Method and apparatus for correcting for non-physiological variations in ECG signals

Abstract: In a method for correcting for non-physiological variations in ECG signals, signals recorded during a heartbeat, or a characteristic part of a heartbeat, are conditioned and digitized. Signal samples are stored in the form of an m*p matrix, where m is the number of samples and p is the number of leads used from measuring electrodes applied to the patient. The difference between this measuring matrix and a reference matrix is minimized by performing one or more of the operations translation, time synchronization, rotation and scaling of the measuring matrix. An apparatus for correcting for non-physiological variations in ECG signals comprises means (4) for conditioning signals, picked up by measuring electrodes applied to the patient, an A/D converter (8) for digitizing the signals and a calculation unit (10). The calculation unit comprises storage means (11) for storing signal samples in the form of a m*p matrix, where m is the number of samples and p is the number of leads used from measuring electrodes (2) applied to the patient (3), and for storing a reference matrix. The calculation unit is arranged to minimize the difference between the measuring matrix, formed from signal samples, and the reference matrix by means of one or more of the operations translation, time synchronization, rotation and scaling of the measuring matrix.

Description: The present invention relates to a method for correcting for non-physiological variations in ECG signals, the signals recorded during a heartbeat or a characteristic part of a heartbeat being conditioned and digitized, and to an apparatus for performing such a correction, comprising means for conditioning signals, picked up by measuring electrodes applied to the patient, an A/D converter for digitizing the signals and a calculation unit. Variations in ECG signals from heartbeat to heartbeat, caused by the patient's breathing movements and possible changes in position, are a complication in a plurality of analysis made of ECG signals. Changes of this kind are mainly due to changes in the geometry of the torso and to changes in the heart's relative position, i.e. changes in the heart's electrical axis in relation to the positions of the measuring electrodes employed. In e.g. morphology classification of QRS complexes, these variations in the ECG signal can cause QRS complexes representing identical heartbeats to be classified as different complexes due to changes in the ECG signals caused solely by geometric changes in the patient's torso. The problem is very great in long-term patient monitoring. In these patients namely, new "normal" QRS complexes occurring when the patient changes position are a risk. Moreover, serial comparison of a plurality of resting ECG's from the same patient often displays undesirable variability, because the placement of electrodes in relation to the heart is not identical in each examination. In variance ECG's in which beat-to-beat variability in the ECG signal is studied, said non-physiological variations in the ECG signals constitute a major complication, since these variations, occasioned e.g. by the patient's breathing, are often greater than the variability which is to be studied and which is related to the function of the myocardium. A number of attempts have hitherto been made to remedy these problems, but the attempts have been inadequate or ineffective. In the morphology classification of QRS complexes, attempts have been made e.g. to solve the problem indirectly by the use of extracted quantities, which to some extent are independent of the exact morphology of the complex, as a measure of the similarity of QRS complexes. Examples of such quantities are the width and area of a two-dimensional single-plane representation of the QRS complex. However, this type of morphology classification generally yields poorer results than morphology classification based on the correlation between samples in the complexes, see Pahlm and Sörnmo, "Data Processing of Exercise ECGs", IEEE Transactions on Biomedical Engineering, vol. BME-34, pp. 158-165, February 1987, Cruts et al., "Arrhythmia Typification in a Real-Time Analysis System for Monitoring Geriatric Patients during Exercises", Proceedings from the Conference on Computers in Cardiology IEEE 1985, pp. 423-426, and Alsté et al., "Beat-to-Beat Analysis of Waveshape and Rhythm in XECG Using Inner Vector Product Hardware", Computers in Cardiology, pp. 355-358, IEEE 1982. However, the latter technic, based on correlation between samples in the complexes, is sensitive to a.o. respiratory variations in the QRS complexes. Attempts to compensate for this usually employ updating of the reference complex or template by averaging. However, this method also has major limitations. Thus no technic is presently available for compensating for variations in the direction of the QRS complex's electric axis before the correlation to reference complexes is performed. In serial comparisons of a plurality of resting ECGs recorded from the same patient on different occasions, there is often an undesirable variability because the location of electrodes in relation to the heart is not identical from one examination to another. One method for reducing this undesirable variability is described in Rubel et al., "Methodology of ECG Interpretation in the Lyon Program". Meth. Inform. Med. Vol. 29, no. 4, pp. 393-402, (1990), Fayn et al., "Quantitative Assessment of Beat-to-Beat Variability in Ambulatory ECG Recordings", ... and Rubel et al., "New Strategies in Serial ECG Comparison and Trend Analysis", Computer ECG Analysis: Towards Standardization, Elsevier Science Publishers B.V. (North-Holland), pp. 323-328 (1986), in which method geometric transformations of three-dimensional vector loops are performed. Thus, this method requires recording of a so-called vector cardiogram, which means that the electrodes are positioned so three orthogonal leads are obtained. The method is relatively complex and in addition thereto an iterative process which is hard to implement in real time, i.e. hard to apply to beat-to-beat variability. Variance ECG, i.e. beat-to-beat variability in the ECG signal, is studied in order to diagnose ischemic heart disease, cf. Prasad and Gupta, "Phase-Invariant Signature Algorithm". "A noninvasive Technique for Early Detection and Quantification of Quabain-induced Cardiac Disorders"; Angiology 30, pp. 721-732 (1979), and Ben-Haim et al., "Beat to Beat Variation in Healed Myocardial Infarction". Am J Cardiol 1992, 70: pp. 1139-1142. In US,A, 5,188,116, one such technic for detecting ischemic heart disease with the aid of variance ECG is described in which correction of respiratory variability in the ECG signal is performed by a scaling of QRS complexes based on the amplitude of the R-spike, see also Shaw and Savard, "On the Detection of QRS Variations in the ECG", IEEE Transactions on Biomedical Engineering, Vol. 42, No. 7, pp. 736-741, (July 1995). The object of the present invention is to overcome the above-discussed disadvantages of the previously known technic and propose a method and provide an apparatus for correcting for non-physiological variations in ECG signals. In this application, the term "non-physiological" refers to variations which are not caused by the heart's electrical activity. This object is achieved with a method and an apparatus of the kind described above and with the characterizing features set forth in claims 1 and 13 respectively. The invention can be implemented and utilized in ECG apparatus which perform various kinds of analysis of ECG signals. The invention is especially useful for analysis based on the comparison of signals from the same patient on different occasions. An example of such an analysis is the morphology classification of QRS complexes which form the basis of substantially all other ECG analysis in both diagnosis and monitoring. Other examples of applications for the invention are serial comparison of stored resting ECGs from the same patient and variance ECGs, whereby effective correction is provided of non-physiological beat-to-beat and day-to-day ECG signal variability, mainly caused by changes in the heart's position in relation to the electrodes because of e.g. breathing movements or differences in electrode placement. In the method or apparatus according to the invention, signals from measuring electrodes applied to a patient are thus sampled and stored. The signal is recorded during a heartbeat or a characteristic part of a heartbeat, such as the QRS complex. Methods for determining the beginning and the end of QRS complexes are previously known, cf. e.g. Sörnmo, "A Model-Based Approach to QRS Delineation", Computers and Biomedical Research, vol. 20, pp. 526-542 (1987). The recorded signal is stored in an m*p matrix where m is the number of samples, i.e. represents the length of the complex, since a complex is normally measured in the number of samples, and the distance between each sample is appropriately constant, and p is the number of used leads from the applied electrodes. The difference between two such matrices, derived from different occasions, is then minimized by the performance of operations which only correct geometric, non-physiological variability in the above expression's previously specified meaning. The operations used are translation, time synchronization, rotation and scaling. If two such matrices are designated A and B respectively, where A is the reference matrix, the translation can be performed by subtracting constant values, i.e. DC levels, from each line in matrix B. However, a better method is to perform baseline filtration of the signal, with the aid of a more advanced algorithm, before it is stored in the matrix. According to an advantageous embodiment of the apparatus according to the invention, the conditioning means thus comprise a high-pass filter, arranged to filter out baseline variations from the ECG signals. In other words, translation is performed before the difference between matrices A and B is minimized. According to one advantageous embodiment of the method according to the invention, measurement data stored in the measuring matrix are shifted, for the time synchronization, one sample for every new measuring matrix, whereupon the measuring matrix exhibiting the smallest difference compared to the references matrix is selected as the time-synchronized measuring matrix. Minimization is consequently performed for a number of B matrices. If it is assumed that the QRS detection point supplies a rough estimate of the synchronization point, minimization can be performed for e.g. 10 B matrices, which thus contain 5 samples shifted in either direction in relation to the synchronization point. Rotation is performed by multiplying the matrix B by a matrix Q which only performs a rotation of the matrix B without changing the lengths of the vectors or the inter-vector angle. Such a matrix is said to be orthogonal and is characterized by the circumstance that a unitary matrix is obtained, in which all the elements are zero except for diagonal elements which are equal to 1, when the matrix is multiplied by its transponate, i.e. reflection in the diagonal. Scaling is performed by multiplying the matrix by a scale factor. According to another advantageous embodiment of the invention the Frobenius norm, obtained by subtracting one matrix from the other, is determined as a measure of the difference between the matrices. The Frobenius norm is calculated by adding the squared sum of all the elements in the matrix and determining the square root of this sum. The problem of minimizing the difference between the A and B matrices can be mathematically expressed as follows: Minimize ∥A-αB(τ)Q∥ F under the condition Q T Q = I p in which α = the scale factor Q = the rotation matrix (p*p) τ = the time shift (e.g. [-5.5]) ∥ ∥ F designates the Frobenius norm. where A = an m*n matrix and a ij designates sampled signal values. Time shift minimization, for the time synchronization, is performed by calculating optimum scaling and rotation for a number of matrices and then selecting the matrix yielding the smallest value for the difference. The solution of problems of the kind formed by minimization of the difference between matrices with respect to scaling and rotation is partially well-known, cf e.g. Golub and Van Loan, Matrix Computations, The Johns Hopkins University Press (1989), chap. 12.4, pp. 581-587. It appears that exact expressions for the rotation matrix Q and the scaling factor α can be formulated. In calculation of the rotation matrix Q, singular value factorization is employed, which means that the matrix is re-written as the product of two orthogonal matrices and a diagonal matrix. The rotation matrix Q, yielding optimum rotation, is given by the product of the two orthogonal matrices, obtained in singular value factorization of the transponate of matrix B, multiplied by matrix A. The optimum scaling factor α is obtained by forming the sum of the diagonal elements in the quadratic matrix, obtained by multiplying the transponate of the optimally rotated B matrix by matrix A and dividing with the sum of the diagonal elements in the matrix obtained, when matrix B is multiplied by its own transponate. The matrix Q and the factor α can then be mathematically derived in the following manner. The minimum of the expression ∥A-αBQ∥ 2 F = sp(A T A)+ α 2 sp(B T B) - 2αsp(Q T B T A), where sp(X) = the sum of the diagonal elements in a quadratic matrix X, is obtained, for a fixed α, by maximizing sp(Q T B T A). The Q which maximizes this expression is equal to UV T , where the matrices U and V are obtained by calculating singular value factorization, SVD, from B T A, see Golub and Van Loan, chap. 12.4.1 for derivation. Minimization in respect of α is performed by setting the corresponding derivative equal to zero, i.e. 2αsp(B T B) - 2sp(Q T B T A) = 0 which yields α = sp ( (BQ) T A) / sp (B T B) Thus, the principle of the invention is to use the above-described method for transforming stored heartbeats, or characteristic parts thereof, such as QRS complexes, so non-physiological variability, in the sense specified above, is minimized in an optimal manner in relation to a reference complex before the complexes are subjected to further analysis. According to yet another advantageous embodiment of the method according to the invention, the rotation and scaling operations are performed simultaneously. According to another advantageous embodiment of the method according to the invention, a predefined number of selected measuring matrices are corrected, for determination of a reference matrix, according to one or more of the above operations, using one of the measuring matrices as a temporary reference, whereupon the mean value is formed of the corrected matrices, and this mean value is set as the reference matrix. After a quality check, a first QRS complex, for example, is thus set as a temporary reference. A number of subsequent complexes are then rotated and scaled, and a mean value is formed. The procedure can be repeated with the next consecutive measuring matrix, the immediately preceding mean value serving as a reference value, until the resultant change in the mean value and, accordingly, in the reference matrix drops below predefined limits. Measuring matrices which, after correction, deviate too much from the existing reference matrix, as measured by the Frobenius norm, are excluded from the mean value calculation, according to another advantageous method according to the invention. In the correction of ECG signals according to the invention, ensuring that medical information is not distorted is of the utmost importance. It would also be advantageous to utilize the invention for correcting signals recorded in so-called patient monitoring, when the patient e.g. turns over at times causing geometric changes of the torso. The QRS complex has been mentioned above as a characteristic part of a heartbeat, but the invention is naturally also applicable to other parts of a heartbeat, e.g. the P wave. One exemplifying embodiment of the apparatus according to the invention, applied to morphology classification of ECG in an analysis ECG recorder, will now be described in greater detail, referring to attached drawings, on which FIG. 1 is a block diagram showing an apparatus for recording and analyzing ECGs; FIG. 2 is a schematic flow diagram illustrating the procedure of the apparatus in FIG. 1; FIGS. 3-5 show the QRS complex from 50-60 heartbeats from a 3-lead ECG recording, plotted in the same diagram after time synchronization, without correction and with correcting optimum rotation and scaling according to the invention, the first heartbeat being used as a reference; FIG. 6 shows the cross-correlation between the reference heartbeat and all the other heartbeats before and after rotation and scaling according to the invention; FIG. 7 shows one of three leads in another ECG recording of a larger number of heartbeats, time-synchronized and superimposed on each other, and FIG. 8 shows the cross-correlation between the reference beat in this instance and the other beats before and after rotation and scaling according to the invention. Thus FIG. 1 shows an apparatus for recording and analyzing ECG signals measured with the aid of electrodes 2 applied to a patient 3. The signals from the electrodes 2 are supplied to an amplifier 4, any analog filters and an A/D converter 8. A calculation unit 10, which comprises storage means 11 for storing signal samples in the form of an m*p matrix, where m is the number of samples and p is the number of leads from measuring electrodes 2 applied to the patient 3, and for storing a reference matrix, is connected to the output of the analog filter device and the A/D converter 8. The calculation unit 10 performs analysis of sampled ECG signals, and the results are presented on a display 12 or printer 14 or are stored on an information storage medium 16, such as a hard disk. The apparatus according to the invention is housed inside the calculation unit 10 which comprises one or more microprocessors. In the present embodiment, the analysis of ECG signals is adapted for morphology classification of heartbeats and is described below in greater detail, referring to FIG. 2. The sampled leads are filtered with a suitable digital high pass filter 5, arranged in the unit 10 in FIG. 1, in order to eliminate baseline variations. Examples of suitable high pass filters are described in the publications WO 92/15242 and WO 92/15243 and in Sörnmo, "Time-Varying Digital Filtering of ECG Baseline Wander", Medical & Biological Engineering & Computing, Vol. 31, pp. 503-508, (1993). The selection and calculation unit 9 selects and calculates, from the filtered leads, the leads to be used for the detection and classification of the QRS complexes, preferably three orthogonal leads are used. High pass filtration can possibly be performed after said selection or calculation operation. The apparatus further comprises a QRS detector 20, and each detected QRS complex is compared with references, based on previously recorded QRS complexes, in the time synchronization and comparison means 30, and the detected QRS complex is compared to a reference point in the reference complexes. The QRS detector 20 is of an appropriate, previously known type. The comparison and time synchronization can be based on calculations of cross-correlation between the current QRS complex and the reference complex according to the method described in greater detail below. A detected QRS complex is rotated and scaled in the rotation and scaling device 40 in a way described in greater detail below, and this is followed by morphology classification in morphology classification means 50. The morphology classification can then be performed with much greater reliability than has hitherto been possible. The classification of the QRS complex is then used for further analysis in the analysis unit 60. Examples of such analysis, based on morphology classification and which can be performed in the analysis unit 60, are averaging for S-T measurements and heart rhythm analysis. If it is assumed that up to five references, representing five different kinds of heartbeats, i.e. five different QRS complex morphologies, are stored in the storage means 32, new QRS complexes are appropriately created each time a new, measured QRS complex is not sufficiently similar to existing references, i.e. the correlation or the Frobenius norm, calculated according to the following with existing references, is below a predefined threshold value. An efficient procedure for creating references is a basic prerequisite for reliable morphology classification. The simplest way to achieve this is simply to use the first occurring QRS complex of each type as a reference. The obvious shortcoming of this method is the risk of getting references very much disturbed by noise. A common solution to this problem is to form a mean value of a number of QRS complexes in order to reduce the noise level. However, such a procedure is not suitable for use in the present invention, since a mean value for any variations in the position of the electrical axis would also be formed instead of "capturing" a direction. One advantageous procedure for achieving noise-free, representative references is instead based on an iterative use of the invention. In one such method, optimum rotation and scaling according to the invention are performed on a number, e.g. 20, of QRS complexes of the same type, with one of them serving as a temporary reference, during a "learning phase", and then forming the mean value for beats corrected in this manner. The procedure can then be repeated an optional number of times with the mean value as a reference until no additional improvement is obtained for the reference. The procedure can be additionally refined by exclusion of QRS complexes which deviate too much from the existing reference, measured with the Frobenius norm below, after optimum rotation and scaling before the mean value is formed. Signal samples in the form of an m*p matrix, where m is the number of samples and p is the number of leads used from measuring electrodes applied to the patient, are stored in the storage means 32. Sample values thus form the matrix points. The length of the QRS complex is appropriately measured in the number of samples m, the distance between each sample being constant. m can either be a fixed number of samples or be selected from calculation of the start and end points of the QRS complex. If T i designates the m*p matrix representing the reference complex number i (i = 1-5 according to the above), and B i designates the m*p matrix containing the most recently detected QRS complex after time synchronization to reference complex number i in the comparison and time synchronization means 30. Subsequent calculations to correct the direction of the electrical axis of each QRS complex, represented by the matrix B i in relation to the reference matrix T i , are performed in the rotation and scaling means 40. 1. C =B T / iT i is calculated 2. Singular value factorization of C is calculated: U T CV = Σ 3. Q = UV T is calculated 4. B ' / i = B i Q 5. is calculated 6. B i is replaced with B opt / i = α*B ' / i If e.g. the cross-correlation between the measured QRS complex and stored references is used for the time synchronization in the comparison and time synchronization means 30, it is possible to elect to correct only those QRS complexes for which the corresponding matrix B i exhibits sufficiently high correlation with the corresponding reference matrix T i . This will save processing capacity by, at an early stage, excluding morphological classes whose reference complexes are completely different from the current complex. Time synchronization in the comparison and time synchronization means 30 can be performed on the basis of the cross-correlation between the current QRS complex and the reference complex. However, the above procedure can also be implemented in the means 30 for time synchronization of the current QRS complex with the reference complex. The means 30 and the device 40 can then be incorporated into a single unit in which the steps 1 to 6 above are performed a number of times with ECG data in the matrix B shifted one sample between each calculation. The optimum time synchronization (also rotation and scaling) is then given by the difference matrix with the smallest Frobenius norm. The optimum time-synchronized, scaled and rotated matrix B i is then used as input data for the morphology classification device 50 in which the classification category is determined for the current QRS complex. Several methods for morphology classification are previously known, usually based on calculation of the cross-correlation between the current QRS complex and a reference complex. The correlation coefficient ρ is then calculated for each lead. where -1 ≤ ρ ≤ 1 where x = the heartbeat to be classified (one lead) y = the reference. The cross-correlation is suitably calculated between the starting point and the end point of the QRS complex, so the classification device 50 suitably includes some technic for determining these points of QRS complexes in the morphology classification, see e.g. Sörnmo, "A Model-based Approach to QRS Delineation", Computers and Biomedical Research, Vol. 20, pp. 526-542 (1987). After the correlation coefficient has been calculated for each lead and and each reference, threshold values are applied to determine the class to which the QRS complex is to be assigned. The present invention offers an advantageous alternative to traditional morphology classification. The Frobenius norm for the difference matrix between the reference matrix and the optimally synchronized, scaled and rotated matrix, representing the currently measured QRS complex, is thus calculated as a measure of likeness. This technic conveys the advantage that values from several leads need not be combined. One single comparison between the Frobenius norm and a threshold value is sufficient. FIGS. 3-5 show the three orthogonal leads for QRS complexes from 50-60 heartbeats, before and after optimum correction, according to the invention, by rotation in relation to "correct" reference complex, and FIG. 6 shows the changes in corresponding correlation coefficient before and after the correction. FIG. 6 shows that the correlation coefficient for lead 3, for which correlation was worst, improved considerably by correction according to the invention, whereas the other two leads, for which the correlation was high already from the beginning, were only affected marginally. It should be noted here that the scale on the vertical axis differs for the three leads shown. These figures clearly illustrate that morphology classification can be performed with much greater certainty after correction by rotation and scaling according to the invention. FIG. 7 shows diagrams corresponding to those of FIGS. 3-5 for one lead for QRS complexes from 58 consecutive beats, wherein two heartbeats risk erroneous classification due to very poor correlation in the lead shown. However, erroneous classification is no longer a risk after correction according to the invention of the direction of the electrical axis. The correlation is then high for all leads, as shown in FIG. 8. It should be noted that the vertical axis also in this figure have different scales for the three leads. One exemplefying embodiment has been described above for morphology classification of QRS complexes. However, the invention is suitable for several other applications. Instead of the QRS complex, other characteristic parts of a heart beat, such as the P wave, can be studied, as noted aboveand the invention is useful for analysis of variance ECG and for so-called serial comparison of resting ECGs in order to compensate for variations in electrode placement. The invention can also be used for monitoring of patients for longer periods of time during which the patient e.g. turns over from time to time, causing a change in the position of the electrodes in relation to the heart.

Claims: A method for correcting within a calculations unit (10) for non-physiological variations in ECG signals, the signals recorded during a heartbeat or a characteristic part of a heartbeat being conditioned and digitized, characterized in that signal samples are stored in the form of an m*p matrix where m is the number of samples and p is the number of leads used from measuring electrodes (2) applied to the patient (3), and in that the difference between this measuring matrix and a reference matrix is minimized by one or more of the operations translation, time synchronization, rotation and scaling of the measuring matrix. A method according to claim 1, characterized in that the Frobenius norm is determined for the matrix, obtained by subtraction of one of the matrices from the other, as a measure of the difference between the matrices. A method according to claim 1 or 2, characterized in that for the time synchronization, measurement data stored in the measuring matrix are shifted one sample for every new measuring matrix, whereupon the measuring matrix exhibiting the smallest difference compared to the reference matrix is selected as the time-synchronized measuring matrix. A method according to any of claims 1 to 3, characterized in that rotation and scaling operations are performed simultaneously. A method according to any of claims 1 to 4, characterized in that , for determining a reference matrix, a predefined number of selected measuring matrices are corrected according to one or more of the above operations with one of the measuring matrices serving as a temporary reference, whereupon the mean value of the corrected matrices is formed, and this mean value is set as the reference matrix. A method according to claim 5, characterized in that the procedure is repeated with the next consecutive measuring matrix and the immediately preceding mean value serving as a reference until the ensuing change in the mean value and, accordingly, the reference matrix drops below prescribed limits. A method according to claims 5 or 6, characterized in that measuring matrices which, after correction, deviate too much from existing reference matrix, measured with the Frobenius norm, are excluded from mean value determination. A method according to any of claims 1 to 7, characterized in that the time synchronization is performed first, and rotation and scaling correction are then performed only if the difference between the current measuring matrix and the reference matrix is less than prescribed limit values. A method according to any of claims 1 to 8, the measuring matrix representing the QRS complex in a heartbeat, characterized in that after correction of the measuring matrix with one or more of the above operations morphology classification of the corresponding QRS complex is performed. A method according to claim 9, characterized in that for the morphology classification of QRS complexes the Frobenius norm for the difference between a class reference matrix, representing the current morphology class, and the corrected measuring matrix in question, is calculated and compared to a predefined threshold value. A method according to claim 9, characterized in that for the morphology classification of QRS complexes the correlation coefficient for each ECG signal lead and a reference value are calculated and compared to a predefined threshold value. A method according to any of claims 1 to 8, characterized in that for serial comparison of stored resting ECG's for one and the same patient or study of beat-to-beat variability in ECG signals the reference matrix represents the immediately preceding heartbeat or characteristic part of the heartbeat. An apparatus for correcting for non-physiological variations in ECG signals, comprising means for conditioning signals picked up by measuring electrodes (2) applied to the patient (3), an A/D converter (8) for digitizing the signals and a calculation unit (10), characterized in that the calculation unit (10) comprises storage means (11, 32) for storing signal samples in the form of an m*p matrix, where m is the number of samples and p is the number of leads used from measuring electrodes (2) applied to the patient (3), and for storing a reference matrix, the calculation unit (10) being devised to minimize the difference between the measuring matrix formed from signal samples and the reference matrix by means of one or more of the operations translation, time synchronization, rotation and scaling of the measuring matrix. An apparatus according to claim 13, characterized in that the calculation unit (10) is arranged to calculate the difference between the measuring matrix and the reference matrix and to calculate, as a measure of the difference between the matrices, the Frobenius norm for this difference matrix. An apparatus according to claim 13 or 14, characterized in that the conditioning means comprises a high pass filter (5), arranged to filter out baseline variations from the ECG signals. An apparatus according to any of claims 13 to 15, characterized in that the calculation unit comprises a QRS complex detector (20) for performing the above correcting operations on detected QRS complexes. An apparatus according to claim 16, characterized in that the calculation unit comprises comparison means (30) for comparing current QRS complex with a stored reference complex. A device according to any of claims 13 to 17, characterized in that the storage means (11, 32) of the calculation unit are arranged to store measured QRS complexes and reference QRS complexes in the form of m*p matrices, and in that the calculation unit (10) is arranged to calculate, for time synchronization of measured QRS complexes, the Frobenius norm for the difference between a plurality of measuring matrices, representing measured QRS complexes, and a reference matrix, representing a reference QRS complex, measurement data stored in the measuring matrices being shifted one sample for each new measuring matrix, said calculation unit being arranged to define the QRS complex as time-synchronized when the Frobenius norm is as small as possible. An apparatus according to claim 18, characterized in that the calculation unit (10) is arranged to calculate the Frobenius norm for the difference matrix between the measuring matrix, representing the current QRS complex, and a reference matrix for different rotation positions of the electrical axis of the QRS complex, said rotation continuing until the Frobenius norm is as small as possible. An apparatus according to claim 18 or 19, characterized in that the calculation unit (10) is arranged to calculate the scaling of the measuring matrix, representing current QRS complex, which gives the smallest value of the Frobenius norm for the difference matrix between the measuring matrix and a reference matrix. An apparatus according to claim 17, characterized in that the comparison means (30) is arranged to determine cross-correlation between the current QRS complex and a stored reference complex. An apparatus according to any of claims 18 to 20, characterized in that the calculation unit comprises morphology classification means (50) for morphological classification of corrected QRS complexes. An apparatus according to claim 22, characterized in that the morphology classification means (50) is devised to calculate the Frobenius norm for the difference matrix between the reference QRS complex stored for morphology classification and measuring matrices, representing corrected QRS complexes, and to compare the calculated norm to predefined limit values. An apparatus according to claim 22, characterized in that the morphology classification means (50) is arranged to calculate, for each lead, the cross-correlation between measured, corrected QRS complexes and reference QRS complexes. An apparatus according to claim 23, characterized in that the calculation unit (10) is arranged to create a new reference QRS complex for storage in the morphology classification means (50), if the correlation coefficient between the current QRS complex and stored reference complexes is less than a predefined threshold value.

Inventors: KARLSSON PETER, LUNDSTROEM LENA, SOERNMO LEIF, KARLSSON, PETER, LUNDSTROEM, LENA, SOERNMO, LEIF, LUNDSTRÖM, Lena, Sörnmo, Leif
Applicants: SIEMENS AG, SIEMENS AKTIENGESELLSCHAFT
Application year: 1996
Main classification: A61B5
IPC codes: A61B5, G06T1, G06F17