CC BY
29
DOI: 10.6084/m9.figshare.5230339
LCC - Q300-390
ANALYSIS OF SUBTLE CHANGES IN BIOMEDICAL SIGNALS BASED ON ENTROPY PHASE PORTRAIT
Fainzilberg Leonid1'2, Orikhovska Kseniia1, Vakhovskyi Ivan2
international Research and Training Center for Information Technologies and Systems of National Academy of Sciences of Ukraine and Ministry of Education and Science of Ukraine (Kiev, Ukraine)
2National Technical University of Ukraine "Kiev Polytechnical Institute" (Kiev, Ukraine) Address for Correspondence: Fainzilberg Leonid, chief Researcher, Str. Heroyiv Dnipra, 36-17, Kyiv, Ukraine, 04214
Institutional affiliation: prosp. Glushkova, 40, Kyiv, 03680 Email: [email protected]
Abstract. A new method for evaluating subtle changes in biomedical signals, caused by external influences on the human organism, is proposed. The method is based on the analysis of chaoticness of the studied parameter, which is calculated in a sliding window along an array of observed values using different entropy estimations. A distinctive feature of the method is the transition from the calculated entropies to their mapping on the phase plane and estimation of the integral parameters of the obtained graphic image (the entropy phase portrait), in particular, the area of the convex hull.
The diagnostic value of the proposed approach in the processing of real clinical data was demonstrated, obtained under conditions of increasing physical activity, coronary artery bypass surgery and intravenous drip infusion.
Keywords: ECG; Heart rate; Phase portrait; Entropy.
Introduction. Modern systems of medical diagnostics are often based on computer processing of physiological signals that are generated by the human organism in the course of its functioning. For example, an electrocardiogram (ECG), which carries information about changes in the electrical activity of the heart, has been one of the most accessible and widespread methods of functional diagnostics in cardiology for more than a hundred years.
The rapid development of computer and information technology has laid the foundation for a new industry - computer electrocardiography. Certainly, digital electrocardiographs that support decision-
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making by a cardiologist facilitate the work of medical staff and shorten the time of obtaining the diagnosis
results.
At the same time, as experts note, computer implementation of traditional approaches to ECG processing in the time domain does not lead to the achievement of a more important goal - increasing the reliability of diagnostic results. In addition, experienced clinicians still prefer a visual interpretation of the ECG, not fully trusting computer algorithms, which sometimes lead to errors at the stage of measuring diagnostic features [1].
Doctors are guided not only by the values of diagnostic signs, but also take into account the general clinical picture and take "informal" decisions, relying on their previous experience and intuition while making a diagnosis. Therefore, in medical practice, cases where several experienced cardiologists interpret the same ECG in different ways are well known.
Computer electrocardiography is based on formal algorithms for analyzing the deviations of ECG values from population norms. In this case, both gross and subtle deviations of the ECG form have diagnostic value.
Gross deviations are a pathological (wide and deep) Q -wave, a significantly expanded QRS -complex and a number of other ECG diagnostic signs, the analysis of which is not very difficult either in visual or in computer analysis of ECG. Significantly greater problems are caused by computer analysis of subtle signal changes such as alternation or symmetrization of the T-wave, which are almost invisible in the visual analysis of the ECG, but carry important diagnostic information.
Scientists are constantly looking for new approaches to the analysis of subtle changes in the ECG-signal. One such innovative approach is phasegraphy, which is based on the transition from a scalar signal z(t) in any of the leads to its processing on the phase plane z(t), z(t), where Z(t) - is assessment of the rate of change of heart electrical activity [2].
It should be emphasized that such an approach fundamentally distinguishes a phasegraphy from analogous methods [3], based on the reflection signal in a plane with coordinates z(t),z(t -x), where x -is time log. This difference allowed expanding the system of ECG diagnostic features, based on the evaluation of the speed characteristics of the process, and thereby improving the sensitivity and specificity of ECG diagnostics.
The phasegraphy method is implemented in the domestic portable complex FAZAGRAPH®, which provided a reliable determination of the PT parameter that describes the symmetry of the repolarization section of the averaged phase trajectory [4]. Clinical studies have confirmed that the PT parameter, which until recently was underestimated by physicians in the analysis of ECG, carries important diagnostic information on the initial signs of ischemic changes in the myocardium [5,6].
The interpretive possibilities of the phasegraphy are constantly expanding. Recently, for studying the dynamics of complex biomedical systems behavior, the methods of synergetics and the theory of dynamic chaos have become popular [7]. Thanks to synergetics, it was possible to move on to understanding how in open chaotic systems ordered structures appear spontaneously as a result of nonlinear processes. For example, in [8] carried out the study of the researching some aspects of human bioelectrical activity from the deterministic chaos positions.
According to [9], not only the entropy itself but also the nature of its change in time has important information about the system properties. Based on the analysis of the entropy changing form, Anishchenko [10] found gender differences in the body's response to stressful environmental influences. In [11] a number of interesting results were obtained using the entropy method in a complex assessment of cardiovascular risk factors dynamics.
The composition of the phasegraphy includes an additional software module that provides an estimation of the chaotic ECG parameters [12]. Further development of the entropy approach for the analysis of the chaotic ECGs and other biomedical signals will provide additional information in assessing the subtle changes in the signal caused by external influences on the body (physical activity, drug therapy, surgical intervention, etc.), which means that it is an actual task both in scientific and applied importance.
The purpose of the article is to develop a new method for analyzing subtle ECG-signal changes based on sliding entropy in phase coordinates and practical testing of the method on clinical data.
Materials and Methods. Let the z(t) be ECG-signal, observed at discrete instants of time tk = kA , k =1,..,K be represented by a finite sequence of individual cycles z1(k), z2(k), ..., zM(k), where A -is the quantization step in time, M - is the total number of cycles.
Following [13], we approximate each mth zm(k) cycle by some ty(k,01,...,0G) function specified up to a finite number of unknown parameters 01,...,0G. To determine the optimal values of these parameters, we use the criterion of the minimum sum of deviations squares
where Km is the number of discrete samples z(t) on the m th cycle.
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In this case, each separate cycle zm(k) represents a point (vector) Qm = (0lm,...,QGm) in the G -
dimensional parameter space, and the sequence of observable cycles zx(k), z2(k), ..., zm(k) generates in this space a phase trajectory that uniquely corresponds to the observed signal z(t) .
As a function that describes with reasonable accuracy the cycles of real ECGs, we will use the sum of asymmetric Gaussian functions
9(k ) = E A exP
(k )2 2[av (k )]2
ve{P,Q, R, S, ST,T},
(2)
v
in which the parameters Ay and determine the values of the amplitudes and instants of time, when the v th fragment assumes extreme values, and the function bv (k) is determined by the expression
bv (t) =
№ V t <|, |b(2) V t>|.
(3)
Under the b^1 ^ b^2) function (3) makes it possible to describe asymmetrical fragments, in particular, an asymmetric T -wave, if b^1 ^ b<f).
Thus, the vth informative fragment ve{P,Q,R,S,ST,T} of the ECG cycle can be represented by only four parameters A, |v, b^, b^, and each m th cycle can be represented by a point in the 24-dimensional parameter space, i.e. vector
0m = ( AP, b? , bf, |P ,..., AT, b?> ,b?\ |T), m = 1,...,M (4)
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Since the Gaussian function is mainly concentrated on the 3 -sigma interval, it is legitimate to assume
that the moments of the beginning t(1) and the ending t(2) of each v th fragment of the ECG are related to the parameters a(v1), a(v2) and as follows:
=|av- 3<) , (5)
tf =lv+ 3aV2). (6)
It follows that the main ECG diagnostic parameters, including an additional PT parameter of the repolarization section symmetry, can be calculated using the ratios given in Table 1.
Experimental studies have shown [14] that even with a high level of interference, the error in estimating these real ECG parameters of various shapes do not exceed 1 %.
Table 1
Calculation formulas of diagnostic parameters
Parameters Calculation formulas
Q-wave duration Aß ^ g -g = 3(aQ + <)
PQ -interval duration Apß A -P =|ß+ 3(G®-agO
QT-interval duration Aßr A tf -/g) =Mt+ 3(aQ1) +aT2))
QRS-complex duration Aqrs A t^2) -= |+ 3(ag) +a^2))
RR-interval duration ARR = Ir [m]-IR [m - !], m > 2
Q-wave depth Aq
ST-segment displacement A AST
T -wave amplitude Aj<
T -wave symmetry a(2) ß = T ßT aT1}
The theory of chaos and synergetics allows us to more fully reveal and analyze the mechanisms of living complex system functioning that combines features of order and disorder, certainty and uncertainty, organization and disorganization [7].
For an integrated assessment of the parameters chaotic dynamics during the ECG recording, the following method is proposed.
MATHEMATICAL FOUNDATIONS OF THE PROPOSED METHOD
It is needed to estimate the chaoticness of the time series
ai, a2, ... , aM .
(13)
elements of which are sequences of any parameters values indicated in Table 1, for example, a sequence of RR-interval values or a sequence of parameter PT values from cycle to cycle.
We divide the series (13) into L consecutive windows containing W points, in each l th window we estimate the chaoticness H of the explored parameter values and calculate the ratio of H to the elements
chaoticness H1 in the first window:
h = H-100%, I =1,..., L, (14)
Hi
assuming, that H1 # 0.
Any mathematical method for analyzing the chaoticness of dynamic series elements can be used to estimate H . In particular, such estimation can be carried out on the basis of the Shannon entropy calculation
j
H1 =-Zp* logpl, (15)
j=1
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where pjl - frequency of hitting the j th interval A. = \a",aJ], j = 1,..., J of the time series values observed in the l th window. The thresholds a~, aJ of the intervals A;, including the alternating elements ai, determine a ratio
where 5 - specified threshold of insensitivity to changes in the parameter.
The procedure (14) can be implemented by shifting the l + 1th window towards l th at the width of window W or when the windows are shifted by one point (sliding window mode). It is clear that in the second case the amount of computation required is greater, but the graph of entropy change will be smoother. In this case, the form of such graph depends on the width of the window W and the threshold 5 (Fig. 1).
a. = mina +5(y-1), a+ = mina +5/, j = 1,..., J, (16)
105
a
100
95
h,%
110
b
105 100 95
h,%
c
100
110
105
95
I 20 ;0 SO £" i00 ¡SO M0 :00 :8I1 200 [
Fig.1. Sliding entropy graphs h(l) by estimation Pr chaoticness: a: W = 100pts., 5 = 0,1 un.; b: W = 60 pts., 5 = 0,04 un.; c: W = 30 pts., 5 = 0,02 un.;
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For the integral chaotic estimation of the parameter during ECG observation, it is proposed to move
from a series of discrete values h(l) calculated by the sliding window method to a phase portrait of entropy on the h(l), h(l) plane, where h(l) is an estimation of the first derivative of h(l) at the l th point.
Despite the fact that the procedure of numerical differentiation of noisy data refers to an incorrectly posed mathematical problem, the application of special filtration and regularization procedures [15] made it possible to obtain acceptable estimates of the derivative h(l) . As a result, it is possible to build an evident graphic representation of the phase portrait entropy as points on the h(l), h(l ) plane (Fig. 2).
h(l),% 101
99
97
96
lV» • • • •• m • m • m
« / • ' • t • • • r.* •r V • ■ •• • • • « • • • • 9 • » •
• * • • • • • • • m • • • • •
■ • » • • • • • • • • •
94
-0,21 -0,13 -0,05 0,03 0,12 h(l),°/o/c
Fig.2. Phase portrait of the Pr sliding entropy (real ECG).
It should be noted that the classical Shannon entropy (15) is invariant under the permutations of the elements in the window. For example, two sequences - regular
1, 0,1, 0,1, 0,1, 0,1, 0,1, 0,1,0
and chaotic
0,1, 0, 0, 0, 0,1,1, 0,1,1,1, 0,1 will have the same entropy values H = 1.
Therefore, for a deeper study of chaotic dynamics, it is possible to calculate permutation entropy [18] in each l th window, instead of estimation (15), which is based on the analysis of the characteristic patterns shape.
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In order to realize this possibility, we modernized the well-known procedure of calculating the
permutation entropy, and evaluated five classes of patterns using the three successive values of am_1, am, am+1 of the time series (13) (Fig. 3).
Un
n3 n4
Fig.3. Five classes of modernized permutation entropy patterns.
The permutation entropy is calculated by the formula
PEl = "Sjl ) l0& jl ) >
(17)
j=i
in which p(% j) is the frequency of the j th class pattern appearance in the l th window.
Classes of patterns are uniquely determined by sequential test of the following conditions: chss , if (am _am_l) > h A (am_am+1) >
class n2 , if (am_i _ am ) > h A (am+i_am ) >
class n3 , if (am _ am_1) > h V(am+1 _ am ) > h V (am+i _ am_l) > h, class , if (am_i _am) > h V(am _am+1) > h V (am_1 _ am+1) > h,
class , if none of the above relations holds,
in which h - is a given threshold of insensitivity to local changes in the signal.
The phase portrait can also be constructed on the basis of the approximate entropy [21] calculation and other known chaotic estimations, a review of which is presented in [12].
Note that the entropy change rate is actively studied in thermodynamic systems [16]. Despite the fact that the question of the relationship between the thermodynamic Boltzmann entropy and the Shannon
5
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entropy for the information processes description is still the subject of scientific discussions, such analogies
are still useful.
Relying on a number of fundamental ideas, contained in the papers of I.R. Prigogine [17], Y.L. Klimontovich [18], A.A. Khadartsev [19], A.A. Yashin [11], V.I. Shapovalov [9] and other scientists, it can be assumed that the shape of the entropy phase portrait and its "size" in the phase space carries additional information on the system-control capabilities of cardiohemodynamics.
For an integral estimation of the dynamics of parameter chaoticness, let's build in the normalized coordinates h(l), h(l) the convex hull of the entropy phase portrait (Fig.5) and determine the area S of the resulting polygon, as well as the coordinates of the phase portrait gravity center X, Y .
Under certain conditions, there is an unambiguous connection between the Shannon entropy and the standard deviation (RMS). For example, with a normal distribution of the random variable, which generating the series (13), this connection can be described by the logarithmic dependence
. H = 2,05+log2 RMS. (18)
Hence, it would seem that the results of the dynamic series variability analysis (13) will be equivalent if in the sliding windows, instead of entropy (15), calculate the RMS of the observed values.
h(l),% 101
97
96
94
■Ms'ti—
X ,Y
1,25
0,99
0,73
0,21
-0,05
S
•
-0,05 0,17 0,39 0,61 0,83 1,05
-0,21 -0,13 -0,05 0,03 h{l),%l C
Fig.5. The phase portrait of the sliding entropy (left) and its convex hull (right).
At the same time, entropy, unlike RMS, does not depend on the values of the observed magnitude and therefore characterizes not so much the spread but the diversity of this quantity values [22]. Therefore, processing the real data will bring different results.
Fig. 6 shows graphs of Shannon entropy H and RMS change calculated by the same sequence of RR -interval.
i
i
i
i
%
73
40 80 120 160 200 240 280 320 360 400 440 480 C
Fig.6. Graphs of entropy change H and standard deviation (RMS).
Let's consider the results demonstrating on the clinical data the possibility of the phasegraphy method for the subtle ECG changes analysis under various effects on the organism, including additional possibilities for analyzing the phase portrait of entropy (EPP).
Results. Table 2 presents the results obtained during the testing a conditionally healthy volunteer for 44 years old on a treadmill. During testing, the speed of the belt reached 5.5 km/h, and the angle of inclination gradually increased to 14 %, which in the second stage ensured the metabolic equivalent MET = 10.2. After that, the test person rested for 3 minutes.
In the process of increasing the stress, the indicator SDNN (RMS of the RR-interval) decreased by 66 % (Fig. 7), which agrees with the known data on the increase in the sympathetic part of the autonomic nervous system under stress [23]. Simultaneously with the decrease in heart rate variability, the integral index SRR, which, unlike SDNN, characterizes not the degree of dispersion, but the variety of RR-interval, increased by 60 %.
It can be assumed that the detected fact testifies that the healthy organism searches the most economical way for the heart rhythm regulation. Of course, such a hypothesis requires further studies.
Two other integral parameters characterizing the variability (RMS PT) and the variety (Spr) of the T -wave symmetry values with increasing stress and rest were unidirectional (Fig. 8). At the same time, the changes in the integral index Spr at the first stage of the stress were more pronounced than the changes in the RMS P T, but on the rest stage, the changes in the RMS pT were more pronounced. The observed effect also requires additional study.
Dynamics of changes in integral parameters for a treadmill test
#
Stage
MET
CONVEX HULLS EPP
R-R interval
Pr parameter
INTEGRAL PARAMETERS
6
Baseline
SRR = 0.497 un. XRR =0.576 un. Yrr =0.606 un. Spr = 0.217 un. Xpr =0.682 un. Ypr =0.831 un.
SDNN=58 ms СКО ßT =0.02 un.
Stress 3 min.
2.3
SRRR = 0.617 un.
XRR =0.507 un.
Yrr =0.521 un. Spr = 0.569 un. XßT =0.496 un. Y =0.751 un.
ßT
SDNN=32 ms СКО ßT =0.04 un.
Stress 15
min.
10.2
SRR = 0.794 un. XRR =0.5 un. Yrr = 0.504 un. Spr = 0.749 un. XßT =0.522 un. Ypr =0.524 un. SDNN=20 ms СКО ßT =0.09 un.
1
2
3
4
5
0
1
1
2
1
2
Rest 3 min.
Srr = 0.716 un. XRR =0.561 un.
Yrr = 0.55 un.
SpT = 0.58 un.
Xßr =0.52 un.
Yt = 0.376 un. SDNN=92 ms CKO ßr =0.08 un.
3
4
5
6
3
Fig.7. Dynamics of changes in the integral parameters of the heart rate
%
400 äOO 200 100
Fig.8. Dynamics of changes in the integral parameters of T-wave symmetry
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Interesting results were obtained in the study of subtle ECG changes in patients with CAD whom
coronary artery bypass surgery (CABG) was performed. Fig.9 shows the dynamics of the Pt parameter before and after the operative treatment of the patient M. 60 years old, owing to the lesion of the coronary arteries, three shunts were established.
Fig.9. Dynamics of the Pt parameter before and after CABG surgery
The day before the surgery, the T-wave symmetry parameter was equal Pt = 1.6 units, which was 60 % higher than the lower limit of pathological values ( Pt = 1.05 units). On the first day after the surgery, the P T values were normalized (pT ~ 0 9 units), which indicates a blood flow restoration. On the 7th day after the surgery, the value of the parameter even more closely approached the norm and reached Pt = 0.8 units, which is 50 % lower than the pathological value before the surgery. The patient successfully underwent the rehabilitation period and was discharged one week after the surgery.
It is noteworthy that against the background of the normalization of the Pt parameter, the dynamics of the entropy phase portraits were observed, which were constructed for the RR-interval and Pt parameter (Table 3). Already on the first day after the surgery, the EPP area SRR of the convex hull of the RR-interval increased by almost 82 %, and the EPP area SpT of the convex hull Pt parameter increased by 2.4 %.
The detected properties indicate the possibility of using the phasegraphy method for evaluating subtle ECG changes before and after surgery and predicting the outcome of treatment.
Dynamics of EPP before and after coronary artery bypass surgery (CABG)
RR -interval EPP
BEFORE SURGERY
SRR = 0.431 units
1 DAY AFTER SURGERY
SRR = 0.784 units
ßT
parameter EPP
Spr = 0.535 units
SpT = 0.548 units
Many medications, including those used in cardiac practice, quite often (from 30 to 70 %) have side effects [24]. Therefore, the actual task is to assess the possibilities of phasegraphy in the analysis of subtle ECG changes directly in the process of intravenous therapy.
Table 4 shows the dynamics of changes in the parameters that were observed on the patient I. ECG (76 years old) in the process of intravenous therapy of Panangin and Mexicor medications.
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Table 4
Dynamics of ECG parameters during the first dropper
Time
AVERAGE CYCLE
ECG PHASE PORTRAIT
EPP convex hull of the Pt parameter
15 min.
0,6 0,4 0,2 0 -0,2 -0.4
* ""IT""
r » s
ßT = 0.65 units
-9,04 -9,02 0 9,02
AT = 0.44 mV.
SpT = 0.764 units
25 min.
ßT = 0.71 units
-0,04 -0,02 0 0,02 0,04
AT = 0.29 mV.
SpT = 0.754 units
40 min.
ßT = 0.64 units
AT = 0.28 mV.
Spr = 0.744 units
During the entire period of drug administration, the T -wave symmetry parameter was within the normal range: Pt = 0.653 ± 0.014 units. The EPP area of the Pt parameter was stable: SpT = 0.743 ± 0.016 units.
Two days later the patient was repeatedly treated with the same drugs (Table 5).
Dynamics of ECG parameters during the second dropper
Time
AVERAGE CYCLE
ECG PHASE PORTRAIT
EPP convex hull of the ßT parameter
5
min.
ßT = 0.61 units
-0,04 -0,00 0
AT = 0.52 mV.
SpT = 0.73 units
10 min.
0,6
0.4 0,2 0 -0,2 -0,4
, T f jV~
Q n
i
ßT = 0.65 units
AT = 0.44 mV.
SpT = 0.697 units
20 min.
ßT = 0.66 units
AT = 0.38 mV.
SpT = 0.677 units
30 min.
ßT = 0.63 units
AT = 0.47 mV.
S = 0.65 units
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During the second dropper, the T -wave symmetry was also within the normal range:
Pt = 0.604 ± 0.006 units. However, noticeable changes in the shape of the average cycle were observed. These changes are caused by a 36 % increase of the T-wave amplitude, which exceeded the R -wave amplitude and led to characteristic changes in the ECG phase portrait shape.
Interestingly, that the increase in T -wave amplitude, which is likely to be associated with hyperkalemia from excessive administration of potassium preparations, was accompanied by a monotonous decrease in the EPP area SpT of the PT parameter by almost 11 %, i^. decreasing T-wave form diversity from cycle to cycle.
A serious manifestation of cardiovascular diseases is sudden cardiac death, where a patient dies almost instantly (from a few seconds to an hour) after the onset of a heart attack. One of the sudden cardiac death predictors, which has recently gained wide popularity in clinical studies, is based on the detection of the electrical alternation of the heart, which on the ECG is manifested by the elements alternation, for example, in alternating RR -interval of different duration.
Computer analysis of the alternation becomes an important characteristic of modern medical diagnostic systems. Currently, according to experts, existing computer algorithms do not provide the required reliability of detection of this effect in real clinical conditions.
We will show that the proposed method makes it possible to detect subtle changes in the signal caused by the cardiac alternation effect and to distinguish such changes from externally similar microvibrations of ECG elements not related to this effect.
Fig.10 shows the ECGs of two patients who have changes in the duration of the RR-interval. One of the ECGs belongs to a conditionally healthy man of 32 years old, the second ECG belongs to a woman of 68 years old, and who has the heart electrical alternation.
Fig.10. Real ECGs of a conditionally healthy patient (above) and a patient with an RR -interval alternation (below)
As you can see, the ECGs practically do not differ in the signal form. Despite this, differences in rhythm are clearly visible on the rhythmograms (Fig. 11), which are based on these ECGs. Note that the values of the traditional statistical parameter of heart rate variability calculated by these rhythmograms are quite close: in a healthy patient SDNN = 50 ms, and in a patient with an alternation SDNN = 62 ms.
ms
O.S
0.6
ms Q.3-
0.6-
UÜ
Fig. 11. Real rhythmograms of a conditionally healthy patient (above) and a patient with an RR-interval alternation (below)
Analysis of the convex hulls area of the RR-interval entropy phase portrait was made to detect electrical alternation of the heart. In this case, in order to construct the EPP in (14) was used expression (17), instead of (15), providing an estimation of elements chaoticness in sliding windows on the basis of permutation entropy calculation. The results are shown in Table 6.
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Table 6
Results of permutation entropy phase portraits analysis
Rhythmogram without RR-interval alternation
Srr = 0.637 units Xm = 0.363 units; Ym = 0.466 units
Rhythmogram with RR-interval alternation
Srr = 0.165 units
Xm = 0.279 units; Ym = 0.28 units
As can be seen from Table 6, on the rhythmogram with electric alternation, the area of the convex phase portrait hull of the RR-interval permutation entropy was almost 4 times less than on the healthy patient rhythmogram, although both rhythmograms had similar RR -interval mean square deviations (traditional SDNN parameter).
Thus, the change in the integral SRR parameter carries important diagnostic information about the reduction of the chaotic heart rhythm, which caused by the heart electrical alternation. Significantly changed the other two integral EPP parameters: a decrease of XRR by 23.1 % and YRR by 39.9 %.
The analysis of integral parameters of the phase portrait of permutational entropy can give important information in the differential diagnosis of other cardiac rhythm disturbances, which will be the subject of our further research.
Conclusion. The article shows that the area of the phase portrait of entropy, calculated in sliding windows according to the heart rate and symmetry of the T-wave on consecutive cycles of the electrocardiogram, carries important information on the subtle changes in the ECG-signal caused by external effects on the body (treadmill test, drug and surgical treatment of cardiac patients) and can be used as an integral diagnostic parameter.
It is also shown that, based on the calculation of the area of the permutation entropy phase portrait, it is possible to reliably detect the effect of the electrical alternation of the heart on real signals that are
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externally virtually indistinguishable from similar signals of a healthy person. This fact allows us to
construct a threshold decision rule for assessing the risk of sudden cardiac death.
The received encouraging results after confirmation of their statistical reliability on representative samples of observations open new possibilities of medical diagnostics in cardiology.
Conflict of interest statement: The authors state that there are no conflicts of interest regarding the publication of this article.
Author Contribution: Conceptualization: Leonid Fainzilberg. Data curation: Kseniia Orikhovska. Formal analysis: Ivan Vakhovskyi. Writing - original draft: Leonid Fainzilberg. Writing - review & editing: Leonid Fainzilberg.
ORCID
Fainzilberg Leonid http://orcid.org/0000-0002-3092-0794
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