EP1608265A1 - Appareil de traitement d'un signal d'electrocardiogramme - Google Patents

Appareil de traitement d'un signal d'electrocardiogramme

Info

Publication number
EP1608265A1
EP1608265A1 EP04721576A EP04721576A EP1608265A1 EP 1608265 A1 EP1608265 A1 EP 1608265A1 EP 04721576 A EP04721576 A EP 04721576A EP 04721576 A EP04721576 A EP 04721576A EP 1608265 A1 EP1608265 A1 EP 1608265A1
Authority
EP
European Patent Office
Prior art keywords
signal
ecg
signal component
component
processor
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP04721576A
Other languages
German (de)
English (en)
Inventor
Malcolm Ellis
Rostislav Vychodil
Jiri Pumprla
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Advanced Medical Diagnostics Group Ltd
Original Assignee
Advanced Medical Diagnostics Group Ltd
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 Advanced Medical Diagnostics Group Ltd filed Critical Advanced Medical Diagnostics Group Ltd
Publication of EP1608265A1 publication Critical patent/EP1608265A1/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/30—Input circuits therefor
    • A61B5/307—Input circuits therefor specially adapted for particular uses
    • A61B5/308—Input circuits 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
    • A61B5/30—Input circuits therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/346—Analysis of electrocardiograms
    • A61B5/349—Detecting specific parameters of the electrocardiograph cycle
    • A61B5/352—Detecting R peaks, e.g. for synchronising diagnostic apparatus; Estimating R-R interval
    • 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
    • A61B5/7235—Details of waveform analysis
    • A61B5/7239—Details of waveform analysis using differentiation including higher order derivatives

Definitions

  • apparatus for processing an ECG signal comprising: " a transmitter having an input for receiving the signal and a processor which separates the signal into first and second signal components, manipulates the first signal component to determine the temporal spacing between consecutive R-peaks in the.QRS complex of the signal, and in which the second signal component consists of the ECG signal; and a receiver; in which the transmitter transmits both the manipulated first signal component and the second signal component to the receiver.
  • the difference is calculated between the maximum amplitude and the minimum amplitude and the result compared with a predetermined amplitude value.
  • the temporal occurrence of the maximum (T max ) is measured relative to a predetermined temporal reference point.
  • a temporal difference is also calculated between the time of occurrence of the turning point (T down ) and the maximum (T max ) and the result is compared to a predetermined time value. If both the amplitude difference and the temporal difference are greater than or equal to the predetermined amplitude value and predetermined time value respectively the temporal occurrence of the turning point is identified as that of a potential R peak.
  • the processor comprises an amplifier which amplifies the ECG signal prior to separation into first and second signal components. This strengthens the signal before further processing.
  • a differential amplifier may be used.
  • the processor further comprises first and second signal filters which separate the electrocardiograph signal into the first and second signal components.
  • the output from the first and/or second high-pass filter is fed into a low- pass filter.
  • Low- pass filters eliminate noise and radio frequency signals which may be greater than the ECG signal spectrum.
  • the low-pass filter includes an operational amplifier. Use of filters which include operational amplifiers suppress noise and radio frequency signals present in the first and/or second signal components.
  • the processor includes a micro-controller which receives the first and second signal components and converts at least the first signal component to a digital signal prior to manipulation to determine the R-R time intervals.
  • the first and second signal components are fed into a data stream for transmission to the receiver.
  • the processor includes a micro-controller which receives the first and second signal components, converts the two components from analogue signals to digital signals for transmission to the receiver.
  • the digitised first and second components are fed into a data stream for transmission to the receiver. Signals transmitted digitally are less prone to data loss or interference than analogue signals.
  • the processor samples the first signal component between 500 Hz and 2000 Hz. Most preferably, the processor samples the first signal component at approximately 1000Hz. Conveniently, the processor samples the second signal component at approximately 500 Hz. The second signal component may be sampled between 120 and 500 Hz. In certain embodiments, the second signal component may be sampled between 120 to 150 Hz.
  • the second signal component comprises a signal which is indicative of the measured ECG.
  • the ECG in the second signal component is required only for visual purposes, the entire ECG need not be transmitted. Reducing the amount of data which needs to be transmitted reduces the transmission bandwidth required. Thus, no wideband telemetry channel is required to transmit the measured ECG signal. Narrowband radio channels are less sensitive to radio interference, have lower power consumption and are generally cheaper to operate.
  • the apparatus uses a relatively high sampling rate for the evaluation of the R-R intervals directly in the transmitter. This gives the required accuracy for determining the temporal spacings between the consecutive R-R peaks. Sampling the first signal component at a rate of around 1000 Hz allows the first signal component to be manipulated to create a string of R-R intervals at the required accuracy i.e. of around 1ms.
  • a method for processing an ECG signal comprising the steps of: receiving the signal at an input of a transmitter, the transmitter having a processor which separates the signal into first and second signal components, and manipulates the first signal component to determine the temporal spacing between consecutive R-peaks in the QRS complex of the signal, and in which the second signal component consists of the ECG signal; and transmitting both the manipulated first signal component and. the second signal component to a receiver.
  • R-R interval values By transmitting both the temporal spacings between consecutive R peaks, or R-R interval values, and the original ECG signal a medical practitioner has much more information than previously available using other devices.
  • the R-R interval values can be analysed to check on the health of the heart and many other autonomic functions of the body.
  • the ECG itself can be viewed simply to check that there are no irregularities occurring in the ECG signal. If the data in an ECG trace appears corrupted an operator can simply stop recording.
  • Figure 1 is a schematic illustrating how a transmitter of an ECG monitor, in accordance with the present invention, operates;
  • Figure 2 is a schematic illustrating how a receiver associated with the transmitter in Figure 1 operates;
  • Figure 5 is a schematic illustrating the operation a diversity reception circuit in the receiver of Figures 2 and 4;
  • Figure 6B shows the result of differentiating the signal in Figure 6A.
  • Figure 7 shows a more detailed view of the differentiated signal of Figure 6B.
  • Figure 1 shows a transmitter 10 which can be placed on a subj ects body to record a cardiac signal.
  • the transmitter 10 may be attached to a belt (not shown) and worn around the subjects chest.
  • the transmitter 10 has two electrodes 12 which can be attached to the subjects body to record an electrocardiograph or ECG.
  • the signal is dealt with by a processor (details of which will follow) which includes first and second signal filters 14, 16 and a micro-controller 18.
  • the recorded signal passes to the first and second signal filters 14, 16 which separate the signal into first and second signal components.
  • the first signal component is then manipulated by the processor to evaluate the temporal spacing between consecutive R wave peaks in the QRS complex of the electrocardiograph signal.
  • the first and second signal components are then fed into the micro-controller 18 where the sampling rate of the second component, which effectively consists of the raw ECG, is reduced.
  • the micro-controller 18 feeds the first signal component and reduced sampling rate second signal component into a digitised data stream and on to a radio transmitting module 20 for telemetric transmission from a transmission antenna 22.
  • An ECG signal is recorded by means of a pair of electrodes 12 which can be placed in contact with the skin of a subject.
  • the recorded ECG signal initially passes through apair of low-pass RC filter circuits 100, 102 which consist of a resistor R3 and a capacitor C 1 , and a resistor R4 and a capacitor C2, respectively.
  • resistors R3 and R4 are set to 10 K ohm and capacitors Cl and C2 are set to 100 pF.
  • the outputs from the filter circuits 100, 102 form the inputs to a differential amplifier 104 based on an AD 627 integrated circuit.
  • the low-pass filter circuits 100, 102 filter high frequency signals which result from radio module operation and protect the amplifier inputs against damage by high level impulse over-voltage (electrostatic discharge voltage).
  • the differential amplifier 104 differentiates the signal from background noise to create a relatively "clean" signal.
  • resistors Rl and R2 serve as a DC bias supply which is necessary for proper functioning of the differential amplifier 104.
  • the values of the resistors Rl andR2 (101, 103) are selected to provide a high impedance to the differential amplifier inputs.
  • resistors Rl and R2 are set to 8 M ohm.
  • a DC bias is created by a resistor divider R21, R26 (105) and blocked by a capacitor C14.
  • the gain of the differential amplifier 104 is set by a further resistor R5 (106).
  • the rough ECG signal 107 is divided into two signal components by the first and second signal filters 14, 16 whi ch adj ust the signal spectra and provide sufficient amplification necessary for the channels of an A/D converter which is integrated on the same silicon chip as the micro-controller 18.
  • the first and second signal components are fed into a pair of high-pass filter circuits 108, 111.
  • the first of these high-pass filter circuits 108 includes a resistor R12 and a capacitor C5 the values of which are set such that the circuit 108 differentiates the signal.
  • the second high-pass filter circuit 111 also has a resistor Rl 1 and a capacitor C4 but does not differentiate the signal.
  • resistors R12 and Rl 1 are set to 100 K ohm and 1 M ohm respectively, and capacitors C5 and C4 set to 47 nF and 220 nF respectively.
  • the sampling rate for the first signal component 109 of the ECG signal is around 1000 Hz. This corresponds to a time interval of around 1ms which is necessary to obtained accurate R-R intervals from the ECG signal.
  • the sampling rate for the second component 112 may be set at somewhere between 100 and 500 Hz.
  • micro-controller 18 Further functions performed by the micro-controller 18 include coding of measured R-R interval values (first signal component), ECG signal samples (second signal component) and battery status " into a serial data stream using a dedicated transfer protocol prior to telemetric transfer, charging control of internal lithium-ion rechargeable battery (two-stage CC and CV charging method), diagnostics and service functions.
  • the recorded ECG signal is amplified and digitally processed directly in the transmitter 10 (on the patient's body) and an instantaneous heart rate (R-R intervals) precisely derived.
  • This information together with the raw ECG signal and battery status information are encoded by a transfer protocol into a serial code (suitable for optimal narrowband radio channel exploitation) and transmitted in the UHF band by the radio transmitting module 20 and transmission ariel 22.
  • the transmitted signal is in digital form.
  • An effective way of overcoming this problem is to use two spaced apart antennae 32, 34 which increases the probability of a good signal level being received in one antenna if the signal received in the other antenna suffers interference. Summing signals from the two antennae is likely to encounter the problem of out of phase signals cancelling each other out.
  • the signals received by the two receiver antennae 32, 34 are switched by the analogue switching circuit which determines the best quality signal.
  • the selected signal is processed in a data recovery circuit (sheer) which separates the digital data from analog signal.
  • the transmitted signal is received by one or both of a pair of receiver antennae 32, 34 which form part of a remote receiver 30.
  • the receiver antennae 32, 34 operate under diversity reception to ensure that the best quality signal available is received by the receiver 30.
  • the received signal (s) pass through a pair of receiver module 36, 38 which pass the signal(s) to a receiver microcontroller 44 either directly or via an analogue switch 40 and a data recovery unit 42.
  • Data processed by the micro-controller 44 by a suitable connector 46 to and from a PC.
  • the connector 46 is an RS232-type interface.

Landscapes

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

Abstract

La présente invention a trait à un appareil de traitement d'un signal d'électrocardiogramme comportant un émetteur (10) avec une entrée (12) pour la réception du signal. L'émetteur (10) comporte également un processeur (14, 16, 18) qui sépare le signal en première et deuxième composantes de signal et manipule la première composante de signal en vue de déterminer l'intervalle temporel entre deux crêtes d'onde R consécutives dans le complexe QRS du signal. La deuxième composante de signal est constituée du signal d'électrocardiogramme lui-même. L'appareil comporte en outre un récepteur (non représenté), auquel l'émetteur (10) transmet à la fois la première composante de signal manipulée et la deuxième composante de signal.
EP04721576A 2003-03-28 2004-03-18 Appareil de traitement d'un signal d'electrocardiogramme Withdrawn EP1608265A1 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
GBGB0307211.3A GB0307211D0 (en) 2003-03-28 2003-03-28 Apparatus for processing an ecg signal
GB0307211 2003-03-28
PCT/GB2004/001186 WO2004084721A1 (fr) 2003-03-28 2004-03-18 Appareil de traitement d'un signal d'electrocardiogramme

Publications (1)

Publication Number Publication Date
EP1608265A1 true EP1608265A1 (fr) 2005-12-28

Family

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EP04721576A Withdrawn EP1608265A1 (fr) 2003-03-28 2004-03-18 Appareil de traitement d'un signal d'electrocardiogramme

Country Status (3)

Country Link
EP (1) EP1608265A1 (fr)
GB (1) GB0307211D0 (fr)
WO (1) WO2004084721A1 (fr)

Families Citing this family (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
ES2713975T3 (es) 2013-04-17 2019-05-24 Rudolf C King Sistema y método para facilitar asistencia en situaciones de peligro
WO2016034297A1 (fr) 2014-09-02 2016-03-10 Rudolf King Système et procédé de sécurité de porte et d'habitation
CN114504326B (zh) * 2022-01-17 2023-07-18 电子科技大学 一种心电信号二进制幅度编码方法
WO2023243065A1 (fr) * 2022-06-17 2023-12-21 三菱電機株式会社 Dispositif d'acquisition d'informations biologiques et procédé d'acquisition d'informations biologiques

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Publication number Priority date Publication date Assignee Title
US4223678A (en) * 1978-05-03 1980-09-23 Mieczyslaw Mirowski Arrhythmia recorder for use with an implantable defibrillator
US6070097A (en) * 1998-12-30 2000-05-30 General Electric Company Method for generating a gating signal for cardiac MRI
US6223072B1 (en) * 1999-06-08 2001-04-24 Impulse Dynamics N.V. Apparatus and method for collecting data useful for determining the parameters of an alert window for timing delivery of ETC signals to a heart under varying cardiac conditions
US6236882B1 (en) * 1999-07-14 2001-05-22 Medtronic, Inc. Noise rejection for monitoring ECG's
AU2001250983A1 (en) * 2000-03-29 2001-10-08 Kinderlife Instruments, Inc. Method and apparatus for determining physiological characteristics
US7187965B2 (en) * 2001-05-29 2007-03-06 Bischoff Edward T Cardiac rhythm monitoring device

Non-Patent Citations (1)

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See references of WO2004084721A1 *

Also Published As

Publication number Publication date
GB0307211D0 (en) 2003-04-30
WO2004084721A1 (fr) 2004-10-07

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