Abstract
Entropy measures have been widely used in analyzing neural signals from micro- to macroscales for the normal or abnormal brain assessment. As it is unrealistic to systematic analysis in all the information entropy-based indices in different application areas within limited chapters, we mainly focus on the comparison of the capability of 12 entropy indices derived from electroencephalogram (EEG) for monitoring depth of anesthesia (DoA) and detecting the burst suppression pattern (BSP), in anesthesia induced by GABAergic agents.
Twelve indices were included: response entropy (RE) and state entropy (SE); three wavelet entropy (WE) measures (Shannon WE (SWE), Tsallis WE (TWE), and Renyi WE (RWE)); Hilbert–Huang spectral entropy (HHSE); approximate entropy (ApEn); sample entropy (SampEn); Fuzzy entropy (FuzzyEn); and three permutation entropy (PE) measures (Shannon PE (SPE), Tsallis PE (TPE), and Renyi PE (RPE)). Two EEG data sets recorded from sevoflurane-induced and isoflurane-induced anesthesia, respectively, were selected to assess the capability of each entropy index in DoA monitoring and BSP detection. To validate the effectiveness of these entropy algorithms, pharmacokinetic/pharmacodynamic (PK/PD) modeling and prediction probability (P k ) analysis were applied.
All the entropy indices could track the changes of anesthesia states. Three PE measures outperformed the other entropy indices, with less baseline variability, higher coefficient of determination (R 2) and prediction probability, and RPE performed best; while ApEn and SampEn discriminated BSP best.
Each entropy index has its advantages and disadvantages in estimating DoA. Overall, it is suggested that the RPE index has a superior performance. Investigating the advantages and disadvantages of these entropy indices could help improve current clinical indices for monitoring DoA.
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Abásolo D, et al. Entropy analysis of the EEG background activity in Alzheimer’s disease patients. Physiol Meas. 2006;27(3):241.
Ahmed MU, Mandic DP. Multivariate multiscale entropy: a tool for complexity analysis of multichannel data. Phys Rev E. 2011;84(6):061918.
Arefian NM, et al. Clinical analysis of eeg parameters in prediction of the depth of anesthesia in different stages: a comparative study. Tanaffos. 2009;8(2):46–53.
Aziz W, Arif M. Multiscale permutation entropy of physiological time series. In: 9th International multitopic conference, IEEE INMIC 2005; 2005, IEEE.
Bandt C. Ordinal time series analysis. Ecol Model. 2005;182(3):229–38.
Bandt C, Pompe B. Permutation entropy: a natural complexity measure for time series. Phys Rev Lett. 2002;88(17):174102.
Bell IR, et al. Nonlinear dynamical systems effects of homeopathic remedies on multiscale entropy and correlation dimension of slow wave sleep EEG in young adults with histories of coffee-induced insomnia. Homeopathy. 2012;101(3):182–92.
Bezerianos A, Tong S, Thakor N. Time-dependent entropy estimation of EEG rhythm changes following brain ischemia. Ann Biomed Eng. 2003;31(2):221–32.
Bruhn J, Röpcke H, Hoeft A. Approximate entropy as an electroencephalographic measure of anesthetic drug effect during desflurane anesthesia. Anesthesiology. 2000;92(3):715–26.
Bruhn J, et al. Shannon entropy applied to the measurement of the electroencephalographic effects of desflurane. Anesthesiology. 2001;95(1):30–5.
Bruhn J, et al. Depth of anaesthesia monitoring: what’s available, what’s validated and what’s next? Br J Anaesth. 2006;97(1):85–94.
Burton D, Zilberg E. Methods and apparatus for monitoring consciousness. 2002. wo patent wo/2002/100,267.
Cao Y, et al. Detecting dynamical changes in time series using the permutation entropy. Phys Rev-Ser E. 2004;70(4; PART 2):46217–46217.
Cao Y, et al. Characterization of complexity in the electroencephalograph activity of Alzheimer’s disease based on fuzzy entropy. Chaos. 2015;25(8):083116.
Chen Y, Yang H. Multiscale recurrence analysis of long-term nonlinear and nonstationary time series. Chaos, Solitons Fractals. 2012;45(7):978–87.
Chen W, et al. Characterization of surface EMG signal based on fuzzy entropy. Neural Syst Rehabil Eng, IEEE Trans. 2007;15(2):266–72.
Chen W, et al. Measuring complexity using FuzzyEn, ApEn, and SampEn. Med Eng Phys. 2009;31(1):61–8.
Chen D, et al. GPGPU-aided ensemble empirical-mode decomposition for EEG analysis during anesthesia. Inf Technol Biomed IEEE Trans. 2010;14(6):1417–27.
Costa M, Goldberger AL, Peng C-K. Multiscale entropy analysis of complex physiologic time series. Phys Rev Lett. 2002;89(6):068102.
Costa M, Goldberger AL, Peng C-K. Multiscale entropy analysis of biological signals. Phys Rev E. 2005;71(2):021906.
Escudero J, et al. Analysis of electroencephalograms in Alzheimer’s disease patients with multiscale entropy. Physiol Meas. 2006;27(11):1091.
He L, et al. Feature extraction with multiscale autoregression of multichannel time series for P300 speller BCI. In: Acoustics speech and signal processing (ICASSP), 2010 IEEE International Conference on. 2010, IEEE.
Hsu W-Y, et al. Wavelet-based fractal features with active segment selection: application to single-trial EEG data. J Neurosci Methods. 2007;163(1):145–60.
Hu M, Liang H. Perceptual suppression revealed by adaptive multi-scale entropy analysis of local field potential in monkey visual cortex. Int J Neural Syst. 2013;23(2):1350005.
Huang NE, et al. The empirical mode decomposition and the Hilbert spectrum for nonlinear and non-stationary time series analysis. Proc R Soc London, Ser A. 1998;454(1971):903–95.
Inouye T, et al. Quantification of EEG irregularity by use of the entropy of the power spectrum. Electroencephalogr Clin Neurophysiol. 1991;79(3):204–10.
Inuso G, et al. Brain activity investigation by EEG processing: wavelet analysis, kurtosis and Renyi’s entropy for artifact detection. In: Information acquisition. 2007. ICIA’07. International Conference on; 2007, IEEE.
Jameson LC, Sloan TB. Using EEG to monitor anesthesia drug effects during surgery. J Clin Monit Comput. 2006;20(6):445–72.
Klockars JG, et al. Spectral entropy as a measure of hypnosis and hypnotic drug effect of total intravenous anesthesia in children during slow induction and maintenance. Anesthesiology. 2012;116(2):340–51.
Labate D, et al. Entropic measures of EEG complexity in Alzheimer’s disease through a multivariate multiscale approach. Sensors J, IEEE. 2013;13(9):3284–92.
Li X. Temporal structure of neuronal population oscillations with empirical model decomposition. Phys Lett A. 2006;356(3):237–41.
Li X, Ouyang G, Richards DA. Predictability analysis of absence seizures with permutation entropy. Epilepsy Res. 2007;77(1):70.
Li X, Cui S, Voss LJ. Using permutation entropy to measure the electroencephalographic effects of sevoflurane. Anesthesiology. 2008a;109(3):448.
Li X, et al. Analysis of depth of anesthesia with Hilbert–Huang spectral entropy. Clin Neurophysiol. 2008b;119(11):2465–75.
Li D, et al. Multiscale permutation entropy analysis of EEG recordings during sevoflurane anesthesia. J Neural Eng. 2010;7(4):046010.
Li D, et al. Parameter selection in permutation entropy for an electroencephalographic measure of isoflurane anesthetic drug effect. J Clin Monit Comput. 2012;27(2):113–23.
Liang H, Lin Z, McCallum R. Artifact reduction in electrogastrogram based on empirical mode decomposition method. Med Biol Eng Comput. 2000;38(1):35–41.
Liang Z, et al. EEG entropy measures in anesthesia. Front Comput Neurosci. 2015;9:16.
Maszczyk T, Duch W. Comparison of Shannon, Renyi and Tsallis entropy used in decision trees. In: Artificial Intelligence and Soft Computing–ICAISC 2008. Springer; 2008. p. 643–51.
McKay IDH, et al. Pharmacokinetic-pharmacodynamic modeling the hypnotic effect of sevoflurane using the spectral entropy of the electroencephalogram. Anesth Analg. 2006;102(1):91.
Monk TG, et al. Anesthetic management and one-year mortality after noncardiac surgery. Anesth Analg. 2005;100(1):4.
Montirosso R, et al. Infant’s emotional variability associated to interactive stressful situation: a novel analysis approach with Sample Entropy and Lempel–Ziv complexity. Infant Behav Dev. 2010;33(3):346–56.
Morabito FC, et al. Multivariate multi-scale permutation entropy for complexity analysis of Alzheimer’s disease EEG. Entropy. 2012;14(7):1186–202.
Natarajan K, et al. Nonlinear analysis of EEG signals at different mental states. Biomed Eng Online. 2004;3(1):7.
Nunez PL, Wingeier BM, Silberstein RB. Spatial‐temporal structures of human alpha rhythms: theory, microcurrent sources, multiscale measurements, and global binding of local networks. Hum Brain Mapp. 2001;13(3):125–64.
Okogbaa OG, Shell RL, Filipusic D. On the investigation of the neurophysiological correlates of knowledge worker mental fatigue using the EEG signal. Appl Ergon. 1994;25(6):355–65.
Olofsen E, Sleigh J, Dahan A. Permutation entropy of the electroencephalogram: a measure of anaesthetic drug effect. Br J Anaesth. 2008;101(6):810–21.
Ouyang G, Dang C, Li X. Multiscale entropy analysis of EEG recordings in epileptic rats. Biomed Eng Appl Basis Commun. 2009;21(03):169–76.
Park J-H, et al. Multiscale entropy analysis of EEG from patients under different pathological conditions. Fractals. 2007;15(04):399–404.
Pincus SM. Approximate entropy as a measure of system complexity. Proc Natl Acad Sci. 1991;88(6):2297.
Rampil IJ. A primer for EEG signal processing in anesthesia. Anesthesiology. 1998;89(4):980–1002.
Renyi A. Probability theory. Amsterdam: North-Holland; 1970.
Rezek I, Roberts SJ. Stochastic complexity measures for physiological signal analysis. Biomed Eng, IEEE Trans. 1998;45(9):1186–91.
Richman JS, Moorman JR. Physiological time-series analysis using approximate entropy and sample entropy. Am J Phys Heart Circ Phys. 2000;278(6):H2039–49.
Rilling G, Flandrin P, Gonçalvés P. On empirical mode decomposition and its algorithms. In: IEEE-EURASIP workshop on nonlinear signal and image processing, NSIP-03, Grado (I). 2003.
Rosso OA, et al. Wavelet entropy: a new tool for analysis of short duration brain electrical signals. J Neurosci Methods. 2001;105(1):65–76.
Rosso O, Martin M, Plastino A. Brain electrical activity analysis using wavelet-based informational tools (II): Tsallis non-extensivity and complexity measures. Physica A. 2003;320:497–511.
Rosso O, et al. EEG analysis using wavelet-based information tools. J Neurosci Methods. 2006;153(2):163–82.
Särkelä MOK, et al. Quantification of epileptiform electroencephalographic activity during sevoflurane mask induction. Anesthesiology. 2007;107(6):928–38.
Shalbaf R, et al. Using the Hilbert–Huang transform to measure the electroencephalographic effect of propofol. Physiol Meas. 2012;33(2):271–85.
Shannon CE. A mathematical theory of communication. ACM SIGMOBILE Mob Comput Commun Rev. 2001;5(1):3–55.
Shannon CE, Weaver W. The mathematical theory of communication. Urbana: University of Illinois Press; 1949, v (ie vii), 125 p.
Smith WD, Dutton RC, Smith TN. Measuring the performance of anesthetic depth indicators. Anesthesiology. 1996;84(1):38–51.
Song Y, Zhang J. Discriminating preictal and interictal brain states in intracranial EEG by sample entropy and extreme learning machine. J Neurosci Methods. 2016;257:45–54.
Stamoulis C, Chang BS. Multiscale information for network characterization in epilepsy. In: Engineering in Medicine and Biology Society, EMBC, 2011 Annual international conference of the IEEE. 2011, IEEE.
Takahashi T, et al. Antipsychotics reverse abnormal EEG complexity in drug-naive schizophrenia: a multiscale entropy analysis. Neuroimage. 2010;51(1):173–82.
Thuraisingham RA, Gottwald GA. On multiscale entropy analysis for physiological data. Physica A. 2006;366:323–32.
Tong S, et al. Parameterized entropy analysis of EEG following hypoxic–ischemic brain injury. Phys Lett A. 2003;314(5):354–61.
Tsallis C, Mendes R, Plastino AR. The role of constraints within generalized nonextensive statistics. Physica A. 1998;261(3):534–54.
Unser M, Aldroubi A. A review of wavelets in biomedical applications. Proc IEEE. 1996;84(4):626–38.
Viertiö‐Oja H, et al. Description of the Entropy™ algorithm as applied in the Datex‐Ohmeda S/5™ Entropy module. Acta Anaesthesiol Scand. 2004;48(2):154–61.
Wang Y, et al. Multi-scale sample entropy of electroencephalography during sevoflurane anesthesia. J Clin Monit Comput. 2014;28(4):409–17.
Wu S-D, et al. Modified multiscale entropy for short-term time series analysis. Physica A. 2013;392(23):5865–73.
Yoo CS, et al. Automatic detection of seizure termination during electroconvulsive therapy using sample entropy of the electroencephalogram. Psychiatry Res. 2012;195(1):76–82.
Yoon YG, et al. Monitoring the depth of anesthesia from rat EEG using modified Shannon entropy analysis. Conf Proc IEEE Eng Med Biol Soc. 2011;2011:4386–9.
Zadeh LA. Fuzzy sets. Inf Control. 1965;8(3):338–53.
Zandi AS, et al. An entropy-based approach to predict seizures in temporal lobe epilepsy using scalp EEG. Conf Proc IEEE Eng Med Biol Soc. 2009;2009:228–31.
Zandi AS, et al. Circadian variation of scalp EEG: a novel measure based on wavelet packet transform and differential entropy. Conf Proc IEEE Eng Med Biol Soc. 2013;2013:6297–300.
Zhang R, et al. Predicting inter-session performance of SMR-based brain-computer interface using the spectral entropy of resting-state EEG. Brain Topogr. 2015;28(5):680–90.
Zhaohui L, Xiaoli L. Estimating temporal causal interaction between spike trains with permutation and transfer entropy. Plos One. 2013;8(8):e70894.
Zou X, Lei M. Pattern recognition of surface electromyography signal based on multi-scale fuzzy entropy. Sheng Wu Yi Xue Gong Cheng Xue Za Zhi. 2012;29(6):1184–8.
Zoughi T, Boostani R, Deypir M. A wavelet-based estimating depth of anesthesia. Eng Appl Artif Intell. 2012;25(8):1710–22.
Zunino L, et al. Fractional Brownian motion, fractional Gaussian noise, and Tsallis permutation entropy. Physica A. 2008;387(24):6057–68.
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Appendices
Appendices
Each entropy index contains several parameters, which can severely impact the output of its index. Therefore, it is very important to select the appropriate parameters. In anesthesia researches, there are many methods to select parameters including the interindividual variations, eg, the relationship with drug effect-site concentration obtained from PK/PD and prediction probability (Li etal. 2012, [88]). In this study, the method of selecting the parameters is based on indices’ performance in distinguishing different anesthesia states and interindividual variations. Fifty data sets in awake, deep anesthesia, and recovery states from 19 patients are selected, respectively. The RE and SE algorithms applied in the study adopts the Datex–Ohmeda S/5™ entropy module (Viertiö‐Oja etal. 2004). The PE’s parameter selection is based on our previous work (Li etal. 2012, 2010). The details of other entropy algorithm’s parameters are discussed as follows. All the results are given by mean ± standard deviation. The blue, red, and green colors represent the awake state, deep anesthesia state, and recovery state, respectively.
8.1.1 Appendix A: WE
There are three types of WE measures (SWE, TWE, RWE) considered in this study. The parameters include basis functions, the data length N, the Tsallis entropy parameter q, and the Renyi entropy parameter a. The basis functions and data length selection are based on the SWE. First, several common basis functions including Haar, Daubechies, Coiflets, Symlets, and Biorthogonal wavelet families were selected. The result is shown in Fig. 8.14a–e. N is assumed to be 1000. As can be seen, only the SWE based on the biorthgonal basis function can completely separate anesthesia state (red color) from awake (blue color), and recovery states (green color), without overlap. However, there are some basic functions in the biorthgonal family. Figure 8.14e–g show the results obtained by bior2.2, bior3.3, and bior4.4. It can be seen that the SWE achieved by bior3.3 not only distinguishes anesthesia states from non-anesthesia but also differentiates between awake and recovery states, especially when the number of layers is 2 and 3. So in this study, the bior3.3 was chosen as the wavelet basis function, and the number of layers was 3. Then, based on them, the selection of N is given in Fig. 8.14h. N ranges from 500 to 3000 points with the step of 500 points under the sample of 100 Hz. The figure shows that when N ≥ 1000, there is no significant difference in WE for each state. So N = 1000 (10 s) was selected to calculate the WE. Furthermore, based on the parameters of basis function and N, the selections of q in TWE and a in RWE are given in Fig. 8.14i–l.
8.1.2 Appendix B: HHSE
In order to choose an appropriate data length N in HHSE algorithm at the sample rate of 100 Hz, a series of N were used to calculate the HHSE in different anesthesia states. The result is shown in Fig. 8.15. All values of N could distinguish different anesthesia states. And when the data length was equal to or greater than 1000, the HHSE value would be nearly invariable with the changes of N. So N = 1000 (10 s) was selected in this study.
8.1.3 Appendix C: ApEn
Figure 8.16a–b, respectively, give the result of ApEn over different r in different anesthesia states with N = 1000, m = 2, and m = 3. With increasing r, the ApEn values in awake state and recovery state increased and then decreased, while it monotonously changes with r in deep anesthesia state. Both figures show that when r is 0.2 or 0.25 of SD, the difference between deep anesthesia and other states is larger. Considering that the r in ApEn is also used to suppress the noise, its value is chosen as small as possible. The r was chosen as 0.2 of SD. Figure 8.16c shows the selection of m with N = 1000 and r = 0.2*SD. It can be seen that ApEn nearly doesn’t change with m. Meanwhile when m is 2, the interindividual variations of ShEn is smaller. With r = 0.2*SD and m = 2, the selection of N is shown in Fig. 8.16d. The ApEn was very dependent on N, and it increased with enlarging N, as well as its interindividual variations, especially in awake and recovery states. The difference between awake and anesthesia state also became larger, but when N was greater than 1000, the difference was not obvious. Therefore, r = 0.2*SD, m = 2, and N = 1000 were selected in this study, which is consistent with the study (Bruhn etal. 2000) through different methods to choose parameter was used.
8.1.4 Appendix D: SampEn
Figure 8.17a–b, respectively, show the changes of SampEn over different r in different anesthesia states, with N = 1000, m = 2 and 3. The SampEn values monotonously decrease with increasing r in all states. The difference between awake state and deep anesthesia was obvious, but not between awake and recovery state. There is much overlap between them. Considering the interindividual variations, r = 0.2 is better. Figure 8.17c shows the changes of SampEn over different m with r = 0.2, N = 1000. There is no significant difference in different m values. For simplicity, m = 2 was selected. The selection of N is given in Fig. 8.17d. The SampEn values with r = 0.2, m = 2 were almost invariable as N increased. This implies that SampEn values are not dependent on N. Finally, N = 1000 (10 s at the sample rate of 100 Hz), m = 2, and r = 0.2*SD were selected in this study.
8.1.5 Appendix E: FuzzyEn
Figure 8.18 gives the changes of FuzzyEn with different parameters in different anesthesia states. Accordingly, we selected r = 0.2, m = 2, and N = 1000 for the computation of FuzzyEn in this study.
8.1.6 Appendix F: TPE and RPE
The embedded dimension m, lag τ, and data length N had been discussed in our previous study (Li etal. 2008a, 2010, 2012). It is suggested that \(m=6\) and \(\tau =1\) are suitable for the sevoflurane DoA monitoring, and \(m=3\) \(\tau =2\) is better for isoflurane analysis. So, for the parameters of TPE and RPE, we only considered the embedded dimension of 3 and 6. For the sevoflurane, using \(\tau =1\) and isoflurane is \(\tau =2\). Figure 8.19a–b are the TPE of three anesthesia states at the \(0<q<1\) and \(q>1\), respectively, the \(m=3\). Figure 8.19c–d show the TPE of \(m=6\) at \(0<q<1\) and \(q>1\), respectively. It can be seen that in \(m=6\), \(q=0.9\) has a better performance in TPE. Figure 8.19e–h are the RPE measure of three anesthesia states similar as Fig. 8.19a–d. We select the \(m=6\) and \(a=2\) for RPE calculation.
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Liang, Z., Duan, X., Li, X. (2016). Entropy Measures in Neural Signals. In: Li, X. (eds) Signal Processing in Neuroscience. Springer, Singapore. https://doi.org/10.1007/978-981-10-1822-0_8
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