EP3145400A2 - Électrocardiographe - Google Patents

Électrocardiographe

Info

Publication number
EP3145400A2
EP3145400A2 EP15735833.4A EP15735833A EP3145400A2 EP 3145400 A2 EP3145400 A2 EP 3145400A2 EP 15735833 A EP15735833 A EP 15735833A EP 3145400 A2 EP3145400 A2 EP 3145400A2
Authority
EP
European Patent Office
Prior art keywords
ecg device
frequency
converter
ecg
input
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Withdrawn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
EP15735833.4A
Other languages
German (de)
English (en)
Inventor
Thomas Hassler
Maximilian Moser
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.)
Human Research Institut fur Gesundheitstechnologie und Praventionsforschung GmbH
Joysys GmbH
Original Assignee
Human Research Institut fur Gesundheitstechnologie und Praventionsforschung GmbH
Joysys GmbH
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 Human Research Institut fur Gesundheitstechnologie und Praventionsforschung GmbH, Joysys GmbH filed Critical Human Research Institut fur Gesundheitstechnologie und Praventionsforschung GmbH
Publication of EP3145400A2 publication Critical patent/EP3145400A2/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Withdrawn legal-status Critical Current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
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. 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
    • 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
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/333—Recording apparatus specially adapted therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0209—Special features of electrodes classified in A61B5/24, A61B5/25, A61B5/283, A61B5/291, A61B5/296, A61B5/053
    • A61B2562/0217—Electrolyte containing
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S128/00—Surgery
    • Y10S128/901—Suppression of noise in electric signal

Definitions

  • the invention relates to an ECG device according to the preamble of claim 1.
  • ECGs therefore an electrocardiogram, to monitor or monitor.
  • the thus determined curves of the heart activity are usually assessed only visually by a physician.
  • the object of the invention is therefore to provide an ECG device of the type mentioned, with which the mentioned disadvantages can be avoided, with which the medical history of a doctor can be improved, and with which unnecessary therapies of a subject can be avoided.
  • Needs of a subject or patient are matched. As a result, misjudgements can be avoided, as these are due to poor
  • Measurement results were made. As a result, unnecessary therapies of a subject can be avoided. This allows easy and accurate additional information from a recorded ECG signal can be determined. Thereby can detailed data are collected, which allow further analysis, for example in the frequency domain or another image area. The data thus determined can be stored.
  • the invention further relates to a method according to the preamble of
  • the object of the invention is therefore to provide a method of the type mentioned above, with which the mentioned disadvantages can be avoided, with which the medical history of a doctor can be improved, and with which unnecessary therapies of a subject can be avoided.
  • Fig. 1 is a block diagram of a preferred embodiment of a
  • Fig. 2 shows a time course of the heart rate.
  • ECG device 1 shows a preferred embodiment of an ECG device 1 with at least one input 2 for an electrical and / or magmetic ECG signal, the input 2 being connected to a low-pass filter 3 having a cut-off frequency of at least 1 kHz, in particular at least 3 kHz , and wherein an output of the
  • Low pass filter 3 is connected to an input of an A / D converter 4 with a sampling rate of at least twice the cutoff frequency of the low-pass filter.
  • Needs of a subject or patient are matched. As a result, misjudgements can be avoided, as these are due to poor
  • Measurement results were made. As a result, unnecessary therapies of a subject can be avoided. This allows easy and accurate additional information from a recorded ECG signal can be determined. As a result, detailed data can be collected, which allows further analysis, for example in the frequency domain or another image area. The data thus determined can be stored.
  • the ECG device 1 has at least one input 2, which is preferably designed as an electrical input.
  • the input 2 is preferably provided and adapted for connecting or connecting a cable connected to at least one electrode 14 for attachment to a body of a living being.
  • a predeterminable number of inputs 2 is provided, in particular it is provided that the ECG device 1 has one, two, three, six, nine or twelve inputs 2.
  • FIG. 1 only one input 2 is shown, which is connected to six electrodes 14 via connection cables 15, which are only shown stylized. Behind the input 2, a multiplexer may be arranged.
  • an input amplifier 12 is arranged behind the input 2, which is preferred as
  • Differential amplifier is formed. It is preferably provided that the
  • Input amplifier 12 has an electrically stabilized mass. Preferably, a fully symmetrical design of the input amplifier 12 is provided.
  • Input amplifier 12 has a high input sensitivity, combined with a high bandwidth and a high noise margin. Furthermore, it is preferably provided that the relevant differential amplifier has no low-pass characteristic but a linear frequency response or a gentle
  • the relevant differential amplifier can thereby provide a High-pass characteristic.
  • the low-capacitive connection cable 15 form.
  • Connection cables 15 are connected, which are each connected to an electrode 14, and that at least connecting cable 15 for connection to the discharge points each have identical lengths.
  • connection cables 15 intended to be connected to certain derivation points. These connection cables 15 are preferably the same length. If one of the connection cable 15 serves as a reference potential or as a ground conductor, this special connection cable 15 can be made shorter than the other connection cable 15.
  • the connecting cables 15 each have an identical characteristic impedance, whereby a different signal dispersion or phase error can be prevented in the case of cables of various design.
  • the characteristic impedance is preferably 50 ⁇ or 75 ⁇ .
  • Connecting cable 15 are shielded formed to electromagnetic
  • the electrodes 14 each have a skin contact surface which has an electrolyte.
  • the electrolyte is preferably embedded in a contact agent, such as a gel.
  • the skin contact surface should have a low contact resistance guarantee. It is preferably provided that the skin contact surface comprises an electrolyte and / or an electrode surface and / or an electrode material, which electrolyte or which electrode surface or which
  • Electrode material for transmitting signals having a frequency of more than 1kHz, in particular more than 4kHz, preferably up to 20 kHz, is formed. Therefore, that the electrolyte allows a good signal transmission with low attenuation and the best possible linear frequency response even in higher-frequency ranges. This positively supports signal acquisition. Thereby can
  • High-frequency signal components are recorded, which are then processed by the A / D converter 4 and further analyzed.
  • the electrolyte should not have a pronounced low-pass characteristic.
  • the formation of the electrolyte has proven to be particularly advantageous lithium.
  • the skin contact area comprises lithium as the essential electrolyte, wherein further electrolytes may be part of the skin contact area.
  • the formation of the electrode surface in or as crosslinked nanostructures has proved to be particularly advantageous.
  • the electrodes are designed as capacitive electrodes.
  • Capacitive electrodes benefit in particular from the possibility of the subject specific digital filtering, whereby the otherwise occurring in capacitive electrodes high-frequency radiation and other interference can be specifically compensated. Digital filtering allows these errors to be selectively removed in phase and with high transconductance.
  • the input 2 is, preferably indirectly via the input amplifier 12, connected to a low-pass filter 3.
  • the low-pass filter 3 is further, at least indirectly connected to an A / D converter 4, therefore an analog-to-digital converter.
  • a repeater 13 is arranged.
  • the ECG device 1 has at least one antenna, which is preferably formed according to a connecting cable 15 with an electrode 1, and that the antenna is connected in circuit technology with an antenna input of the ECG device 1.
  • Noise influences from the ECG signal are excluded. It may also be preferred to provide the antenna with an input of a
  • Differential amplifier trained input amplifier 12 to connect.
  • a / D converter 4 a high sampling rate or
  • Sampling frequency which may also be referred to as sampling frequency or sampling rate.
  • Conventional or commercially available ECG devices operate with sampling frequencies of a maximum of 256 Hz. This has been shown to lead to aliasing problems when using such devices in a 50 Hz mains frequency environment.
  • such commercially available devices have a low-pass filter with a cut-off frequency of typically 40 Hz at the input, which makes it systemically impossible for such devices to detect the R-wave time in useful accuracy. It has been found that the ECG contains far more information about the condition of the human or animal body than previously thought or evaluated so far. However, these information present in the original ECG signal is lost in the ECG devices used today in the course of sampling or A / D conversion due to the low sampling frequencies and / or resolution.
  • Heart rate variability values determined with conventional ECG devices with a current maximum sampling frequency of 256 Hz, are therefore strongly determined by the respective sampling errors, phase errors and aliasing effects (50 Hz represents almost a multiple of 256 Hz) Fluctuations in the heart rate adds another error.
  • This error always acts as an apparent increase in heart rate variability and falsifies the measurement results, thus contributing to the measured heart rate variability low sampling rates, as in the prior art, systematically distorted larger.
  • the measurement errors are therefore greater than the differences in the time duration between two heartbeats, which temporal duration can be determined, for example, as a time period between two successive R-waves. This will be at the
  • the R wave is an impulse which is very high frequency
  • a low sampling error and a low phase error can be achieved.
  • the R-waves can be detected very accurately in time, and consequently also the distances between the successive R-waves, as a result of which a meaningful value for the anamnesis can be obtained
  • Heart rate variability can be determined. Due to the high resolution, the digitization noise or the phase noise can be kept very low. The phase noise, as well as the noise due to the sampling errors, has the effect of systematically increasing measured values of heart rate variability.
  • the A / D converter 4 samples the low-pass-filtered ECG signal at a sampling rate of 3 kHz or 6 kHz.
  • the sampling rate of the A / D converter 4 is an integer multiple of a network frequency of an electrical energy supply network. It has been shown that, for example via the measuring electrodes on the skin of the subject, to interference from
  • Interference signals with the mains frequency of at least one electrical network comes.
  • the relevant, interspersed interference fields can thereby originate from the electrical network to which the relevant ECG device 1 in the case of mains-powered operation connected. It has been found that even in the case of battery-powered devices, disturbances in the range of the mains frequency of electrical conductors in the subject's environment can be detected. This can lead to beats in unfavorable choice of the sampling rate of the A / D converter 4. By sampling at an integer multiple of the mains frequency, which is 50 Hz in Europe and 60 Hz in the USA, such a disturbance can be avoided.
  • the network frequency of 16.7 Hz used in the railway industry and the 400 Hz usual in many on-board networks of aircraft can also be relevant in this connection, and make a corresponding adaptation of the sampling rate advantageous.
  • a preferred embodiment of an ECG device 1 for Europe provides a sampling rate of 8 kHz, which corresponds to an integer multiple of 50 Hz.
  • the sampling rate is an integer multiple of substantially 3 kHz, which is possible with a device both a particularly low-noise operation on a 50 Hz network and a 60 Hz network.
  • the ECG device 1 a can preferably be provided that the ECG device 1 a
  • Frequency analysis unit is at least indirectly connected to the A / D converter 4, for tracking the sampling rate of the A / D converter 4 in response to a frequency of a detected alternating field.
  • the sampling rate of the A / D converter 4 a is an integral multiple of at least one frequency determined by the frequency analysis unit of the detected alternating field. It is therefore provided that with an alternating field detector of the ECG device 1 at least one
  • Alternating field is determined, and that the sampling rate of the kl D-converter 4 is set to an integer multiple of the frequency of the detected alternating field. As a result, it can be effectively achieved already during the signal recording that the recorded ECG signal has only small interference signal components or artifacts.
  • the sampling rate of the kl D-converter 4 is set to a frequency which is an integer multiple of the frequencies of all detected alternating fields. Since this is only conditionally possible with a larger number of detected alternating fields, it is further particularly preferred, in this regard, only the strongest two detected alternating fields, with respect to the further preferably detected field strength, to
  • the prevailing mains frequency is measured, and the sampling rate is tracked accordingly, although the electrical grids in the industrialized nations are usually very stable and the grid frequency hardly fluctuates around the specified values, but above all In emerging countries, there are some significant fluctuations in the grid frequency, which can be compensated for. This allows very accurate measurements even in areas with less stable electrical networks
  • the low-pass filter 3 has a cut-off frequency which corresponds at most to half the sampling frequency of the kl D-converter 4.
  • the low-pass filter therefore preferably has a cutoff frequency of not less than 1 kHz, in particular 2.9 kHz, preferably not less than 4 kHz.
  • the cutoff frequency is assumed to be the -3dB limit of the signal.
  • the low-pass filter 3 has a flat filter characteristic.
  • the low-pass filter 3 is designed as a filter of the first order. Filters with a flat characteristic in the attenuation range generally have lower phase rotations than steep-edged filters.
  • Data storage 5 is connected to preserve the determined high-resolution data undistorted for later analysis.
  • a signal path between the A / D converter 4 and the data memory 5 is formed filter-free. As a result, the raw data can be preserved, making them available for later analysis.
  • the relevant signal path between the A / D converter 4 and the data memory 5 is as linear as possible
  • a data reduction unit 10 is arranged for information loss-free data reduction. Such methods are in the digital
  • the output of the A / D converter 4 is connected to a digital filter arrangement 6. It is provided that - if also a storage of digital ECG signals is provided - the
  • Filter assembly 6 is arranged parallel to the data memory 5.
  • the digital filter arrangement 6 preferably comprises a predefinable plurality of differently configured filters 7, 8, 9, wherein one of the filters 7, 8, 9
  • the ECG device 1 can be selected and switched into the signal path between A / D converter 4 and data memory 5.
  • the ECG device 1 at least one input device, not shown.
  • the ECG device 1 is designed as a mobile device, and has an electrical energy storage means 11 for supplying power to the ECG device 1.
  • the corresponding energy storage means 11, which is preferably designed as a battery, is registered in the block diagram, wherein the
  • the filter assembly 6 is connected according to the preferred embodiment with an evaluation unit 16, which may also include a display unit, as well as a data interface. It can also be provided that the evaluation unit 16 is connected directly to the output of the A / D converter 4.
  • the evaluation unit 16 has a transformation unit for transferring the ECG data from a time range to a time domain
  • the transformation unit is preferably designed to perform an FFT and / or a wavelet transformation and / or a Gabor transformation. Particularly preferred is a Wigner-Ville transformation is provided.
  • the image area is a frequency range when the transformation unit for performing an FFT is formed.
  • At least one electrical signal on the subject is picked up by means of at least one electrode 14, the recorded signal is filtered with a low-pass filter 3 with a cutoff frequency of more than 1 kHz, preferably 3 kHz Subsequently, the now-filtered analog signal will be analog-to-digital converted at a sampling rate of at least twice the cut-off frequency of the low-pass filter in the A / D converter 4.
  • the preferably digitized signal is unfiltered in one
  • a digital filter 7, 8, 9 is selected from a predefinable plurality of digital filters 7, 8, 9, and
  • the digitized signal is fed to an evaluation unit 16.
  • the digitized signal in the transformation unit of a Time domain in an image area, in particular a frequency range, transferred, with further evaluation methods can be provided. Furthermore, one is
  • a good time resolution can also be achieved by means of FFT, in that the data determined in this way are subsequently combined. It is preferably provided that the window function is further shifted in each case between two consecutive measurements by a time which is between 0.1 and 0.9 times the window length, with a value of 0.2 times the window length being particularly preferred.
  • values of heart rate variability are determined from the digitized signal. Due to the high sampling rate and / or the high resolution of the A / D converter 4 meaningful values of the
  • Heart rate variability are determined.
  • FIG. 2 shows a temporal progression 17 of the heart rate RR illustrated by way of example.
  • the time t is plotted on the abscissa axis, and the heart rate RR on the ordinate axis.
  • the zero point position on the ordinate axis is freely selectable, and can be predefined as a statistically known mean value of a typical heart rate RR, relative to which the heart rate RR measured in the test subject is entered.
  • the individual points represent the respective ones
  • the temporal progression 17 of the heart rate RR with respect to frequency and / or amplitude, wherein different methods in the time domain as well as in an image area can be provided. It proves to be a hindrance for the analysis of the relevant data by FFT that the distances of the values on the abscissa axis are not constant. This can advantageously be circumvented by assigning discrete and equal distances to the individual heartbeats. Instead of time as a basis, the sequence of individual heart beats is used as the basis. This creates a system with equal intervals between the individual values. For example, not every 10 ms appears to have a value, but just two consecutive heartbeats each.
  • the actual intervals between two successive heartbeats form the values (ordinate axis), which are each assigned at constant intervals to the respective discrete event "heartbeat” or "between two heartbeats" (abscissa axis) ,
  • the system in question is normalized, as it were, to the heartbeat, as the body's own time base.
  • Such an analysis provides results from a "point of view" of the body whose time base, unlike an external clock, does not always have the same rhythm.
  • the problem of the irregular time intervals of the successive values of the heart rate can also be solved by sampling these values even at a high sampling rate, which can also be referred to as oversampling, and subsequently using these data to make pseudo measurements close in time actual measured values are determined, which have constant time intervals to each other.
  • a value for the occurring heart rate variability is determined, which is determined as a distance between two successive inflection points or as a peak-to-peak value of the time course 17.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • Physics & Mathematics (AREA)
  • General Health & Medical Sciences (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Cardiology (AREA)
  • Signal Processing (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Artificial Intelligence (AREA)
  • Psychiatry (AREA)
  • Physiology (AREA)
  • Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
  • Analogue/Digital Conversion (AREA)

Abstract

Électrocardiographe (1) comprenant au moins une entrée (2) destinée à un signal ECG électrique, l'entrée (2) étant reliée à un filtre passe-bas (3) d'une fréquence limite d'au moins 1 kHz, et une sortie du filtre passe-bas (3) étant reliée à une entrée d'un convertisseur A/N (4) ayant une fréquence d'échantillonnage correspondant au moins au double de la fréquence limite du filtre passe-bas.
EP15735833.4A 2014-05-23 2015-05-22 Électrocardiographe Withdrawn EP3145400A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
ATA397/2014A AT515873B1 (de) 2014-05-23 2014-05-23 EKG-Gerät
PCT/AT2015/000080 WO2015176088A2 (fr) 2014-05-23 2015-05-22 Électrocardiographe

Publications (1)

Publication Number Publication Date
EP3145400A2 true EP3145400A2 (fr) 2017-03-29

Family

ID=53539419

Family Applications (1)

Application Number Title Priority Date Filing Date
EP15735833.4A Withdrawn EP3145400A2 (fr) 2014-05-23 2015-05-22 Électrocardiographe

Country Status (3)

Country Link
EP (1) EP3145400A2 (fr)
AT (1) AT515873B1 (fr)
WO (1) WO2015176088A2 (fr)

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AT520026B1 (de) * 2017-05-22 2021-06-15 Human Res Institut Fuer Gesundheitstechnologie Und Praeventionsforschung Gmbh Verfahren zur Ermittlung wenigstens eines Kreislaufparameters eines Probanden
CN110742581B (zh) * 2019-10-08 2020-11-06 北京邮电大学 Bcg信号的处理方法及装置

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US20010045901A1 (en) * 2000-02-07 2001-11-29 Marc Auerbach Optimized sampling rate

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Also Published As

Publication number Publication date
AT515873A1 (de) 2015-12-15
AT515873B1 (de) 2017-11-15
WO2015176088A2 (fr) 2015-11-26
WO2015176088A3 (fr) 2016-01-07

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