Method for calculating the heart rate variability for being applied in an ECG monitor, and ECG monitor comprising an appropriate calculation programme

Abstract

A method of calculating the heart rate variability of the human heart to be used in an ECG monitor comprises the following procedural steps:

Description

BACKGROUND OF THE INVENTION

[0001] 1. Field of the Invention

[0002] The present invention relates to a method for calculating the heart rate variability of the human heart for being implemented in an ECG monitor, and an ECG monitor the operating programme of which implements said calculation programme. In this context, “ECG monitor” is to be understood as any external or implantable device which detects and evaluates ECG signals, that is, apart from actual monitors, also for instance, the respective functional components included in pacemakers and defibrillators.

[0003] 2. Background Art

[0004] Regarding the background of the invention, it has to be stated that heart rate variability is a risk indicator in the clinical practice with regard to patients having suffered from a cardiac infarction. It is therefore a declared objective of cardiology to record and evaluate the heart rate variability of such post-infarction patients in order to be able to initiate appropriate measures in case of appalling values.

[0005] Another aspect in the context of the present invention is the trend to design cardiological monitoring devices for patients suffering from heart diseases in a way so as to make the device implantable into the body of the patient. When determining the heart rate variability, the frequency spectrum of the heart rate is determined, and the ratios of the maximum values are evaluated. Usually, the frequency spectrum is analysed using the so-called “Fourier transformation” by scanning the ECG signal received by the ECG monitor during a specific scanning interval and determining from this signal a number of discrete measuring values representative of the heart rate variability, such as RR intervals.

[0006] As will be explained in greater detail in the description of the example embodiment with reference to the specific formulas, the frequency spectrum of the measuring values is calculated using the Fourier coefficients of the Fourier transformation. The Fourier coefficients themselves are calculated using a combination of the measuring values and the sinus- or cosinus-shaped Fourier vectors of the Fourier transformation. The problem of the usual Fourier transformation lies in the fact that for the mathematical implementation the (continuous) Fourier vectors have to be transformed into discrete support points. The support points are real figures reflecting the sinus- or cosinus-shaped course of the Fourier vectors. Depending upon the selected number of support points the number of multiplications required for calculating the Fourier coefficients from the Fourier vectors and the measuring values increases superproportionately. Therefore, the large number of multiplications using real figures requires an extreme calculating effort and an enormous need of memory capacity.

[0007] These high calculating and memory needs exceed by far the capacity of micro-processor systems available for implanted cardiological devices, thus rendering the application of a Fourier transformation for frequency analysis impossible as long as the prior art calculation methods and processor systems are used.

SUMMARY OF THE INVENTION

[0008] As a solution for these problems, the present invention suggests the replacement of the known (Fast) Fourier transformation in the analysis of the heart rate variability by an approximation method which, on the basis of the Fourier transformation, replaces the numerical vector values for calculating the frequency spectre of the scanned measuring values by a limited number of rough approximate vector values wherein these approximate vector values roughly reflect the course of the Fourier vectors. This method allows a considerable reduction of the calculating and memory needs and thus the application in implanted devices. The simplification is achieved by no longer presenting the Fourier vectors by support points of the sinus and cosinus functions in the form of real figures. Instead, said support points are selected as rough, integral approximate vector values, preferably based on the figures −1, 0, and +1. A preferred upper limit for the number of approximate values may be five figure values −2, −1, 0, +1, +2 symmetrically surrounding the value 0. As a whole, this “roughening” of the support points generates a sort of “fuzzy Fourier transformation”.

[0009] Suitable evaluation results have been obtained when the limit for transforming the real numerical vector values into the approximate values −1, 0, and +1 was +/−0.33. A numerical vector value between −0.33 and +0.33 results in an approximate value of 0 while numerical vector values >+0.33 or <−0.33 result in approximate values of +1 and −1, respectively. As in the conventional Fourier transformation the sum of the approximate vector values for each Fourier vector has a value of 0, it is possible in case of a deviation of the sum of approximate vector values from the 0 value to correct at least one approximate value to obtain a sum value of 0. Thus, an ostensible offset in the analyzed frequency spectre and/or a wrong peak in the calculated frequency spectre at low frequencies are avoided.

[0010] The invention further relates to an ECG monitor comprising an operating programme which implements the calculation method described above. Thus, said ECG monitor becomes implantable into the human body and/or can be integrated into a pacemaker.

[0011] Now, the calculation method according to the invention shall be explained in greater detail with respect to an example embodiment and with reference to the drawings attached hereto.

BRIEF DESCRIPTION OF THE DRAWINGS

[0012] FIG. 1 shows a comparative diagram of the sinus vector of the Fourier transformation itself and its representation by integral approximate vector values,

[0013] FIG. 2 shows a representation of the spectral components of a single sinus signal calculated using the fuzzy Fourier transformation approximation method,

[0014] FIG. 3 shows a representation of the spectral components calculated in this manner and the frequency-depending amplitudes for a mix of two sinus signals and one random signal,

[0015] FIG. 4 shows a diagram of an RR interval course from an ECG section and the spectral components calculated using the fuzzy Fourier transformation approximation method plus frequency analysis, and

[0016] FIG. 5 shows a diagram similar to FIG. 1 with corrected approximate vector values.

DESCRIPTION OF THE PREFERRED EMBODIMENT

[0017] For a better understanding of the invention, the calculation principle of the Fourier transformation shall be concisely recalled at the beginning of this description. The Fourier theorems say that a series of measuring values Ri (i=0 . . . 2N-1) can be described as 1$\begin{array}{cc}{R}_i=1/N\sum _{n=1}^{N-1}{s}_n\sin \left(\pi \mathrm{ni}/N\right)+1/N\sum _{m=0}^{N-1}{c}_m\cos \left(\pi \mathrm{mi}/N\right)& \left(1\right)\end{array}$

[0018] The spectral components sn and cn are defined by 2$\begin{array}{cc}{s}_n=\sum _{i=0}^{2N-1}{R}_i\sin \left(\pi \mathrm{ni}/N\right)=\stackrel{\_}{R}·{\stackrel{\_}{\sin }}_n{c}_0=1/2\sum _{j=0}^{2N-1}{s}_i{c}_m=\sum _{j=0}^{2N-1}{R}_i\cos \left(\pi \mathrm{mj}/N\right)=\stackrel{\_}{R}·{\stackrel{\_}{\cos }}_n& \left(2\right)\end{array}$

[0019] Thus, the Fourier coefficients result from a linear combination of the measuring value vector {overscore (R)} and the sinus- or cosinus-shaped Fourier vectors {overscore (sin)}n or {overscore (cos)}n, respectively. These Fourier vectors

{overscore (sin)}n=(0, sin (πn/N), sin (2πn/N)), . . . , sin ((2N-1) πn/N))  (3)

[0020] {overscore (cos)}n=(0, cos (πn/N), cos (2πn/N)), . . . , cos ((2N-1) πn/N)) are the system's eigenvectors.

[0021] In case of a scanning interval of At the following formula applies to the amplitude A of a frequency component f:

A (f=n/2N Δt)={square root}(sn2+cn2)  (4)

[0022] If the above equation system were implemented by a control programme in an ECG monitor, a value of N=16 in the equation system (2) would require 1024 multiplications for this discrete Fourier transformation. The eigenvectors at an 8-bit resolution and 32 eigenvectors comprising 32 components would require 1 kbyte of memory. This requirement make the use in an implanted device impossible.

[0023] The fuzzy Fourier transformation according to this invention shall now be explained with reference to FIG. 1. Using the formulas (3), the numerical vector values are replaced by rough integral approximate vector values, i.e. −1, 0, and +1. The assignment rule is as follows:

[0024] −0.33<numerical vector value<+0.33: approximate value=0

[0025] numerical vector value<−0.33: approximate value=−1

[0026] numerical vector value>+0.33: approximate value=+1

[0027] FIG. 1 shows this approximation for the magnitudes 2N=32, n=4. In the upper region, the sinus eigenvector is shown with the respective support points in the form of real numerical values. In accordance with the assignment rule mentioned above, this sinus eigenvector is transformed into the course shown in the lower region of FIG. 1. That is, the numerical vector values sin (πni/N) and cos(πni/N) of the equations (2) are replaced by −1, 0, or +1, respectively. Thus, no multiplications are required any more to calculate the magnitudes sn, and cn, but essentially only additions. Further, the components of the own vectors can be stored in the form of the approximate vector values in 2-bit resolution memories which reduces the memory need to one fourth compared with the example described above.

[0028] The aforementioned numerical approximate vector values for the fuzzy Fourier transformation may be stored in a table describing these trigonometric function approximations. Alternatively, those points in which the function values are changed according to the assignment rule mentioned above can be calculated by a small mathematical effort. This means a kind of “online calculation” of the fuzzy Fourier support points which results in saving calculating capacity and power need compared with the storage of precalculated support points.

[0029] Thus, the following equation applies to the approximate value=+1: 3$\sin \left(\pi \mathrm{ni}/N\right)\ge 0.33\Rightarrow 0.3363+/-2\pi \le \pi \mathrm{ni}/N\le 2.8053+/-2\pi \Rightarrow 0.1070N+/-2N\le \pi \mathrm{ni}\le 0.8930N+/-2N$

[0030] The approximate value 0 applies to 0.8930N+/−2N<ni<1.1070N+/−2N

[0031] The approximate value −1 applies to 4$1.070N+/-2N\le \mathrm{ni}\le 1.8930N+/-2N.$

[0032] Similarly the cosinus approximate values are calculated to obtain an

[0033] approximate value=+1, if ni>0+/−2N and <0.393 N +/−2N or >1.6070 N +/−2N and <2N +/−2N,

[0034] approximate value =−1, if ni ranges between 0.6070 N +/−2N and 1.3930 N +/−2N, and

[0035] approximate value =0, if ni is beyond the above value ranges.

[0036] As a further simplification, the equation (4) may be replaced by

A (f=n/2NΔt)≈|sn|+|cn|  (5)

[0037] The fuzzy Fourier transformation basically described above was applied in a simulation test, and the respective spectral components sn and cn were calculated and compared with the discrete Fourier transformation using exact values. As an input signal Ri the following signal was used which represented a sum of two sinus signals, one random signal and one offset:

[0038] Ri=C1 sin (δφ1i+φ′1)+C2 sin (δφ2iφ′2)+C3 Randomi[−1, . . . +1]+C4

[0039] The amplitude coefficients C1, C2, C3 and C4 and the phase coefficients δφ1, φ′1, and φ′2 are freely selectable.

[0040] As a simulation test, a single sinus signal was calculated with δφ1=5π/19 and φ′1=π/4. The amplitude coefficients C2, C3 and C4 were set to 0.

[0041] The discrete Fourier transformation results in only one single discrete peak in the cn course at n=5 as the phase displacement of π/4 assumes a cosinus signal. In FIG. 2, this peak is not actually shown.

[0042] The application of the fuzzy Fourier transformation approximation method results in the courses of the spectral components sn and cn shown in FIG. 2. It is completely obvious that the approximation method also reproduces the peak at n=5 in the spectral component cn, which provides an evidence for the correctness of the approximation method. However, the base lines of sn and cn do not constantly equal 0 but vary around this value. Up to 20 % of the maximum amplitude value are reached, but this is tolerable.

[0043] The result of a more complex simulation using the input signal mentioned above is shown in FIG. 3. Here, a mix of two random sinus signals having the following parameters was used as basis:

C1=C2=0.5 C3; δφ1=5π/19; φ′1=0; δφ2=9π/19; φ′1=π/4

[0044] FIG. 3 shows the two spectral components sn and cn and the frequency-dependent amplitude A calculated using the formula (5). The results obtained by using the approximation method according to this invention are drawn as uninterrupted lines and the results obtained from the discrete Fourier transformation as dotted lines.

[0045] A comparison between the two signal courses in the various parts of the diagram shows that the results of the discrete and of the fuzzy Fourier transformation method are very similar which renders the approximation method useful. Only the base line of the frequency-dependent amplitude A(f) in the lowest part of FIG. 3 has been raised by the random portion. However, although the random signal is twice as large as the two sinus signals the existence of these two signals is visible in the frequency spectrum at n=5 and n=9.

[0046] FIG. 4 shows the evaluation results using the approximation method according to this invention in a concrete, practical example. The uppermost diagram in FIG. 4 shows a portion of the measurement of the RR intervals determined from an ECG signal by scanning at a scanning interval of 1.25 sec. It is obvious that the period duration of the RR intervals varies between approx. 970 and 1,130 ms.

[0047] When using the discrete Fourier transformation and the aforementioned approximation method, both calculation types result in maximum values at n=3 and n=14 as can be seen in the lower diagram of FIG. 4. These two maximum values represent frequencies of 0.075 Hz and 0.35 Hz, respectively.

[0048] During the use of the approximation method, it was also found that the condition applicable to the discrete Fourier transformation requiring that the sum of the components of a single eigenvector (except the vector cos0) equals 0 is not met by some approximations of the cosinus eigenvectors. A sum of −2 or 2 was obtained as shown as a dashed line of the approximate vector values in the lower diagram of FIG. 5. This would result in a very low-frequent peak in the calculated frequency spectrum. To avoid this, the approximate vector values are corrected so that the sum value equals 0. In the example shown in FIG. 5, two approximate values equalling 0 are raised to be +1 as indicated by the two arrows. This correction results in a sum of 0 of the approximate vector values.

[0049] Finally, it should be noted that the vector length 2N has a significant influence on the accuracy of the fuzzy Fourier transformation. If it is possible to split the length N into a plurality of smaller vectors of an equal length 1, so that N=n•1 applies, similar approximations occur several times during the transformation of the eigenvectors. In certain frequencies, this may produce considerable secondary maximum values up to 30 % in the calculated frequency spectre A(f). So the optimum vector length is one in which the length N corresponds to a prime number, i.e.

2N=2•prime number.

[0050] In the examples described above, the value of 2N=2•19=38.

[0051] The following tables 1 and 2 show suitable approximate vector values for the own vectors sinn,i and cosn,i.

Claims

1. A method of calculating the heart rate variability of the human heart to be used in an ECG monitor, said method comprising the steps of: scanning of an ECG signal received from the ECG monitor during a scanning interval, determining from the scanned ECG signals a number of discrete measuring values representative of the heart rate variability, and evaluating these discrete measuring values on the basis of a Fourier transformation, wherein a frequency spectrum of the measuring values is calculated from Fourier coefficients of the Fourier transformation, which are for their turn calculated from a combination of said measuring values with sinus- and cosinus-shaped Fourier vectors of the Fourier transformation wherein the Fourier vectors are involved in the calculation in a form of a number of discrete real numerical vector values, and replacing of the numerical vector values for calculating the frequency spectrum of the scanned measuring values by rough, integral approximate vector values of a limited number which roughly reproduce the course of the Fourier vectors.

2. A method according to claim 1, wherein a maximum of 5 numerical values symmetrically surrounding the value zero are used as rough approximate values for said Fourier vectors.

3. A method according to claim 2, wherein −1, 0, and +1 are used as approximate values for the Fourier vectors.

4. A method according to claim 3, wherein said approximate values are made dependent from the actual numerical vector values as follows: −0.33<numerical vector value<+0.33: approximate value=0 numerical vector value<−0.33: approximate value =−1 numerical vector value>+0.33: approximate value=+1.

5. A method according to claim 4, wherein the assignment of the approximate values to the actual numerical vector values is stored as a table in said ECG monitor.

6. A method according to claim 4, wherein the approximate values are assigned by calculating those points in which the approximate vector values are changing.

7. A method according to claim 1, wherein the sum of the approximate vector values for each Fourier vector is formed and wherein in case of a deviation from the value 0 at least one approximate value is corrected in order to obtain a sum value of 0.

8. An ECG monitor comprising an operating programme, wherein said operating programme implements a calculation method according to claim 1.

9. An ECG monitor according to claim 8, wherein said ECG monitor is implantable into a human body.

10. An ECG monitor according to claim 8, wherein said ECG monitor is integrated into a pacemaker.