• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    The method allows the filtering of an initial RR series consisting of a plurality of samples (RRi) which are respectively a function of the time intervals (δti) which separate two successive heart beats. To perform this filtering, one automatically detects in the initial RR series if one or more successive samples (RRi) are erroneous, and one or the samples (RRi) detected as being erroneous are automatically corrected in the series RR by replacing them with one or more several reconstructed samples (RRc), so as to obtain a series RR if necessary partially reconstructed, and possibly one resamples the series RR, so as to obtain a series RR, if necessary partially reconstructed, and resampled . The quality of the RR series is automatically controlled by counting in a predefined sliding window the number (NbPertub) of RR samples (RRc) that have been reconstructed and / or, if applicable, the number (NbPertub) of samples ( RRrc) of the RR series that have been reconstructed and resampled.
    公开号:FR3017789A1
    申请号:FR1451487
    申请日:2014-02-25
    公开日:2015-08-28
    发明作者:Regis Logier；Jonckheere Julien De；Mathieu Jeanne；Thomas Margez
    申请人:Centre Hospitalier Regional Universitaire de Lille；
    IPC主号:
    专利说明:

    [0001] FIELD OF THE INVENTION The present invention relates to the field of digital processing of a bioelectric signal, which is characteristic of the heart rhythm of a living being, and which is referred to in this text as the cardiac signal. This is for example, but not exclusively, an electrocardiographic signal (ECG). In this technical field, the invention relates to the filtering of a series RR, obtained by sampling a cardiac signal, with implementation of an automatic quality control of the RR series. Prior art From a physiological point of view, the heart of a living being, isolated from any outside influence, automatically contracts itself very regularly like a metronome, under the action of the sinus node which generates an independent nerve impulse, and by this means causes a spontaneous contraction of the heart muscle. The heart is not isolated, however, but is connected to the Autonomic Nervous System (ANS), through the parasympathetic and sympathetic systems. This autonomic nervous system influences the activity of the heart: the sympathetic system accelerates the heart rate, while the parasympathetic system slows it down. Thus, despite a certain autonomy, the heart undergoes influences of the autonomic nervous system, which allows the body of a living being to adapt the heart rate according to its needs, within reasonable limits. It is therefore understood that the analysis of the evolution over time of the cardiac rhythm, and in particular of the variations of the cardiac rhythm (variation of the beats of the heart), makes it possible to obtain an important information on the activity of the cardiac system, and more particularly on the activity of the autonomic nervous system. Knowledge of ANS activity can be of great help in developing a diagnosis of many clinical situations. On this subject, reference may be made, for example, to the following publication: Lacroix D, Logier R., Kacet S., Hazard JR, and Dagano J. (1992): "Effects of consecutive administration of central and peripheral anticholinergic agents on in the normal subjects, J. of the Autonomic Nervous System, Vol 39, pp. 211-218. To study these fluctuations of the heart rate, since 1970 we have developed different techniques for filtering and spectral analysis of a signal that represents the evolution over time of the instantaneous cardiac rhythm (or frequency), which is obtained after sampling. an analog bioelectric signal, characteristic of the heart rhythm of a living being, and subsequently called "analog cardiac signal". To acquire this cardiac signal, various invasive or non-invasive acquisition techniques are known. A known invasive technique is for example to use a blood pressure sensor connected to a catheter introduced into an artery. Among the known non-invasive methods are, for example, the use of an infrared pulse sensor, or the acquisition of an electrocardiographic (ECG) signal by means of an electrocardiograph. The latter method of acquiring an ECG signal is in practice the most commonly used to date, because in addition to its non-invasive nature, it advantageously makes it possible to obtain a more precise signal than that obtained, for example, by means of a sensor. of infrared pulse. The ECG signal is in known manner consisting of a succession of electrical depolarizations whose appearance is shown in Figure 3 attached. The P wave, which corresponds to the depolarization of the atria, has a small amplitude, and a dome shape. The PQ space reflects the atrioventricular conduction time. The QRS complex reflects the ventricular contraction, and the T wave the ventricular repolarization. In practice, peak R is considered as a marker of ventricular systole, ie, heartbeat.
    [0002] In practice, since the R wave is most often the thinnest and widest part of the QRS, it is generally used to localize the heartbeat punctually with a very good accuracy, in practice of the order of a thousandth of a second. Thus the time interval between two successive waves R precisely characterizes the time separating two successive heart beats; this is the period of the ECG signal, and the opposite of this period gives the instantaneous heart rate. To automatically construct the signal, subsequently called series RR, representing the evolution in time of the instantaneous heart rate, the ECG signal is sampled which is an analog signal (analog / digital conversion of the ECG signal), and the signal is processed. Digital ECG sampled, automatically detecting R waves in this digital signal. A series RR is thus in the usual manner, consisting of a plurality of successive samples (or points) RR, each sample RR being a function of the time interval separating two successive waves R of the ECG signal. It must be emphasized, however, that the other depolarization waves (P, Q, S or T) of the ECG signal can also be used to characterize the heart rate, even if the accuracy of the measurement is worse than that of Moreover, depending on the acquisition technique chosen, the cardiac signal may have a shape different from that mentioned above of an ECG signal. This heart signal is not necessarily analog, but can be a digital signal. Accordingly, in the present text, the term RR series is not limited to the aforementioned specific definition based on the R-waves of an ECG signal, but is defined more generally in the context of the present invention as a series of several digital samples called RR, obtained from a cardiac signal which is characteristic of the heart rhythm, each RR sample being a function of the time interval between two successive heart beats. Each RR sample may be proportional, and especially equal, to the time interval between two successive heart beats or inversely proportional to the time interval between two successive heart beats. In practice, disturbances in the cardiac signal, and in particular in an ECG signal, induce, in the RR series resulting from this cardiac signal, abrupt variations of short duration commonly called artifacts. Disturbances, which cause artefacts in the RR series, may be physiological and intrinsically related to a momentary dysfunction of the cardiac system; it is for example an extrasystole. These disturbances may also be external and not related to the functioning of the cardiac system; it is for example a movement of the patient briefly altering the measurement signal. Artifacts in a RR series may result in a single erroneous sample or a plurality of erroneous successive samples. In practice, an artifact in the RR series can be likened to a Dirac pulse, and is translated into the frequency domain by a broadband rectangular continuous spectrum. Consequently, in the event that a series RR would be transposed into the frequency domain (by Fourier or other transform), without taking any particular precaution, the presence of artifacts in the RR series would translate into the frequency domain. by obtaining a frequency spectrum of the highly disturbed RR series, of rectangular broadband shape, masking the spectrum of the real signal. For this reason, in order to obtain correct frequency information, it is essential to eliminate the artifacts before performing the frequency translation. It has thus been proposed in the international patent application WO 02/069178, as well as in the article Logier R, De Jonckheere J, Dassonneville A, "An efficient algorithm for R-R intervals series filtering". Conf Proc IEEE Eng Med Biol Soc. 2004; 6: 3937-40, digital filtering algorithms, which in general allow real-time filtering of a RR series, obtained from a cardiac signal, by automatically detecting in the RR series the presence of one or more RR samples; successive errors, and automatically replacing the RR samples in the RR series; errors that were detected by RR samples, corrected. The detection of RR samples; Mistakes can be performed in different ways and the corrected samples (RRs) can also be calculated in various ways, and for example, but not exclusively by linear interpolation.
    [0003] A problem of these filtering algorithms, referred to hereafter as algorithms or filtering method "with reconstruction of erroneous samples of an RR series" resides in the fact that the reconstruction of the RR series, by replacement of the RR samples; errors that have been detected by corrected RRc samples, may ultimately result in a partially reconstructed RR series which is itself partially or totally distorted, particularly when the cardiac signal that has been collected is of poor quality. The quality defect of this cardiac signal can result from numerous factors, such as, for example, and in a nonlimiting and non-exhaustive manner, a bad positioning of the electrodes or sensors for measuring the cardiac signal, an insufficient amplification of the signal in the chain of signal processing, etc ... Now the reconstruction of a distorted RR series is currently not detected by the filtering algorithms of an RR series. As a result, the information provided by these filtering algorithms can be totally erroneous or insignificant without being noticed. OBJECT OF THE INVENTION The present invention aims at providing a filtering solution of a series RR obtained from a cardiac signal, which implements an automatic reconstruction of erroneous samples of the RR series, but which makes it possible to automatically check the quality of the partially rebuilt RR series.
    [0004] SUMMARY OF THE INVENTION The first object of the invention is a method of filtering an initial RR series consisting of a plurality of samples (RRi) which are respectively a function of the time intervals (Esti) which separate two heart beats. successive, filtering method in which is automatically detected in the initial RR series if one or more successive samples (RRi) are erroneous, and is automatically corrected in the RR series or samples (RRi) detected as being erroneous by replacing them by one or more reconstructed samples (RRc), so as to obtain a series RR, if necessary partly reconstructed, and during which the RR series may be resampled, so as to obtain a series RR, where appropriate in part reconstructed, and resampled. Characteristically according to the invention, the quality of the RR series is automatically controlled by counting in a predefined sliding window the number (NbPertub) of RR series samples (RRc) that have been reconstructed and / or, if appropriate, the number (NbPertub) of RR series samples (RRrc) that have been reconstructed and resampled. In the present text, and especially in the claims, the term "cardiac signal" denotes any physical signal characteristic of the instantaneous rhythm (or frequency) of the living being. For the implementation of the invention, various invasive or non-invasive techniques may be used to acquire this cardiac signal. A known invasive technique is for example to use a blood pressure sensor connected to a catheter introduced into an artery. Among the non-invasive methods known (and for which preference will be chosen), there may be mentioned for example the use of an infrared pulse sensor, the use of an ultrasonic sensor for the detection of cardiac cycles, of the type the sensor implemented in a cardiotocograph, or the acquisition of an electrocardiographic signal (ECG). The acquisition of an electrocardiographic signal (ECG) is in practice the most commonly used method, because in addition to its non-invasive nature, it makes it possible to obtain a more accurate cardiac signal than that obtained, for example, by means of a pulse sensor. infrared pulse.
    [0005] In the present text, and in particular in the claims, is generally designated by the terms "RR series", a series of several successive samples RR, obtained from a cardiac signal characteristic of the heart rhythm of being living, each RRi sample being generally a function of a time interval (Esti) between two successive heart beats. Generally, each sample (RRi) is proportional, and more particularly equal, to the time interval (Esti) between two successive heart beats. Each sample (RRi) can also be proportional, and more particularly equal, inversely (1h5ti) of the time interval between two successive heart beats.
    [0006] In the preferred embodiment described hereinafter with reference to the appended figures, this series RR is more particularly constructed from the R waves of an ECG signal. This is however not limiting of the invention. In the case of an ECG-type heart signal, the so-called "RR" series can be constructed using the other depolarization waves (P, Q, S or T) of the ECG signal to construct the RR series, but the accuracy is less good only by using the R waves of the ECG signal. Also, when the cardiac signal is not an ECG signal, the samples of the RR series are not calculated by determining the time interval (Esti) separating two successive R waves of the ECG signal, but are in a more determined by detecting in the cardiac signal the time interval between two successive heart beats. More particularly, but optionally according to the invention, the method of the invention may comprise the following additional and optional technical characteristics, taken separately or in combination: - A quality index (NivQual) which is significant is automatically calculated of the quality of the RR series, and which depends on the number (NbPertub) of RR series samples (RRc) that have been reconstructed and / or, if applicable, the number (NbPertub) of samples (RRrc) of the series RRs that have been reconstructed and resampled. The quality index (NivQual) also depends on the instantaneous heart rate FCi, with FCi = 60000 / RRi, RRi being the instantaneous value in millisecond of a sample (RRi) of the RR series, if necessary partially reconstructed. . The quality index (NivQual) also depends on the mathematical norm, in said sliding window, of the RR series, if necessary partially reconstructed, and re-sampled, said mathematical norm being given by the following formula: 2 STANDARD = RR I. - (RR;) i = 1 1 = 1, where N is the number of RRi samples in said window. - An action is automatically triggered when the number (NbPertub) of RR series samples (RRc) that have been reconstructed and / or where appropriate the number (NbPertub) of RR series samples (RRrc) which have have been reconstructed and resampled, is greater than a predefined value (THRESHOLD1). - An action is automatically triggered when the number (NbPertub) of RR series samples (RRc) that have been reconstructed and / or where appropriate the number (NbPertub) of RR series samples (RRrc) which have have been reconstructed and resampled, is greater than at least a quarter of the number (N) of samples (RRi) in the window. - An action is automatically triggered when the calculated mathematical standard (NORM) is outside a predefined range (NormMin; NormMax). - An action is automatically triggered when the calculated instantaneous heart rate (FCi) is outside a predefined range (FCMin; FCMax). 30 - The action that is triggered includes triggering a visual and / or audible alarm. - The action that is triggered includes resetting the acquisition and sample construction (RRi) of the initial RR series. the method comprising the acquisition and the real-time construction of successive samples (RRi) of the initial RR series from a cardiac signal, the detection and correction of the erroneous samples (RRi) as well as the counting of the reconstructed samples are performed in real time as and when said acquisition and construction of successive RR samples (RRi).
    [0007] The invention also relates to a filtering device of a series RR consisting of a plurality of samples (RR) which are respectively a function of the time intervals (Esti) which separate two successive heart beats, said device being designed to automatically filter the RR series and to control the quality of this RR series by implementing the above method. Another subject of the invention is a system for acquiring and processing a cardiac signal, said system comprising electronic means for acquiring a cardiac signal, and electronic processing means designed to construct a series RR, at from the cardiac signal acquired by the electronic acquisition means, said series RR consisting of a plurality of samples (RR) which are respectively a function of the time intervals (Esti) which separate two successive cardiac beats of the cardiac signal. Characteristically according to the invention, said electronic processing means are designed to automatically filter the RR series and to control the quality of this RR series by implementing the aforementioned method. The invention also relates to a computer program comprising computer program code means adapted to be executed by electronic processing means, and allowing, when executed by electronic processing means, to implement the filtering process of a RR series referred to above. BRIEF DESCRIPTION OF THE DRAWINGS Other features and advantages of the invention will emerge more clearly on reading the following detailed description of a preferred embodiment of the method of the invention, which detailed description is given as a nonlimiting and non-exhaustive example, and with reference to the accompanying drawings in which: - Figure 1 schematically shows the main elements of an exemplary system for acquiring and processing an ECG signal implementing the FIG. 2 shows the set of waves (PQRST) characteristic of a heartbeat in an ECG signal, and FIG. 3 represents an example of an ECG digital signal obtained after sampling a signal. Analog ECG, FIG. 4 shows an exemplary RR series (still referred to as RR signal) constructed from the signal of FIG. 3. Detailed Description Acquisition System One example of a system 20 for acquiring and processing the cardiac signal of a living being (human or animal) which is used for carrying out the method of the invention is shown in FIG. 'invention. This system comprises: conventional electronic means for acquiring an ECG signal, comprising a plurality of measuring electrodes 1 connected at input to an electrocardiographic monitor (ECG) 2, electronic means 3 for processing the ECG signal delivered as output by the ECG monitor 2. The processing means 3 of the ECG signal comprise an analog / digital converter 30, and an electronic processing unit 31. The input of the converter 30 is connected to the output of the ECG monitor 2, and the output of the converter 30 is connected to an input port of the electronic processing unit 31. In a particular non-limiting embodiment of the invention, the processing unit 31 is constituted by a microcomputer, the converter 30 being connected to an RS232 serial port of this microcomputer. The invention is not limited to the implementation of a microcomputer, the electronic processing unit 31 can be implemented differently, and for example in the form of a programmable electronic circuit FPGA type or in the form of an integrated circuit type AS IC. In operation, the electrodes 1 are applied to the body 10 of the living being, and the ECG monitor 2 outputs as usual an analog electrical signal, called ECG signal, which for each heart beat, has the shape of the signal represented in FIG. 2. With reference to FIG. 2, for each heart beat, this electrocardiographic signal (ECG) consists of a set of electric waves: the P wave, which corresponds to the depolarization of the atria, and which has a low amplitude and a dome shape; the PQ space which reflects the atrioventricular conduction time; The R wave considered in practice as a marker of ventricular systole, or heartbeat, the QRS complex reflecting ventricular contraction, and - the T wave which reflects ventricular repolarization. This analog ECG signal is digitized by the converter 4, with a predetermined sampling frequency (fc), for example 256 Hz. The sampled signal outputted from the converter 30 (signal shown in FIG. processing unit 31, by means of a specific processing software (filtering software) which is described in detail later. This filtering software is stored in the memory of the processing unit 31, and allows, when executed, to automatically build, from the digital signal delivered by the analog / digital converter 30, a series RR with, where appropriate automatic reconstruction of erroneous RR samples, and automatically calculate a NivQual quality index which allows to check the quality of the RR series if necessary partially reconstructed. A preferred variant of this filtering software will now be detailed. Example of an algorithm of the filtering software In a particular variant embodiment of the invention, the 10 main successive steps of the filtering algorithm are the following: 1. Acquisition and construction of the RR samples from the signal delivered by the converter analog / digital 30, 2. Filtering of the RR series with the automatic detection if appropriate of erroneous RR samples and replacement by reconstructed samples identified in the following RRc samples. 3. Resampling the RR Series at a Preset Frequency f to obtain Resampled RR Samples 4. Selection of the RR Samples Within a Time Window of n seconds (n> 1 / f) 5. Calculation of a quality index NivQual 6. Offset, of a time step worth p seconds (preferably pn), of the time window of n seconds, and reiteration of the computation from step 2. This shift corresponds to the sliding of the 25 time window for selecting samples. In practice, the system can be programmed to be used in real time or in deferred time. When the system is used in deferred time, step 1 is carried out in real time in real time so as to build all the RR samples over the entire desired analysis period; the entirety of these successive RR samples is stored in memory, for example in an acquisition file in memory of the processing unit 31. In a second step, steps 2 to 6 are performed in a loop, delayed, on the RRi samples stored in the acquisition file. When the system is operating in real time, the step 1 of building the RRi samples on the one hand, and the other processing steps 2 to 6, on the other hand, are performed by two separate software modules operating in parallel, the first building module (step 1) feeding the second processing and calculation module (steps 2 to 6) for example via a file or register buffer or equivalent. Steps 1 to 5 will now be detailed. Step 1: Acquisition and construction of the RRi samples The acquisition and construction of the RRi samples is performed by a first software sub-module which is fed with the successive digital data constituting the digitized ECG signal (signal of FIG. 3). delivered by the digital analog converter 30. Each data (or point) of the ECG signal is defined by the instantaneous ECG amplitude; of the ECG signal, and by the sampling instant ti (ti = ni / fc, with no sample number and fc representing the sampling frequency of the converter 30). The first sample acquisition sub-module RRi is designed to automatically detect each successive peak Ri in the digital signal delivered by the converter 30, and to automatically build a series RR (FIG. 4) consisting of a succession of 25 d RRi samples. Each sample RRi is defined by the pair of coordinates: ti [a sampling instant (or number)]; time interval bti (expressed as a multiple of the sampling frequency fc) separating a peak Ri from the next peak Ri_o (in another variant it could be the previous peak Ri-1). Usually as such, since the R wave is most often the thinnest and widest part of the QRS, it is preferably used to detect the heartbeat with very good accuracy, the corresponding time interval being in practice at the time separating two successive heart beats. Nevertheless, in another variant, it could be envisaged to use other waves (for example Q wave or S wave) of a heart beat of the ECG signal to detect and construct the RR series. In another variant, one could also consider using other cardiac signals such as plethysmographic wave or invasive blood pressure. Step 2: Filtering of the RR series with the optional automatic detection of the RR samples; erroneous and replacement by RRc reconstructed samples. This filtering step generally consists in automatically detecting in the RR series the presence of one or more RR samples; successive erroneous, and to automatically replace the RR samples in the RR series; errors that were detected by RRc reconstructed samples. The number of RRc reconstructed samples is mostly different from the number of erroneous samples that were detected. This filtering step with automatic reconstruction of the RR samples; The error is known per se, and examples of implementation of this filtering step are for example described in international patent application WO 02/069178, as well as in the article Logier R, De Jonckheere J, Dassonneville A., An efficient algorithm for RR intervals series filtering. Conf Proc IEEE Eng Med Biot Soc. 25 2004; 6: 3937-40. It should nevertheless be noted that in the context of the invention, the detection of RR samples; This error is not limited to the detection methods described in these two publications, and the RR reconstructed samples can also be calculated in various ways, and for example, but not exclusively, by linear interpolation as described in both publications. aforementioned.
    [0008] Each RRc reconstructed sample of the RR series is identified, for example by an associated identification variable of flag type. Thus, at the end of this step, the RR series consists of RR samples; some of which may be identified by their identification variable as RRc reconstructed samples. Step 3: Resampling the RR Series at a Preset Frequency f to Obtain RR Samples; resamplers The filtered RR series (FIG. 4) delivered by the aforementioned first submodule is resampled automatically by a second software sub-module at a predefined frequency f, which is preferably lower than the sampling frequency fc ( for example, for a sampling frequency fc equaling 250 Hz, the resampling frequency f will be set to 8hz). The objective of this resampling is to obtain at the output a series RR whose RR samples; are equidistant from a temporal point of view, that is to say in other words a series RR whose sampling times are regular. This resampling is performed in a manner known per se by interpolation, and for example by linear interpolation. During this resampling, each reconstructed sample RRc is replaced as appropriate by one or more reconstructed samples resampled RRrc. Each RR RR reconstructed and resampled sample of the RR series is identified, for example by an associated flag-type identification variable. Thus, at the end of this step, the RR series consists of RR samples; some of which may be identified by their identification variable as reconstructed and resampled RRrc samples. Step 4: Selection of RR samples; (of the RR series, if necessary partially reconstructed and resampled) included in a main time window of n seconds (n> 1 / f) This step amounts to isolating a number N of RR samples; successive (N = n.f). For example, we choose for example a main window of 64 seconds (n = 64), which corresponds to 512 RR samples; successive (N = 512), for a resampling frequency f of 8hz. The following steps are applied to the samples in this main window. Step 5: Calculation of a NivQual Quality Index This step is carried out using a software sub-module that automatically calculates a quality index NivQual significant of the quality of the RR series.
    [0009] In the particular variant described in detail below, this NivQual quality index has four quality levels of 0 to 3; the higher the index, the more reliable the RR series from step 1 is. More specifically, the NivQual quality index is based on three variables (FC,; NORM, NbPertub) that are calculated in step 5: 1 / the value of the instantaneous heart rate (HR;) calculated on each RR sample; of the RR series from step 2, that is to say from the RR series after filtering (if necessary partially reconstructed) and before resampling. 2 / the mathematical standard (STANDARD) of RR samples; of the series RR (if necessary partly reconstructed, and resampled), resulting from the step 4 of selection in the time window of n seconds. 3 / the number (NbPertub) of RRrc reconstructed and resampled samples contained in the time window of n seconds (or the number of RRc reconstructed samples corresponding to the RRrc reconstructed and resampled samples contained in the n second time window) ). The heart rate is defined by FC; = 60000 / RR, where RR; is the instantaneous value of the RR sample; in millisecond. The calculation of the mathematical norm of the RR series re-sampled at the frequency f in the window of n seconds consists, firstly, in calculating the average value M of the RRs; in the window. M = (RR) where RRi is the value of each RR interval and N is the number of samples in the window.
    [0010] This average value is then subtracted at each RR interval; from the window. RR; = (RRi-M). The RRi values obtained are used for the calculation of the norm (STANDARD), ie: N I 2 STANDARD = RR. - (RR) i = 1 1 = 1 Concerning the number (NbPertub) of RRrc reconstructed and resampled samples contained in the time window of n seconds, it is considered that if the filter (step 2) has replaced a part too many RR samples; erroneous by reconstructed RRc samples in the window of n seconds, the RR signal is actually uninterpretable. Thus, in a first variant, the number (NbPertub) of reconstructed and resampled samples RRrc contained in the time window of n seconds is automatically counted, and this number (NbPertub) is used in step 5 for the calculation of the NivQual quality index. In a second variant, the number (NbPertub) of reconstructed RRc samples corresponding to the reconstructed and resampled samples RRrc contained in the time window of n seconds is automatically counted, and this number (NbPertub) is used in step 5 to the calculation of the NivQual quality index. The second variant referred to above may be implemented with or without resampling of the RR series. In this case, the calculation of the number NbPertub can be performed by automatically counting, in the RR series resulting from the filtering step 2, the number of RRc samples of the RR series which have been reconstructed, in a sliding window comprising a predefined number (N) of samples and equivalent to a time window. In this case, the above-mentioned step 6 consists of shifting the calculation window by a predefined number of samples p (preferably p N), and by reiterating the calculation from step 2. This offset corresponds to the slip from the sample selection window. The first and second variants above can also be combined. An example of an algorithm for calculating the quality index NivQual from the three variables referred to above (FC, NORM, NbPertub) is given below: If ((STANDARD <NormMin) OR 15 (STANDARD> NormMax) or (FC;> FCMax) or (FCi <FCMin)) 20 then Nivqual = 0 ELSE If NbPerturbSEUIL1 then NivQual = 0 If (NbPerturb <THRESH1) and (NbPerturbSEUIL2) then NivQual = 1 If (NbPerturb <THRESHOLD2) and (NbPerturbSEUIL3) then NivQual = 2 25 If NbPerturb <THRESH3 then NivQual = 3 The values of the parameters FCMax, FCmin, NormMax, NormMin are predefined constants, which depend for example on the age of the human being or which depend for example on the animal species as part of a veterinary application. The threshold values FCMax, FCmin 30 are those usually used by all the cardiac monitoring devices. NormMax, NormMin threshold values of the standard are for example determined experimentally on more than 200 individuals in each category. By way of non-limiting example: for a newborn: FCMax = 250; FCMin = 80; Normmax = 3; Normmin = 0 for an adult: HRax = 180; FCMin = 30; Normmax = 4; Normm in = 0.07 The values of the parameters THRESHOLD1, THRESHOLD2, THRESHOLD3 are predefined constants, which depend on the number N (N = n.f) of samples RR; in the window of n seconds. For example the value of the THRESHOLD1 can be set a quarter of the number N (N = n.f) of RR samples; in the window of n seconds, either THRESH 1 = N / 4. The value of the THRESHOLD2 can be set to one eighth of the number N (N = n.f) of RR samples; in the window of n seconds, ie 15 THRESH 2 = N / 8. The value of the THRESHOLD3 may be set at one sixteenth of the number N (N = n.f) of RR samples; in the window of n seconds, THRESH 3 = N / 16. The NivQual quality index calculated at each step 5 may, for example, be displayed, in particular in real time, so as to inform a practitioner of the quality level of the measured RR signal. In the case of a quality index NivQual equal to 0, it is considered that the RR series from step 1 is too poor quality, and is actually unusable. This quality defect of the RR series may arise from numerous factors, such as, for example, and without limitation and without limitation, poor positioning of the electrodes 1 or sensors for measuring the cardiac signal, insufficient amplification of the signal in the signal processing chain, etc. In the case of calculation of a quality index NivQual equal to 0, the training unit 31 can be programmed to automatically trigger several actions, among which, and in a non-exhaustive manner, the triggering a visual and / or audible alarm and / or resetting the step 1 acquisition of RRi samples, including manual or automatic modification of the source signal gain (ECG). In the context of the invention, for the implementation of step 5, the NivQual quality index calculation algorithm can be simplified by taking into account only the number NbPertub referred to above, and by not taking into account the other two FC parameters; and STANDARD, or taking into account the number NbPertub referred to above, and only one of the other two parameters Fci or STANDARD. When the NivQual quality index does not take into account the STANDARD parameter, step 3 of resampling is not necessary and may be omitted.
    权利要求:
    Claims (12)
    [0001]
    REVENDICATIONS1. A method of filtering an initial RR series consisting of a plurality of samples (RR) which are respectively a function of the time intervals (Esti) separating two successive heart beats, a filtering method in which the series is detected automatically in the series Initial RR if one or more successive (RR) samples are erroneous, and the RR sample (s) detected as erroneous is automatically corrected into the RR series by replacing them with one or more reconstructed samples (RRc), so as to obtain a series RR, if necessary partly reconstructed, and during which the RR series is optionally resampled, so as to obtain a series RR, if necessary partially reconstructed, and resampled, characterized in that it controls automatically the quality of the RR series by counting in a predefined sliding window the number (NbPertub) of samples (RRc) of the RR series which have been reconstructed and / or where appropriate the number (NbPertub) of RR series samples (RRrc) that have been reconstructed and resampled.
    [0002]
    2. Method according to claim 1, in which a quality index (NivQual) which is significant for the quality of the RR series and which depends on the number (NbPertub) of RR series samples (RRc) is automatically calculated. were reconstructed and / or where appropriate the number (NbPertub) of RR series samples (RRrc) that were reconstructed and resampled.
    [0003]
    The method of claim 2, wherein the quality index (NivQual) also depends on the instantaneous heart rate FCi, with FC; = 60000 / RR, where RR is the instantaneous millisecond value of a sample (RR) of the RR series possibly partially reconstructed.
    [0004]
    4. The method as claimed in claim 2, in which the quality index (NivQual) also depends on the mathematical normemathematics, in said sliding window, of the RR series, where appropriate partially reconstructed, and sampled, said mathematical norm being given by the formula: NI 2 STANDARD = RR - N (RR 1), where N is the number ', 1 = 1 1 = 1 of RR samples; in said window.
    [0005]
    5. Method according to any one of the preceding claims, in which an action is automatically triggered when the number (NbPertub) of RR series samples (RRc) that have been reconstructed and / or where appropriate the number (NbPertub). of RR series samples (RRrc) that have been reconstructed and resampled, is greater than a predefined value (THRESHOLD1).
    [0006]
    Method according to one of the preceding claims, in which an action is automatically triggered when the number (NbPertub) of RR series samples (RRc) which have been reconstructed and / or where appropriate the number (NbPertub). of RR series samples (RRrc) that have been reconstructed and resampled, is greater than at least a quarter of the number (N) of samples (RRs) in the window.
    [0007]
    The method of any one of claims 5 or 6, wherein the action that is triggered includes triggering a visual and / or audible alarm.
    [0008]
    The method of any one of claims 5 to 7, wherein the action that is triggered comprises resetting the acquisition and construction of the samples (RR) of the initial RR series.
    [0009]
    A method according to any one of the preceding claims, comprising acquiring and constructing in real time successive samples (RR) of the initial RR series from a cardiac signal, and wherein the detection and correction of erroneous samples (RR) as well as the counting of the reconstructed samples are performed in real time as and when said acquisition and construction of successive samples (RRi) of the RR series.
    [0010]
    10. A device (3) for filtering a series RR consisting of a plurality of samples (RR) which are respectively a function of the time intervals (Esti) separating two successive heart beats, said device (3) being designed to automatically filtering the RR series and for controlling the quality of this RR series by carrying out the method of any one of the preceding claims.
    [0011]
    11.A system for acquiring and processing a cardiac signal, said system comprising electronic means (1,2) for acquiring a cardiac signal, and electronic processing means (3) for constructing a series RR initial, from the cardiac signal acquired by the electronic acquisition means (1,2), said series RR consisting of a plurality of samples (RR) which are respectively a function of the time intervals (Esti) which separate two successive heart beats of the cardiac signal, characterized in that said electronic processing means (3) are designed to automatically filter the RR series and to control the quality of this RR series by carrying out the method of any one of the claims 1 to 9.
    [0012]
    Computer program comprising computer program code means adapted to be executed by electronic processing means (3), and allowing, when executed by electronic processing means (3), to implement the method for filtering an RR series according to any one of claims 1 to 9.
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    同族专利:
    公开号 | 公开日
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    WO2015128567A1|2015-09-03|
    US20170172443A1|2017-06-22|
    FR3017789B1|2016-02-12|
    引用文献:
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    US20110270346A1|2010-04-29|2011-11-03|Mark Frei|Method, apparatus and system for validating and quantifying cardiac beat data quality|EP3763283A1|2019-07-10|2021-01-13|Commissariat à l'Energie Atomique et aux Energies Alternatives|Method for estimating the quality of a heart rate signal|FR2821460B1|2001-02-28|2003-06-27|Chru Lille|METHOD AND DEVICE FOR FILTERING AN RR SERIES FROM A CARDIAC SIGNAL, ESPECIALLY AN ECG SIGNAL|EP3932298A1|2016-09-27|2022-01-05|Boston Scientific Neuromodulation Corporation|System for pain management using objective pain measure|
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    CN109567788B|2018-11-29|2021-08-20|武汉中旗生物医疗电子有限公司|Electrocardiosignal filtering method for removing ringing|
    法律状态:
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    2016-01-08| TQ| Partial transmission of property|Owner name: MDOLORIS MEDICAL SYSTEMS, FR Effective date: 20151204 Owner name: CENTRE HOSPITALIER REGIONAL UNIVERSITAIRE DE L, FR Effective date: 20151204 |
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    优先权:
    申请号 | 申请日 | 专利标题
    FR1451487A|FR3017789B1|2014-02-25|2014-02-25|METHOD AND DEVICE FOR FILTERING A SERIES RR OBTAINED FROM A CARDIAC SIGNAL WITH AUTOMATIC CONTROL OF THE QUALITY OF THE RR SERIES|FR1451487A| FR3017789B1|2014-02-25|2014-02-25|METHOD AND DEVICE FOR FILTERING A SERIES RR OBTAINED FROM A CARDIAC SIGNAL WITH AUTOMATIC CONTROL OF THE QUALITY OF THE RR SERIES|
    EP15709291.7A| EP3110321A1|2014-02-25|2015-02-20|Method, device, system and computer programme for filtering an rr series obtained from a cardiac signal with automatic checking of the quality of the rr series|
    PCT/FR2015/050417| WO2015128567A1|2014-02-25|2015-02-20|Method, device, system and computer programme for filtering an rr series obtained from a cardiac signal with automatic checking of the quality of the rr series|
    US15/118,409| US20170172443A1|2014-02-25|2015-02-20|Method, device, system and computer programme for filtering an rr series obtained from a cardiac signal with automatic checking of the quality of the rr series|
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