Computational and Mathematical Methods in Medicine
Volume 2015 (2015), Article ID 983479, 7 pages
http://dx.doi.org/10.1155/2015/983479

Research Article

Computation of Nonlinear Parameters of Heart Rhythm Using Short Time ECG Segments

Berik Koichubekov, Ilya Korshukov, Nazgul Omarbekova, Viktor Riklefs, Marina Sorokina, and Xenia Mkhitaryan

Department of Medical Biophysics and Informatics, Karaganda State Medical University, Gogol Street 40, Karaganda 100008, Kazakhstan

Received 10 June 2014; Revised 15 September 2014; Accepted 30 September 2014

Academic Editor: Konstantin G. Arbeev

Copyright © 2015 Berik Koichubekov et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

Abstract.

We propose the method to compute the nonlinear parameters of heart rhythm (correlation dimension and correlation entropy ) using 5-minute ECG recordings preferred for screening of population. Conversion of RR intervals’ time series into continuous function allows getting the new time series with different sampling rate dt. It has been shown that for all dt (250, 200, 125, and 100 ms) the cross-plots of and against embedding dimension for phase-space reconstruction start to level off at . The sample size at different sampling rates varied from 1200 at dt = 250 ms to 3000 at dt = 100 ms. Along with, the and means were not statistically different; that is, the sampling rate did not influence the results. We tested the feasibility of the method in two models: nonlinear heart rhythm dynamics in different states of autonomous nervous system and age-related characteristics of nonlinear parameters. According to the acquired data, the heart rhythm is more complex in childhood and adolescence with more influential parasympathetic influence against the background of elevated activity of sympathetic autonomous nervous system.

1. Background

Heart rate variability (HRV) is a noninvasive measurement of cardiovascular autonomic regulation. Specifically, HRV is a measurement of the interaction between sympathetic and parasympathetic activity in autonomic functioning. The analysis of heart rate variability is based mainly on analysis of RR intervals. RR intervals are the series of time intervals between heartbeats. There are two main approaches for analysis: time domain analysis of HRV and frequency domain analysis. Recent results on HRV signal analysis show that its dynamic behavior involves nonlinear components that also contribute in the signal generation and control. There are publications thoroughly elaborating the effectiveness of linear and nonlinear techniques in analyzing heart rate variability [1–3]. Many authors agree that nonlinear methods complement the linear ones. In some cases, these methods may uncover hidden abnormalities or alterations in heart rate and have prognostic value. Previous studies have assessed gender and age-related differences in some nonlinear components of HRV [4–6]. There also seemed to be a significant difference between day and night observation of HRV nonlinear indices using spectral and time domain methods [6].

Some authors suggested detecting and classifying arrhythmia based on nonlinear modeling of ECG [7, 8], predicting various cardiovascular diseases like ventricular tachycardia and congestive heart failure [9]. Chua et al. [10] introduced a method to extract bispectral entropy from HR signals by employing Higher Order Spectra techniques. In their study, HOS features from HR signals were used to differentiate between a normal heartbeat and seven arrhythmia classes.

Based on nonlinear parameters there are methods developed for fetal heart rate classification [11], spotting heart rhythm patterns in patient with diabetes [12], and detecting ventricular fibrillation [13]; the fractal structure of heart rate variability was identified in obese children [14]; the concurrent linear and nonlinear analysis of normal and CAD-affected heart rate signals was conducted [15]. Schubert et al. applied a dimensional complexity measure to heart rate time series in two stress conditions: chronic stress reported by healthy subjects and acute stress to psychologically challenging speech task stressor [16]. Su et al. analyze the dynamics of the heart rate signal before, during, and after an epileptic event [17]. Some authors reported the association between the HRV correlation dimension of patients with various clinical disorders and their survival prognosis [18].

The advantages of one group of methods over another are not yet that obvious. Possibly, it is because of the yet unknown mechanisms of complex heart rate regulation leading to the changes in specific nonlinear parameters. There is only a prevailing opinion that nonlinear dynamics of heart rate is the result of joint effect of parasympathetic and sympathetic influences.

For example, the correlation dimension gives the information about the number of independent functional components necessary to describe the underlying system and the degree of nonlinear coupling between these components. In biological systems, the higher the is, the more degrees of freedom the system has and, therefore, the greater range of possible adaptive responses is. The correlation dimension is usually calculated through the correlation integral using the algorithm of Grassberger and Procaccia [19]. There has been a lot of research lately on dimension of heart rhythm. The authors focused on investigating dimension of normal sinus rhythm, including the effect of circadian rhythms, influence of autonomous nervous system, and rhythm after heart transplants and in different pathologic conditions [20–25].

The correlation integral is also used to calculate the correlation entropy . Meanwhile, the correlation entropy describes the behavior of a system in terms of randomness and quantifies information about underlying dynamics. It is a dynamic measure and represents the rate at which information needs to be created as the chaotic system evolves in time. Entropy refers to system randomness, regularity, and predictability and allows systems to be quantified by rate of information loss or generation. Traditionally, has been much less popular compared to as a discriminating statistic in analyzing time series in practice. However, has a significant and more relevant status, especially in the context of colored noise contamination, as indicated by many authors [26–28].

Nevertheless, there are still significant methodological problems of computation of nonlinear parameters, one of which is the choice of minimally acceptable sample size of RR intervals time series. Different criteria exist for minimal length of time series for analysis. For example, Tsonis criterion defines minimal length as , where is assumed correlation dimension of reconstructed attractor [29]. According to other criteria, [30], [31], or [32]. Finally, there is an opinion that the minimal series length depends not only on dimension parameters but also on process autocorrelation, and (where is autocorrelation time, i.e., number of steps till its first zero or minimum, and is embedding dimension) [33].

To fulfill these requirements, the RR intervals’ time series could be as long as 10000 intervals or even more, which, at the average heart rate of 70 per minute, requires more than 2 hours of ECG recording. In majority of publications, the data belongs to 24-hour monitoring of ECG; some researchers use time series of 500 to 1000 intervals without providing any rationale [15, 34–36]. In mass screenings and in some functional probes, such long recordings are not possible. The most preferable recording time at these situations is 5 minutes as recommended by Task Force of the European Society of Cardiology and the North American Society of Pacing and Electrophysiology [37].

Our goal was to develop the method to calculate the nonlinear parameters using 5-minute ECG recordings. We applied and tested our method in calculation of correlation dimension and correlation entropy. However, using the same approach, one could also calculate other nonlinear parameters.

2. Materials and Methods

We analyzed 383 ECG recordings of practically healthy subjects aged 8 to 63. We sampled the ECG signals at a rate of 1,000 Hz and digitized them with a 16-bit analog-to-digital converter. The digitized signal was then averaged by shifting window of 32 ms to get rid of high-frequency noise. The modified Pan and Tompkins real-time QRS detection algorithm [38] was used to automatically detect R-waves and build RR interval series. According to its authors, this time-frequency algorithm has the reported correct detection rate of 99.3%. The original RR interval series were resampled by cubic spline interpolation using sampling time to obtain equidistantly sampled time series , (Figure 1).

Figure 1: Resampling of RR series.

To provide the rationale for parameters of the proposed method, we processed 38 sequences of RR intervals of persons aged 18–25 and 27 sequences of children aged 12-13 recorded for 5 minutes in rest. Quantization of the acquired continuous function at 5-minute interval of registration was done at different sampling rate of 250, 200, 125, and 100 ms.

We then computed the correlation dimension and entropy of these reprocessed time series using the algorithm proposed by Grassberger and Procaccia [19] with % from SDRR (standard deviation of RR intervals) [38].

Correlation dimension () is a useful measure of self-similarity of a signal. According to the algorithm, correlation integral function is constructed first. The correlation integral, which counts the fraction of pairs () whose distance is smaller than , is defined by

where and indicate phase-space trajectory points, is total amount of phase-space points, is the Heaviside step function, if , and if .

Correlation dimension is computed as

will have higher value if RR intervals vary more and vice versa.

Correlation entropy () characterizes the probability of visiting space points by the trajectory of the examined system. If entropy reaches zero, the system becomes completely predictable. This is the case of regular processes. For truly random processes, the entropy is unlimitedly large. Entropy of “limited chaos” is positive but has the terminal value. The numerical entropy value quantitatively characterizes the level of system orderliness and is computed as

with the same procedures used as for correlation dimension.

We used TISEAN software to compute these parameters. The given method was then tested in two models.

The first model included persons with different autonomic balancing of heart rate regulation. This balancing may be measured by HRV spectral characteristics. The amplitude of high-frequency (HF) component of HRV spectrum (ranged from 0,16 to 0,40 Hz) is considered to be related to vagal influence on heart rate [39]; the low frequency (LF) component at the same time is considered to be the market of sympathetic activity [40]. Correspondingly, the LF/HF ratio could be used to measure the level of autonomic balancing of heart rate regulation.

Using LF/HF, we selected three groups among the subjects included into research. The first group () included the subjects with higher parasympathetic influence (LF/HF = 0,514 ± 0,041); the second group () included subjects with balanced regulation (LF/HF = 1,130 ± 0,049); in the third group (), balancing was shifted towards sympathetic autonomous regulation (LF/HF = 3,474 ± 0,325).

We also tested the second model of age-related properties of nonlinear dynamics of heart rate. We used such a model because of certain knowledge on interrelation of neural regulation mechanisms and structural and functional development of organs and systems in different periods of human life. Relying on this knowledge, we could make assumptions about involvement of different parts of autonomous nervous system into the heart rate regulation and about mechanisms of aperiodic oscillations in HRV. We computed and in the following age groups: 8–13 (), 14–17 (), 18–21 (), 22–35 (), 36–55 (), and 55–63 () years of age.

We used one-way ANOVA followed by Scheffé’s test for multiple comparisons to compare various groups. Differences with were considered to be statistically significant.

3. Results and Discussion

3.1. Rationale for the Choice of Computation Parameters

Since different sampling time produces time series with different sample size, we had to make sure how that influenced computation of nonlinear parameters and what should be embedding dimension for phase-space reconstruction. To do that, we calculated correlation dimension of each time series using different embedding dimensions and sampling time .

If the examined system contains determined chaos, the cross-plot of against is initially rising and then levels off. Table 1 and Figure 2 show the results of such computations for adult ECG. It is obvious that, for all starting with , the changes in become statistically insignificant and cross-plots level off.

Table 1: Means (standard deviations) of correlation dimension using different sampling times.

Sampling time
= 100 ms
= 125 ms
= 200 ms
= 250 ms

Embedding dimension
Mean (SD)
Mean (SD)
Mean (SD)
Mean (SD)

m = 1
0,943 (0,037)
0,943 (0,037)
0,939 (0,037)
0,941 (0,037)

m = 2
1,845 (0,111)*
1,844 (0,105)*
1,843 (0,099)*
1,841 (0,105)*

m = 3
2,66 (0,277)*
2,69 (0,253)*
2,708 (0,222)*
2,724 (0,228)*

m = 4
3,448 (0,425)*
3,525 (0,29)*
3,511 (0,284)*
3,499 (0,308)*

m = 5
4,14 (0,462)*
4,244 (0,512)*
4,235 (0,462)*
4,178 (0,493)*

m = 6
4,57 (0,561)*
4,736 (0,518)*
4,628 (0,752)*
4,645 (0,684)*

m = 7
4,857 (0,888)*
4,992 (0,777)*
5,101 (0,808)*
4,981 (0,783)*

m = 8
4,992 (0,771)*
5,177 (0,992)*
5,163 (0,992)*
5,321 (0,875)*

m = 9
4,922 (0,814)
5,264 (0,925)
5,193 (0,986)
5,304 (1,023)

m = 10
4,996 (0,083)
5,364 (0,931)
5,412 (1,054)
5,637 (1,147)

m = 11
5,051 (0,863)
5,451 (0,888)
5,62 (1,091)
5,575 (1,042)

m = 12
5,133 (0,814)
5,631 (0,826)
5,717 (0,962)
5,732 (1,153)

m = 13
5,18 (0,826)
5,741 (0,974)
5,889 (1,103)
5,847 (1,251)

Statistically significant changes with m from 1 to 13 (Scheffé’s test, P < 0.05).

Figure 2: Dependence of correlation dimension on embedding dimension for phase-space reconstruction.

Since physiological data tends to have significant intragroup variability and mean data does not always reflect individual patterns, we propose computing   as the average of three measurements at .

The sample size at different sampling time was from 1200 at  ms to 3000 at  ms. At this, on average, the values of correlation dimension were not statistically significant (Table 2); that is, sampling time did not influence the results. We got similar results analyzing ECG in children. Since the children’s heart rhythm has different pattern compared to adults, we tested out assumptions in the second sample of junior schoolchildren aged 12-13. The differences in means at different were not statistically significant (Table 2).

Table 2: Means (standard deviations) of correlation dimension at different sampling times of ECG in adults and children.

Age group
Sampling time
ANOVA test

= 100 ms
= 125 ms
= 200 ms
= 250 ms

Mean (SD)
Mean (SD)
Mean (SD)
Mean (SD)

Adults
5,069 (0,815)
4,959 (0,861)
5,041 (1,132)
5,062 (1,142)
n.s.

Children
5,757 (0,784)
5,814 (0,821)
5,851 (0,956)
5,745 (0,748)
n.s.

We also had to provide the rationale for selection of the same parameters for computation of correlation entropy . As obvious from Table 3 and Figure 3, its values decrease with the increase of and then start to level off when embedding dimension at all .

Table 3: Means (standard deviations) of correlation entropy using different sampling times.

Sampling time
= 100 ms
= 125 ms
= 200 ms
= 250 ms

Embedding dimension
Mean (SD)
Mean (SD)
Mean (SD)
Mean (SD)

m = 1
9,764 (1,123)
9,829 (1,139)
9,751 (1,202)
9,868 (1,185)

m = 2
9,407 (1,360)
9,204 (1,291)*
8,709 (1,232)*
8,418 (1,183)*

m = 3
7,766 (0,930)*
7,486 (0,852)*
7,066 (0,861)*
6,806 (0,877)*

m = 4
6,493 (0,941)*
6,612 (0,975)*
5,771 (0,717)*
5,750 (0,758)*

m = 5
5,664 (0,846)*
5,788 (0,701)*
5,346 (0,514)
5,109 (0,829)*

m = 6
4,951 (0,790)*
5,114 (0,719)*
4,917 (0,714)
4,448 (0,660)*

m = 7
4,580 (0,927)
4,553 (0,770)*
4,146 (0,917)*
4,285 (0,828)

m = 8
4,215 (0,691)
4,423 (0,570)
3,983 (0,697)
4,006 (0,626)

m = 9
4,140 (0,663)
3,905 (0,458)*
3,617 (0,776)
3,402 (0,590)*

m = 10
3,927 (0,783)
3,926 (0,645)
3,477 (0,739)
3,210 (0,492)

m = 11
3,867 (0,749)
3,809 (0,548)
3,167 (0,721)
3,178 (0,581)

m = 12
3,674 (0,622)
3,579 (0,492)
3,111 (0,651)
3,050 (0,505)

m = 13
3,665 (0,708)
3,296 (0,634)
2,993 (0,661)
2,757 (0,642)

m = 14
3,565 (0,645)
3,255 (0,676)
2,977 (0,592)
2,665 (0,470)

m = 15
3,428 (0,552)
3,262 (0,663)
2,923 (0,719)
2,574 (0,492)

Statistically significant changes with m from 1 to 13 (Scheffé’s test, P < 0.05).

Figure 3: Dependence of correlation entropy on embedding dimension for phase-space reconstruction.

Table 4 displays the means of correlation entropy at different . We can see from this data that, at  ms, is statistically significantly reduced. Apparently, it is due to the smaller sample size ( at  ms). The largest sample size is at  ms, at this  , which is the closest to the specified requirements. That is why we considered it  reasonable to compute the same way as at  ms.

Table 4: Means (standard deviations) of correlation entropy at different sampling times of ECG.

Parameter
Sampling time

= 100 ms
= 125 ms
= 200 ms
= 250 ms

Mean (SD)
Mean (SD)
Mean (SD)
Mean (SD)

3,915 (0,428)
3,942 (0,428)
3,534 (0,418)*
3,459 (0,362)

Statistically significant changes compared to previous (Scheffé’s test, P < 0.05).

3.2. Nonlinear HRV in Persons with Different Balancing of Autonomous Nervous System

Table 5 presents the results of computing correlation dimension and correlation entropy in groups with different balancing of activity of sympathetic and parasympathetic autonomous nervous systems. We see that when autonomous balancing shifts towards sympathetic regulation, the correlation dimension and entropy decrease; Group 3 has even statistically significant differences from Group 2.

Table 5: Nonlinear parameters of HRV in groups with different balancing of activity of autonomous nervous system.

Group 1
Group 2
Group 3

5,782 (1,068)
5,671 (1,106)
5,063 (1,342)*

4,556 (0,805)
4,506 (0,733)
4,110 (0,854)*

Statistically significant differences from the previous group (Scheffé’s test, P < 0.05).

The analysis of age-related differences indicated that the most complex heart rate dynamics was in junior and adolescent age groups of 8–13 and 14–17 years of age (Table 6). In comparison to 14–17-year olds, the age group of 18–21 had statistically lower values of and .

Table 6: Means (standard deviations) of HRV nonlinear parameters in different age groups.

Age groups, years of age

8–13
14–17
18–21
22–35
36–55
Older than 55

Mean (SD)
Mean (SD)
Mean (SD)
Mean (SD)
Mean (SD)
Mean (SD)

5,96 (0,70)
6,06 (0,63)
5,11 (0,73)*
4,92 (0,89)
4,37 (0,64)*
3,78 (1,65)*

4,37 (0,52)
4,72 (0,51)*
3,94 (0,50)*
3,85 (0,57)
3,60 (0,64)*
3,38 (0,95)*

Statistically significant differences from the previous group (Scheffé’s test, P < 0.05).

Starting with age group of 22–35, the heart rate dynamics becomes simpler; the rhythm becomes less “chaotic” and more regular due to increased sympathetic activity. It is known that, starting with this age, the variation of RR intervals decreases; that is, the sympathetic nervous system starts to exercise its stabilizing effect. These processes are even more expressed in the age group of 55 and older, which is characterized by the lowest values of nonlinear parameters, that is, displaying the most regular rhythm without significant “chaotic” modulations.

Thus, our research provides the rationale for computation method of correlation dimension and correlation entropy using short (5-minute-long) HRV segments, which is especially important for mass screening outside the lab conditions. For this, the 5-minute RR intervals time series is presented as continuous function . This function is then transformed into a new discrete time series through quantization with the sampling time  ms. Then, the phase trajectory is reconstructed using the time delay method with time delay selected as the first minimum of autocorrelation function. The correlation dimension and correlation entropy are then computed using the presented algorithm with parameters % of SDRR averaged for .

We proved the rationale for the proposed method using it to measure autonomous balancing. According to acquired results, the autonomous nervous system significantly affects heart rate irregularity. The largest complexity and “chaotic character” of heart rhythm are  observed in persons with predominant influence of parasympathetic branch of autonomous nervous system. The shift towards sympathetic regulation brings, on contrary, the regularity and makes the heart rhythm less “chaotic” and simpler in dynamics. Nevertheless, the outcome is not simply the sum of these influences but the result of simultaneous activation of both sympathetic and parasympathetic branches of autonomous nervous system. We confirmed this fact analyzing nonlinear parameters in different age groups. It is known that, by the age of ten, the cholinergic influence becomes predominant, but adrenergic mechanisms still play a role. Adrenergic influences affect different pieces of acetylcholine metabolism, defining the development speed of cholinergic regulation of heart. The joint effect of both sympathetic and parasympathetic effects causes changes in heart rhythm, including its irregular component. According to our data, the childhood and adolescence are characterized by the most complex heart rate dynamics, when parasympathetic nervous system plays a dominant role against the background of elevated tonus of sympathetic branch. Similar results were acquired in the research of autonomous nervous system reaction to cold pressure test as well as in the experiment with intravenous administration of different doses of noradrenaline, accompanied by the reduction of heart rate and elevation of blood pressure [41, 42].

4. Conclusion

Even though the nonlinear methods are currently widely used to analyze the heart rate in different functional conditions and diseases, the computation methods used are not standardized as it has been done for linear parameters [37]. It would be convenient to use 5-minute ECG recordings as the basic methodology. Our proposed method of computation may become the basis for such standardization. We displayed its suitability for computation of and , but there is a need for further research to show its application to calculation of other nonlinear parameters.

Conflict of Interests

The authors declare that there is no conflict of interests regarding the publication of this paper.

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