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    • 专利摘要:
    In a method for, in particular continuous, determination of at least one cardiac load duration and / or a cardiac recovery period, and preferably a cardiac stress quotient and / or a cardiac recovery quotient, from a heartbeat signal, in particular an electrocardiogram (3) and / or magnetocardiogram and / or impedance cardiogram and / or BalUstokardiogramm and / or seismocardiogram and / or phonocardiogram, it is proposed that the heartbeat signal is recorded on a human or animal subject, wherein subsequently from the heartbeat signal as cardiac stress duration at least one atrial contraction duration and / or a ventricular contraction duration and / or an atrio-ventricular contraction duration is determined and / or as a cardiac recovery an atrial Dllatationsdauer and / or a ventricular Dllatationsdauer and / or an atrio ventricular Dation duration is determined.
    公开号:AT517071A4
    申请号:T570/2015
    申请日:2015-08-28
    公开日:2016-11-15
    发明作者:
    申请人:Human Res Inst Für Gesundheitstechnologie Und Präventionsforschung Gmbh；Joysys Gmbh；
    IPC主号:
    专利说明:

    The invention relates to a method for determining at least one cardiac load duration and / or a cardiac recovery period from a heartbeat signal according to the preamble of patent claim 1.
    It is known to observe or monitor the activities of the heart of a subject by means of a so-called ECG, therefore of an electrocardiogram. The thus determined curves of the heart activity are usually assessed only visually by a physician.
    Although the ECG is the most widely used method for detecting a heartbeat signal, other methods are known or used.
    It has been shown that considerably more information could be obtained from a heartbeat signal of a test person, which may be helpful for the diagnosis of a physician than has hitherto been the case. In particular, the conventional ECG devices have proven to be unsuitable for providing this information. As a result, only a fraction of the information that is possible per se about the condition of the subject is made available to a doctor. Thus, this provides a diagnosis, which is based on a poor history. This makes it difficult or prevent the creation of an accurate diagnosis, which in turn may result in poor treatment or treatment of the subject in question. This has a negative impact on the subject. In addition, wrong or unnecessary treatment is an avoidable burden on the health system.
    Thus, for example, the perfusion of the heart can currently be detected from a heartbeat signal, in particular an ECG signal, only incompletely and only in extreme situations, such as a change in stimulus conduction due to lack of oxygen in the course of a myocardial infarction.
    The detection of the blood circulation by means of ultrasound methods and devices has considerable disadvantages. The corresponding equipment is complex, costly, heavy and voluminous, which stands in the way of mobile use as far as possible. In addition, an ultrasound examination is a higher burden on the heart of a subject than the creation of a heartbeat signal, for example by means of ECG.
    The object of the invention is therefore to provide a method 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.
    This is achieved by the features of claim 1 according to the invention.
    As a result, a better history and diagnosis of a subject can be made. As a result, if appropriate, a therapy can be better tailored to the actual needs of a subject or patient. As a result, misjudgements can be avoided as they were due to poor measurement results. As a result, the condition of a subject can be determined considerably more accurately than was previously the case. As a result, a better tailored to the actual condition of the subject therapy can be developed and carried out, if such appears necessary, and in return, unnecessary therapies of a subject can be avoided. This can easily and accurately determine additional information from a recorded heartbeat signal, such as information or values for: Circulation state, the duration of systole, the duration of diastole, the different stress on the heart during the day and night, the different recovery of the heart Day and night. The corresponding values or information can easily be determined in the course of a 24-hour recording of a heartbeat signal, with no additional burden for the subject, as would be the case with an ultrasound examination, which also can not be done over 24 hours.
    As a result, the blood circulation state can be determined again with each heartbeat. Furthermore, it has been shown that numerous drugs lead to an extension of the ventricular contraction period. This can lead to a metabolic imbalance with a tendency to fibrillation and cardiac arrest. By the subject method, such an extension of the ventricular contraction period can be easily determined.
    By means of the present method, a respective current or situational recovery state of the heart can be determined. In particular, in physically demanding activities, such as these are exposed to firefighters, steel workers, it may lead to acutely dangerous prolongations of the ventricular contraction period, or has been shown that very high individual burden can be detected by extending the ventricular contraction period, even before Serious damage to the subject occurred. Through this knowledge, a person can stop the stress situation in good time before life-threatening conditions develop in the heart. It has been shown, for example, in the increased disaster relief operations of recent years that help people are often no longer able to detect a state of fatigue in time, so it comes again and again to fatigue-related death of firefighters or soldiers in the relief operation, which victims through the Objective procedures can be avoided.
    The invention further relates to an ECG device according to the preamble of claim 30.
    The object of the invention is therefore to provide an ECG device of the aforementioned type, 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.
    This is achieved by the features of claim 30 according to the invention.
    This achieves the advantages set forth above for the method.
    The subclaims relate to further advantageous embodiments of the invention.
    It is hereby expressly referred to the wording of the claims, whereby the claims at this point are incorporated by reference into the description and are considered to be reproduced verbatim.
    The invention will be described in more detail with reference to the accompanying drawings, in which only a preferred embodiment is shown by way of example. Showing:
    1 shows a time course of the heart rate; and
    Fig. 2 is a block diagram of a subject ECG device.
    The subject invention relates to a method for, in particular continuous, determination of at least one cardiac stress period and / or a cardiac recovery, and preferably a cardiac stress quotient and / or a cardiac recovery, from a heartbeat signal, in particular an electrocardiogram and / or magnetocardiogram and / or impedance cardiogram and / or ballistocardiogram and / or seismocardiogram and / or phonocardiogram, wherein the heartbeat signal is recorded on a human or animal subject, wherein subsequently determined from the heartbeat signal as cardiac stress duration at least one atrial contraction duration and / or a ventricular contraction duration and / or an atrio-ventricular contraction duration and / or an atrial dilation duration and / or a ventricular dilation duration and / or an atrio-ventricular dilation duration is determined as the cardiac recovery time.
    As a result, a better history and diagnosis of a subject can be made. As a result, if appropriate, a therapy can be better tailored to the actual needs of a subject or patient. As a result, misjudgements can be avoided as they were due to poor measurement results. As a result, the condition of a subject can be determined considerably more accurately than was previously the case. As a result, a better tailored to the actual condition of the subject therapy can be developed and carried out, if such appears necessary, and in return, unnecessary therapies of a subject can be avoided. This can easily and accurately determine additional information from a recorded heartbeat signal, such as information or values for: Circulation state, the duration of systole, the duration of diastole, the different stress on the heart during the day and night, the different recovery of the heart Day and night. The corresponding values or information can easily be used in the course of a 24-hour recording of a
    Heartbeat signal are determined, with no additional burden for the subject, as would be the case for an ultrasound examination, which also can not be done over 24 hours.
    As a result, the blood circulation state can be determined again with each heartbeat. Furthermore, it has been shown that numerous drugs lead to an extension of the ventricular contraction period. This can lead to a metabolic imbalance with a tendency to fibrillation and cardiac arrest. By the subject method, such an extension of the ventricular contraction period can be easily determined.
    By means of the present method, a respective current or situational recovery state of the heart can be determined. In particular, in physically demanding activities, such as these are exposed to firefighters, steel workers, it may lead to acutely dangerous prolongations of the ventricular contraction period, or has been shown that very high individual burden can be detected by extending the ventricular contraction period, even before Serious damage to the subject occurred. Through this knowledge, a person can stop the stress situation in good time before life-threatening conditions develop in the heart. It has been shown, for example, in the increased disaster relief operations of recent years that help people are often no longer able to detect a state of fatigue in time, so it comes again and again to fatigue-related death of firefighters or soldiers in the relief operation, which victims through the Objective procedures can be avoided.
    It is provided to determine a cardiac output duration and / or a cardiac recovery period from a heartbeat signal.
    The indices used in each case indicate whether the respective wave or tine is a wave or a tine which is assigned to a first heartbeat or to a second heartbeat immediately following it.
    The cardiac load duration is at least one atrial contraction duration and / or one ventricular contraction duration and / or one atrio-ventricular contraction duration. The atrial contraction duration is the loading duration of the atrium. In an ECG signal this corresponds to the interval P1-Q.1. The ventricular contraction duration is the load duration of the ventricles. In an ECG signal, this corresponds to the interval Q1-T1. The atrial-ventricular contraction duration is the loading duration of the atrium or ventricle. In an ECG signal, this essentially corresponds to the interval Ρι ^.
    The cardiac recovery period is an atrial dilation duration and / or a ventricular dilation duration and / or an atrio-ventricular dilation duration. The atrial dilation duration is the recovery time of the atrium or atrial diastole. In an ECG signal, this corresponds to the interval Qr P2. The ventricular dilation duration is the recovery time of the ventricles, or ventricular diastole. In an ECG signal, this corresponds to the interval Ti - Q2. The atrial-ventricular dilatation time is the recovery time of atrium and ventricle, or cardiac diastole. In an ECG signal, this corresponds to the interval Ti -P2.
    The durations concerned were explained above for a quick orientation on the basis of an ECG signal, and the usual designations of the waves and spikes. This will be explained in more detail later. In addition to a heartbeat signal in the form of an ECG signal, the time periods in question can each be determined from other heartbeat signals obtained. In particular, it is provided that the heartbeat signal is a magnetocardiogram or impedance cardiogram or ballistocardiogram or seismocardiogram or phonocardiogram.
    The course of a magnetocardiogram or impedance cardiogram is very similar to the course of an ECG signal.
    Furthermore, the use of capacitive electrodes can be provided.
    A ballistocardiogram, a seismocardiogram or a phonocardiogram are time-delayed or out-of-phase with respect to an ECG signal, although the corresponding intervals can also be determined therefrom. However, since, in contrast to the ECG, the points at which the decrease takes place are not standardized to the same extent, a correspondingly unified and unambiguous nomenclature can not be given, especially since the rashes in a ballistocardiogram, a seismocardiogram or a phonocardiogram are clearly dependent on the location. where each will be recorded. Due to the representational general naming of the individual durations or intervals, it is easily possible for a person skilled in the art or a doctor to identify the respective cardiac load durations and / or cardiac recovery durations with a concretely taken ballistocardiogram, seismocardiogram and / or phonocardiogram. If necessary, an ECG for synchronization is required, therefore, to uniquely identify the respective cardiac events in the ballistocardiogram, the seismocardiogram or the phonocardiogram.
    The respective intervals or durations comprise, at least when the heartbeat signal is formed as an ECG signal, in each case the associated waves essentially entirely. Therefore, if a certain interval has a wave as the beginning and / or end, then this wave is essentially entirely part of the interval in question.
    The indicated intervals are each scheduled to begin at the event indicated by the former letter and terminate at the event indicated by the second letter. Thus, for example, an interval QT is not identical to an interval TQ.
    It is preferably provided that, in addition to the durations already described, quotients of specific durations are also determined.
    It is preferably provided that as the heart stress quotient: a stress quotient atrium as the ratio of the atrial contraction durations to the atrial dilatation duration and / or a stress quotient ventricle as the ratio of the ventricular contraction duration to the ventricular dilation duration and / or a stress quotient total heart as the ratio of the atrio - Ventricular contractile duration to atrial-ventricular dilatation period and / or - Cardiac diastole-related exercise rate atrium as the ratio of atrial contraction duration to atrio-ventricular dilation duration and / or - Ventricle related to cardiac diastole Ventricle as ratio of ventricular contraction duration for the atrio-ventricular dilatation period.
    Furthermore, it is preferably provided that as heart recovery quotient - a recovery quotient atrium as the ratio of the atrial contraction durations to the atrial dilatation duration and / or - a recovery quotient ventricle as the ratio of the ventricular contraction duration to the ventricular dilation duration and / or - a recovery quotient total heart as the ratio of the atrio Ventricular contractile duration to atrial-ventricular dilatation period; and / or a cardiac diastole-related recovery ratio atrium as the ratio of atrial contraction duration to atrio-ventricular dilation duration; and / or ventricle-related recovery ratio ventricle as the ratio of ventricular contraction duration for the atrio-ventricular dilatation period.
    It is provided in particular that the at least one cardiac load duration and / or the at least one cardiac recovery period, and preferably the at least one cardiac stress quotient and / or the at least one cardiac recovery quotient, are output and / or stored.
    Preferably, the relevant cardiac load duration and / or the cardiac recovery period and, if appropriate, the respective cardiac stress quotients and / or cardiac recovery quotients are newly formed on an ongoing basis. This leads to the output of constantly changing values for the individual cardiac load durations or heart recovery periods, which is sometimes undesirable. It is preferably provided, in particular, in addition to the formation and output of the respective current values of the cardiac load and / or the cardiac recovery, and also the at least one cardiac load duration or cardiac recovery duration as median and / or median to a predeterminable number at previous heartbeat intervals determined cardiac load durations and / or to make the cardiac recovery periods and spend accordingly.
    It is particularly preferably provided that the at least one cardiac load duration and / or the at least one cardiac recovery period, and preferably the at least one cardiac stress quotient and / or the at least one cardiac recovery quotient, are output, in particular displayed, essentially parallel to the recording of the heartbeat signal. The relevant at least one value is therefore determined essentially continuously or gradually from the measured heart rate signal and also displayed or output. Particularly in the case of the particularly preferred mobile implementation of the subject method in a device which the test person carries with him on the body, it is provided that the cardiac load duration and / or the cardiac recovery period and / or the cardiac stress quotient and / or the cardiac recovery quotient are stored directly in the mobile device determined and preferably also displayed on this device. In contrast to the known devices for recording a 24-hour ECG can be responded directly by the subject on the determined values, for example, by immediate changes in his current life circumstances. According to a particularly preferred embodiment, it is provided that the display does not take place on the device itself, but on a smartphone of the subject. Due to the widespread use of such smartphones this can be conveniently used for display, which can be dispensed with a separate display in said device.
    It is preferably provided in a further development of the present method that at least one determined cardiac load duration and / or at least one determined cardiac recovery period, and preferably at least one determined cardiac stress quotient and / or at least one determined cardiac recovery quotient, is compared with at least one predeterminable boundary condition, and that when exceeding the at least one limit condition is output by the cardiac load duration or the cardiac recovery period or the cardiac stress quotient or the cardiac stress quotient. Thus, a subject can be warned in time of an impending critical condition in order to relinquish his present activity. In this case, provision is made in particular for a plurality of boundary conditions of different levels to be provided, so that a first signal is output when a first boundary condition is exceeded and / or during a further change of the cardiac load duration and / or the cardiac recovery period, which results in exceeding a second limit Boundary condition leads to a signal that is different from the first signal is output.
    The at least one boundary condition can be taken from a database, for example as a function of age, gender, medical history, environmental parameters and the like. In such a database corresponding boundary conditions based on the experience with other subjects can be stored. In particular, data may be contained in the database, which were obtained from studies with substantially healthy volunteers.
    In addition to the selection of boundary conditions from a database, provision is made in particular for the at least one cardiac loading period and / or cardiac recovery period and / or cardiac stress quotient and / or cardiac recovery quotient to be recorded over a predefinable first period, which is preferably between one day and fourteen days in particular by means of a mobile ECG device 1, that the first period is divided into a predefinable plurality of second time periods, which are preferably between 15 minutes and 2 hours, and that for at least a second period at least the boundary condition from the determined cardiac load duration or Heart recovery or heart stress quotient or recovery rate is formed. Here, the at least one boundary condition of so-called. Historical
    Data of the subject himself or from data of a comparison database determined.
    It is further provided that the at least one boundary condition is not constantly left the same, but is adapted over the course of the day. Preferably, it is therefore provided that the at least one boundary condition is adapted to the respective prevailing time of day by selecting the boundary condition which was determined for the second time period in which the current time of day lies. This can be responded to different load conditions of the subject. If appropriate, a corresponding database or comparison database, which database or comparison database has data of the same or other subjects, may be provided for this purpose.
    The present method will be described below with reference to the recording of a heartbeat signal in the form of an ECG signal 3. In addition to the most widespread and customary form of recording a heartbeat signal by means of an ECG, the subject invention can be modified accordingly, as already explained, also be applied to a differently determined heartbeat signal. The description based on an ECG signal 3 is therefore preferably not restrictive to an ECG signal 3 to understand.
    The recorded heartbeat signal is recorded in the form of an ECG signal in a subject. The subject can be any kind of living being with at least one heart, ie both a human and a corresponding animal.
    In the following, unless expressly stated, the use of the described procedure is also provided for a cardiac recovery period.
    The processing of the ECG signal 3 preferably takes place in accordance with the subject method in a correspondingly designed ECG device 1.
    The ECG signal 3 received by the subject in a manner known per se is transmitted to the input of an analog-to-digital converter 4, which is preferably part of an ECG device 1, and digitized by the analog-to-digital converter 4.
    The pick-up points of the ECG are preferably selected such that the R-wave R, the P-wave P and the T-wave T as positive signals, and the Q-wave Q. and the S-wave S as negative signals to a Reference potential can be spent.
    It is preferably provided in the preferred digital signal processing in the context of the present invention that the analog-to-digital converter has a sampling rate greater than or equal to 6 kHz and a resolution greater than or equal to 12 bits. It is particularly preferred that the analog-to-digital converter has a sampling rate of 8 kHz and a resolution of 16 bits.
    It should be noted that corresponding and commonly used signal conditioning circuits, such as input amplifiers, may be provided. Furthermore, a low-pass filter is provided in front of the analog-to-digital converter 4, to comply with the sampling theorem.
    Within the digital ECG signal 3, successive R-waves R are preferably detected. In this case, it is provided in particular to determine the times of occurrence of the respective R-waves R, preferably the times in each case between the R-waves R.
    Furthermore, at least one time duration between an R-wave R of the successive R-waves R and one of the R-waves R upstream and / or subsequent wave P, T and / or wave Q, S of the ECG signal 3 is determined. For this purpose, the at least one wave P, T and / or Zacke Q, S is also detected. From the at least one determined period of time, at least one cardiac load duration or cardiac recovery period is determined.
    As already mentioned in the previous paragraph, it is an indirect goal to determine the time periods between the teeth Q, S or waves P, T and in each case one R-wave R, in order to process them further. It is therefore particularly preferred to determine the times of occurrence of the spikes Q, S or waves P, T.
    For processing reasons, in the implementation of the subject invention, in particular, the periods of anticipatory waves or spikes are calculated from the continuous signal.
    It is particularly preferred that the time position of the peaks of the Q wave Q, the R wave R and the S wave S be detected. It is preferably provided that the peaks Q, R, S are each also the largest positive and / or negative slope, therefore, the largest slope at rise and / or fall, is determined. Furthermore, it is preferably provided, the temporal positions of the beginning, middle and end of the P-wave, the T-wave and, if detectable, the U-wave. In this case, such a detection is preferably provided for each of the mentioned parameters, even if this is not stated in the following text in each case declined.
    Preferably, a continuous detection of both the R-wave R and the at least one wave P, T and / or wave Q, S within the continuous ECG signal 3 is provided. Furthermore, it is preferably provided to detect all waves P, T and waves Q, S which are typical for an ECG, wherein a selection of individual waves P, T or waves Q, S may also be provided. The ECG signal 3 typically has the P-wave P, the Q-wave Q, the S-wave S and the T-wave T next to the R-wave R, as shown in FIG. In addition, in some subjects between the T-wave T and the P-wave P of the next heartbeat further exists a U-wave and also measurable. If such a U-wave appears, its detection is also provided.
    It is preferably provided that in each case the time intervals or the time periods between the R-wave R and the waves P, T or waves Q, S of a "self-contained" first heartbeat are measured or determined. A heartbeat consists in a conventional manner from the process, which begins in time with the occurrence of the P-wave and ends with the decay of the T-wave. It is therefore intended to determine the durations within a heartbeat. In this case, it may further be preferable to measure the time duration between a wave and / or a tine of a first heartbeat and that of a wave and / or a tine of a second heartbeat following immediately after the first heartbeat.
    Hereinafter, a preferred method for detecting specifically the R-wave R is described, which can be used according to adapted also for the detection of the Q-wave Q and the S wave.
    It is preferably provided that the digital ECG signal 3 is filtered by means of a predefinable FIR filter. FIR stands for Finit Impulse Response in a familiar way. An original, untreated ECG signal 3 generally has a fluctuating baseline, which can be represented as a superposition of a low-frequency disturbance. The appropriate filtering can be used to smooth the baseline. In particular, the time intervals of the individual waves P, T and / or tines Q, S of the ECG signal 3 are relevant in the formation of the subject cardiac load duration or cardiac recovery time. It can therefore be respected during the filtering according to a time or phase true filtering. In this case, a gain of the waves P, T and / or tines Q, S can be implemented in order to simplify their subsequent detection.
    Particularly preferably, it is provided that the FIR filter has filter components which are formed only by the integer values -1, 0 and / or + 1. As a result, a very fast processing can be achieved and / or very low hardware requirements, thereby supporting an implementation of the subject method on a mobile platform.
    It is preferably provided that the subject method is or can be performed on a mobile platform. When implementing the individual algorithms and routines, it is therefore preferable to ensure low processor load and low energy consumption.
    The, preferably filtered, digital ECG signal 3 is subsequently divided into segments of predefinable duration. The individual segments are preferably chosen with a length of 2 seconds to 3 seconds, with a length of 2.5 seconds has proven to be particularly advantageous. In this case, the individual segments preferably begin in each case with the last detected R wave, whereby, of course, the first segment, in the absence of an already detected R wave, begins at a random time with respect to the heart beat. Within each segment, a maximum value of the ECG signal 3 is subsequently determined.
    In the following, it is preferably provided that the median of the values in the respective segments is formed over a predeterminable number of preceding consecutive segments. In particular, the median is formed over three to seven, preferably over five, of such segments in order to mittein variations by breathing. It should be noted that the segments can overlap themselves.
    The samples within a segment are now compared with the median formed from the previous segments, which is preferably divided by a predeterminable value, which value is greater than or equal to one. Only samples which have a value greater than this median are processed further. As a result, a constantly newly adapted limit is formed with the help of which the computational effort can be reduced. The samples which are larger than the divided median are compared with the immediately preceding sample of the same segment. In this case, only samples having an absolute value difference from the preceding sample value greater than a predefinable limit value are further processed as R-wave candidates for detecting the R wave. Preferably, the falling edge of the R-wave R is considered or evaluated. Through the objective selection, a large part of the samples can be eliminated quickly and with little computational and energy expenditure.
    The limit value with which the sampled values are compared is preferably selected to be greater than the noise and / or the jitter of the analog-to-digital converter.
    Subsequently, further samples are eliminated from the group of R-wave candidates. For this purpose, samples which fall within periods in which, for physiological reasons, no R-wave R can occur, are deleted from the set of R-wave candidates. In this case, provision is made in particular for R-wave candidates to be discarded within a predefinable time span, of at most half the expected refractory period of the subject's heart, following a previously detected R wave. The refractory period of a human's heart is about 250 ms. However, when determining the period in question, account must also be taken of the required computing time, which is platform-dependent, so that the length of the period concerned, in addition to the subject's genus, also depends on the existing processing power of the devices used.
    In particular, it has proved to be advantageous in human subjects as practicable to erase R-wave candidates that appear within less than 80 ms of an already detected R-wave R from the set of R-wave candidates ,
    Subsequently, the remaining R-wave candidates are preferably evaluated with at least one predeterminable evaluation criterion.
    Upon satisfaction of the evaluation criterion, an R-wave candidate is output as a detected R wave R and / or stored and / or further processed.
    In addition to the time of occurrence of the relevant R wave R, the amplitude to the following minimum, in the form of the following S wave S, is also detected and stored and / or output together with the time of the R wave.
    It is preferably provided that for the detection of the S-wave S and / or the Q-wave Q, the respective minimum values are determined in respectively predeterminable time windows around the detected R wave R, that the minimum value occurring immediately before the R wave R occurs Q-wave Q is output, and / or that the time occurring immediately after the R-wave R minimum value is output as an S wave. For this purpose, a simple comparison of the samples with the respectively adjacent samples is provided. Owing to the strict coupling of the Q wave Q and the S wave Z to the time of occurrence of the R wave, in each case the search for the corresponding minimums can be restricted to a very short time interval before and after the R wave R, respectively remain, whereby the computational effort can be kept low. In this case, it is further preferably provided to detect the minima occurring in each case at the time closest to the detected R peak R. Preferably, the time intervals to the associated R-wave R are determined to the respective prongs Q, S, and further processed or output respectively.
    With regard to the detection of the Q wave Q, it has been found that the distance of the Q wave Q to the R wave R is very constant, regardless of the heart rate in a certain subject. It is therefore preferable to determine the time between the Q-wave Q for R-Racke purely as accurately as possible in a particular subject, such as in a laboratory environment, and thereafter for the further detection in the context of the subject invention, the temporal position determined thereby Q-wave Q to the R-wave R constant to set the value determined thereby.
    It can further be provided, if this is not possible or impractical or appears that the temporal position of the Q-wave Q is determined by this 100ms is defined in time before the determined R-wave R. It has been shown that the time span in question is very close to this value of 100 ms for most subjects, and as a result only a very small and justifiable error occurs.
    It has also been shown that in certain types of recording of the heartbeat signal, in particular the Q wave Q and the S wave or the underlying processes of the heart are not clearly recognizable by corresponding rashes of the respective heartbeat signal. However, it has been shown that these, or the times of their occurrence, can be determined by mathematical derivation of the heartbeat signal. It is therefore further preferred that the Q wave Q, the R wave R and / or the S wave S are each determined from the largest positive and / or negative change in the slope of the heartbeat signal.
    It is further preferably provided that for detection of the T-wave T and / or the P-wave P, the respective maximum values are determined in respectively predeterminable time windows around the detected R-wave R, wherein the maximum value occurring immediately before the R-wave is outputted as P-wave P, and the maximum value occurring immediately after the R-wave R is output as T-wave T. In this case, just as with the above-described preferred detection of the Q wave Q or the S wave Z, it is provided that only in a limited expected time window the relevant maximum values are searched. In this case, it is further preferred to detect the maxima occurring in each case temporally closest to the detected R peak R. Preferably, the time intervals are determined to the respective waves P, T, the associated R-wave R and each further processed or output.
    It is preferably provided that the duration of the successive segments and / or the duration of the expected refractory period of the heart and / or the length of the predeterminable time windows around the detected R wave R are selected as a function of the heart rate. As a result, a significantly better performance of the described algorithm can be achieved since the expected values are already better adapted to the real conditions, and consequently the numerical method used converges more quickly.
    It can also be provided to perform the prongs Q, S and / or waves P, T in accordance with the described detection of the R wave.
    Particularly preferred in the described preferred detection of the spikes Q, S and / or waves P, T is provided to check the ECG signal 3 in principle for abnormal changes out, such as cardiac arrhythmia, and optionally for the detection of the individual waves P, T. or jags Q, S adjust the respective expected time windows accordingly.
    2 shows an ECG device 1 with at least one input 2 for an electrical and / or magnetic ECG signal 3, wherein the input 2 is connected to an input of an analog-to-digital converter 4, wherein an output of the analogue Digital converter 4 is connected to an R-wave detection unit 5, and wherein an output of the R-wave detection unit 5 is connected to a Herzbelastungsdauer- and / or Herzerholungsdauer- and / or Herzbelastung quotient and / or cardiac recovery quotient determination unit 6.
    The input 2 of the ECG device 1 is connected in a manner known per se with corresponding electrodes 8.
    The Herzbelastungsdauer- and / or Herzerholungsdauer- and / or Herzbelastung quotient and / or recovery rate determination unit 6 is preferably formed comprising a microcontroller, and for performing at least one embodiment of the subject method for determining at least one cardiac load and / or at least one cardiac recovery and / or at least one cardiac stress quotient and / or at least one cardiac recovery quotient from an ECG signal 3.
    The subject ECG device 1 is preferably designed as a mobile device, and preferably has a wireless data interface for transmitting the ECG signals 3 or the at least one cardiac load duration and / or at least one cardiac recovery period and / or the at least one cardiac stress quotient and / or at least one Heart recovery quotient, as well as an accumulator for energy supply.
    It is furthermore preferably provided not only to display or store the determined cardiac load duration and / or cardiac recovery quotient and / or the cardiac stress quotient and / or the cardiac pacing quotient, but also to perform control and / or regulating procedures on the basis of this data. In this case, provision is made in particular for at least one setting of the device to be predetermined by a control and / or regulating unit when a predefinable control and / or regulating criterion is met.
    In this case, the device may in principle be any type of device which is activated or deactivated, for example on the basis of the condition of the subject, or changed in another setting, wherein it is provided in particular to increase the well-being of the subject by means of said change.
    Preferred embodiments of the device include devices for the flow of an essential oil, or the regulation of the lighting, or the room climate.
    Accordingly, according to a preferred embodiment it is provided that the device is an HVAC system, and that settings of the HVAC system are modified such that the cardiac recovery time and / or the
    Cardiac recovery quotient of the subject rises. HVAC is the abbreviation for Heating, Ventilating and Air-Conditioning, which is commonly used in the English language area, and refers to a generic term for building services systems for the heating, ventilation and air-conditioning of rooms. It is envisaged that the room climate will be modified by changes to the HVAC system so that the cardiac recovery and / or the recovery rate of the resident in the room in question subjects is improved.
    According to a further preferred embodiment it is provided that the device is a lighting system and / or a sound system, and that settings of the lighting system and / or the sound system are modified such that the cardiac recovery and / or the recovery rate of the subject increases. It is intended to regulate light effects, the room lighting and / or sounds, sounds and / or music, in such a way that the cardiac recovery and / or the recovery rate of the person residing in the room in question subjects is improved.
    According to a further preferred embodiment, it is provided that the device is a system for the predeterminable release of fragrances, and that settings of the system for the predeterminable release of fragrances are modified such that the cardiac recovery period and / or the cardiac recovery quotient of the subject increases. Such a device is designed to be able to deliver different fragrances into the room in a predeterminable manner, it being provided that the device emits such fragrances that the cardiac recovery time and / or the recovery rate of the subject residing in the respective room is improved.
    claims:
    权利要求:
    Claims (30)
    [1]
    1. A method for, in particular continuous, determination of at least one cardiac stress period and / or a cardiac recovery, and preferably a cardiac stress quotient and / or a cardiac recovery, from a heartbeat signal, in particular an electrocardiogram (3) and / or magnetocardiogram and / or impedance cardiogram and / or ballistocardiogram and / or seismocardiogram and / or phonocardiogram, wherein the heartbeat signal is recorded on a human or animal subject, wherein subsequently determined from the heartbeat signal as cardiac stress duration at least one atrial contraction duration and / or a ventricular contraction duration and / or an atrio-ventricular contraction duration and / or an atrial dilation duration and / or a ventricular dilation duration and / or an atrio-ventricular dilation duration is determined as the cardiac recovery time.
    [2]
    2. The method according to claim 1, characterized in that as a heart stress quotient: a stress quotient atrium as the ratio of the atrial contractile durations to the atrial dilatation duration and / or a stress quotient ventricle as the ratio of the ventricular contraction duration to the ventricular dilatation duration and / or Exposure quotient total heart as ratio of atrio-ventricular contraction duration to atrio-ventricular dilation duration and / or - a heart diastole-related stress ratio atrium as ratio of atrial contraction duration to atrio-ventricular dilatation duration and / or - a ventricle related to cardiac diastole is determined as the ratio of the ventricular contraction duration to the atrio-ventricular dilation period.
    [3]
    3. Method according to claim 1, characterized in that the heart recovery quotient is a recovery ratio atrium as the ratio of the atrial contraction durations to the atrial dilation duration and / or a recovery quotient of the ventricle as the ratio of the ventricular contraction duration to the ventricular dilation duration and / or a recovery ratio of total heart as the ratio of the atrial-ventricular contraction duration to the atrial-ventricular dilation duration and / or - a heart diastole-related recovery ratio atrium as the ratio of the atrial contraction duration to the atrial-ventricular dilation duration and / or - a recovery ratio related to the cardiac diastole Ventricle is determined as the ratio of the ventricular contraction duration to the atrio-ventricular dilation period.
    [4]
    4. The method according to any one of claims 1 to 3, characterized in that the at least one cardiac load duration and / or the at least one cardiac recovery period, and preferably at least one cardiac stress quotient and / or the at least one cardiac recovery quotient, output and / or stored.
    [5]
    5. Method according to claim 1, characterized in that the at least one cardiac load duration and / or the at least one cardiac recovery period, and preferably the at least one cardiac stress quotient and / or the at least one cardiac recovery quotient, as average value and / or as median of is formed at a predeterminable number of previous heartbeat intervals determined cardiac load and / or cardiac recovery.
    [6]
    6. The method according to claim 4 or 5, characterized in that the at least one cardiac load duration and / or the at least one cardiac recovery period, and preferably the at least one cardiac stress quotient and / or the at least one cardiac recovery quotient, issued substantially in parallel to the recording of the heartbeat signal, in particular , becomes.
    [7]
    7. Method according to claim 1, characterized in that at least one determined cardiac load duration and / or at least one determined cardiac recovery period, and preferably at least one determined cardiac stress quotient and / or at least one determined cardiac recovery quotient, is compared with at least one predeterminable border condition, and if the at least one boundary condition is exceeded, a signal is emitted by the cardiac load duration or the cardiac recovery period or the cardiac stress quotient or the cardiac pacing quotient.
    [8]
    8. The method according to claim 7, characterized in that the at least one cardiac load duration and / or the cardiac recovery period and / or the cardiac stress quotient and / or the cardiac recovery quotient over a predefinable first period, which is preferably between one day and fourteen days, is recorded the first time period is divided into a predeterminable plurality of second time periods, which are preferably between 15 minutes and 2 hours, and that for at least a second time period at least the limit condition is formed from the determined cardiac load durations or cardiac recovery quotients or cardiac recovery quotients.
    [9]
    9. A method according to claim 8, characterized in that the at least one boundary condition is adapted to the prevailing time of day by selecting the boundary condition determined for the second time period in which the current time of day lies.
    [10]
    10. The method according to any one of claims 1 to 9, characterized in that the heartbeat signal is an ECG signal that detects at least one R-wave (R), preferably a time of occurrence of the R-wave (R) in the heartbeat signal in which at least one time duration between the R wave (R) and one of the R wave (R) before and / or following wave (P, T) and / or wave (Q, S) of the heartbeat signal is determined, and so that the at least one cardiac load duration and / or the at least one cardiac recovery period, and preferably the at least one cardiac stress quotient and / or the at least one cardiac recovery quotient are determined.
    [11]
    11. The method according to claim 10, characterized in that as, the R-wave (R) leading and / or trailing wave (P, T) and / or tine (Q, S), at least one, in particular directly, before the R wave occurring P wave (P) and / or Q wave (Q) and / or an immediately after the R wave (R) occurring S wave (S) and / or T wave (T), in particular a time of occurrence of the respective wave (P, T) and / or tine (Q, S) is detected.
    [12]
    12. The method according to claim 10 or 11, characterized in that the ECG signal is recorded as an analog ECG signal, and is subsequently converted with an analog-to-digital converter into a digital ECG signal.
    [13]
    13. The method according to claim 12, characterized in that the digital ECG signal is filtered by means of a predefinable FIR filter, wherein preferably filter components of the FIR filter are only selected from the group -1, 0 and / or +1.
    [14]
    14. The method according to any one of claims 10 to 13, characterized in that in the R-wave detection, the ECG signal is divided into segments of predeterminable duration, preferably between 2 seconds and 3 seconds, and that determines a maximum value within each segment becomes.
    [15]
    15. The method according to claim 14, characterized in that over a predetermined number, preferably three to seven, preceding successive segments of the median of the values is formed in the respective segments.
    [16]
    16. Method according to claim 15, characterized in that the samples within a segment are compared with the median divided by a predefinable value, that only samples having a value greater than the shared median are compared with the previous sample, and that only samples having an absolute value difference from the preceding sample value greater than a predefinable limit value are further processed as R-wave candidates for detection of the R wave (R).
    [17]
    17. The method according to claim 16, characterized in that the limit greater than the noise and / or the jitter of the analog-to-digital converter (4) is selected.
    [18]
    18. The method according to claim 16 or 17, characterized in that R-wave candidates within a predetermined period of time, of a maximum of half expected refractory period of the subject's heart, following a previously detected R-wave (R) are discarded.
    [19]
    19. The method according to claim 18, characterized in that the remaining R-wave candidates are evaluated with at least one predeterminable evaluation criterion, and that an R-waves candidate when fulfilling the evaluation criterion as a detected R-wave (R) spend and / or stored and / or further processed.
    [20]
    20. The method according to any one of claims 11 to 19, characterized in that for detecting the S-wave (S) and / or the Q-wave (Q), the respective minimum values in each predeterminable time windows around the detected R wave (R) determining that the minimum value occurring in time immediately before the R wave (R) is output as a Q wave (Q), and that the minimum value occurring immediately after the R wave (R) is output as an S wave (S) becomes.
    [21]
    21. The method according to any one of claims 11 to 20, characterized in that the temporal position of the Q wave (Q) is determined by this 100ms is defined in time before the determined R wave (R).
    [22]
    22. The method according to any one of claims 11 to 21, characterized in that the Q-wave (Q), the R wave (R) and / or the S wave (S) in each case from the largest positive and / or negative change the slope of the heartbeat signal is determined.
    [23]
    23. The method according to any one of claims 11 to 22, characterized in that for detecting the T-wave (T) and / or the P-wave (P), the respective maximum values in each predetermined time windows to the detected R-wave (R) It can be determined that the maximum value occurring in time immediately before the R wave (R) is output as a P wave (P), and that the maximum value occurring immediately after the R wave (R) is output as a T wave (T) becomes.
    [24]
    24. The method according to any one of claims 11 to 23, characterized in that the Q-wave (Q), the R wave (R) and the S wave (S) each determined the largest positive and / or negative slope of the heartbeat signal becomes.
    [25]
    25. The method according to any one of claims 18 to 24, characterized in that the duration of the successive segments and / or the duration of the expected refractory period of the heart and / or the length of the predeterminable time window to the detected R-wave (R) in dependence the heart rate can be selected.
    [26]
    26. A method for controlling and / or regulating at least one device, wherein a heartbeat signal of a subject is recorded, characterized in that from the heartbeat signal a cardiac load duration and / or a cardiac recovery period and / or a cardiac stress quotient and / or a cardiac recovery quotient according to one of claims 1 to 25 is determined, and that when a predefinable control and / or control criterion at least one setting of the device by a control and / or regulating unit is specifiable changed.
    [27]
    27. Method according to claim 26, characterized in that the device is an HVAC system, and that settings of the HVAC system are modified such that the cardiac recovery time and / or the patient's cardiac recovery quotient increase.
    [28]
    28. The method according to claim 26 or 27, characterized in that the device is a lighting system and / or a sound system, and that settings of the lighting system and / or the sound system are modified such that the cardiac recovery period and / or the cardiac recovery ratio of the subject increases.
    [29]
    29. The method according to claim 26, 27 or 28, characterized in that the device is a system for the predeterminable release of fragrances, and that settings of the system for the predeterminable release of fragrances are modified such that the cardiac recovery period and / or the cardiac recovery quotient of the subject increases.
    [30]
    30. ECG device (1) with at least one input (2) for an electrical and / or magnetic ECG signal (3), characterized in that the input (2) is connected to an R-wave detection unit (5) in that an output of the R-wave detection unit (5) is connected to a cardiac stress duration and / or cardiac stress quotient and / or cardiac recovery quotient determination unit (6), which is preferably used to carry out a method according to one of claims 1 to 29 is formed.
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    同族专利:
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    AT517071B1|2016-11-15|
    EP3340870A1|2018-07-04|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    US6169919B1|1999-05-06|2001-01-02|Beth Israel Deaconess Medical Center, Inc.|System and method for quantifying alternation in an electrocardiogram signal|
    CN101969850B|2008-03-14|2016-01-20|皇家飞利浦电子股份有限公司|For maintaining the method and system of the state of object|
    EP2421430B1|2009-04-24|2020-11-18|Advanced Brain Monitoring, Inc.|Adaptive performance trainer|
    AT515102B1|2013-12-04|2015-06-15|Human Res Inst Für Gesundheitstechnologie Und Präventionsforschung Gmbh|Method and device for generating and outputting a stimulus and / or a request for respiration for a human and / or animal|CN108354612B|2018-01-19|2021-01-01|深圳和而泰数据资源与云技术有限公司|Signal processing method and device|
    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    ATA570/2015A|AT517071B1|2015-08-28|2015-08-28|Method and device for determining at least one cardiac load duration and / or a cardiac recovery period from a heartbeat signal|ATA570/2015A| AT517071B1|2015-08-28|2015-08-28|Method and device for determining at least one cardiac load duration and / or a cardiac recovery period from a heartbeat signal|
    EP16754535.9A| EP3340870A1|2015-08-28|2016-08-24|Method for determining at least a cardiac stress duration and/or a cardiac recovery duration from a heartbeat signal|
    PCT/EP2016/070016| WO2017036890A1|2015-08-28|2016-08-24|Method for determining at least a cardiac stress duration and/or a cardiac recovery duration from a heartbeat signal|
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