18 (h)是本发明两种电极并用的第八种形式的示意图。
图 18 (i)是本发明两种电极并用的第九种形式的示意图。
图 19是本发明电容耦合式电极与干电极共享一电路的示意图。
图 20是本发明中内含气嚢或液囊的电极的侧视图。
图 21 (a)是本发明中两电极内含的气嚢或液嚢相互连接并互相辅助的 侧视图。
图 21 (b)是本发明中两电极内含的气嚢或液嚢相互连接并互相排斥的 侧视图。
图 22 (a)是本发明在织品及电极上各加装一磁石的示意图。
图 22 (b)是本发明采用环型永久磁性物质的示意图。
图 22 (c)是本发明在衣服上将永久磁性物质设置于电极两侧的示意图。 图 23是本发明由脉波侦测电极是否接触不良的示意图。
图 24 (a)是本发明体表电容为 2. 7 nF时所测得的 R波的波形图。
图 24 (b)是本发明体表电容为 21. 7 nF时所测得的 R波的波形图。
图 25 (a)是本发明中两个电极不同形状但电性连接的示意图。
图 25 (b)是本发明中两个电极不同形状但电性连接的信号产生图。
图 26是本发明中四个连接不同电子組件的电极的示意图。
图 27是本发明中由弦波测电极是否接触不良的示意图。
图 28是本发明判断电极与皮肤是否接触不良的第五种方法的示意图。 图 29是本发明判断电极与皮肤是否接触不良的第六种方法的示意图。 图 30是本发明判断电极与皮肤是否接触不良的第七种方法的示意图。 图 31是本发明判断电极与皮肤是否接触不良的第八种方法的示意图。 图 32是本发明判断传输线是否导通不良的示意图。
5 : 永久磁性物质 10: 按扣；
20: 双层结构 40: 电极
50: 控制盒 60: 连接器
65: 导电布 75 : 导体
80: 传输线 82： 光滑材料
83: 止滑条 85：
90: 弹性体 95: 间隔 实现发明的最佳方式
为更进一步阐述本发明为达成预定发明目的所采取的技术手段及功 效，以下结合附图及较佳实施例， 对依据本发明提出的一种侦测心跳或电极 接触良好与否的物品、 方法及系统其具体实施方式、 结构、 方法、 步骤、 特征及其功效， 详细说明如后。
有关本发明的前述及其他技术内容、 特点及功效， 在以下配合参考图 式的较佳实施例的详细说明中将可清楚呈现。 通过具体实施方式的说明，应 当可对本发明为达成预定目的所采取的技术手段及功效获得一更加深入且 具体的了解， 然而所附图式仅是提供参考与说明之用， 并非用来对本发明 加以限制。
第 1实施例 日衣
本发明中所述的日衣意指日间活动所穿着的衣服。 如图 1 (a)所示， 图 1 (a)是本发明较佳实施例的日衣的电极、 控制盒与传输线的架构与心电信 号的等位线的位置关系的的示意图。 本发明的架构是将两个电极 40分别设 置于日衣的左右腋下。 其中，左腋下的电极 40是设置于最高电位（+1. 4)的 区域内； 但为了避免呼吸干扰并且避免对于女性使用者正好是穿着内衣的 位置， 另一电极 40并不设在最低电位（-1)的区域内， 而是设在电位为 -0. 3 的右腋下位置。 除了上述的两个电极之外， 本发明还可选择性地再增加一 个第三电极， 作为负反馈电流输入人体的电极， 以降低噪声， 或是和上述 的两个电极一同工作来取得三导联心电图， 或是以控制盒和人体之间的杂 散电容， 作为负反馈电流输入电极。 按扣 10是用来将心电信号传导至控制 盒 50的连接器， 如图 1 ( b )所示， 图 1 (b)是图 1 (a)中控制盒的放大示意 图， 其中控制盒 50的上下分别设有两个按扣 10 , 上下两个按扣 1 0不在控 制盒 50的同一平面上， 因此可以避免两个按扣 10同时受到汗水或雨水的 浸湿而影响信号的传输。 上述的按扣 10也可采用可导电的魔鬼毡代替， 也 能够获得相同的功效。其中按扣 10或魔鬼毡的周围设有吸水材料 (如海绵）， 其底部设有一防水层， 例如热熔胶薄膜、 尼龙布、 疏水性材料或保鲜膜等 不透水材料， 以防止汗水影响信号的传输。 为了减少肢体运动拉扯电极引 起干扰， 日衣可釆用上下两部分或上中下三部分拼接构成， 其中每一部分 采用不同的材料制造，例如电极所在的一部分采用弹性较强的莱卡（Lycra ) 布制造， 以将电极固定在人体的上， 而其他部分则采用较易延展的布料制 造， 这样就不易拉扯 Lycra布部分 ό
本发明的控制盒 50经由按扣 10作为连接器， 与电极电性连接， 以感 测心电信号。 控制盒 50内可设有仪表放大器、 带通滤波器、 微控制器及无 线通信模块， 可将信号无线传送至其他通信设备， 使用户不会受到电线的 束縛。
为了降低体动干扰，本发明在选取电极设置的位置时首先是以实验来 测量身体运动牵扯肌肉与皮肤的相对移动距离。 如图 1 (c)及图 1 (d)所示， 图 1 (c)是本发明由运动时皮肤的相对移动距离决定电极位置的示意图，图 1 (d)是图 1 (c)左侧的示意图，我们先在人体上预先选好的 11个位置上分别 设置 6*6平方厘米的方型纸片， 其中纸片只有中心的一小点与人体粘接，其 他面积均可以自由移动。 当人体静止站立时在纸片的 4 角对应的人体皮肤 上画上标记作为原点， 然后当人体运动时， 记录此时纸片 4 角与原点标记 的差值， 即得出运动时皮肤的相对移动距离。 下面将由典型的身体运动引 起的皮肤的相对移动距离列于表 1中。 表 1 三种运动下各位置的皮肤的相对移动距离
Figure imgf000011_0001
由于人体的皮肤是左右对称的， 故图 1 (d)中人体左侧的位置 2与 3与 右侧的位置 2， 与 3， 的相对移动距离是一样的。 从表 1来看， 相对移动距 离最小的是位置 9， 其次是置位 1 , 再次是位置 3。 然而，位置 9与位置 3的 电位较低，：而位置 10 由于其处于人体的凹面处，故不利于与电极接触。 综 合人体心电 R 波等电位图及皮肤相对移动距离来看， 将电极设置在位置 3 与 3， 处是较佳的。
经过多次实验， 本发明较佳的设置侦测电极的位置是在左右腋下， 向 胸骨方向 ^^平移动约 2至 6厘米处， 以尽量达到电极在电位 1. 4和 -1. 0的 区域可侦测最大 R波的两个位置。本发明日衣的袖口应较一般上衣大 2至 4 厘米， 以避免双臂运动牵引衣物而引起电极位置的移动造成运动干扰。 对 于女性使用者， 为了避开胸衣， 左右腋下的电极可再下移 3至 5厘米。
身体运动常会干扰测得的心电信号， 这种干扰主要是由运动时皮肤和 衣服的移动， 导致电极会相对于皮肤移动以及电极也会相对于衣服移动，产 生体动噪声而引起。 体动噪声的振幅都比较接近, 不随电极的位置而有大 幅的变化。 为了降低体动干扰， 本实施例提出七种殳置电极于织品上的方 法， 目的是在运动时使电极不会有相对于皮肤运动， 更进一步地希望能够 达到电极相对于衣服也不会移动。 故本发明在刚开始使用时， 会先侦测在 行为动作中两个电极 40间的阻抗， 例如在刚开始的十秒钟， 若阻抗稳定且 在设定范围内， 则控制盒 50启动侦测心电信号， 否则控制盒 50会以告知 使用者束紧衣带、 增加导电液体、 增加第三个电极或启动主动电极启动主 动电极 (act ive electrode, 參考 Merri t 等人著 " Fabr ic-Based Act ive Electrode Des ign and Fabricat ion for Heal th Moni tor ing Clothing" ， IEEE TRANSACTIONS ON INFORMATION TECHNOLOGY IN BI0MEDICINE, VOL. 13, NO. 2， 2009)等方式， 来改善信号的品质。 具体的七种方法如下所述： 第一种方法： 吸盘结构型
第一种吸盘结构， 是在电极与人体接触的平面上设置吸盘结构。 其中， 吸盘结构是以亲水性佳且不透气的材料制成， 并且吸盘结构连接一具有弹 性并在受压之后能够恢复原形的容器， 容器上设有小孔供液体或气体出入。 在洗涤织品时， 容器内能够容纳可导电的液体（例如洗涤织品的水）； 而在 织品本身烘干或晒干后， 容器内仍有液体储存； 等到人穿戴使用织品时， 容 器内的液体即可依毛细现象渗出， 或者在容器受挤压时， 容器内的液体即 被挤到电极上； 当容器内的液体流出后容器变成容纳空气时，容器所具有的 弹性又可在受挤压后使容器内部呈负压， 以吸住人体皮肤， 使电极不会相 对于人体运动， 同时又可将皮肤上可导电的液体（例如水）吸在电极上以利 于导电，如图 2 (a)所示， 图 2 (a)是本发明中有吸盘结构的电极的剖面图。
为了使容器能够更好的保存液体， 可在容器的小孔上增加一阀门或塞 头， 该阀门或塞头可在洗涤时打开让液体进入， 而在烘干或晒干织品时关 闭以保存容器内的液体。 或者也可以在容器的小孔上设置一自动封闭的开 关或阀门， 当使用者以硬管插入开关或阀门时即可向容器内灌液体， 而当 使用者将硬管拔出开关或阀门后开关或阀门即自动封闭以保存容器内的液 体。
另外两种类似的电极结构如图 2 (b)及图 2 (c)所示， 图 2 (b) 是本发明 中电极内设有容器的剖面图。 图 2 (c)是本发明中电极内设有以不易透水或 气的胶膜形成的袋子的剖面图。其中， 图 2 (b)所示的电极的外层是导电布， 内部设有一具有弹性并在受压之后能够撑开的容器， 容器上设有小孔供液 体或气体出入。 其作用如前述的第一种吸盘型结构。 此外在电极的导电布 与容器之间还设有一具有孔隙并可吸水的弹性材料 (例如海绵） , 该弹性材 料也可储存液体以有助于导电。 如图 2 (c)所示的电极是在导电布内设置一 不易透水或透气的胶膜形成的袋子， 而在袋子内设置具有孔隙并可吸水的 弹性材料 (例如海绵） 。 把袋子撑开以便容纳液体或气体， 同时在袋子上还 设置有小孔供液体或气体出入。 这两种结构产生的负压不是完全用于吸住 人体， 而是緩慢减压， 当人体运动时， 又可压迫容器或袋子产生新的负压， 同时也可使容器或袋子内储存的液体緩慢译出。 与图 2 (a)同理， 图 2 (b)及 图 2 (c)所示的容器和袋子既可提供可导电的液体， 在使用时将可导电的液 体緩慢释出至电极与皮肤上； 同时图 2 (b)与图 2 (c)所示的容器和袋子还可 直接作为吸盘使用， 而使电极贴紧在人体上。
第二种吸盘结构， 是在电极的导电布的纤维上设置微小的吸盘结构，使 电极一但受到人体挤压吸盘内的空气即会被挤出， 同时吸盘材料的弹性又 可使吸盘内部呈负压、 吸住人体， 如图 2 (d)所示， 图 2 (d)是本发明中有吸 盘结构的导电布的纤维的剖面图。 此结构可使电极外层的导电布与人体的 摩擦力大于织品与人体的摩擦力， 因而可降低体动干扰。 当此方法实施于 电容辆合式电极时， 可以采用一般非导体纤维先与人体接触。
上述的吸盘型结构也可采用电极与织品分离设置， 而通过在电极上设 置的一传输线， 以此传输线（图未示出）的长度为 L，将吸盘型结构的电极连 接到织品上， 达到电极相对于人体不会移动的目的。 此时， 电极就能够抗 衡体动所产生的干扰， 使心电信号传输至控制盒内的处理器。
第二种方法， 刷毛结构型
其是在电极上设置由直立且可曲挠的导电纤维所组成的， 长度为 L， 例 如是由含石墨的橡胶、 银纤维、 导电高分子或导电硅胶材料所构成的， 类 似牙刷的刷毛型结构， 以增加电极与皮肤之间的摩擦力。 其中， 导电纤维 与电极之间可设置一层由可曲挠的金属制成的导体， 例如以不锈钢纤维织 成的不锈钢布， 以增加导电性， 如图 3 (a)所示， 图 3 (a)是本发明含导电纤 维的电极的侧视图。 当人体运动时， 位于电极与皮肤之间的导电纤维可在 一定范围内维持皮肤与电极之间的接触， 使两者不会有相对运动并扩大皮 肤与电极的接触面积。
但可曲挠的导电纤维容易刺激皮肤导至皮肤发生红肿反应， 因此本发 明可通过在电极上延伸出两、 三块可曲挠的光滑的由导电材料制成的导电 条， 例如银纤维导电布条、 导电硅胶条、 或高分子导电布条， 代^^上述由 导电纤维所构成的刷毛型结枸， 并将其设置在电极的外围以增加电极与皮 肤之间的摩擦力， 达到与 3 (a)所示的刷毛型结构相同的效果， 同时又不易 引起皮肤的不良反应， 如图 3 (b)所示， 图 3 (b)是本发明含导电条的电极的 侧视图。
以上图 3 (a)及图 3 (b)所示的两个电极也可设有一弹性体， 且电极可设 有一长度为 L (一般约 0. 2至 3厘米）的传输线，并通过该传输线连接到织品 上， 因此电极可与织品分离设置 (以下称为分离式结构）， 以达到电极相对 于人体也不会移动的目的、 并以此降低体动千扰。
在此方法中电极与人体之间的摩擦力远大于电极与衣服之间的摩擦 力， 使得在运动时电极不会相对于皮肤运动。 另外本方法中的电极还可采 取分离式结构设置于衣服上， 以更进一步达到电极也不会隨衣服运动的目 的， 其效果与上述方法相同。
第三种方法， 悬挂结构型
其电极如图 4 (a)至图 4 (d)所示为弧型， 也可为平底型或其他型， 以传 输线 80连接到与人体接触的织品 85上。 其中传输线 80可具有弹性， 例如 传输线 80是织在松紧带或其他织带上，传输线 80悬空长度为 L (一般约 0. 5 至 0. 3厘米） , 以备电极与织品 85相对移动之用。 电极的表面是采用摩擦 力较大的导电布 65 , 例如绒毛结构的导电布。 电极和织品 85的接触面至少 有一面是由摩擦力低的光滑材料 82所制成，例如衬布、 防水光滑布、铁片、 铜片、 不锈钢片、 玻璃材质或有铁氟龙包覆的织品等， 以便于电极滑动。 电极内部则设置有弹性体、 导电硅胶、 或一般织品等。 电极的外缘可选择 性的设置有止滑条 83以增加电极与人体之间的摩擦系数， 此时电极与织品 85接触的表面就可采用光滑材料 82制成。 当人体和织品有相对移动时， 电 极上的光滑材料 82使电极可以在织品上滑动或滚动， 同时使导电布 65仍 能和人体维持接触， 并相对固定不动来接收信号， 而不会产生噪声。 电极 与织品 85之间的传输线可以是如图 4 (a)所示的半径固定的螺旋形传输线， 或是如图 4 (b)所示的半径渐增的螺旋形传输线再或者是折片形（如图 4 (d) 中织带对折三次）传输线， 以备伸缩之用。 螺旋型线或折片形传输线被拉长 时会自动缩回， 不会占空间。 其中， 图 4 (a)是本发明弧形电极滑动于织品 上的侧视图。 图 4 (b)是本发明弧形电极采用半径渐增的螺旋形传输线的侧 视图。 图 4 (c)是本发明电极采用两悬挂条固定的侧视图。 图 4 (d)是本发明 电极以织带作为悬挂条缝在织品上的示意图。 另外， 电极也可是平底型 , 这样就至少要采用两条长度为 L 的悬挂条 将电极连接到织品上， 例如是由尼龙线或弹性纱线等光滑线材织成的悬挂 条， 如图 4 (c)所示， 其中一条悬挂条可以是传输线， 若所有悬挂条皆不导 电， 就要另设一条传输线连接电极与织品。 含有传输线的悬挂条可以外覆 绝缘层， 例如包胶铜线； 或是不覆绝缘层， 例如银纤维； 或者整个悬挂条 都是导电材料， 例如不锈钢导电条构成， 此时悬挂条本身也可兼做电极， 当其与人体接触时即可拾取生理电信号， 以增加感测心电信号的机会， 同 时也可减少另接的一传输线。 其中止滑条可以是硅胶、 乳胶、 绒毛、 或魔 鬼毡等， 其本身也可是导电材料， 即可当作电极使用。
悬挂条也可以用电极上具有可活动长度为 L的织带来制作， 如图 4 (d) 所示， 其中织带与织品组合时可留有长度为 L (0. 2 :到 3厘米）的空间使电极 可自由活动。 当人体运动时， 电极可在活动的范围为 0. 2到 3厘米的三维 空间随皮肤自由活动， 而不会与皮肤相对运动， 更进一步地能够达到电极 不会隨织品运动的目的。 在此实施例中， 止滑条 83是用止滑面料直接缝在 织品 85上， 达到电极相对于人体不会移动、 降低体动干扰的效果。 具体是 利用止滑面料在织品受外力移动时其相对于皮肤的摩擦力远大于织品相对 止滑面料的拉力。 止滑面料在织品上的结构也可适用于本发明中其他的结 构上， 其中止滑面料可为硅胶、 乳胶、 绒毛、 魔鬼毡或高张力的弹性布料 等， 如丝袜。 织带本身可以内含传输线 80或本身就是导电材料， 也可同时 当作电极使用， 因此可减少外加的传输线 80。
第四种方法， 通道结构型
其中电极本 内设有通道， 可使传输线 80在此通道内滑动， 传输线在 织品 85上有多余的长度 L, 以供电极滑动。 此外， 若传输线 80与此通道皆 为导体， 则无须再另接一条传输线， 如图 5 (a)所示， 图 5 (a)是本发明中电 极内设有通道使电极可沿传输线滑动的侧视图。 另一例如图 5 (b)所示， 图 5 (b)是本发明中电极的侧边设有通道的示意图， 其中电极为平面结构且在 电极两侧各设有一通道， 并且每一通道中都各设有一条连接线来将电极固 定在织品上。 上述的连接线可以为尼龙线、 弹性纱线、 布线、 布条、 金属 线、 塑料线、 塑料条、 导电线或导电条等， 以具有弹性且光滑的材料较佳。
另外， 也可以将通道设在织品上， 并且在织品上的每一条通道内都各 设置一条连接线，该连接线的两端是固定于电极上，如图 5 (c)所示，图 5 (c) 是本发明中电极所处的织品上设有通道的示意图； 或者也可以在电极与织 品上皆设有通道，两者的通道是利用连接线来连结，如图 5 (d)所示，图 5 (d) 是本发明中电极的侧边与织品上皆设有通道的示意图。 连接线多余的长度 为 L (0. 5至 3厘米）， 电极与衣物接触的两表面是采用光滑材料（例如衬布、 防水光滑布、 铁片、 铜片、 不锈钢片、 玻璃材质或有铁氟龙包覆的织品等） 制造， 以降低摩擦力， 电极边缘可选择性加装止滑条（未示出）或将止滑面 料设在织品上， 以增加摩擦力。 因此当人体运动时， 电极可活动的范围为
0. 2到 0. 3厘米的三维空间，并且电极可随皮肤的自由活动而不会与皮肤相 对运动， 更进一步地能够达到电极不会隨织品运动的目的。 其中通道内可 设有导电材料， 可以导电材料外覆绝缘层或是不覆绝缘层制造。 连接线例 如为传输线， 并可以导电材料， 例如导电布且外覆绝缘层或是不覆绝缘层 制造， 当导电布不覆绝缘层时可兼做电极， 接触人体即可拾取生理电信号。 若通道与连接线皆不导电， 则须外加一传输线来连接电极， 以接收信号。 连接线的材料如上面所述， 以具有弹性且光滑的材料较佳。
第五种方法， 开孔结构型
如图 6 (a)至图 6 (d)所示，图 6 (a)是本发明中电极所处的织品设有开孔 以容许连接线穿过的示意图。 图 6 (b)是本发明中电极设有开孔以容许连接 线穿过的示意图。 图 6 (c)是本发明中电极与织品皆设有开孔以容许连接线 穿过的示意图。 图 6 (d)是本发明中连接线成环型穿过织品上的开孔的示意 图。 其中， 在电极和 /或织品上设有开孔， 此开孔可供连接线穿过, 电极与 衣物的接触面采用光滑材料制造以降 4氐摩擦力， 电极边缘可选择性加装止 滑条。 开孔除了如图 6 (a)所示设在织品上以外； 也可设在电极本身上， 如 图 6 (b)所示； 或者电极与织品上皆设有开孔， 如图 6 (c)所示。 开孔可以为 如图 6 (a)至图 6 (c)所示的圓型孔，也可以是如图 6 (d)所示狭长型孔，供作 为连接线的织带通过。 穿过开孔的织带可以是两端分别固定在电极上、 织 品上、 或是连成环型。 止滑条、 开孔及连接线的导电性如上述第三、 第四 种方法所述， 连接线供滑动的长度 L约为 0. 2至 3厘米， 以确保有效降低 体动干扰。 连接线本身也可以是导电材料， 若不是则需另增加一条传输线。 连接线的材料如上述第四种方法所述。
在上例中， 若不外接一传输线， 则可在电极内设置一无线传输系统将 电极获取的信号传输出去。
其中， 上述方法所述的所有结构皆可以采用在电极内设置无线传输系 统的方式实施。
第六种方法， 滑块结构型
使电极 40 不固定在织品上， 而是固定在一滑台的滑块上， 如图 7 (a) 所示，图 7 (a)是本发明中电极设置于滑台上的第一较佳实施形式的示意图； 或者将电极固定在滑台上，而织品上则设有一滑块，如图 7 (b)所示，图 7 (b) 是本发明中电极设置于滑台上的第二较佳实施形式的示意图， 使电极可以 利用滑块在滑台内以二维方向任意滑动， 滑块可移动的范围为 L, 使得电极 40能够紧随人体， 达到电极与皮肤没有相对运动的效果。 其中， 滑块与滑 台间为光滑表面。 图 7 (a)及图 7 (b)所示的电极仅可在同一平面上移动， 不能在三维空间 移动， 不过滑块与滑台本身是导体， 故毋须在电极上另外接传输线就可以 传送心电信号。 图 7 (c)是在织品 85上设有一开口， 将电极 40与滑块分别 设置在该开口的上下实现三维移动的例子。其中电极 40可移动的范围为 L，L 约为 0. 2至 3厘米。 此时须有一传输线与电极连接将信号传送出去。 或者 在织品 85的开口处可设有导电材料， 使其与电极或滑块本身的导电材料相 接通来传输信号。
为了验证上述分离式电极抑制体动干扰的效果， 本发明在同一日同一 温湿度的环境下，由同一使用者先以生理电极贴片在左右腋下（如图 1)作为 对照组， 进行四种姿势及动作的检测： 其中， 四种姿势及动作分别为站立 静止、 走动、 由坐姿站起以及原地高抬腿。 同时在实验内衣外还披附一外 套 ， 以取得 R波。 然后以图 4 (d)的分离式电极取得 R波， 所得的结果如图 8 (a)至图 8 (d)所示， 此时直流阻抗为 0. 6 M欧姆（ Ohms ), 其中， 图 8 (a)是 本发明在站立静止时电极侧面以织带为悬挂条所取得的 R 波的波形图， 图 8 (b)是本发明在走动时电极侧面以织带为悬挂条所取得的 R 波的波形图， 图 8 (c)是本发明由坐姿站起时电极侧面以织带为悬挂条所取得的 R波的波 形图， 图 8 (d) 是本发明原地高抬腿时电极侧面以织带为悬挂条所取得的 R 波的波形图。 比较生理电极贴片在左右腋下的结果与图 8 (a)至图 8 (d)所示 的悬挂型结构电极的结果， 可以得知分离式电极所得的体动干扰， 仅略大 于生理电极贴片在左右腋下时的体动干扰， 但满足实际应用的要求。 本发 明中其他上述设计的电极所产生的结果也类似。
第七种方法 双层分离式结构
以图 9 (a)为例， 图 9 (a) 是本发明的欢层分离式结构电极以连接线结 合的第一较佳实施形式的示意图。 其中电极以连接线与一面积较大的粗糙 面料相连接， 粗糙面料与另一片光滑材料贴合， 并且电极和粗糙面料的接 触面设有摩擦力低的光滑材料， 使电极与粗糙面料容易相对滑动，以使身体 活动时电极与皮肤没有相对运动； 此粗糙面料又以连接线与织品结合， 并 且织品和粗糙面料的接触面至少有一面是摩擦力低的光滑材料， 以降低面 料与织品之间的摩擦力。 当身体运动而使织品和人体相对移动时， 织品和 粗糙面料会滑动， 因而电极受到的体动干扰降低。 然而， 即使粗糙面料会 紧贴人体而不致在人体上滑动， 人体肌肉与皮肤还是会有一些局部的运动 可能牽动电极， 这种局部的运动就可由电极 40和粗糙面料之间的分离式结 构予以緩解。 因此， 双层分离式结构可以有效抑制体动干扰。 或者可以织 带取代图 9 (a)中的连接线，并使织带穿过电极下方的粗糙面料与光滑材料， 形成一环形， 如图 9 (b)所示， 其中图 9 (b) 是本发明的双层分离式结构电 极以织带结合的第二较佳实施形式的示意图。 其中， 电极内织带的方向与 粗糙面料平行。 另一种方式是使电极内织带的方向与粗糙面料垂直， 在粗 糙面料的外侧形成一环状，绕过粗糙面料，如图 9 (c)所示 ，其中图 9 (c)是 本发明的双层分离式结构电极以织带结合的第三较佳实施形式的示意图。 其效果如图 9 (d)所示， 图 9 (d) 是以欢层分离式结构的电极所获得的使用 者在走动时的 R 波的波形图。 其中双层分离式结构可以采用前述第一至第 六种方法中的结构中的任两种， 并且上下两个分离式结构可以选用相同或 者相异的结构来实现。 更进一步地， 本发明还可以在上述双层分离式结构 上再增加一层或多层， 成为多层分离式结构； 双层或多层分离式结构同样 适用于电容耦合式电极， 其具体内容请详见第 3 实施例的描述。 其中双层 分离式结构中连接线的材料如第四种方法所述。
上述第一至第七种方法， 皆可选择性地加装止滑条或止滑面料在电极 或织品上， 降低电极与织品之间的摩擦力或电极与皮肤之间的相对运动。
上述第一至第七种方法所述之连接电极与织品的物品， 例如连接线与 悬挂条等， 也可经由子母扣或可导电魔术贴（Velcro) 来连接， 以使电极便 於折卸和更换， 见表 2。
若以海绵做为弹性体， 则可利用其可储水特性来帮助电极导电。 如图 9 (a) 所示， 弹性体上下两面皆设有防水胶膜， 其外再设光滑面料。 光滑面 料及防水胶膜本身皆不易透水， 故在上层光滑面料与防水胶膜以针刺开数 个小孔， 以便在洗涤时， 让海绵吸收水， 而在使用时让水緩慢释放至靠近 人体的导电布。 即使在刚穿戴织品时海绵已完全干涸不含水， 在穿戴后上 述的防水胶膜仍可以阻止汗液蒸发， 而将汗液留在导电布与海绵， 以帮助 电极导电。
前述电极的导电布下方也都可有一弹性体， 例如海绵，硅胶，弹簧或类 似的材料， 如图 9a所示， 两者之间也要设置光滑材料来减少电极与弹性体 之间的摩擦力，同时电极面积要比弹性体大 0. 4 平方厘米以上，以使导电布 在皮肤移动且变形时可以同时移动且变形，例如由正方形变成菱形，而不会 受到弹性体的限制。 即有一光滑材料来包住弹性体或是利用以上的方法与 弹性体分离而非直接缝接或黏贴在弹性体上成为一体。
本发明采用的每一片电极的表面是富有弹性的导电布或导电片（例如 银纤维、 不锈钢片）， 内部可设有一含导体的弹性体。 其中导体是用来增加 电极的导电能力， 同时在电极被水洗或穿着而损坏时， 可以使电极仍保有 感测能力， 增加电极的使用寿命。
本发明中电极与人体接触的表面的导体较佳的可为摩擦力较大的材 料， 例如毛料、 止滑条， 或者可通过加大电极面积来增加摩擦力。 电极内 部增加的弹性体可以选用富有弹性且吸水的海绵，硅胶或类似的材料，或者 弹性体可以采用例如弹簧或者类似的材料， 并且在内部增加可吸水的保水 剂。 其中保水剂不溶于水，但能吸收相当于自身重量成百倍的水， 并可有效 抑制水分蒸发。 保水剂共分为两大类， 一类是丙烯酰胺-丙烯酸盐共聚交联 物（聚丙烯酰胺、 聚丙烯酸钠、 聚丙烯酸钾、 聚丙烯酸铵等）； 另一类是淀 粉接枝丙烯酸盐共聚交联物（淀粉接枝丙烯酸盐）。 常用的保水剂有无定型 颗粒、 粉末、 细末、 片状和纤维状。 或者弹性体本身就是导电材料，就是电 极， 因其可保有水分同时又具有防震、 滤波功能， 故可以增加并稳定其导 电性。 此外， 为了增加导电性， 本发明可以选择性地在弹性体可以选用的 富有弹性且吸水的材料外增加一不易透水的薄层、 半透水的薄层或针头刺 孔不透水织品、 印刷不透水胶浆涂层、 防水织品、 防水贴条， 以阻隔水份， 使其不易渗入。 或者弹性体本身就具有半透水的功能， 目的是使水分留在 弹性体内再緩慢渗出。 在水洗织品时使水分留在电极的内部， 即使经过烘 干或硒干后织品的布料已全干， 但在电极内的水分仍能够保留。 当用户穿 戴织品时，身体会压迫弹性体， 使弹性体内储存的液体緩慢释出， 至电极与 皮肤上。 当弹性体内容纳的液体置换成空气时，一但弹性体受挤压后其内部 即呈负压， 可以吸住人体皮肤， 同时又可以将皮肤上导电的液体（例如水） 吸在电极内以利于导电。 此外， 为了增加导电性， 本发明可以选择性地在 电极的导电布和弹性体之间再增加一导体， 例如由不锈钢纤维织成的导体。 控制盒也可以电流通过发热元件来提升电极或其附近织品的温度， 或本身 加热电极或其附近织品， 使人体或电极表面温度上升致汗液增多， 以降低 电极与人体之间的阻抗。
增加导电性还有一方法， 即在电极位置及其四周的织品加一层机能性 保暖衣料， 例如羽绒保暖布， 以提高电极位置皮肤的温度， 使汗液增多。 为了使本发明的日在冬季或夏季皆可使用， 机能性保暖衣料可制成可拆卸 型式， 天热时取下， 天冷时装上， 如表 2 所述。 我们实验的初步结果， 是 在低温低湿（温度 16 Ό、 相对湿度 55%)的环境下， 电极的阻抗由刚穿时的 40 M Ohms , 经 30分钟后可逐渐降至 20 M Ohms , 此后维持稳定， 可取得心 跳。 同理由实验结果可知皮肤的温度、 电极的阻抗与心电信号的品质三者 有很高的相关性， 本发明可在电极内设置一热敏电阻， 以量测该电极的温 , 再据以实施适当的对策， 详细内容请参阅表 2。
人体表面的温湿度并非完全一样， 而是可以用等温线或等湿线， 画出 温度及湿度在人体表面的分布情形， 类似心电等位线图。 人体表面的等温 线图或等湿线图， 会随环境温湿度而改变， 夏天和冬天会不一样。 本发明 可整合心电等位线图及等温线图， 来选择较佳的电极位置。 例如在天气炎 热时， 全身皮肤的导电性皆良好， 此时可仅考虑心电等位线图来决定电极 位置， 如图 1 (a)所示； 在天气寒冷时， 胸部温度以心窝处最高， 离心窝愈 远则温度愈低， 考虑等温线图， 图 1 (a) 所示位置的温度会稍低于心窝， 对 传导心电信号较不利， 故可将电极向心窝移动大约 1至 6厘米， 以取得较 佳的心电信号， 详细内容请参阅表 2。
当将电极分别设置于图 10 (a)所示的右腋下靠前胸的 A 处（-0. 3 等位 线）与左腋下靠前胸的 B处（1. 4等位线）处时， 所测得的心电图如图 11 (a) 所示， 其中 R波的振幅约为 1. 8mV; 图 11 (b)是将电极分别设置于图 10 (a) 的 A处与 C处（0. 3与 0. 5等位线之间）所测得的心电图，其中 R波的振幅约 为 0. 7mV, 与前述文献所模拟的结果吻合， 由此可以确定由 A与 B处的电极 可以获得较大振幅的 R波。 图 11 (c) 是将电极分别设置于图 10 (a)的 B处 (1. 4 等位线）与 H (-l. 0 等位线）所测得的心电图， 其中 R 波的振幅约为 2. 2mV, 最大， 但是该处易受呼吸干扰， 而且该处等位线密集， 电位变化大， 电极很容易移位， 甚至跨越零等位线而到达正电位区域， 这样不仅振幅缩 小也很可能造成波峰方向逆转， 而不易辨识； 再者该处也易受女性胸衣阻 挡， 故选取在 A与 B处设置电极， 而不选取在 H (-1. 0等位线）处设置电极。 由图 10 (a)所示， 可知本发明选取电极位置的原则，是使一电极位于正电位 区， 另一电极位于负电位区， 以零等位线为界且不跨过零等位线。
同理，将电极设置于人体的后背也可取得 R波。 图 11 (d)是将电极分别 设置于图 10 (c)的人体后背的 D处（0. 3等位线）与 E处（-0. 3等位线）所测得 的心电图， 其中 R波的振幅约为 0. 6mV; 图 11 (e)是将本发明的电极分别设 置于图 10 (c)的 F处（0. 3与 0等位线之间）与 G处（-0. 3与 0等位线之间） 所测得的心电图， 其中 R波的振幅约为 0. 45 mV, 也就是说在背部电极设置 得愈靠内侧所获得 R波的振幅就愈小， 与前述文献所模拟的结果吻合。
同理， 将电极设置于人体的左右侧也可取得 R波。 图 11 (f)是将电极分 别置于图 10 (b)的人体的左侧的 I处（0. 3与 0. 5等位线之间）与 J处（零等 位线）所测得的心电图， 其中 R波的振幅约为 0. ¼V; 与前述文献所模拟的 结果吻合。
比较图 11 (a)至 11 (f)的 T波， 可知其大小不一，例如 11 (a)与 11 (b) 的 T波皆比 11 (c) 的 T波大， 且 11 (d) 与 11 (e) 的 T波皆比 11 (f) 的 T 波大， 并且各图中 T波与 R波振幅的比例也不一样， 这是因为 T波、 R波、 Q波、 S波与 P波的等位线图不同。
由于人体背部的 R波的等位线的电位并不高， 并且不像前胸那样密集， 故由 D、 E处所获得的 R波的振幅差异仅为 0. 15mV, 其中 R波与 T波的比例 也与图 11 (a) , 图 11 (b) , 图 11 (c)不同。 在后背若采用更大面积的电极 时， 最好是采用沿右下或左下方向延伸的电极， 即离开中央为零的等位线， 朝向更高或更低的等位线， 这样可以获得更大的振幅。
同理， P， Q, R, S, T各波的等电位线皆不相同， 因此， 本发明可由心 电图各波的波形结构， 来推估该心电信号是由何处的电极所获得。 由图 10 (a)至图 10 (c)也可以推论出电极面积的大小对心电信号的影 响。 由于本发明所用的电极是一片， 而非一小点， 故其输出的电位应为其 涵盖区域的电位的平均值。 对于位于 D或 E处的电极而言， 由于该处等位 线相对而言较稀疏， 其输出的电位仍为接近 0. 3或 -0. 3的电位； 对于位于 B处（1. 4等位线内）的小面积电极， 其输出的电位可达 1. 4， 但是位于该处 而面积较大的电极， 就可能因覆盖到等位线 1 外的区域， 而使其输出的电 位降低为大约 1 mV或者更低。 依此原理， 本发明可在等位线密度较低的区 域设置大面积的电极， 这将不会造成振幅的衰减并且能增加电极的摩擦力。
如图 12 (a)至图 12 (c)所示， 是由不同面积的电极设置于图 10 (a)的 A 与 B处所测得的 R波，其中图 12 (a)对应的电极为 6*3平方厘米；图 12 (b)对 应的电极为 6*6平方厘米；图 12 (c)对应的电极为 6*9平方厘米。 可见随着 电极面积的增加， 其振幅的衰减并不明显。 此 卜， 将止滑条缝;置于电极或 者将止滑面 #缝置于织品上，以达到电极相对于织品不会产生明显位移， 这 种模式在电极面积再缩小至 2*2平方厘米时也能读取到稳定的心电信号。
增大电极面积有两个好处： 一是比较不易发生接触不良的情况， 二是 可增大与皮肤的摩擦力， 降低体动干扰。 上述的电极是用于成人的尺寸， 对于儿童或婴幼儿， 则可依市售的成人与婴幼儿电极的比例缩小。
由本发明的图 1 ( a )还可以讨论本发明使用棵露的传输线或者连接端 子的可行性。 在电极 40与控制盒 50之间的传输线可以为具有绝缘层的导 线或者没有绝缘层的棵线， 若其绝缘层失效或者是采用棵线时可能会受到 两种影响， 一是易受汗湿或雨水的影响， 二是受静电影响。 不过静电干扰 可以采用电路或固件进行处理， 故其影响不大。 而在绝缘层失效或是采用 棵线碰到皮肤或衣物上的汗水或雨水时， 就有可能形成一个非预期的电极， 从而将该处的心电信号一并传导至控制盒 50, 引起非预期的干扰。 若非预 期电极位于电位高于 0. 3或电位低于 -0. 3的区域，则振幅至少还有 ± 0. 3mV, 可供判断 R波； 若非预期电极位于电位介于 0. 3与 -0. 3的区域，一但绝缘 层失效或者是采用棵线又碰到汗水或雨水， 则振幅就会小于 0. 6 mV， 因此 本发明应在 0. 3与 -0. 3之间的区域设置绝缘体，除了采用本身具有绝缘层 的传输线外， 还可在人体与传输线之间加装不透水的织品或印刷不透水胶 浆涂层或者使用防水织品、 防水贴条包裹棵线后再加装至织品上， 以阻隔 水分渗入。 在区 的心电信号传导 ΐ控制 5。 内的处理器， 因此: 控 盒 50所设置 的位置最好应避免 1. 4或- 1这样最高或最低的等位线区域， 而以电位为 0 的区域（如图 1 ( a ) 的 Μ点）附近较佳， 这样即使其中一个输入端子因汗水 或雨水而形成电极， 至少此端子拾取的是接近零的电信号， 还有另一个未 受汗水或雨水干扰的输入端子， 能够将位于图 1的 1. 4或- 0. 3等位线的电 极的心电信号传入处理器， 如此仍可得到 0. 5mV的振幅。 考虑到等位线并 非是由零对称延伸的， 即正端可达 +1. 4mV， 负端仅为- 1. OmV, 即使控制盒 位于图 1 ( a ) 的 W处（+0. 5等位线） ， 则控制盒 50接收负端信号的输入端 子可能会因汗水而导致电位为 +0. 5， 但仍可能获得 0. 9 mV的振幅。 由此可 知， 本发明适合控制盒 50设置的区域为 R波等位线 0至 0. 5的区域。
若是使控制盒 50的两个端子位于靠近胸窝的零等位线处， 因该处等位 线很密集（即电位变化剧烈） ， 又因织品的延展性， 在汗湿状况下， 控制盒 50的端子很可能碰到电位不是零而是相当高或低的区域。 因此， 即使在汗 湿的状况下， 控制盒 50的处理器仍可读到振幅相当大的 R波。 同时将控制 盒 50设置于此处也可缩短传输线的长度。
此外， 为了降低汗水或雨水的影响， 本发明将控制盒 50与传输线连接 的两个输入端子分别设置于控制盒 50外壳的上下两面， 以避免两个端子同 时沾到雨水或汗水， 造成心电信号短路成零电位， 致使控制盒 50内的处理 器接接收不到信号。 总之， 本发明控制盒 50上的两个端子只要其中一个端 子不会受到水分的影响而导致两端子都在同一电位上， 均可测得明显的 R 波。 同理， 相同的设计也可得到明显的 P、 Q、 S、 T波的信号。
利用图 10 (a)至图 10 (c) , 本实施例提出一种 "互补电极组" 以降低体 动干扰的方法， 如图 10 (a) 至图 10 (c)所示， 在 B， I, Z处各设置一电极， 并将 B与 I处的电极一起连接至控制盒 50的正输入端， 1处电极则连接至 控制盒 50的负输入端。 Z处电极选在身体中间且是零等位线的原因是身体 中间受到左右臂摆动的干扰最小， 而位于零等位线可使 Z 电极可搭配位于 高等位线（例如 B处 +1. 4等位线）以及 ^[氏等位线（例如 I处 0. 3等位线） 的电 极来测得 R波。如图 13 (a)所示， 由 Z处电极和单独的 B处电极测得 R波的 振幅为 1. 2 mV ；如图 13 (b)所示， 由 Z处电极和单独的 I处电极测得 R波 的振幅为 0. 3 mV ；如图 13 (c)所示， 由 Z处电极和并联的 B处与 I处电极 测得 R波的振幅为 0. 6 m V ； 如图 13 (d所示，当左手臂往前会将上衣左侧 向前拉伸致使 B处电极与人体之间的压力降低， 但同时 I处电极与人体之 间的压力就增加了； 反之， 当左手臂往后会将上衣左侧向后拉伸致使 B处 电极与人体之间的压力增加， 但同时 I处电极与人体之间的压力就降低了。 由此， B处电极与 I处电极成互补的一对电极， 无论左手在前还是在后， 至 少会有一个电极有足够的压力在人体上以拾取 R波。 若测得 R波的振幅， 藉由图 13 (a)至图 13 (d) , 即可推测其手臂的位置， 若接近 1. 2 mV， 则表示 手臂向后致使 I处电极接触不良； 若接近 0. 3mV， 则表示手臂向前致使 B处 电极接触不良； 若接近 0. 6mV， 则表示手臂在中间致使 B处与 I处两个电极 皆有良好接触。 当手臂向后或者向前运动时， 会产生一些噪声干扰， 则会 产生如图 13 (d)所示的 R波， 其是由 B、 I处电极并联与 Z处电极在行走时 测得的 R波的波形， 虽然存在干扰但仍可得见 R波， 可见互补式电极可得 到较低的体动干扰。
上述位于零电位处的电极除了设在背后的 Z处，也可设在前面如图 1 (a) 中的 M处， 会获得类似的效果。 此外， 互补式电极也可以如图 14所示采用 分离式电极设置于一弹性导电布与人体之间。 本实施例以大面积弹性导电 布作为 B处电极， 以分离式电极作为 I处电极
同理，也可在身体的右边也设置两个电极，其中一个电极设在前胸- 0. 7 等位线处， 另一个电极设在后背 -0. 3等位线处， 即可由此得知右手的姿势 状态。
同理， 本发明可引入前述的分离式电极， 将其设置于一弹性导电布与 人体下， 也可降低体动干扰， 此时弹性导电布也可当做电极使用， 如图 14 所示。
当使用者穿短袖或者长袖日衣时， 在左右两侧腋下的前后两侧各设置 一个电极， 各侧的两个电极皆并联连接至控制盒的处理器。 当手臂向前举 起时， 衣袖会牵引腋下的衣服向前， 使得设置于腋下后方的电极贴近身体， 而设置于腋下前方的电极远离身体。 同理， 当手臂向后拉时， 则设置于腋 下后方的电极远离身体， 而设置于腋下前方的电极贴近身体。 不同手臂的 姿势， 造成撷取心电信号的电极的位置也不同， 因而心电信号的形态也不 同， 如图 15 (a)至图 15 (d)所示。 其中， 图 15 (a)是本发明右臂在后左臂在 前时取得的心电图，图 15 (b)是本发明双臂皆在前时取得的心电图，图 15 (c) 是本发明双臂在后时取得的心电图，图 15 (d)是本发明右臂在前左臂在后时 取得的心电图
比较图 15 (a)与图 15 (d) , 可知相对于 R波， 图 15 (a)的 Q波较大而图 15 (d)的 Q波较小； 图 15 (a)的 T波较小而图 15 (d)的 T波较大。
比较图 15 (c)与图 15 (d) , 可知相对于 R波， 图 15 (d)的 Q波较小而图 15 (c)的 Q波较大。
比较图 15 (b)与图 15 (d)， 可知图 15 (b)的 T波较小而图 15 (d)的 T波 较大。
以上仅为举例， 实际上可由不同面积或不同位置的电极， 例如位于袖 口、 胸前、 后臂等位置的电极， 由其所获得的心电图的 P， Q, R, S, T波 的比例， 来辨识身体的姿势。
与后述的第 2 实施例相比较， 本实施例是在心电信号清晰可辨识的情 况下， 由波型分析获得其姿势， 第 2 实施例则是由噪声分析获得其动作， 两者恰可相辅相成。
当电极紧贴在身体上时， 电极与身体之间的阻抗较低， 可获得噪声较 低的心电信号。 由不同位置所获得的心电信号， 其 Q, R, S, T波的比例也 有所不同。 此两项原则， 也可应用于判定穿戴者的睡姿。 本实施例在前胸、 后背、 左侧、 右侧四处分别设置两个电极。 当穿戴者仰卧时， 设置于后背 的电极被身体压迫而有良好的导电性， 其余电极虽与身体碰触但导电性不 佳， 故对于心电图波型影响不大。 同理， 当穿戴者处于其他睡姿时也会由 不同的电极组提供心电信号。 比较其心电图， 即可推得知穿戴者的睡姿。 本实施例可在白天身体运动时读取 R波， 晚上静止时读取完整的心电图。
本发明为了让使用者在使用时感到舒适且方便， 其电极是釆用以织品 制成的干电极， 而非医院常用的生理电极贴片。 由于干电极与人体之间的 阻抗较大且不稳定， 使得在某些环境下（例如低温低湿）可能无法获得良好 质量的心电信号， 例如易受到体动干扰， 或者在身体静止不动时仍有电源 引起的电磁干扰。 因此， 本实施例针对此课题提出相应的对策， 以使本发 明得以更符实用要求。
当一用户在低温低湿（温度 16 °C、 相对湿度 55%)的环境下， 仅穿着上 述的日衣, 以织品制成的干电极所测得的波型 , 同时测得两电极之间的直 流阻抗（详细方法见第 6实施例的第八种方法）， 图 16 (a)是当电极阻抗为 15M Ohms时静止所得的 R波的波形图 ， 图 16 (b)是当电极阻抗为 30M Ohms 时静止所得的 R 波的波形图。 此时皮肤和电极的阻抗太高， 难以传导心电 信号， 此时由电源耦合进入处理器的电磁干扰相对而言较心电信号大得多， 故无法辨识 R波； 即使用力按压电极， 仍无法改善。 若将一电极脱离人体， 阻抗更大,则噪声波型漂至上饱和区或下饱和区。比较图 16 (a) , 图 16 (b) , 图 16 (c) , 可知阻抗愈高， 噪声愈大。
当直流阻抗下降至 10M Ohms时，可在静止状态下拾得 R波，如图 17 (a) 所示， 但仍难辨识在行走及原地抬腿体动干扰下的 R 波， 如图 17 (b)、 图 17 (c)所示 。 当直流阻抗下降至 0. 8M Ohms时， 则可在静止及行走状态下 拾得 R波， 如图 17 (d)、 图 17 (e) 所示， 但在原地抬腿时体动干扰仍太大 艮而难识 R波， 如图 17 (f)所示。 当直流阻抗下降至 0. 6Μ Ohms时， 则可在 原地抬腿等各种动作时都能辨识出 R波， 如图 8 (a) 至图 8 (d)所示。 由图 8 (a) 至图 8 (d)、 16 (a) 至图 16 (c)及 17 (a)至图 17 (f) 所示， 可知其规 律为： 直流阻抗愈低， 则噪声愈低； 体动干扰愈大， 则直流阻抗愈高； 若 静止时噪声较大， 则运动时噪声更大。 前述规律， 反之亦然。 引用此原则， 本实施例可在一开机时， 就先连续侦测电极阻抗一段时间（例如 10 子^估使用者在何种运动状况下仍能读到心电信号。 若、是阻抗够低:
Figure imgf000024_0001
撷取心电信号； 若是阻抗太高控制盒内的处理器即采取适当的对策， 以使 整个系统达到优化，然后再开始撷取心电信号。例如当量得直流阻抗为 10 M Ohms时， 可知在静止时仍可读取 R波， 但在运动状态下是读不出 R波。 若 是当时的阻抗过高， 无法满足使用者需求时， 例如需求是辨识出行走时的 R 波， 本实施例提出对策如下。
我们实验的初步结果， 是当电极阻抗小于 1 M Ohms时， 用图 1 (a)所示 的控制盒即可测得心跳， 而且身体运动造成的干扰相对而言很低， 即使不 使用上述的分离式电极结构， 仍能在读取行走时的 R波， 此时两电极之间 电容值约为大于 10 nF。 当电极阻抗介于 1 M与 2 M Ohms时， 用分离式电 极结构可测得行走时的 R波， 此时两电极之间电容值约为大于 5 nF。 在 2 M Ohms以上时， 仅用图 1 (a)所示的控制盒很容易只测到噪声， 而噪声大小与 动作呈正相关； 若是电极阻抗在 2 M至 20 M Ohms之间（此时两电极之间电 容值约为 0. 5至 5 nF之间）， 一般而言仅启动负反馈电路可将噪声降低至 辨识静态的心跳， 负反馈电路所连接的电极的位置， 可利用图 1 (a)所示的 等位线图来选定， 只要在低于较高电位电极、 且高于较低电位电极达 0. 4 以上的区域， 即电位介于 0. 1至 1. 0的区域， 皆可有效抑制噪声又不会显 著降低心电信号； 若是电极阻抗在 20 M至 30 M Ohms之间（此时两电极之 间电容值约为 0. 33至 0. 5 nF之间）， 一般而言仅启动主动电极电路 (将前 级放大电路设置于近电极处） 可将噪声降低至辨识静态的心跳； 若是电极 阻抗在 30 M至 40 M Ohms之间（此时两电极之间电容值约为 0. 25至 0. 33 nF 之间）， 则必须启动负反馈电路和主动电极电路， 才足以将噪声降低至辨识 静态的心跳。 若测到的阻抗大于 40 M Ohms (此时两电极之间电容值约为小 于 0. 25 nF) , 则处理器可通过通信设备指引使用者拉紧衣带、 添加衣物、 加上机能性保暖衣料、 更换电极位置、 或在电极上加入可导电液体， 使阻 抗小于 40 M Ohms , 才开始侦测心跳， 否则也测不到心跳， 只能测到噪声且 浪费电源， 不过由此噪声可测得人体的动作状态。 若电极阻抗已降到 40 M Ohms 以下， 而噪声仍然太大而难以测得心跳， 控制盒可启动前述的尚未启 动的电路， 或启动电容耦合式电极电路 (详见第 3 实施例）、 抑制体动和电 源干扰的固件或软件， 来侦测心跳。 这些电路在电极阻抗很低时可以关闭 或处于休眠状态， 以节省电力消耗。 由此结果， 本实施例会在开机时先侦 测时电极阻抗， 并启动不同的电路， 如表 2所示。 表 2 开机时各种电极阻抗下处理器采取的对策
Figure imgf000026_0001
上述电阻值仅为一用于说明的范例， 在大量应用时， 上述电阻值应依 实际环境调整。 本实施例会以一资料库储存各种状况下电阻值， 作为判断 的基准。
同理， 上述方法也可应用于脑电图、 电图、 经皮神经电剌激 (TENS) 或电击用的电极。
表 2 所列的电极的温度、 电阻及电容， 当电极稳定贴紧身体时， 其值 稳定， 反之就会剧烈变化， 可能是电极未贴身或用户剧烈运动引起， 此时 无法取得心电信号。 由此， 电极的温度、 电阻及电容可当成可否获得心电 信号的指标， 优其是其取样率可以较低， 易于辨认， 不像心电信号取样率 复杂而较难辨认。 电极的温度、 电阻及电容， 不仅可以供处理器来提出适 当的对策， 还可经通信设备送至远端的监控中心， 由远端来激活适当的电 路、 固件、 软件或指引。
若是已用尽上述所列的各项对策， 仍不能降低电极阻抗以获得噪声较 4氐的心电信号， 此时处理器可以输出一特定代码， 而不必输出无法辨识心 电波型的噪声， 以节省电力消耗。
同理， 上述的对策也可反向实施。 当电极阻抗下降至某一临界值（例如 2 M Ohms) 以下且维持一段时间（例如 30秒）， 此时在人体静止下可得很小 的噪声， 则处理器可以选择频带较宽的带通滤器（0. 1 ~ 40 Hz) 以撷取完整 的心电图， 此时处理器也可以建议使用者稍加放松衣带以求舒适。 若电极 阻抗在 2与 20 M Ohms之间， 则处理器可以选择频带较窄的带通滤器（10 ~ 30 Hz) 以撷取 R波同时降 4氐干 ·ί尤， 或以 Hi lber t- Huang transform来求取 心率。 由此， 本发明可依实际状况， 在省电、 舒适及信号品 ^三方面维持 优化。 此法对于脑电图、 肌电图、 经皮神经电剌激（TENS)或电击用的电极 也同样适用。
本实施例可以第 6实施例第一种方法同时测量织品电极之间的电容值， 若其电容值仍不小（例如 10 nF) 而电阻值 ί艮大（例如 10 M Ohms)时， 代表 电极仍在身体上， 只是皮肤太干不易导电。 若是电容值很小且电阻值很大， 很可能是电极脱落或传输线故障 , 此时本发明可通过通信设备指引用户检 查或排除故障。
前述的电极阻抗会随身体运动而迅速变化， 例如某一使用者在静止时 电极的电阻为 2. 3 M Ohms, 电容为 5. 2 nF; 步行时电阻为 5. 7 M Ohms, 电 容为 2. 6 nF; 跑步时电阻为 9. 3 M Ohms, 电容为 1. 2 nF。 这是因为电极因 身体运动而与人体接触得不紧密， 致使电阻升高电容下降， 而其他变因（例 如环境温湿度或非运动造成的流汗）并不容易造成电极阻抗有如此迅速的 变化。 利用此一特性， 我们可以由电极阻抗的变化来推估人体运动的状态， 即变化幅度愈大代表运动愈激烈。 同理， 比较使用者在静止和运动下阻抗 的差异， 可推知本发明所采用织品、 光滑材料或止滑条的抑制体动干扰的 能力。 两者之间的差异愈大， 即代表其抑制体动干扰的能力愈低。 为了增 加由电极阻抗推估人体运动的正确性， 处理器可选择性地读取加速规、 陀 螺仪、 摄影机或其他可感测人体运动的传感器的信号， 以确认人体运动。
对于噪声波型漂至上或下饱和区的状况， 本实施例可将滤波电路中的 电容器并联一电子开关（由场效晶体管构成）， 由微控制器控制， 与电路的 地线相连接。 当信号未达到饱和区时， 电子开关为断路， 滤波电路正常操 作。 当信号达到饱和区时， 微控制器开启电子开关， 使电容器的电荷泄漏 至地， 信号即迅速由饱和区拉回至中间， 如此可缩短滤波电路的暂态响应 时间， 就有更多时间可以辨识 R波。
为确保在电极或传输线接触不良时， 仍能获得心电信号， 本实施例在 图 1 (a)的两个电极之外， 再增加一个电极， 则在此三个电极之中任选两个 即能获得心电信号。 此第三个电极设置于 0等位线附近区域， 可得到较佳 的效果。 以图 10 (a)为例， 有一个电极位于 B处（1. 4等位线）， 另一个电极 位于 -0. 3等位线， 此两个电极可得到一导程心电信号， 振幅为 1. 7 «iV, 若 多一个电极位于 0等位线， 则可得到三个导程的心电信号，振幅分别为 1. 7 mV、 1. 4 mV与 0. 3 mV， 即使位于 1. 4等位线的电极损坏， 所得到唯一导程 的振幅为 0. 3 mV，仍可明显看出 R波。反之， 若多加的第三个电极位于 -0. 3 等位线， 且位于 1. 4等位线的电极损坏， 则所得的唯一导程的振幅为 0 mV， 就无法辨识其 R 波了。 又考虑等位线并非是由零对称延伸， 第三个电极的 设置位置， 以 0至 +0. 5等位线之间的区域较佳， 例如第三个电极的位置是 在 +0. 5处， 则可得到振幅 1. 7 mV, 0. 9 mV与 0. 8 mV的心电信号。 若第二 个电极是位于 -1. 0等位线处， 则效果更佳。
本实施例可在日衣的左臂、 右臂、 左腿处各设置一电极， 则不只产生
Lead I， Lead I I， Lead I I I肢导， 也可产生测量胸导的参考电位， 并在胸 前 -1的等位线至 +1. 4等位线之间的区域， 即胸导 VI至 V6位置， 设置一个 或多个面积为 2*2 厘米的电极。 由于织品有弹性， 很可能会不经意在此区 域内移动， 处理器即可收集 VI至 V6的心电信号。 参考电位除了由肢导取 得之外， 也可用连接器连接衣服和裤子， 甚至帽子或手套而获得。 第 2实施例 由噪声推估人体运动
在身体运动时， 电极与皮肤难免会产生相对位移， 体内的离子也会随 之移动， 此时心电信号会受到干扰而含有相当多的噪声。 反过来看， 噪声 即是身体运动的指标。 本实施例提出五种方法由噪声推估人体运动的情形。
第一种方法： 由噪声误判为 R波的次数推估人体运动
在本实施例中， 当要通过分析噪声以推估人体运动的情形时， 若不以 滤波固件抑制噪声， 则会有很多噪声被误判成 R 波。 由于噪声的间隔时间 远小于正常心跳的间隔时间， 而且一般人在正常情况下， 不可能在一分钟 之内 , 心跳由一般活动下的 72次（R波间隔为 0. 833秒)跳到极端激烈运动 下的 200次（R波间隔为 0. 3秒），故控制盒内的 t控制器可以轻易辨识出有 无噪声，辨识的规则如下：取一分钟内次数最多的心率，设其 R波间隔为 1， 取 R波间隔小于 1的一部分（例如二分之一或三分之二）， 即视为噪声。 把 统计图中噪声区间的次数累计， 即可视为噪声大小的指针， 即运动量的大 小。
人在熟睡时身体不太会动， 而翻身或手脚不自主运动时即会形成噪声。 把一段时间（例如七小时的睡眠）的运动量作成统计图， 即得到睡眠活动图， 进而了解用户的睡眠质量。 其中利用噪声次数累积作为活动指标的睡眠活 动图， 横轴为时间， 纵轴则是利用噪声次数累积作为活动量。 噪声大小也 可以利用心电图水平轴上的噪声振幅来表示， 振幅越大表示运动量越大。
同理， 对于日间活动， 也可制作成日间活动图。 若噪声有规律性， 例 如每 0. 5 秒有一次大量噪声， 持续为三分钟， 则可推断使用者在进行有规 律的运动， 例如行走； 若偶而出现大量噪声， 可能是焦虑引起的噪动； 或 是穿戴者情绪紧张， 此时就会有大量肌电信号干扰心电图。 由此得到的曰 间活动图可用于居家照护的老人， 照护者可以据此判别老人的行为， 适时 介入。
第二种方法 由波峰振幅推估人体运动
当在小幅体动千扰下， 信号未达到饱和， 微控制器仍能辨识出 R 波， 但也会得到噪声， 这些噪声振幅可能呈忽大忽小不规则变化。 然而， 正常 的 R 波振幅是相当稳定的， 不会忽大忽小没有规则。 利用此特性， 处理器 可以记录每一小段时间内的极大值（即波峰的振幅）， 以时间为横轴， 振幅 为纵轴作图， 此图即可代表体动干扰的程度。 当无体动干扰时， 此图所呈 的会是近似一直线， 体动愈剧烈则此线起伏愈大。
第三种方法 由上下饱和所占时间比例推估人体运动
当身体运动过于激烈时， 心电信号很容易漂移至上饱和区或下饱和区。 对于到达饱和区的信号， 是无法解读出 R 波的， 然而， 到达饱和区占全部 时间的比例， 即代表运动干扰的程度。 在一定时间内， 到达饱和区的时间 愈长， 即代表其运动干扰愈强烈。
第四种方法 由线性范围推估人体运动
图 13 (d)呈现的是在运动中的信号， 此时固件会自动调降其增益值，扩 大线性范围， 使整个信号皆在线性范围内不致饱和； 相对而言， 若是用户 在静止状态， 信号就不会有剧烈的变化， 此时固件会自动调高其增益值， 缩小线性范围， 以得良好的分辨率， 此即是现有习知的自动增益控功能 (Auto Ga in Control) 0 由增益值或线性范围的大小变化， 也可推估身体运 动的程度， 即增益值大 (线性范围小）即表示身体运动和緩， 反之则为剧烈。
第五种方法 由单位时间内正常 R波个数推估人体运动
由图 17 (a)至图图 17 (f)所示及第四种方法所述可知， 当信号受到体动 干扰而漂移至上饱和区或下饱和区时， 是无法解读出 R 波的。 反之， 在正 常状况下， R波会以合理的间隔稳定呈现， 因此， 本实施例可以取单位时间 内正常 R波个数为指标， R波个数愈低即代表人体运动愈剧烈。
当电极未贴身， 也会使信号漂移， 而呈现类似运动干扰下的噪声。 因 此， 本实施例可在控制盒内或织品上选择性地增加一加速规、 陀螺仪、 地 磁计、 或倾斜计等姿势传感器， 通过其量得的加速度等信号， 作为行动或 噪声的指针。 第 3实施例. 电容耦合式电极
以上所述电极皆不像医院常用的生理电极一样有含有水及氯化钾的凝 胶以增加导电性， 故被称为干电极（dry electrode)。
在温度湿度很低或使用者本身皮肤很干燥的情况下， 干电极与皮肤之 间的电导会变得很低， 不利于撷取心电信号， 只剩下电容性。 在这种状况 下， 可以使用电容耦合式电极及电路， 即电极与皮肤之间没有直流的电导， 而是以电容耦合来传递心电信号。 然而对生理监视衣而言， 由于其必须承 受洗涤之力， 而电容耦合式电极上的绝缘层可能会因为洗涤而破损， 从而 不再是完美的电容而兼有电导特性。 总而言之， 考虑实际应用的情况， 生 理监视衣最好是能兼有干电极和电容耦合式电极这两种电极， 以因应环境 的变化。
上述的电容耦合式电极的绝缘层， 是介电质， 选用相对介电常数较高 的、 导电系数较低的材料较佳， 如尼龙 (Nylon, 相对介电常数为 2)， 二 氧化硅 (相对介电常数为 3. 9)、 聚氯乙烯（PVC, 相对介电常数为 3)、 钛酸 铜钙（CCT0,相对介电常数约为 10000)等材料。介电盾除了整体附着于导体 之外， 也可附着于织物上。 以下举例进行说明， 将介电质与溶剂或粘着剂 混合， 再以棉纱沉浸其中， 使棉纱沾附介电盾， 再织成布， 或与其他纤维 捻成线再织成布， 即制成一具有高介电系数的织物， 作为电容耦合式电极 的绝缘层。 另一例， 是将上例中的棉纱以导电纤维取代， 织成布即是一电 容耦合式电极， 在和其他导体连接时， 可用物理或化学方法去除介电质， 即可使导电纤维外露， 再与其他导体连接。
电容耦合式电极的导体与干电极， 可藉由不同的方式设置于织品上， 例如：
1.藉由将非导电纤维及导电纤维经由一纺织工艺 ( Text i le process ) 共同纺织而成， 该纺织工艺是针织（kni tt ing)、 平织（weaving)、 梭织 (tat t ing)、 刺缘（embroidering)或其它适当工艺；
2.藉由将导电金属片嵌入、 粘结或缝入该织品而形成;
3.藉由将导电细线缝入该织品而形成；
4.由在该织品上涂布或贴覆导电物质而形成；
5.藉由将导电织品粘贴或缝合于织品上而形成；
6. 采用导电硅胶或橡胶而形成。
前述的非导电纤维例如可以采用但不限于棉、 麻、 尼龙等， 而该导电 纤维可以采用但不限于多分子导电纤维或是导电金属纤维， 也可由不锈钢 纤维与非导电纤维混纺而成， 或是在绝缘纤维上涂布或渗入导电物质而形 成，该导电材料占该导电区的比例可为 1%至 100%。
本实施在织品上装有前述的干电极和电容鵪合式电极， 两种电极的并 用型式如下：
1、 将导体 75嵌入导电布下方的弹性体 90内， 导体 75即同时是电容 耦合式电极， 如图 18 (a)所示， 图 18 (a)是本发明两种电极并用的第一种 形式的示意图；
2、 将导体 75覆一绝缘层， 设置在织品 85与人体之间， 并位于干电极 40的旁边， 如图 18 (b)所示， 图 18 (b)是本发明两种电极并用的第二种形式 的示意图；
3、将导体 75嵌入织品 85内，并使其位于干电极 40的侧面，如图 18 (c) 所示， 图 18 (c)是本发明两种电极并用的第三种形式的示意图；
4、 将导体 75设置在织品 85外表面， 并位于干电极 40的旁边， 如图 18 (d)所示， 图 18 (d)是本发明两种电极并用的第四种形式的示意图；
5、 将导体 75覆一绝缘层， 设置在织品 85与人体之间， 并位于干电极 40之上， 如图 18 (e)所示， 图 18 (e)是本发明两种电极并用的第五种形式的 示意图；
6、 将导体 75嵌入在织品 85 内， 并位于干电极 40之上， 如图 18 (f) 所示， 图 18 (f)是本发明两种电极并用的第六种形式的示意图；
7、将导体 75设置在织品 85外表面，并位于千电极 40之上，如图 18 (g) 所示， 图 18 (g)是本发明两种电极并用的第七种形式的示意图；
8、 将导体 75作为电极设置于织品 85内， 导体 75本身即可当干电极， 又可当电容耦合式电极。 当皮肤较干时电阻较大， 控制盒内的微控制器可 切换使用电容耦合式电极的电路撷取心电信号， 当皮肤较湿时电阻较小， 微控制器可切换使用干电极的电路撫取心电信号（如图 19所示， 其中， 可 视噪声大小选择性使用负反馈电极， 并在电极下可选择性增加一绝缘层作 为介电盾， 以增加其电容性， 如图 18 (h)所示， 图 18 (h)是本发明两种电极 并用的第八种形式的示意图；
9、 将弹性导体 75设置在织品 85的内表面， 并位于干电极 40上， 另 有一绝缘层介电质附着在干电极 40上， 如图 18 (i)所示， 而干电极 40另以 弹性带（图 18 (i)未示出）连接以附着在织品 85，图 18 (i)是本发明两种电极 并用的第九种形式的示意图
为了降低外界干扰， 电容耦合式电极用前级放大电路设置的位置应尽 量靠近电极， 即是 "主动电极" (act ive electrode) 。
在另一具体实施例中， 干电极与电容耦合式电极共享一条传输线， 如 图 19所示， 图 19是本发明电容耦合式电极与干电极共享一电路的示意图。 当皮肤较湿润致导电性良好时， 心电信号由干电极传导至放大器， 反之， 则由电容耦合式电极传导。
对于电容耦合式主动电极， 由于信号很小， 必须以良好的屏蔽 (shielding)与保护（guarding) 技巧来阻止外界的电磁干扰， 在本发明中 为求与织品相匹配， 屏蔽与保护皆可选用导电布（例如银纤维布或钢布）， 采用原先用于一般电路的铜箔、 导电镀膜等技巧， 用于织品上， 或者用其 他导电布或导电材质取代， 来达到屏蔽与保护的目的。 第 4实施例. 在电极外部或内部增加气囊或液囊
其中气嚢或液嚢可设置于导电布下， 如图 20所示， 在电极内部设有一 气嚢或液嚢（内含空气、 水或油等流体）， 当身体仅压到某一侧时， 气嚢或 液嚢内的流体会流向另一侧使另一侧的导电布更接近身体， 可增加导电性。 气嚢或液嚢内也可选择性地加装海绵、 硅胶或弹簧等弹性体， 以具有吸水 性的材料较佳， 作为緩沖之用。
上述气嚢或液嚢也可实施于不同位置的电极， 例如一个电极是设在右 腋下， 一个电极是设在右侧腰部。 理想上， 当人右側卧时， 右腋下与右侧 腰部应当会被身体压到， 但是由于身体的曲线或床板的凹凸形状， 有可能 只有其中一个电极被完全压下， 另一个接触情况不佳， 此时若有如图 21 (a) 所示的一组（两个）气嚢或液嚢以连通管相接， 当一电极被压下时， 可以使 另一側电极更接近身体， 可增加导电性。
以连通管相接的一组气嚢或液嚢， 也可以用于避免另一个电极误触人 体。 例如， 在第 1 实施例中， 是由心电信号波型来判别睡姿， 理想上右侧 卧时应只有右腋下与右侧腰应当会被身体压到, 但是偶而前胸电极也会被 手压迫而误触身体。 本实施例可以在右腋下与前胸电极处设置气嚢或液嚢， 并将两者以连通管相接， 但是此气嚢或液嚢并非在导电布和衣物之间， 而 是在导电布的周围， 如图 21 (b)所示， 呈环状以露出中心供导电布与人体接 触。 当右侧卧时右腋下的气嚢或液嚢会被压迫， 使得胸前的气嚢或液嚢膨 胀， 就不易被手压迫而误触身体了。
以上所述的电极为干电极， 是与人体相接触， 但对于电容輛合式电极， 同样适用。 也可选择性地增加一小片或带状的具有高相对介电常数的材质 在电极上， 例如尼龙 (Nylon, 相对介电常数为 3. 2)， 二氧化硅 (相对介电常 数为 3. 9)、 聚氯乙烯（PVC， 相对介电常数为 3)、 钛酸铜钙（CCT0, 相对介 电常数约为 10000)等材料， 如第 3实施例所述， 以增加电容量。
对于装盛水的液嚢， 可以釆用在不受压时能撑开的弹性结构， 而且是 有些微渗漏的， 即非完全密封的， 这样即可在洗涤时吸收水， 在使用时 受压即可渗出微量水分至电极上， 以增加导电性。 若液嚢有上述的弹性体， 也可阻止内含的水分过快渗出。 当液嚢内变成容纳空气时，液嚢的弹性可在 受挤压后使内部呈负压， 以吸住人体皮肤， 同时又可将皮肤上可导电的液 体（例如水）吸在电极上以利于导电。
在本法明中， i 空制器可控制一泵推动空气、 油或水， 此泵经由一密 闭管连接至一固定在电极与织品之间的气嚢或液嚢。 当侦测到任一电极阻 抗太高致使信号太小时， 微控制器可开启泵使气嚢或液嚢膨胀， 以通过气 嚢或液嚢的压迫使电极紧贴皮肤。 当使用油或水以膨胀液嚢时， 控制盒内 可另设有一油或水的储存槽。
第 5实施例 利用磁力固定电极以减少体动干扰
本实施例的第一种方法是在电极的外面或旁边设置永久磁性物质 5，例 如铝镍钴（AlNiCo)、 铁氧体 (Ferr i te)、 钐钴 (SmCo)及钕铁硼 (NdFeB) , 而 在身体的对应侧设置导磁物质如硅钢， 或是永久磁性物质 5 ,但与前述永久 磁性物盾的极性相反， 利用异极相吸的原理， 即可对电极 40产生吸引力， 使其附着在身体的力量更大， 从而可以减少体动干扰， 如图 22 (a)所示， 图 22 (a)是本发明在织品及电极上各加装一磁石的示意图。。 同理， 在电极的 外面或旁边设置导磁物质 5， 而在身体的对应侧设置永久磁性物质，也具有 相同的效果。 此外， 也可以电极本身就是永久磁性物质 5或导磁物质， 例 如不锈钢和硅钢可导磁又可导电， 故本身也可做为电极； 铝镍钴、 钐钴及 钕铁硼本身也可导电， 即可做为电极 40; 永久磁性物质 5或导磁物质（例如 铁氧体）可以抽成丝、 或设置于中空纤维内、 与其他材料结合抽成丝、 或用 染色或电镀方式涂于一般纱线外，以捻或混纺方式，与导电体（例如银纤维） 结合， 制成导电布， 即可导电又可导磁。
本实施例第二种方法是利用同极相斥的原理， 把电极 40推向身体。 例 如在腋下电极的外面设置永久磁性物质 5，同时在上臂内侧同样设置永久磁 性物质 5， 使此二永久磁性物质 5的同极相对， 就会互相排斥， 使腋下电极 40被推向身体， 即可减少体动干扰。 同理， 也可在与身体靠近的物体（例如 床、椅等）上设置永久磁性物质 5，使其同极相对，也可将电极 40推向人体。 同理，在外衣或胸罩设置永久磁性物质 5，在内衣内裤上设置电极及永久磁 性物质 5; 在外裤、 鞋子上设置永久磁性物质 5， 在袜子上设置电极及永久 磁性物质 5 , 使其同极相对产生斥力将电极推向人体。
例如在图 22 (a)中，在电极 40及织品 85各设有一为同极相斥的永久磁 性物质， 即会将电极 40推向人体； 同理， 在图 4 (a)至图 4 (d)所示的分离 式电极 40与织品 85上也可各设有一为同极相斥的永久磁性物质 5 ,即会将 电极 40推向人体； 同理， 在图 21 (b)所示的气嚢或液嚢与导电布也可各设 有一为同极相斥的永久磁性物质 5 , 即会将电极 40推向人体。
此外， 可选择性地在图 7 (a)所示的滑块与织品上各设有一为同极相斥 的永久磁性物质 5 , 即会将电极 40推向人体； 或者在图 7 (b)所示的电极 40 与滑块上各设有一为同极相斥的永久磁性物质 5,即会将电极 40推向人体； 或是， 在图 7 (c)所示的电极 40与织品 85上各设有一为同极相斥的永久磁 性物盾 5 , 即会将电极推向人体。
本实施例可以采用环型永久磁性物质 5， 来增加互斥磁力的稳定度，如 图 22 (b) 所示， 图 22 (b)是本发明采用环型永久磁性物质的示意图。 其中 环型永久磁性物质 5与电极 40周遭永久磁性物质的斥力可使电极 40在环 型之内， 不易移至其外。
永久磁性物质 5可置于电极 40两侧， 以吸引磁力将电极贴近人体， 如 图 22 (c) , 图 22 (c)是本发明在衣服上将永久磁性物质设置于电极两侧的示 意图。 其中位于两侧腰部的永久磁性物质 5， 将电极 40下方或周遭的导磁 性物质或永久磁性物质 5拉近胸前导致电极贴近人体。 也可在肩上设置的 电极 40下方或周遭设置导磁物质或永久磁性物质 5， 在肩下方前后侧置永 久磁性物质 5， 使电极 40贴近人体。
永久磁性物质 5 除了是一整块固体， 也可是由多个小块组成， 使其南 极与北极互相衔接， 此永久磁性物质 5组即可随身体外型变化而曲挠， 磁 力效果更佳， 对于使用者也更加舒适。 第 6实施例. 侦测电极接触不良
当电极与皮肤接触不良（即阻抗太高） 或是传输线折断时， 就难以看到 R波。 因此本发明提供了八种方法侦测电极与皮肤是否接触不良：
第一种方法， 是对于仅用两个电极的场合， 如图 23所示， 图 23是本 发明由脉波侦测电极是否接触不良的示意图。 其是由微控制器或振荡器（例 如 LM555)产生一脉波，经一限流电阻，再经一模拟开关 （ana log swi tch)选 择连接至一电极， 模拟开关 1与模拟开关 2 由数字输出控制， 以选择电极 连接脉波来侦测电极接触不良， 或是连接至仪表放大器以取得心电信号。 当模拟开关 1 与模拟开关 2选择电极接脉波时， 一电极即连接至微控制器 的模拟输入端， 量测其振幅或频率或有效周期， 即得知两电极之间的阻抗， 此方法类似万用电表量测电容器的方法， 即是侦测电极与人体表皮层之间 的阻抗， 而人体表皮的导电方式在一般情况是以电容为主， 故此法量得的 是電容值， 也可採万用电表量测电容器之方法， 其結果如表 2。 若该阻抗大 于某一临界值， 即判定为接触不良。 如图 24 ( a )至图 24 (b)所示， 其同一 使用者同一组电极在不同电容下所得的心电图， 其中图 24 (a) 的电容值为 2. 7 nF, 振荡器产生的脉波频率为 16. 8 K Hz; 图 24 (b) 的电容值为 21. 7 nF， 振荡器产生的脉波频率为 2. 1 K Hz; 比较 24 (a)与 24 (b)， 易见前者噪 声较后者大, 其振动频率也远大于后者。 本发明可设 5 nF为临界值， 当电 容值小于 5 nF即采取各项对策， 如表 2所示。
对于多于两个电极的情况， 若想侦测每一个电极是否接触不良， 可以 在织品上增加一个环绕身体、 手臂、 或大腿的电极， 确定此电极可不会因 肢体的动作而接触不良， 脉波即可由此电极送入， 再由其他电极读出， 以 侦测各电极是否接触不良。 此方法可以参考申请人之前提出的 PCT 国际专 利案 PCT/CN2010/001931 ,其中详细阐述了当人体与电极之间有压力、拉力、 扭力或张力时， 使得人体表面与电极之间的阻抗变化， 尤其是电容的变化， 由一电路发出信号， 并以频率、 电压或电流的变化来表现该阻抗变化的方 法。 此方法不只可以用于判别电极是否接触不良， 同时也可用来读取呼吸、 姿势、 或进行步态分析。 例如：直接用电极与人体接触，当人躺下时振荡器 产生的脉波频率为 170kHz,站立时为 120 kHz 坐下时为 80 kHz , 这是由于 重力方向和姿势改变了胸围及腹围， 脉波频率随之改变。 在此时，呼吸又可 使脉波频率随之上下变动， 若此时可测到呼吸， 就代表电极与人体接触良 好， 即可激活相关电路来测得心电信号。 同理， 此方法也可适用于电容耦 合式电极， 电极可以不直接碰触人体， 因为电路是发出脉波而非直流， 故 仍可量测电极的电容值。 同时， 电极也可以隔着衣服而与衣服无直接碰触。
此方法还可配合不同形状、 大小、 或材盾的电极一起实施， 如图 25 (a) 所示， 图 25 (a)是本发明不同形状但电性连接的两个电极的示意图。其中两 个电性连接但是不同形状、 大小、 或材质的电极， 在与皮肤接触由松至紧 的过程中，其阻抗的变化过程是不同的（如图 25 (b)的 A与 B所示）， 即使在 完全紧贴的状况下， 其阻抗也不一样， 由此， 该方法可以推断是那一个电 极与人体接触， 从而推知那个电极的位置， 从而推知其姿势。
此方法还可配合电极外加的电子组件一起实施， 如图 26 所示， 图 26 是本发明四个连接不同电子组件的电极的示意图。 两个电性连接但串联或 并联不同电子组件的电极， 在接受脉波输入时， 会有不同的反应， 其波型、 相位、 阻抗、 共振频率会因而改变， 例如对于连接电容的电极， 其波形就 会是指数函数充放电， 而不再是原来的脉波。 微控制器可以辨别这些改变， 因而可以推断是那一个电极与人体接触， 因此， 这个与人体接触的电极就 可以被用来接收心电信号。 更进一步， 从而推知其姿势， 例如当左右腋下 的电极与人体接触时， 可推知左右臂是靠近躯体或没有在动作， 反之则为 离开躯体。
第二种方法， 请参考前述的第 1 实施例， 微控制器若在一段时间（例 如一分钟）内都无法得到正常的 R波、 Q波或 S波的间隔时间（正常的间隔时 间约为 1. 5秒至 0. 3秒） , 由此判断所得信号为噪声。 此时可能出现下列状 况： 一、 是电极与皮肤接触不良或是皮肤太干而难以导电； 二、 身体运动 造成的干扰太大， 信号成上或下饱和， 无法解读出 R 波； 三、 外界的电磁 干扰太大。
第三种方法， 如图 27所示， 图 27是本发明由弦波测电极是否接触不 良的示意图。 在任一电极输入端依次连接一限流电阻（约 10 K Ohms)、 由被 动组件组成的高通滤波器、 和一高频信号产生器（如弦波产生器）， 其他电 极的输入端则依次连接一高通滤波器、 一放大电路， 最后连接至微控制器 的模拟输入端。 若弦波频率够高， 即可进入肌肉组织， 再由另一电极回到 处理器。 若该电极的放大电路可以得到足够大的正弦波， 即代表该电极的 阻抗够低。 在仪表放大器的前端则连接低通滤波器， 让低频的心电信号（低 于 40 Hz)传导至仪表放大器， 并阻止正弦波进入以避免干扰心电信号， 即 可同时取得心电信号， 又可以弦波侦测电极是否接触不良。 图 27可以放在 主动电极电路， 以降低外界电磁干扰， 并有益于判定噪声。
第四种方法， 是以现有习知的阻抗式呼吸描计图 （impedance pneumogram) 技术实施， 若能够由呼吸描计图读取呼吸率， 则表示电极是 贴在身体上的。 相反地， 若是呼吸描计图中出现大量的高频成份， 即可推 断此高频必为噪声， 因为正常人呼吸的频率很低（小于 1 Hz)。 有噪声即代 表接触不良。
第五种方法， 在织品上和控制盒的电路如图 28所示， 是不输出任何信 号至电极， 使电极电位接近漂浮（f loat ing) ， 再撷取由单一电极获得的信 号。 此时运算放大器输入端的阻抗是其本身的内阻（以 Rinl， Rin2表示）， 为了能使输入端随外界噪声漂浮， 应选用输入阻抗大于 100 M Ohms的运算 放大器。 在此状况下， 若电极与人体接触良好， 则人体形成一良导体， 易 与 50或 60 Hz的电源产生电容性或电感性耦合， 此时单一电极会得到相当 强的 50或 60 Hz的千扰源。 反之， 单一电极由于传输线并不长， 不易耦合 到来自电源的 50或 60 Hz的干扰源， 而得到相当弱且类似白噪声 ( whi te noi se ) 的不规则背景噪声。
第六种方法， 在织品上和处理器的电路如图 29所示， 是输出一脉波至 电极， 记录其充电放电期间的电压变化。 若电极与人体接触良好， 则人体 与电极之间形成一电容， 接触愈紧密则电容值愈高， 充放电时间就愈长。 处理器经由此电极进行充电放电， 电流再经过处理器与人体之间的杂散电 容回到控制盒内的处理器。 反之， 若电极与人体接触不佳， 则此电容值就 很低， 几乎没有充放电时间。 处理器可以量测单一次的充放电时间， 或是 用一振荡电路 (例如 LM555)连续充放电再量测其振荡频率，如第五实施例所 述， 皆可判断电极与皮肤是否接触不良。 为了增加电极与人体之间的电容 性， 可选择性地加一小片或带状的高相对介电常数材质在电极上， 例如尼 龙（Nylon, 相对介电常数为 3. 2)， 二氧化硅 (相对介电常数为 3. 9)、 聚氯 乙烯（PVC相对介电常数为 3)、 钛酸铜钙（CCT0，相对介电常数约为 10000) 等材料， 上述方法也可以用弦波实现。
第七种方法， 其处理器内部的架构如图 30所示， 一个电极本身有两条 传输线连接电极和处理器， 微控制器发出弦波或脉波经一传输线连接到电 极经另一传输线回到微控制器， Rou 11及 Rou 12取 10M Ohms以上的电阻， 以便和杂散电容和电感相当， 仿照第五种方法进行分析， 若电极与人体接 触良好， 则人体形成一良导体， 易与 50或 60 Hz的电源产生电容性或电感 性耦合， 模拟输入 1与模拟输入 3即可得到 50或 60 Hz的干扰； 反之， 则 不易得到 50或 60 Hz的干扰。 由此， 即可判断电极与皮肤是否接触不良， 同时， 若输入信号无弦波或脉波， 则可能是传输线或电极损坏而断路造成。
第八种方法， 由干电极量测皮肤表面直流电阻来评估电极是否接触良 好， 是通过在处理器的输入端加一模拟式开关， 如图 31所示， 藉由一电阻 及齐纳二极管或类似的参考电压源， 产生一电压约为 1 Vol t的直流电源， 以测量直流电阻。 取较低电压是为了避免在电极端产生极化和电解水反应， 用直流电的目的是直流电不能通过皮肤最外的角质层， 只有小部分能由汗 腺进入体内， 大部分的直流电将会经皮肤表面的汗液， 由一个电极流向另 一个电极， 皮肤愈干就愈不容易将生理电信号传导至电极， 即是电极与人 体接触不好。
本实施例由实验得知，当左右腋下电极的直流电阻大于 5000K Ohms时， 皮肤太干， 心电信号质量不佳。 上述方法类似万用电表测量电阻， 处理器 可藉以量测电极是否接触良好， 当皮肤太干时， 处理器可暂停由干电极取 得心电信号， 而改由电容耜合式电极取得心电信号， 或由通信设备提醒用 户多穿衣物以保暖， 即可增加皮肤表面的汗液， 以提高心电信号质量， 如 表 2所示。 量测皮肤表面的直流电阻， 同时也是侦测电极是否贴在皮肤上， 若是则其值应是稳定的， 否则即表示电极接触不稳定。 若是电阻值很大， 即表示有一电极没有贴到人体。
第九种方法是在电极附近设置以织品为基底的传感器， 以侦测电极是 否紧贴人体， 以及人体该部位是否有运动 ά 织品传感器可以采用申请人之 前提出的美国专利 7, 750, 790所述的织品应变规，或是 PCT/CN2008/001571 所述的裂缝式拉力传感器， 或者 PCT/CN2008/001570 所述的压力传感器， 或其他类似的传感器。 同时， 压力和拉力传感器本身也可当做是电极的一 部份。 现以图 1 ( a )说明， 若要侦测左右腋下电极接触是否良好， 可在两 极之间的衣物上装设上述的织品传感器， 当人穿上此衣物时且松紧适当时， 衣物织品的弹性会产生拉力， 此拉力会对人体产生压力， 织品传感器即可 侦测此拉力或压力。 反之， 若太宽松， 衣物即无足够的压力或拉力让电极 与皮肤有良好接触。 另一方面， 若织品传感器侦测到的拉力或压力是维持 在一定值无很大变化， 即表示使用者没有运动， 此时即无体动干扰； 反之， 若拉力或压力有变化， 即表示使用者在运动， 此时有体动干扰。
第十种方法， 是以两片导电布中间夹一绝缘体形成一电容式压力或拉 力传感器， 此绝缘体可为弹性体或含有高介电常数材料。 在外部的压力或 拉力作用下，其电容值也跟着变化。 处理器可以用第五实施例第一种方法所 述的电路， 量测其电容值。 电容式压力或拉力传感器可设置于衣物与人体 之间， 当人的姿势一有变动， 其电容值也跟着变化。 处理器可设定一临界 值， 即是在一定程度的压力下， 生理信号才被接受， 例如压力大于一临界 值才启动心电图侦测。 若电容值有大幅变化， 即代表有体动干扰。 同时， 两片导电布中贴近人体的一片可同时做为电阻（干)式心电图电极， 另一片 可同时做为电容耦合式心电图电极， 故两个导电布形成一电容， 当作一个 开关， 同时导电布也可当作电极，故也同时侦测接触不良。
在前述的第 2 实施例中本发明揭露的由噪声推估身体活动的方法， 同 理， 本实施例也可由侦测电极阻抗来推估身体活动， 例如某电极位于腋下， 当其接触不良时， 即表示手臂未紧靠身体。
另外， 本实施例也可应用于脑电图、 肌电图、 经皮电刺激治疗、 电击 治疗的电极， 测试其电极是否接触良好。
第十一种方法， 由其他生理信号传感器， 来判别电极是否贴身。 在与 身体接触的织品上， 除了心电图电极之外, 也可以装设其他生理信号传感 器， 例如听诊器（必须与身体完整接触但不须要等待其瞬时反应即可测得心 肺音）、 超音波探头、 体温计（须要等待其瞬时反应约 3分钟， 若体温值突 然改变即代表传感器没有贴身）、 血氧饱和度计（须要等待其瞬时反应约 20 秒）、 血压计（若血压值不稳定即表示人在运动）等， 本实施例可以将心电图 电极设置于这些传感器旁边， 当测得心电图电极接触良好时， 即可确定这 些传感器也有良好接触， 也可获得良好的信号。 本实施例还可通过在电极 附近设置其他生理传感器， 例如肌电图传感器、 血氧饱和度计、 体温计、 心肺音传感器、 或超音波血流计等， 藉由分析其他生理传感器的信号或噪 声， 推估该部位的体动干扰。 例如， 当肌电图传感器取得较大信号时， 即 代表该处肌肉活动较剧烈， 即是有体动干扰； 同理， 当血氧饱和度计仅取 得剧烈晃动的噪声而无稳定的脉波时， 即表明有体动干扰。
反之， 若这些传感器有良好的信号， 即可确定心电图电极接触良好。 由上述方法中， 处理器可以量测各电极的阻抗， 选出阻抗最低的两个 电极， 或由其他方法来选取电极， 来拾取心电信号， 可得最佳信号质量。
Z 上述十一种方法中， 用来判断电极与人体接触是否良好的输出值， 例如第一种方法的会随电容值而变化的脉波频率， 都会因身体运动而改变。 这些输出值的振幅， 即代表身体运动的程度， 运动愈剧烈则振幅愈大， 若 身体在静止状态或电极与人体接触良好则输出值稳定。 因此， 由这些输出 值的振幅， 即可判断身体运动的程度与状态。
若是采用上述任一方法， 测得电极与人体接触良好， 但却不能取得长 期且稳定的心跳信号， 这就可能是电极或是传输线有接触不良状况。 此时， 可依第 7实施例所示的方法检查与维修， 如下所述。 第 7实施例. 判断传输线或电极是否导通不良
本发明是可承受一般洗涤的搓揉， 若是搓揉力量太大， 则传输线或电 极可能损坏， 就无法传输心电信号给控制盒了。 本实施例提出两种方法： 第一种方法， 可让处理器能判断传输线是否导通不良， 如图 32所示。 以左右腋下的干电极为例， 除了各有一条传输线连接至处理器之外， 另有 一条传输线连接此两个电极， 此传输线串联一按键开关（push but ton swi tch) 或切换开关（toggle swi tch) , 设置于本发明的织品上。 按键开关 未受压时不导通， 当受压时即导通。 当使用者想检查传输线或电极是否导 通不良或受损时， 只要按下此按键， 若传输线为良好的通路， 此时信号输 出所呈现的是接近零的一条水平直线； 若传输线或电极已损坏， 则信号输 出所呈现的是纷乱的噪声。 两种状况下信号输出有极大差异， 可由使用者 的肉眼或控制盒内设的程序， 由噪声的振幅来判断传输线或电极是否导通 不良。
第二种方法， 在织品上与第一种方法一样， 即是另有一条传输线连接 此两个电极， 此传输线串联一按键开关或切换开关， 不同之处只是在处理 器上是如图 29或图 30的架构， 由处理器经由一输出电阻、 一电极及传输 线输出脉波或弦波作为测试用的载波， 再经过连接此两个电极的另一条传 输线和其串联的按键开关或切换开关， 和另一电极及其传输线， 若此路径 的电线或电极皆无损坏， 栽波即回到控制盒， 即可以此法来判断传输线是 否损坏。 此外， 比较输出波与返回波的振幅， 若有大幅落差， 即表示其导 电性不佳， 此系统有故障， 应送修不宜继续使用。 同理， 我们也可以同样 方法， 量测某一段电极或电线是否导通不良， 即在要量测的电极或电线两 端另加一条传输线， 此传输线串联一按键开关或切换开关。 同时， 比较输 出波与返回波频谱的差异， 即表示外界的噪声干扰。 例如， 我们已知载波 的频谱， 和其主频带附近的信噪比 （S/N ), 然后分析返回波频谱主频带附 近的 S/N, 两者之差即为外界噪声干扰的量化指针。若传输线及电极导通情 形良好， 则两者之差应为极小， 反之则为较大。
一般而言， 传输线或电极的导通由良好而劣化至完全损坏是一渐进过 程， 其导电性会逐渐下降而非一瞬间从有至无。 因此， 本发明可以为各传 输线及电极， 设定上述两方法输出的量化指针（第一种方法的噪声振幅， 第 二种方法的载波与返回波主频带附近的 S/N之差） 的阀值， 例如第一种方 法的阀值是出厂值的 50%,当电极或是传输线受损时而使量化指针到达阀值 时， 即提醒用户进行维修， 以保有良好的工作质量。 维修方法， 是针对导 通不良的电极或是传输线， 在其导体的接点多加缝线以强化其导电性， 或 多缝一条导电线， 或多缝一片导电布。
以上所述， 仅是本发明的较佳实施例而已， 并非对本发明作任何形式 上的限制， 虽然本发明已以较佳实施例揭露如上， 然而并非用以限定本发 明，任何熟悉本专业的技术人员，在不脱离本发明技术方案范围内， 当可利 用上述揭示的方法及技术内容作出些许的更动或修饰为等同变化的等效实 施例， 但凡是未脱离本发明技术方案的内容， 依据本发明的技术实质对以 上实施例所作的任何简单修改、 等同变化与修饰， 均仍属于本发明技术方 案的范围内。

Claims

权 利 要 求
. 1. 一种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有一 件织品， 其中：
该织品具有至少两个电极以撷取心电信号，所述的两电极分别设置在 人体表面心电图 R波的等电位线相差至少 0. 2的两条等电位线上。
2. 根据权利要求 1所述的物品， 其特征在于其中所述的两个电极有两 个连接器用于电性连接控制盒与电极，同时连接器设置于人体表面心电图 R 波的等位线图中的零与 +0. 5的等电位线之间。
3. 根据权利要求 2所述的物品， 其特征在于其中所述的连接器是设置 于人体表面心电图 R 波的最高（+1. 4)等电位区与最低 (-1. 0)等电位区之间 的零电位线附近的区域。
4. 根据权利要求 2所述的物品， 其特征在于另有一导线连接所述的连 接器与所述电极， 此导线在 0. 3等电位线和 0等电位线之间或 0等电位线 和- 0. 3等电位线之间的区域有绝缘层披覆， 在其他区域棵露以兼作电极使 用。
5. 根据权利要求 1所述的物品， 其特征在于其中所述的两个连接器与 所述控制盒连接时是位于不同的平面上， 以避免同时被汗水或雨水浸湿。
6. 根据权利要求 1所述的物品， 其特征在于其中所述的两个电极分别 设置在人体表面心电图 R波的等电位线图中的零等电位线的相异的两侧。
7. 根据权利要求 1所述的物品， 其特征在于其中所述的电极至少有一 个设置于人体表面心电图 R 波的最高（+1. 4)等电位线或最低 (-1. 0)等电位 线上。
8. 根据权利要求 1所述的物品， 其特征在于另设有一第三个电极， 其 设置于心电图 R波的等位线图中的零等电位线和 +0. 5等电位线之间。
9. 一种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有一 件织品， 其中：
该织品具有两个电极以撷取心电信号， 至少有一所述的电极的内部设 有一具有弹性的容器， 该容器上设有一孔道供气体或液体进出， 且可产生 负压， 让气体或液体进入容器， 或将电极吸附于皮肤。
10. —种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有 一件织品， 其中：
该织品具有至少两个电极以撷取心电信号，所述的电极，是综合考量人 体心电图 R波等电位图及皮肤相对移动距离来设置。
11. 一种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有 一件织品， 其中： 该织品具有至少两个电极以撷取心电信号，其中所述的电极至少有一 个电极与织品分离， 电极与织品两者接触面至少有一面为光滑面或电极底 部为弧型， 以减少电极与织品的摩擦， 同时至少有一连接线连接分离的电 极与织品。
12. 根据权利要求 11所述的物品， 其特征在于其中所述的电极至少有 一个为吸盘结构，吸盘结构可由导电纤维组成。
13. 根据权利要求 11所述的物品， 其特征在于其中所述的电极与人体 的接触面由可曲挠的导电布条或导电长纤维组成。：
14. 根据权利要求 11所述的物品， 其特征在于其中所述的连接线为螺 旋状连接线、 半径渐增的螺旋状连接线、 条状连接线、 或织带状连接线。
15. 根据权利要求 11所述的物品， 其特征在于其中分离的所述电极或 所述织品设有一滑道， 以一连接线穿过滑道连结所述电极或所述织品， 所 述连接线的长度较通道长以利于电极滑动。
16. 根据权利要求 15所述的物品， 其特征在于其中所述的通道和所述 连接线为导电材料兼作信号传送之用。
17. 根据权利要求 11所述的物品， 其特征在于其中分离所述电极或所 述织品设有穿孔， 以一连接线穿过此穿孔连结所述电极和所述织品， 以利 于电极滑动。
18. 根据权利要求 17所述的物品， 其特征在于其中所述的穿孔的周围 和所述连接线为导电材料兼作信号传送之用。
19. 根据权利要求 11所述的物品， 其特征在于其中分离所述电极与所 述织品， 其中的一个设置有一滑块， 另一个则设置有一滑台， 所述滑块与 所述滑台之间有空间可相对移动。
20. 根据权利要求 19所述的物品， 其特征在于其中所述的滑块及所述 滑台可为导电材料， 兼作信号传送之用。
21. 根据权利要求 11所述的物品， 其特征在于其中所述的织品设有穿 孔， 分离的所述电极连结一滑块， 所述电极与所述滑块设置于所述织品的 穿孔的两侧。
22. 根据权利要求 21所述的物品， 其特征在于其中所述的穿孔周围和 所述滑块为导电材料， 兼作讯号传送之用。
23. 根据权利要求 11所述的物品， 其特征在于其中分离所述电极与所 述织品之间设有一分离的面料，形成双层分离式结构可以抑制体动干扰， 同 时在分离的所述电极与所述面料， 分离的所述面料与所述织品之间设有一 连接线连接分离的所述电极与所述面料， 还设有一连接线连接分离的所述 电极与所述织品，
24. 根据权利要求 23所述的物品， 其特征在于其中所述的双层分离式 结构可包括权利要求 11， 15， 17, 19, 21及 27 中任两项权利要求所述的结 构， 并且形成所述的双层分离式结构的两个分离式结构可以是祖异或相同。
25. 根据权利要求 1或 11所述的物品， 其特征在于其中所述的电极内 设有一具有弹性的容器， 该容器在受压之后能撑开同时有小孔供液体或气 体出入。
26.根据权利要求 1或 11所述的物品， 其特征在于其中所述的电极内 设有一不易透水或透气的薄层形成的袋子， 该袋子内设有可吸水的弹性材 料把袋子撑开以便容纳液体或气体， 同时该袋子上还设有小孔供液体或气 体出入
27. 根据权利要求 11所述的物品， 其特征在于其中所述的连接线可为 尼龙线、 弹性纱线、 布线、 布条、 织带、 金属线、 塑料线、 塑料条、 导电 线或导电条等， 以具有弹性且光滑的较佳。
28. —种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有 一件织品， 其中：
该织品具有至少两个电极以撷取心电信号，其中所述的电极中，至少一 个电极下设有弹性体.电极与弹性体之间设有光滑材料来减少电极与弹性 体之间的摩擦力，同时电极面积要比弹性体大 0. 2 平方厘米以上，以当电极 因皮肤移动而变形时， 可以同时移动且变形。
29. 根据权利要求 1或 11或 28所述的物品， 其特征在于其中所述的 电极与织品分离，电极上或电极周围的织品上， 设有止滑条或止滑面料来增 加摩擦。
30. 根据权利要求 29所述的物品， 其特征在于其中所述的止滑条或止 滑面料为导电材料。
31. 根据权利要求 1或 11或 28所述的物品， 其特征在于其中的一个 电极内增加有吸水的保水剂。
32. 根据权利要求 1所述的物品， 其特征在于其中所述的两个电极，一 个是在织品上设有一导电材料， 另一个是分离式电极。
33. 一种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有 一件织品， 其中：
该织品具有至少两个电极以撷取心电信号，同时电极本身就是永久磁 性物质， 或电极旁边设置永久磁性物质， 而在身体对应侧的织品设置导磁 物质， 或是永久磁性物质， 使两者其异极相对以使电极受到磁力吸引而紧 靠人体。
34. —种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有 一件织品， 其中：
该织品具有至少两个电极以撷取心电信号，， 同时电极本身就是永久磁 性物质， 或外面设有永久磁性物质， 其他位置的织品上也设置永久磁性物 质， 使两者同极相对以使电极受到磁力排斥而紧靠人体。
35. —种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有 一件织品， 其中：
该织品具有至少两个电极以撷取心电信号，同时电极与织品分离， 电极 本身就是永久磁性物质， 或在外面设有永久磁性物质， 织品上也设置永久 磁性物质， 使两者同极相对以使电极受到磁力排斥而紧靠人体。
36. 一种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有 一件织品， 其中：
该织品具有至少两个电极以撷取心电信号， 同时电极与织品分离， 电 极外面或旁边设置永久磁性物质或导磁物质， 而在电极两侧的织品设置导 磁物质或是永久磁性物质， 使两者异极相对使电极受到磁力吸引而紧靠人 体。
37. 一种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有 一件织品， 其中：
该织品具有至少两个电极以撷取心电信号， 同时在不同位置的电极下 或其旁边， 设有一气嚢或液嚢， 两个气嚢或两个液嚢之间有一连通管连通。
38. 一种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有 一件织品， 其中：
该织品具有至少两个电极以撷取心电信号，所述的电极分为两部分， 同 时在此两部分的下方设有气嚢或液嚢， 两个气嚢或液囊之间有一连通管连 通。
39. 根据权利要求 37 或 38所述的物品， 其特征在于其中两个液嚢并 非完全密封。
40. .一种侦测心跳或电极接触良好与否的物品， 其特征在于其包含有 一件织品， 其中：
该织品具有至少两个电极以撷取心电信号， 同时其中所述的电极为干 电极， 并且在每一个干电极的旁边， 或同一位置的上方设有一电容耦合式 电极； 或不必增加电容耦合式电极， 电阻式电极本身就是电容耦合式电极。
41. 根据权利要求 1或 11或 28所述的物品， 其特征在于所述电极的 内部设有一弹性体，所述弹性体上设有一不易透水的薄层、 半透水的薄层、 以针头刺孔不透水薄层或者弹性体本身具有半透水的功能。
42. 一种侦测心跳或电极接触良好与否的方法， 其特征在于其包含一 处理器， 和至少一个电极， 利用该处理器所撷取的噪声或阻抗， 来侦测电 极是否贴近人体。
43. 根据权利要求 42所述的方法， 其特征在于其中所述的阻抗， 可为 表皮阻抗、 肌肉阻抗或呼吸阻抗。
44. 根据权利要求 43所述的方法， 其特征在于可由人体表皮组织阻抗 的信号， 来辨别是由那个电极与人体接触。
45. 根据权利要求 44所述的方法， 其特征在于每个电极可分别连接电 阻、 电容、 电感或二极管等不同的电子组件， 来辨别是由那个电极与人体 接触。
46. 根据权利要求 42所述的方法， 其特征在于处理器分析电极所收到 的信号受到外界干扰的幅度， 来推估电极与人体接触是否良好。
47. 根据权利要求 42所述的方法， 其特征在于所述处理器输出一弦波 或脉波至所述电极， 再经过所述处理器与人体之间的杂散电容回到所述处 理器， 来推估所述电极与人体接触是否良好。
48. 根据权利要求 42所述的方法， 其特征在于其中一个电极本身有两 条导线连接所述电极和所述处理器， 所述处理器发出弦波或脉波经一导线 到所述电极经另一导线回到所述处理器， 来推估所述电极与人体接触是否 良好。
49. 根据权利要求 42所述的方法， 其特征在于所述处理器的输入端设 有模拟式开关， 经由电阻连接至定电压源， 以测量两个电极之间的直流电 阻， 来侦测电极是否贴近人体。
50. 根据权利要求 42所述的方法， 其特征在于其还设有一以拉力、 压 力、 或人体机能传感器， 以侦测该处是否有运动， 或电极是否紧贴人体。
51. 根据权利要求 42所述的方法， 其特征在于以两片导电布中间夹一 绝缘体形成一电容式压力或拉力传感器， 在外部的压力或拉力下，其电容值 也跟着变化， 用来侦测体动干扰， 同时导电布也可当作所述电极。
52. 一种侦测心跳或电极接触良好与否的方法， 其特征在于其包含一 处理器， 和至少二个电极， 是利用所述处理器所撷取的噪声， 来侦测人体 活动状态。
53. 根据权利要求 52所述的方法， 其特征在于其是由单位时间内噪声 被误判为心跳的次数， 来推估人体活动状态。
54. 根据权利要求 52所述的方法， 其特征在于其是由波峰振幅， 来推 估人体活动状态。
55. 根据权利要求 52所述的方法， 其特征在于其是由信号漂移至饱和 所占时间比例， 来推估人体活动状态。
56. 根据权利要求 52所述的方法， 其特征在于其是由自动增益控制功 能所设定的线性范围， 来推估人体活动状态。
57. 根据权利要求 52所述的方法， 其特征在于其是由单位时间内正常 心跳的个数， 来推估人体活动状态。
58. —种侦测心跳或电极接触良好与否的系统， 其特征在于其包含有 一件织品， 及一处理器； 该织品上设有至少两个电极， 其中一电极与织品 之间是分离式结构 , 电极与织品之间有一连接线连接；
该处理器与上述电极电性连接来产生心电信号， 以利用该心电信号来 侦测人体姿势状态。
59. 根据权利要求 58所述的系统， 其特征在于其中所述的电极， 仅以 一对即可产生不同胸导程的心电信号。
60. 一种侦测心跳或电极接触良好与否的系统， 其特征在于其包含有 一件织品， 及一处理器， 该织品上设有至少三个电极， 其中有两个电极是 位于不同电位处， 该处理器与上述电极电性连接来产生心电信号， 以利用 该心电信号来侦测人体姿势状态。
61. 根据权利要求 60所述的系统， 其特征在于其中有两个电极独立输 入到处理器， 分别以一第三电极为参考点， 由分析心电信号的振幅或波型， 来侦测人体姿势状态。
62. 根据权利要求 60所述的系统， 其特征在于其中有两个电极是相连 接的， 随着人体姿势变化， 而有不同的电极紧贴人体， 处理器由分析心电 信号的振幅或波型， 来侦测人体姿势状态。
63. 根据权利要求 60所述的系统， 其特征在于其中有三个电极不相连 接， 处理器是由其中任两个电极撷取心电信号， 分析其振幅或波型， 来侦 测人体姿势状态。
64. 根据权利要求 60所述的系统， 其中有一个电极与织品之间是分离 式结构。
65. 一种侦测心跳或电极接触良好与否的系统， 其特征在于其包含有 一件织品， 及一控制盒， 其中：
该织品上设有至少两个电极；
该控制盒包含一微控制器， 用以处理电极所得到的信号， 以产生心电 信号， 或侦测电极的导线或电极是否受损。
66. 根据权利要求 65所述的系统， 其特征在于织品上两个电极之间另 设有一条导线连接此两个电极， 此导线串联一按键开关， 由观察控制盒输 出的心电信号是否为接近零的一条水平直线， 来侦测电极的导线或电极是 否受损。
67. 根据权利要求 65所述的系统， 其特征在于织品上两个电极之间另 设有一条导线连接此两个电极， 此导线串联一按键开关， 控制盒输出一讯 号至导线， 再观察其输入信号的频谱， 以测量此电极或电极的导线上所受 到的干扰。
68. 根据权利要求 65所述的系统， 其特征在于微控制器由测量两个电 极阻抗， 即可预估使用者在何种运动状况下仍能读到心电信号。
69. 一种侦测电极接触良好与否的系统, 其特征在于其包含有一件织 品， 及一控制盒， 其中：
该织品上设有至少两个电极；
该控制盒包含测量电极的温度、 电阻或电容的电路， 和一微控制器， 微控制器由侦测两个电极之间的温度或阻抗是否在设定范围内， 来激活不 同设定的电路、 固件或软件， 或启动心电图、 肌电图、 脑电图、 阻抗式呼 吸计、 经皮神经电刺激、 电击电路、 体脂计或汗湿计。
70. 根据权利要求 69所述的系统， 其特征在于微控制器由测量两个电 极之间的阻抗， 来引导使用者， 以改善信号品质、 或提高使用者的舒适感。
71. 根据权利要求 69所述的系统， 其特征在于微控制器由测量两个电 极之间的阻抗， 来推估使用者的运动状态。
72. 根据权利要求 71所述的系统， 其特征在于微控制器测量的两个电 极之间的阻抗， 可为表皮阻抗、 肌肉阻抗或呼吸阻抗。
73. 根据权利要求 69所述的系统， 其特征在于微控制器是依据两电极 之间的阻抗在不同范围内， 而启动不同的电路、 固件或软件。
74. 根据权利要求 69所述的系统， 其特征在于两电极之间的阻抗是以 一资料库储存各种状况下的阻抗值， 作为判断的基准， 以启动不同的电路、 固件或软件。
75. 根据权利要求 69所述的系统， 其特征在于当无法由降低电极阻抗 以获得信号时， 控制盒会输出一特定代码， 而不必输出无法辨识的噪声， 以节省电力消耗。
76. 根据权利要求 69所述的系统， 其特征在于当两电极之间的阻抗不 在设定范围内时， 处理器会告知使用者束紧衣带、 更换衣物、 更换电极位 置或增加导电液体， 或增加导电液体， 使两电极之间的阻抗降低在设定范 围内。
PCT/CN2012/000417 2011-11-25 2012-03-30 一种侦测心跳或电极接触良好与否的物品、方法及系统 WO2013075388A1 (zh)

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Cited By (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2015077321A (ja) * 2013-10-18 2015-04-23 日本電信電話株式会社 生体信号取得電極、生体信号取得装置および方法
WO2015107339A1 (en) * 2014-01-15 2015-07-23 Imperial Innovations Limited Biosensing electrodes
CN105266765A (zh) * 2014-11-10 2016-01-27 北京至感传感器技术研究院有限公司 用于检测乳房生理变化的装置
JP2016016042A (ja) * 2014-07-07 2016-02-01 日本電信電話株式会社 電極
JP2016036642A (ja) * 2014-08-11 2016-03-22 日本電信電話株式会社 電極およびウェアラブル電極
JP2016054890A (ja) * 2014-09-09 2016-04-21 Cyberdyne株式会社 接触型センサ
WO2016125214A1 (ja) * 2015-02-06 2016-08-11 パナソニックＩｐマネジメント株式会社 生体信号取得装置および生体信号取得方法
CN106073739A (zh) * 2016-08-15 2016-11-09 武汉清易云康医疗设备有限公司 集成可穿戴式多生理指标采集设备
CN107249451A (zh) * 2014-10-15 2017-10-13 外分泌腺系统公司 汗液传感装置通信安全性和依从性
CN107567302A (zh) * 2015-02-24 2018-01-09 外分泌腺系统公司 动态汗液传感器管理
CN107669259A (zh) * 2017-09-27 2018-02-09 联想(北京)有限公司 一种心电衣
CN107735013A (zh) * 2015-03-31 2018-02-23 诺基亚技术有限公司 用于测量皮肤电阻的装置和方法
CN111617382A (zh) * 2020-05-20 2020-09-04 四川大学华西医院 一种预防压力性损伤的电刺激装置
EP3785621A1 (en) * 2014-09-23 2021-03-03 RR Sequences Inc. Contactless electrocardiography
US11166644B2 (en) 2015-05-06 2021-11-09 Taiwan Textile Research Institute Module for detecting electrical signals from body skin
TWI886944B (zh) 2024-05-08 2025-06-11 中原大學 單臂式心電訊號測量裝置以及單臂式心電訊號測量方法

Families Citing this family (113)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10002545B2 (en) * 2007-10-10 2018-06-19 Jennifer Robin Hanners System and method for controlling gaming technology, musical instruments and environmental settings via detection of neuromuscular activity
FI123363B (fi) 2011-01-31 2013-03-15 Clothing Plus Holding Oy Tekstiilinen alusta fysikaalisen suureen mittaamiseksi
US9494474B2 (en) * 2013-04-03 2016-11-15 Texavie Technologies Inc. Core-shell nanofiber textiles for strain sensing, and methods of their manufacture
CN103927009B (zh) 2014-04-16 2017-12-05 北京智谷睿拓技术服务有限公司 交互方法和系统
CN103927013B (zh) 2014-04-16 2017-12-22 北京智谷睿拓技术服务有限公司 交互方法和系统
US9575560B2 (en) 2014-06-03 2017-02-21 Google Inc. Radar-based gesture-recognition through a wearable device
US9770185B2 (en) 2014-08-06 2017-09-26 Verily Life Sciences Llc Sharing a single electrode between skin resistance and capacitance measurements
US9811164B2 (en) 2014-08-07 2017-11-07 Google Inc. Radar-based gesture sensing and data transmission
US9588625B2 (en) * 2014-08-15 2017-03-07 Google Inc. Interactive textiles
US10268321B2 (en) 2014-08-15 2019-04-23 Google Llc Interactive textiles within hard objects
US9778749B2 (en) 2014-08-22 2017-10-03 Google Inc. Occluded gesture recognition
US11169988B2 (en) 2014-08-22 2021-11-09 Google Llc Radar recognition-aided search
US9600080B2 (en) 2014-10-02 2017-03-21 Google Inc. Non-line-of-sight radar-based gesture recognition
US11540762B2 (en) 2014-10-30 2023-01-03 West Affum Holdings Dac Wearable cardioverter defibrtillator with improved ECG electrodes
US9833607B2 (en) 2014-10-30 2017-12-05 West Affum Holdings Corp. Wearable cardiac defibrillation system with flexible electrodes
EP3028587B1 (en) 2014-12-03 2020-03-11 Clothing Plus MBU Oy Device for determining effects of aging of a wearable device
EP3233185B1 (en) * 2014-12-18 2019-06-26 Koninklijke Philips N.V. Wearable cardioverter defibrillator (wcd) apparatus and method for improved comfort and longer wear
US11307665B2 (en) * 2018-11-06 2022-04-19 Maximilian Ralph Peter von und zu Liechtenstein Wink gesture based control system
TWI547264B (zh) * 2015-01-12 2016-09-01 李順裕 量測貼片裝置
AU2015379572B2 (en) 2015-01-27 2018-09-27 Apple Inc. A system for determining the quality of sleep
FR3033242A1 (fr) * 2015-03-03 2016-09-09 Soorianarain Baligadoo Dispositif d'auto-enregistrement et d'auto-analyse d'electrocardiogramme permettant d'obtenir un rapport en absence de personnel medical
US10016162B1 (en) 2015-03-23 2018-07-10 Google Llc In-ear health monitoring
US9983747B2 (en) 2015-03-26 2018-05-29 Google Llc Two-layer interactive textiles
JP2016195747A (ja) * 2015-04-06 2016-11-24 セイコーエプソン株式会社 生体情報処理装置、生体情報処理システム、生体情報処理方法及び生体情報処理プログラム
EP3885882A1 (en) 2015-04-30 2021-09-29 Google LLC Rf-based micro-motion tracking for gesture tracking and recognition
WO2016176574A1 (en) 2015-04-30 2016-11-03 Google Inc. Wide-field radar-based gesture recognition
JP6517356B2 (ja) 2015-04-30 2019-05-22 グーグル エルエルシー タイプに依存しないｒｆ信号表現
US10088908B1 (en) 2015-05-27 2018-10-02 Google Llc Gesture detection and interactions
US9693592B2 (en) 2015-05-27 2017-07-04 Google Inc. Attaching electronic components to interactive textiles
RU2732344C2 (ru) * 2015-06-12 2020-09-15 Конинклейке Филипс Н.В. Система, регистратор и способ поверхностной электромиографии
CA2989424A1 (en) * 2015-06-15 2016-12-22 Cvr Global, Inc. Non-invasive method for measuring sound frequencies created by vortices in a carotid artery
US10646142B2 (en) 2015-06-29 2020-05-12 Eccrine Systems, Inc. Smart sweat stimulation and sensing devices
EP3298960B1 (en) * 2015-07-08 2020-08-26 Nippon Telegraph and Telephone Corporation Wearable electrode
EP3287071B1 (en) 2015-07-08 2020-11-25 Nippon Telegraph and Telephone Corporation Biomedical electrode and wearable electrode
JP6453722B2 (ja) * 2015-07-08 2019-01-16 日本電信電話株式会社 生体センサー装置
US10835141B2 (en) 2015-07-08 2020-11-17 Nippon Telegraph And Telephone Corporation Wearable electrode
US10588574B2 (en) * 2015-07-14 2020-03-17 Smart Solutions Technologies, S.L. System and methods for adaptive noise quantification in dynamic biosignal analysis
FR3039979B1 (fr) * 2015-08-11 2017-09-01 Bioserenity Procede de mesure d'un parametre electrophysiologique au moyen d'un capteur electrode capacitive de capacite controlee
US20180271416A1 (en) * 2015-09-25 2018-09-27 Eccrine Systems, Inc. Headgear-mounted sweat sensing devices
US10817065B1 (en) 2015-10-06 2020-10-27 Google Llc Gesture recognition using multiple antenna
TWI552721B (zh) * 2015-10-21 2016-10-11 國立交通大學 生物信號之感應器
WO2017070640A1 (en) 2015-10-23 2017-04-27 Eccrine Systems, Inc. Devices capable of sample concentration for extended sensing of sweat analytes
US20170119310A1 (en) * 2015-10-30 2017-05-04 King's Metal Fiber Technologies Co., Ltd. Physiological detection structure
JP6597790B2 (ja) * 2015-11-17 2019-10-30 株式会社村田製作所 脈波伝播時間計測装置、及び、生体状態推定装置
US10824282B2 (en) 2015-11-30 2020-11-03 Drexel University Fabric touch sensor
JP6746300B2 (ja) 2015-11-30 2020-08-26 株式会社リコー 神経刺激装置、生体磁界計測システム
US10674946B2 (en) 2015-12-18 2020-06-09 Eccrine Systems, Inc. Sweat sensing devices with sensor abrasion protection
US20170209097A1 (en) * 2016-01-21 2017-07-27 King's Metal Fiber Technologies Co., Ltd. Suction-attachment structure
US20170303808A1 (en) * 2016-04-21 2017-10-26 Medical Design Solutions, Inc. Capacitive Electrocardiography (ECG) Systems
US11179103B2 (en) * 2016-04-29 2021-11-23 Sanko Tekstil Isletmeleri San. Ve Tic. A.S. Wearable step counter system
US10492302B2 (en) 2016-05-03 2019-11-26 Google Llc Connecting an electronic component to an interactive textile
US10285456B2 (en) 2016-05-16 2019-05-14 Google Llc Interactive fabric
WO2017200570A1 (en) 2016-05-16 2017-11-23 Google Llc Interactive object with multiple electronics modules
US10278602B2 (en) 2016-06-22 2019-05-07 General Electric Company System and method for rapid ECG acquisition
US11154246B2 (en) 2016-06-24 2021-10-26 Georgia Tech Research Corporation Systems and methods of IV infiltration detection
WO2018017619A1 (en) 2016-07-19 2018-01-25 Eccrine Systems, Inc. Sweat conductivity, volumetric sweat rate and galvanic skin response devices and applications
EP4223217A3 (en) 2016-08-12 2023-12-27 Apple Inc. Vital signs monitoring system
CN206333895U (zh) * 2016-09-26 2017-07-18 深圳市岩尚科技有限公司 一种非一次性干电极
US10736565B2 (en) 2016-10-14 2020-08-11 Eccrine Systems, Inc. Sweat electrolyte loss monitoring devices
US10437314B2 (en) 2016-11-30 2019-10-08 Anhui Huami Information Technology Co., Ltd. Detecting wearing state of wearable devices using body capacitance
US10579150B2 (en) 2016-12-05 2020-03-03 Google Llc Concurrent detection of absolute distance and relative movement for sensing action gestures
GB2557612A (en) * 2016-12-12 2018-06-27 Kokoon Tech Ltd Electroencephalography sensors
US11547355B2 (en) * 2016-12-21 2023-01-10 General Electric Company Capacitive leadwire for physiological patient monitoring
ES2687823B1 (es) * 2017-03-29 2019-07-03 Dkd Tech & Health S L Método para la comprobación del funcionamiento correcto de electrodos en prendas de electroestimulación y dispositivo para llevar a cabo dicho método
CN107049307A (zh) * 2017-05-02 2017-08-18 臧大维 全自动脑电信号读取头盔
CN110612060B (zh) 2017-05-22 2022-09-02 苹果公司 用于生理测量的多元件压电传感器
US11191469B2 (en) * 2017-05-26 2021-12-07 Analog Devices, Inc. Biopotential measurement system and apparatus
EP3415086A3 (en) * 2017-06-15 2019-04-03 Analog Devices, Inc. Sensor module for vital sign monitoring device
CN107432745B (zh) * 2017-06-27 2020-11-24 芯海科技（深圳）股份有限公司 一种人体阻抗测量中判断错误站姿的方法
US11311225B2 (en) * 2017-07-11 2022-04-26 General Electric Company Systems and methods for shielded and adjustable medical monitoring devices
US20200221965A1 (en) * 2017-08-29 2020-07-16 Toyobo Co., Ltd. Living-body contact electrode and garment for measuring living-body information
JP6949638B2 (ja) * 2017-09-15 2021-10-13 オムロンヘルスケア株式会社 脈波測定ユニット、および脈波測定装置
US10499827B2 (en) 2017-09-19 2019-12-10 Honeywell International Inc. System and method for interpretation of signal-to-noise ratios detected in an array of electrodes sensors in terms of physical and cognitive state
DE102017220827A1 (de) * 2017-11-22 2019-05-23 Bayerische Motoren Werke Aktiengesellschaft Kraftfahrzeug
KR102061614B1 (ko) * 2017-12-13 2020-01-02 한국과학기술원 능동형 피부 접촉 센서
EP3586743A1 (en) * 2018-06-29 2020-01-01 Nokia Technologies Oy Method and apparatus for determining information regarding body position
WO2020017013A1 (ja) * 2018-07-19 2020-01-23 Ｐｏｓｈ Ｗｅｌｌｎｅｓｓ Ｌａｂｏｒａｔｏｒｙ株式会社 検出装置、シートベルト、及び運転手監視システム
US11478193B2 (en) 2018-09-11 2022-10-25 Apple Inc. Contact detection for physiological sensor
KR102053546B1 (ko) * 2018-10-04 2019-12-06 순천향대학교 산학협력단 근긴장 완화와 근활성화 정보의 모니터링을 위한 시스템
US20200107779A1 (en) * 2018-10-05 2020-04-09 Chang Ming Yang Sensing system utilizing multifunctional fabric, method, and object
KR101988017B1 (ko) * 2018-12-11 2019-06-11 국방과학연구소 흡기 호흡수 모니터링 장치
JP7137844B2 (ja) * 2019-01-31 2022-09-15 国立研究開発法人産業技術総合研究所 衣類に配置可能な電極体アレイおよび衣類
US20200281496A1 (en) * 2019-03-06 2020-09-10 General Electric Company Sensor assembly for patient monitoring systems
CN109745039A (zh) * 2019-03-11 2019-05-14 浙江荷清柔性电子技术有限公司 心电监测电极组件与心电监测装置
CN109745040A (zh) * 2019-03-11 2019-05-14 浙江荷清柔性电子技术有限公司 用于胎心监测的腹带
WO2020196830A1 (ja) * 2019-03-28 2020-10-01 株式会社Mtg 電気刺激装置
GB201908818D0 (en) * 2019-06-20 2019-08-07 Kymira Ltd Electrode and garment
US11147494B2 (en) 2019-07-22 2021-10-19 Koninklijke Philips N.V. Wearable biopotential patch with method to optimize comfort and accuracy
US20220378375A1 (en) * 2019-11-14 2022-12-01 Asahi Fr R&D Co., Ltd. Bioelectrode, production method and installation method for bioelectrode
CN113229821A (zh) * 2020-01-22 2021-08-10 民扬生医科技股份有限公司 检测心电图信号及姿势变化的衣服、方法及系统
EP3858232A1 (en) * 2020-01-29 2021-08-04 Koninklijke Philips N.V. Sensing system and method for electrophysiological sensing by capacitive coupling with estimation of the electrode to skin coupling
JP7505215B2 (ja) 2020-03-16 2024-06-25 住友ベークライト株式会社 脳波測定用電極および脳波測定装置
JP7585490B2 (ja) 2020-12-25 2024-11-18 シェンツェン・ショックス・カンパニー・リミテッド 筋電信号の収集処理装置及び方法
JP7625193B2 (ja) * 2021-04-09 2025-02-03 井上リボン工業株式会社 生体信号測定用センサ
CN113080987A (zh) * 2021-05-20 2021-07-09 四川大学华西第二医院 一种穿戴式的心电监护背心
CN113397513B (zh) * 2021-07-21 2022-11-18 杭州电子科技大学 一种基于微电磁驱动的便携式血压传感器固定装置
KR20230018080A (ko) * 2021-07-29 2023-02-07 삼성전자주식회사 생체 정보를 측정하는 전자 장치 및 그 동작 방법
CN113508951B (zh) * 2021-08-04 2025-04-25 北京华脑技术发展有限公司 一种脑电安全帽帽衬
CN115957445A (zh) * 2021-08-05 2023-04-14 合源医疗器械(上海)有限公司 脉冲刺激装置、方法及医疗设备
WO2023086554A1 (en) * 2021-11-15 2023-05-19 Neuro20 Technologies Corp. Systems and methods to promote tissue health via electrical stimulation
TWI784852B (zh) * 2021-12-22 2022-11-21 友達光電股份有限公司 應用壓電感測器的感測方法及系統
CN114431871A (zh) * 2021-12-30 2022-05-06 重庆市急救医疗中心(重庆市第四人民医院、重庆市急救医学研究所) 一种穿戴式心电监测装置
CN114732414A (zh) * 2022-02-18 2022-07-12 清华大学深圳国际研究生院 一种用于心电图成像的采集装置
CN115349870B (zh) * 2022-07-04 2024-11-26 首都医科大学宣武医院 一种可穿戴智能除颤监护设备
CN115153580B (zh) * 2022-07-29 2025-05-27 广东粤港澳大湾区国家纳米科技创新研究院 一种用于胎儿心电监测的皮肤阻抗测量方法和系统
US20240041374A1 (en) * 2022-08-02 2024-02-08 Atsens Co.,Ltd. Bio-signal measurement patch device and method of using the same
CN115708688A (zh) * 2022-11-24 2023-02-24 浙江强脑科技有限公司 脑电检测头环
CN115553791B (zh) * 2022-12-07 2023-03-10 深圳市心流科技有限公司 脑电头环及其生产方法以及成型模具
FR3143593A1 (fr) * 2022-12-20 2024-06-21 Aequilliving Inc Limited Procédé de fabrication d’un produit de traitement.
WO2024161641A1 (ja) * 2023-02-03 2024-08-08 合同会社ユニバーサル・ブレイン 生体電気信号計測電極、生体電気信号計測装置及び生体電気信号計測電極の製造方法
CN120167927A (zh) * 2023-12-19 2025-06-20 华为技术有限公司 一种监测方法、系统及相关装置
CN119257576B (zh) * 2024-11-26 2025-06-13 河北军涛科技有限公司 一种具有生理检测功能的穿戴式智能实训装置
CN119757836B (zh) * 2025-03-06 2025-06-17 中北大学 一种负压吸盘式电压信号测量装置

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6080690A (en) 1998-04-29 2000-06-27 Motorola, Inc. Textile fabric with integrated sensing device and clothing fabricated thereof
US6198394B1 (en) 1996-12-05 2001-03-06 Stephen C. Jacobsen System for remote monitoring of personnel
CN201139563Y (zh) * 2006-10-18 2008-10-29 东华大学 一种服装式心电监护装置
US7474910B2 (en) 2005-03-16 2009-01-06 Textronics Inc. Textile-based electrode
CN201394014Y (zh) * 2009-03-06 2010-02-03 李志冰 远程十二导联心电监护衣
US7750790B2 (en) 2006-01-23 2010-07-06 Chang-Ming Yang Fabric-based strain gauge
CN101801456A (zh) * 2007-07-20 2010-08-11 奥瑟Hf公司 具有反馈的修复或矫形装置

Family Cites Families (65)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2983273A (en) * 1958-09-15 1961-05-09 William L Howell Electrode
SU392643A1 (ru) 1971-05-13 1974-01-15 вители И. Ф. Головко Всесоюзный научно исследовательский институт хирургической анпаратуры , инструментов , Московский государственный университет М. В. Ломоносова Электрод для регистрации биоэлектрических
JPS505170A (zh) * 1973-05-15 1975-01-20
JPS5618087Y2 (zh) * 1976-07-08 1981-04-27
JPS55114605U (zh) * 1979-02-06 1980-08-13
JPS55114605A (en) 1979-02-28 1980-09-04 Yokohama Rubber Co Ltd:The All-weather tire
EP0022060B1 (fr) * 1979-06-07 1983-10-19 Bioself International Inc. Calculatrice de poche pour le planning familial
US4669468A (en) 1979-06-15 1987-06-02 American Hospital Supply Corporation Capacitively coupled indifferent electrode
ZA803166B (en) * 1979-06-15 1981-05-27 Ndm Corp Capacitively coupled indifferent electrode
US4469105A (en) * 1981-06-18 1984-09-04 Clinton Meyering Medical electrode apparatus and kit of components therefor
JPH0734801B2 (ja) 1986-12-10 1995-04-19 富士通株式会社 超音波ｃｗドプラ血流計
JPH0534641Y2 (zh) * 1988-11-11 1993-09-02
JPH02139608A (ja) 1988-11-21 1990-05-29 Mitsubishi Electric Corp 定電流回路起動装置
JPH02139608U (zh) * 1988-12-30 1990-11-21
JPH04220235A (ja) * 1990-12-19 1992-08-11 Megumi Hashimoto 生体誘導電極
US5353793A (en) * 1991-11-25 1994-10-11 Oishi-Kogyo Company Sensor apparatus
IT1255065B (it) * 1992-05-22 1995-10-17 Rotolo Giuseppe Dispositivo di posizionamento di elettrodi per elettrocardiografia
JPH088913B2 (ja) * 1992-08-26 1996-01-31 惠 橋本 心電図測定用着身具における電極取付構造
JP3153409B2 (ja) 1994-03-18 2001-04-09 株式会社日立製作所 遠心圧縮機の製作方法
US6265978B1 (en) * 1996-07-14 2001-07-24 Atlas Researches, Ltd. Method and apparatus for monitoring states of consciousness, drowsiness, distress, and performance
US5995861A (en) * 1996-08-16 1999-11-30 Price; Michael A. Precordial overlay for positioning electrocardiograph electrodes
EP1013221A4 (en) * 1997-02-24 2001-05-02 Tanita Seisakusho Kk INSTRUMENT FOR MEASURING THE IMPEDANCE OF A LIVING BODY AND INSTRUMENT FOR MEASURING THE COMPOSITION OF A BODY
KR100396055B1 (ko) * 1997-09-26 2003-08-27 우길선 머리를 이용한 질병 치료 자석
US6065154A (en) * 1998-04-07 2000-05-23 Lifecor, Inc. Support garments for patient-worn energy delivery apparatus
JPH11342120A (ja) * 1998-05-29 1999-12-14 Supika Kk 接触型電極を使用した心拍自律神経の状態測定方法とこれを使用した心拍自律神経の測定装置
US6157041A (en) * 1998-10-13 2000-12-05 Rio Grande Medical Technologies, Inc. Methods and apparatus for tailoring spectroscopic calibration models
CN100420482C (zh) 2000-11-03 2008-09-24 精达制药公司 ω干扰素在制备用于治疗丙型肝炎的药物中的用途
US6571115B2 (en) * 2000-12-26 2003-05-27 Axelgaard Manufacturing Company, Ltd. Compress garment facilitating the use of medical electrodes
FI110915B (fi) * 2001-02-19 2003-04-30 Polar Electro Oy Iholle asetettava sensori
JP2003102695A (ja) * 2001-09-28 2003-04-08 Fukuda Denshi Co Ltd 生体信号収集装置及びその制御方法
GB0230361D0 (en) * 2002-12-27 2003-02-05 Koninkl Philips Electronics Nv Electrode arrangement
US7168117B2 (en) * 2003-02-19 2007-01-30 Dreamwell Ltd. Multi-stranded coil spring
DE10315863B4 (de) * 2003-04-08 2013-03-14 Dräger Medical GmbH Elektrodengürtel
GB0311320D0 (en) * 2003-05-19 2003-06-25 Univ Manchester Knitted transducer devices
EP1659940B1 (en) * 2003-08-22 2014-07-23 Foster-Miller, Inc. Physiological monitoring garment
JP2005110801A (ja) * 2003-10-03 2005-04-28 Aprica Kassai Inc 生体計測センサおよび生体計測方法
FI120181B (fi) * 2003-10-08 2009-07-31 Mega Elektroniikka Oy Anturointi ihon pinnalta saatavien signaalien mittaamiseksi ja anturoinnin valmistusmenetelmä
ATE415124T1 (de) 2003-10-10 2008-12-15 Psi Heartsignals Global Ltd Qt-intervallmessung am elektrokardiogramm
DE102004004699A1 (de) * 2004-01-29 2005-09-01 Sigma-Elektro Gmbh Elektrodenbauteil zur Herzfrequenzmessung, Verfahren zur Befestigung eines Elektrodenbauteils am Körper einer Person
KR100592934B1 (ko) * 2004-05-21 2006-06-23 한국전자통신연구원 착용형 생체신호 검출모듈 및 이를 포함한 측정장치
US7173437B2 (en) * 2004-06-10 2007-02-06 Quantum Applied Science And Research, Inc. Garment incorporating embedded physiological sensors
CA2477615A1 (en) * 2004-07-15 2006-01-15 Quantum Applied Science And Research, Inc. Unobtrusive measurement system for bioelectric signals
JP2006102191A (ja) * 2004-10-06 2006-04-20 Nippon Telegr & Teleph Corp <Ntt> 血圧測定装置
US7996075B2 (en) * 2004-10-20 2011-08-09 Cardionet, Inc. Monitoring physiological activity using partial state space reconstruction
IL165232A0 (en) * 2004-11-16 2005-12-18 Tapuz Medical Technologies T M An ergometry belt
US7154071B2 (en) * 2004-12-07 2006-12-26 Dräger Safety AG & Co. KGaA Device for transmitting an electric signal detected by contact with the skin surface
KR100734986B1 (ko) * 2005-09-23 2007-07-06 한국전자통신연구원 생체신호 측정의복
GB0519836D0 (en) * 2005-09-29 2005-11-09 Smartlife Technology Ltd Contact sensors
US20070078324A1 (en) * 2005-09-30 2007-04-05 Textronics, Inc. Physiological Monitoring Wearable Having Three Electrodes
KR100759948B1 (ko) * 2005-12-08 2007-09-19 한국전자통신연구원 생체신호의 측정을 위한 스마트 의복
FI120482B (fi) * 2006-06-08 2009-11-13 Suunto Oy Anturointijärjestely
US8560044B2 (en) * 2007-05-16 2013-10-15 Medicomp, Inc. Garment accessory with electrocardiogram sensors
US8527028B2 (en) * 2007-05-16 2013-09-03 Medicomp, Inc. Harness with sensors
US8060175B2 (en) * 2007-06-15 2011-11-15 General Electric Company System and apparatus for collecting physiological signals from a plurality of electrodes
KR100863064B1 (ko) 2007-08-03 2008-10-13 한국전자통신연구원 생체 신호 측정용 의복 및 그 제조 방법
WO2009030068A1 (en) * 2007-09-04 2009-03-12 Yang, Tzu-Lin Fabric with separate inductive area
EP2072009A1 (en) * 2007-12-21 2009-06-24 Brian Keith Russell An Electrocardiogram Sensor
JP2009226025A (ja) * 2008-03-24 2009-10-08 Citizen Holdings Co Ltd 生体情報測定装置
FI20085384A0 (fi) * 2008-04-29 2008-04-29 Polar Electro Oy Suoritemittarin lisälaite
TW201023826A (en) * 2008-12-24 2010-07-01 Micro Star Int Co Ltd Anti-interference wearable physiological sensing device
US8776264B2 (en) * 2009-04-03 2014-07-15 Ware Llc Garments for providing access for sensors to contact skin
JP3153409U (ja) * 2009-06-23 2009-09-03 財団法人大阪バイオサイエンス研究所 ドライ式生体信号検出用電極
JP5434356B2 (ja) * 2009-08-17 2014-03-05 日本電気株式会社 生体用電極
WO2011137566A1 (zh) * 2010-05-07 2011-11-10 Yang Changming 利用布料电容传感器来产生生理信号的方法及系统
KR101747858B1 (ko) * 2011-01-03 2017-06-16 삼성전자주식회사 생체용 전극 및 이를 포함하는 생체 신호 측정 장치

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6198394B1 (en) 1996-12-05 2001-03-06 Stephen C. Jacobsen System for remote monitoring of personnel
US6080690A (en) 1998-04-29 2000-06-27 Motorola, Inc. Textile fabric with integrated sensing device and clothing fabricated thereof
US7474910B2 (en) 2005-03-16 2009-01-06 Textronics Inc. Textile-based electrode
US7750790B2 (en) 2006-01-23 2010-07-06 Chang-Ming Yang Fabric-based strain gauge
CN201139563Y (zh) * 2006-10-18 2008-10-29 东华大学 一种服装式心电监护装置
CN101801456A (zh) * 2007-07-20 2010-08-11 奥瑟Hf公司 具有反馈的修复或矫形装置
CN201394014Y (zh) * 2009-03-06 2010-02-03 李志冰 远程十二导联心电监护衣

Non-Patent Citations (3)

* Cited by examiner, † Cited by third party
Title
"Fabric-Based Active Electrode Design and Fabrication for Health Monitoring Clothing", IEEE TRANSACTIONS ON INFORMATION TECHNOLOGY IN BIOMEDICINE, vol. 13, no. 2, 2009
See also references of EP2783725A4
WT MILLER; DB GESELOWITZ: "Simulation studies of the electrocardiogram. 1. the normal heart", CIRC. RES., 1978, pages 43

Cited By (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2015077321A (ja) * 2013-10-18 2015-04-23 日本電信電話株式会社 生体信号取得電極、生体信号取得装置および方法
WO2015107339A1 (en) * 2014-01-15 2015-07-23 Imperial Innovations Limited Biosensing electrodes
JP2016016042A (ja) * 2014-07-07 2016-02-01 日本電信電話株式会社 電極
JP2016036642A (ja) * 2014-08-11 2016-03-22 日本電信電話株式会社 電極およびウェアラブル電極
JP2016054890A (ja) * 2014-09-09 2016-04-21 Cyberdyne株式会社 接触型センサ
EP3785621A1 (en) * 2014-09-23 2021-03-03 RR Sequences Inc. Contactless electrocardiography
CN107249451A (zh) * 2014-10-15 2017-10-13 外分泌腺系统公司 汗液传感装置通信安全性和依从性
CN105266765A (zh) * 2014-11-10 2016-01-27 北京至感传感器技术研究院有限公司 用于检测乳房生理变化的装置
JPWO2016125214A1 (ja) * 2015-02-06 2017-11-09 パナソニックＩｐマネジメント株式会社 生体信号取得装置および生体信号取得方法
WO2016125214A1 (ja) * 2015-02-06 2016-08-11 パナソニックＩｐマネジメント株式会社 生体信号取得装置および生体信号取得方法
US10016144B2 (en) 2015-02-06 2018-07-10 Panasonic Intellectual Property Management Co., Ltd. Biological signal acquisition device and method for acquiring biological signal
CN107567302A (zh) * 2015-02-24 2018-01-09 外分泌腺系统公司 动态汗液传感器管理
CN107735013A (zh) * 2015-03-31 2018-02-23 诺基亚技术有限公司 用于测量皮肤电阻的装置和方法
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US11166644B2 (en) 2015-05-06 2021-11-09 Taiwan Textile Research Institute Module for detecting electrical signals from body skin
CN106073739A (zh) * 2016-08-15 2016-11-09 武汉清易云康医疗设备有限公司 集成可穿戴式多生理指标采集设备
CN107669259A (zh) * 2017-09-27 2018-02-09 联想(北京)有限公司 一种心电衣
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