Local Band Spectral Entropy Based on Wavelet Packet Applied to Surface EMG Signals Analysis

An efficient analytical method for electromyogram (EMG) signals is of great significance to research the inherent mechanism of a motor-control system. In this paper, we proposed an improved approach named wavelet-packet-based local band spectral entropy (WP-LBSE) by introducing the concept of frequency band local-energy (ELF) into the wavelet packet entropy, in order to characterize the time-varying complexity of the EMG signals in the local frequency band. The EMG data were recorded from the biceps brachii (BB) muscle and triceps brachii (TB) muscle at 40 ̋, 100 ̋ and 180 ̋ of elbow flexion by 10 healthy participants. Significant differences existed among any pair of the three patterns (p < 0.05). The WP-LBSE values of the EMG signals in BB muscle and TB muscle demonstrated a decreased tendency from 40 ̋ to 180 ̋ of elbow flexion, while the distributions of spectral energy were decreased to a stable state as time periods progressed under the same pattern. The result of this present work is helpful to describe the time-varying complexity characteristics of the EMG signals under different joint angles, and is meaningful to research the dynamic variation of the activated motor units and muscle fibers in the motor-control system.


Introduction
Surface electromyogram (EMG) activities have been reported that can represent the inherent characteristics and movement intention in motor-control systems, which are widely used in the field of prosthesis control [1,2], rehabilitation [3,4], muscle fatigue analysis [5,6] and clinical diagnosis [7,8].An accurate and efficient analytical method, therefore, is of great significance to differentiate the motor patterns and explore the potential mechanism for motor control and function evaluation.
Over last few years, lots of techniques, such as root mean square (RMS) [9], short-time Fourier transform (STFT) [10] and mean power frequency (MPF) [11], have been applied to analyze the energy features of the EMG signals in the time or frequency domain.The simple time domain or frequency domain feature methods contribute to the online anaysis and classification of the EMG signals due to their lower computational complexity and less time consumption, but they have some limitations in the process of non-stationary signal and feature extraction in high resolution [12], which lose sight of the mirror changes in motor unit action potentials (MUAPs).According to the physiological properties of the EMG signal, the discriminable features often hide in some narrower frequency bands [13].Therefore, techniques need to be developed for further analysis of the non-stationary signal with high resolution.
The theories of wavelet transform (WT) and wavelet packet transform (WPT) [14][15][16][17][18], as an effective tool to describe the local-band characteristics, are introduced to decompose the EMG signals into several sub-bands or sequences of coefficients in different time-frequency resolutions.In particular the wavelet packet transform is widely applied due to the high resolusion in high and low frequency.The application of the WPT combining the spectral energy distribution, named the WPE, further reveals the temporal energy distribution in the considered sub-bands of the EMG signals [19,20] and accounts for different properties in various motion patterns [21], These methods can exploit the discriminable features in the local frequecy band.
Additionally, multivariate techniques and nonlinear methods have been developed in recent years.The independent component analysis (ICA) [22,23], the principal component analysis (PCA) [24,25] and the nonegative matrix factorization (NMF) [26] have been widely used for the EMG channel minimization [27][28][29] and classification [29][30][31][32][33]; the correlation dimension [34], the maximum Lyapunov Exponent [35], the complexity [36] and the information entropy [37] have been applied into the nonlinear analysis of the EMG signals.Especially, the exrtensive entropy-based measures, such as the Kolmogorov-Sinai (K-S) entropy [38], the approximate entropy (ApEn) [39,40] and the sample entropy (SampEn) [41,42], have achieved many applications in bioelectricity signals processing.These methods can describe the order/disorder features in all the frequency ranges, but lose the insight of the information in a specific frequency band.The combination of the wavelet or wavelet packet with information entroy, named wavelet entropy (WE) [43] or wavelet packet entropy (WPTE) [44] can describe the complex features in the local frequency band, and has been applied for feature extraction and pattern classification.However, this combination has limitation in describing the time-variation characteristics in the local frequency band.In order to resolve this problem, the concept of frequency band local-energy (ELF) which can denote the energy distribution with time variation in each frequency-bandis widely adopted in fault diagnosis [45] and endpoint detection [46].Therefore, the combination of wavelet packet, frequency band local-energy and information entropy could have mutual compensation functions in analyzing the time-varying complexity characteristics of the EMG signals in the local frquency band.To account for the hypothesis that the firing of the motor units and the discharge of muscle fibers play an important role in modulating the contraction of muscle groups to generte different motor patterns, a novel algotithmic model is designed to describe the time-varying complexity features of the EMG signals and to provide new insight into the physiological systems.
This study attempts to explore the potiental mechnism of the motor control under different motor patterns using the proposed novel approach named wavelet-packet-based local band spectral entropy (WP-LBSE) by introducing the concept of ELF into the wavelet packet entropy.This study involves the investigation of the EMG signals recorded from the flexor muscle (biceps brachii (BB)) and extensor muscle (triceps brachii (TB)) under three motor patterns (elbow flexion at 40 ˝, 100 ˝and 180 ˝) by 10 healthy participants.This studies can provide new insgiht into the time-varying complexity characteristics of the EMG signals in the local frequency band and add to the understanding of the mechanisms underlying the motor control.The results demonstrate the efficiency and reliability of this new algorithm.

Participants
Ten healthy subjects (six males, mean age, 25.2 ˘2.3 years; ranging from 22 to 28 year old) without any history of neurological disease were enrolled in the study.These subjects were tested according to the Oldfield questionnaire [47].The experiment, in which all subjects participated, was in accordance with the Declaration of Helsinki and the whole experiment obtained the consent and approval from the local ethics committee.All subjects who participated had no similar experimental experiences before.

Experiment Paradigm
During the experimental session, the subjects sat in an electrically shielded, dimly lit room.All subjects were instructed to perform elbow movement at different angles with their dominant arms on the fixed flat as shown in Figure 1A.The fixed flat was a frame with four crossed bars and there was a hole to place the electrode to acquire the signals, so the EMG signals from the TB muscle cannot be disturbed by the flat.Firstly, their arms were placed with the elbow flexion at 100 ˝, which was defined as the intermediate reference position (see Figure 1B).Based on the reference plane, the elbow flexion at 180 ˝corresponded to the full elbow extension (Figure 1C) and the elbow flexion at 40 ˝corresponded to the full elbow flexion (Figure 1D).To enhance the activities of muscle, all subjects were required to finish an action with 1.5 kg dumbbell in their hands.Each pattern maintained 5 s contraction with 5 s rest in between, and the whole movement included ten sessions.The ten sessions for the same pattern were carried out one after another without any mixture of different patterns.Thirty data sets of EMG signals were recorded in total.During the experimental session, the subjects sat in an electrically shielded, dimly lit room.All subjects were instructed to perform elbow movement at different angles with their dominant arms on the fixed flat as shown in Figure 1A.The fixed flat was a frame with four crossed bars and there was a hole to place the electrode to acquire the signals, so the EMG signals from the TB muscle cannot be disturbed by the flat.Firstly, their arms were placed with the elbow flexion at 100°, which was defined as the intermediate reference position (see Figure 1B).Based on the reference plane, the elbow flexion at 180° corresponded to the full elbow extension (Figure 1C) and the elbow flexion at 40° corresponded to the full elbow flexion (Figure 1D).To enhance the activities of muscle, all subjects were required to finish an action with 1.5 kg dumbbell in their hands.Each pattern maintained 5 s contraction with 5 s rest in between, and the whole movement included ten sessions.The ten sessions for the same pattern were carried out one after another without any mixture of different patterns.Thirty data sets of EMG signals were recorded in total.

Data Recording
The surface EMG was digitized at a sampling frequency (1000 Hz) and amplified (2000×) by a Trigno™ Wireless EMG (Delsys Inc., Natick, MA, USA).Off-line data were further processed and analyzed in the MATLAB (R2013b) environment.The EMG signals were acquired from the BB muscle and TB muscle.The electrodes were placed on the muscle belly along with the muscle fibers.The skin at the electrodes sites were prepared by shaving and rubbing with alcohol.

Data Preprocessing
EMG signals are very easily contaminated by baseline drift, slight tremors and the power line interference (50 Hz and its higher harmonics).In order to remove the artifacts in EMG signals, a preprocessing scheme was designed in this study.The slight tremors (>250 Hz) were isolated by a 1-250 Hz band-pass filter (digital 8th-order Butterworth) and the baseline drift was removed by an adaptive high-pass filter (digital 8th-order Butterworth).Then the power line interference was suppressed using independent component analysis (ICA).The signal to noise ratio (SNR) of the preprocessed EMG signals is 23.46 dB according to the calculation method [48].

Data Recording
The surface EMG was digitized at a sampling frequency (1000 Hz) and amplified (2000ˆ) by a Trigno™ Wireless EMG (Delsys Inc., Natick, MA, USA).Off-line data were further processed and analyzed in the MATLAB (R2013b) environment.The EMG signals were acquired from the BB muscle and TB muscle.The electrodes were placed on the muscle belly along with the muscle fibers.The skin at the electrodes sites were prepared by shaving and rubbing with alcohol.

Data Preprocessing
EMG signals are very easily contaminated by baseline drift, slight tremors and the power line interference (50 Hz and its higher harmonics).In order to remove the artifacts in EMG signals, a preprocessing scheme was designed in this study.The slight tremors (>250 Hz) were isolated by a 1-250 Hz band-pass filter (digital 8th-order Butterworth) and the baseline drift was removed by an adaptive high-pass filter (digital 8th-order Butterworth).Then the power line interference was suppressed using independent component analysis (ICA).The signal to noise ratio (SNR) of the preprocessed EMG signals is 23.46 dB according to the calculation method [48].

Wavelet-Packet-Based Local Band Spectral Entropy
In this paper, preprocessed signals were decomposed into N-th resolution levels based on the WPT, and 2 N subspaces in frequency domain can be obtained correspondingly.The sub-signal at the j-th subspace on the N-th level can be reconstructed by: where D N,j k is the wavelet packet coefficient at the j-th subspaces on the N-th level and ψ j,k ptq is the wavelet function.The reconstructed signal S j N ptq is also divided into m parts in time domain, and the energy of each frequency band in different time periods, called frequency band local energy, is calculated.Then a sequence of energy, ) is obtained.The total energy in each time period is: In consequence, the relative energy at the j-th subspaces in the m-th period of time is: where p m Nj pkq quantifies the probability distribution of the frequency spectral energy in different time intervals.
Shannon entropy is introduced to analyze the complexity of the EMG signal and reduce the feature dimensions of frequency band local-energy.Then the frequency spectral energy distribution in different time periods of EMG signal is measured as follows: where En m is the WP-LBSE value in the m-th time interval, which can describe the nonlinear, time-varying and complex energy distribution of EMG signals.The same processes were carried out for all the preprocessed EMG signals of three motor patterns (40 ˝, 100 ˝and 180 ˝of elbow flexion).

Statistical Analysis
SPSS Version 19.0 (SPSS Inc., Chicago, IL, USA) was used for the statistical data analysis.The WP-LBSE values under the three motor patterns were compared by the paired sample t-tests to distinguish the differences.The statistical significance was set at p < 0.05.

Wavelet Packet Energy and Frequency Band Local-Energy
In this paper, the EMG signals recorded from the BB muscle and TB muscle under three patterns (elbow flexion at 40 ˝, 100 ˝and 180 ˝) were analyzed according to the above procedures.Considering the EMG signals without clear physical significance in specific frequency, we need to choose appropriate WPT resolution levels.Previous studies on the WPT applied in EMG analysis mainly choose resolution levels between three and five [12].In our study, the resolution levels were chosen from three to seven for further analysis.The analytical results in different resolution levels showed that the relative energy in each subspace under four resolution levels was significantly different from the others.However, there was no significant difference between the relative energies in adjacent subspaces when the EMG signals were divided into five, six or seven resolution levels.As a result, the preprocessed EMG signals were decomposed into four resolution levels and the whole bands were correspondingly divided into 16 frequency subspaces.The wavelet-packet energy (WPE) of each subspace was calculated as depicted in Figure 2a.Next, the reconstructed signal in each subspace was divided into three time intervals, and the frequency band local-energy of the EMG signals was also calculated as showed in Figure 2b.The three motor patterns yielded almost the same distributed regularity covering all the frequency bands, as shown in Figure 2a.Further analysis showed that the WPE for each EMG signal was dominant in the range of 1-125 Hz (1st, 2nd, 3rd and 4th subspaces).Statistic analysis indicated that there was no significant difference among different joint angles (t = 0.285, p > 0.05).Figure 2b shows that the frequency band local-energy was most dispersive at the elbow angle of 40°, but concentrated at the elbow angle of 180°.In addition, the distributions of the spectral energy were decreased to a stable state as time progressed under the same pattern.For example, the frequency band local-energy of the EMG signals in the first time interval under 180° of elbow extension mainly focused on 31.25-62.5Hz (2nd subspace) band and 93.75-125 Hz (4th subspace) band ranges, but the spectral energy of the other two time-intervals was more dispersive.An analogous case occurred in the TB muscle.

WP-LBSE Distribution
The scatter diagram of WP-LBSE under 40°, 100° and 180°of elbow flexion in Figure 3 showed the feature vectors constituted by the WP-LBSE in BB muscle and TB muscle under three patterns.The three motor patterns yielded almost the same distributed regularity covering all the frequency bands, as shown in Figure 2a.Further analysis showed that the WPE for each EMG signal was dominant in the range of 1-125 Hz (1st, 2nd, 3rd and 4th subspaces).Statistic analysis indicated that there was no significant difference among different joint angles (t = 0.285, p > 0.05).Figure 2b shows that the frequency band local-energy was most dispersive at the elbow angle of 40 ˝, but concentrated at the elbow angle of 180 ˝.In addition, the distributions of the spectral energy were decreased to a stable state as time progressed under the same pattern.For example, the frequency band local-energy of the EMG signals in the first time interval under 180 ˝of elbow extension mainly focused on 31.25-62.5Hz (2nd subspace) band and 93.75-125 Hz (4th subspace) band ranges, but the spectral energy of the other two time-intervals was more dispersive.An analogous case occurred in the TB muscle.

WP-LBSE Distribution
The scatter diagram of WP-LBSE under 40 ˝, 100 ˝and 180 ˝of elbow flexion in Figure 3 showed the feature vectors constituted by the WP-LBSE in BB muscle and TB muscle under three patterns.Concurrently, the line graphs of the WP-LBSE in each time-interval for each subject were plotted as shown in Figure 4.     Concurrently, the line graphs of the WP-LBSE in each time-interval for each subject were plotted as shown in Figure 4.

Relationship between the WP-LBSE and the Angles
The error bars of the average WP-LBSE values across all subjects are shown in Figure 5 in three time intervals under different angles.Figure 5a intuitively depicts a significant decline of the mean WP-LBSE values from 40 ˝to 80 ˝of elbow flexion, though they were overlapped with each other.In addition, there was a decreasing tendency from time interval 1 to time interval 3, which meant the variation of the complexity of the EMG signals in the local frequency band during the process of maintaining the motion state.The line graph of the mean WP-LBSE values in Figure 5b further showed that there were significant differences among the different motor patterns.

Relationship between the WP-LBSE and the Angles
The error bars of the average WP-LBSE values across all subjects are shown in Figure 5 in three time intervals under different angles.Figure 5a intuitively depicts a significant decline of the mean WP-LBSE values from 40° to 80° of elbow flexion, though they were overlapped with each other.In addition, there was a decreasing tendency from time interval 1 to time interval 3, which meant the variation of the complexity of the EMG signals in the local frequency band during the process of maintaining the motion state.The line graph of the mean WP-LBSE values in Figure 5b further showed that there were significant differences among the different motor patterns.

Discussion
In this paper, a novel technique, named WP-LBSE, was proposed to describe the time-varying complexity characteristics of the EMG signals collected from the BB muscle and TB muscle about elbow movement under different joint angles.Compared with the WPE and the frequency band local-energy method, the WP-LBSE has been proved to be helpful for quantitatively describing the time-varying complexity characteristics of the EMG signals in the local frequency band.The quantification of multi-aspect characteristics and the variation tendency of the WP-LBSE values expounded the changes of the firing of motor units and discharge of muscle fibers in motor control.
In our study, the WPE values under the three motion patterns yielded almost the same distributed regularity in the frequency bands, and were dominant in the range of 1-125 Hz as shown in Figure 2a.It is difficult to describe the discriminable features in the local frequency bands [13].The result is inconsistent with the literature which claimed that the angles have a significant effect on the median frequencies of BB and TB muscles [49].
The ELF values based on the WPE showed that the distributions of relative energy decreased to a stable state with time periods going on under the same pattern (Figure 2b).These changes may be related to the motoneurons innervated by the central command.A thorough elucidation has showed that both the α and γ motoneurons are active during movement and posture [50][51][52].Dynamic α and γ motoneurons are mainly responsible for movement, while static α and γ motoneurons are related to posture maintenance [53].The activated dynamic γ neuron will enhance the Ia afferent neurons during the initially dynamic movement, then the activated γ neuron will shift to be static neurons to increase the perception of II afferent neurons for the muscle length.These explanations demonstrate the time-dependent of the neurophysiological system under single motor task.In our study, the change of the EMG spectral energy corroborated well for these time-varying characteristics of the motor system.In addition, each motor pattern from the onset to the end can be divided into a series of dynamic movements and static postures, and the shift of the γ neurons might account well for the tendency to stability of spectral energy of the EMG signals in each motor patterns.With respect to

Discussion
In this paper, a novel technique, named WP-LBSE, was proposed to describe the time-varying complexity characteristics of the EMG signals collected from the BB muscle and TB muscle about elbow movement under different joint angles.Compared with the WPE and the frequency band local-energy method, the WP-LBSE has been proved to be helpful for quantitatively describing the time-varying complexity characteristics of the EMG signals in the local frequency band.The quantification of multi-aspect characteristics and the variation tendency of the WP-LBSE values expounded the changes of the firing of motor units and discharge of muscle fibers in motor control.
In our study, the WPE values under the three motion patterns yielded almost the same distributed regularity in the frequency bands, and were dominant in the range of 1-125 Hz as shown in Figure 2a.It is difficult to describe the discriminable features in the local frequency bands [13].The result is inconsistent with the literature which claimed that the angles have a significant effect on the median frequencies of BB and TB muscles [49].
The ELF values based on the WPE showed that the distributions of relative energy decreased to a stable state with time periods going on under the same pattern (Figure 2b).These changes may be related to the motoneurons innervated by the central command.A thorough elucidation has showed that both the α and γ motoneurons are active during movement and posture [50][51][52].Dynamic α and γ motoneurons are mainly responsible for movement, while static α and γ motoneurons are related to posture maintenance [53].The activated dynamic γ neuron will enhance the Ia afferent neurons during the initially dynamic movement, then the activated γ neuron will shift to be static neurons to increase the perception of II afferent neurons for the muscle length.These explanations demonstrate the time-dependent of the neurophysiological system under single motor task.In our study, the change of the EMG spectral energy corroborated well for these time-varying characteristics of the motor system.In addition, each motor pattern from the onset to the end can be divided into a series of dynamic movements and static postures, and the shift of the γ neurons might account well for the tendency to stability of spectral energy of the EMG signals in each motor patterns.With respect to the decrease of the EMG spectral energy, it might be related to the strength of the activated γ motoneurons.The dynamic γ motoneurons may need more strength within a little time to reach the required level, while the static γ motoneurons need less strength to modulate the accurate and subtle position.
The centrally encoded joint angle information is conveyed to the periphery by a plausible function of γ fusimotor control through regulating spindle sensitivity, so that the Ia signaling from spindle afferents is kept faithfully proportional to the joint angle during the movement and muscle contraction [54].In our study, significant difference on the mean WP-LPSE values in each time interval exists among different angles of elbow flexion (Figures 3 and 4).The WP-LBSE of the EMG signals in the BB muscle and TB muscle demonstrates a decreased tendency of from 40 ˝to 180 ˝of elbow flexion (Figure 5).The difference indicates that the complexity in the EMG signals has a declined tendency from flexion to extension.The decreased complexity might derive from the multifactor effects.The integration of the centrally encoded 40 ˝angle information of elbow flexion is likely more complicated than that of the 180 ˝angle.In addition, the muscles under 40 ˝angle need more motor units to maintain and adjust the discharge of the muscle fibers or reinforces the shorter fibers [55], as a result, the firing of the motor units and the discharge of muscle fibers might be more complex than that under 180 ˝angle.The conclusion is consistently fitted with the literature as Chen et al. [56] reported.This supports the hypothesis that the firing of the motor units and the discharge of the muscle fibers play a direct role in modulating the contraction of muscle groups to generate different motor patterns.

Conclusions
In this study, the proposed method introducing the concept of ELF into the wavelet packet entropy, WP-LBSE, has been proved a suitable approach to quantify the time-varying complexity characteristics of the EMG signals in the local frequency band.The variation tendency of the WP-LBSE values in each time interval is obtained under different motion patterns (40 ˝, 100 ˝and 180 ˝of elbow flexion).The quantification of multi-aspect characteristics in the EMG signals expounds the functional modulation of the firing of motoneurons (α and γ) and the discharge of the fusimotor in motor control.This study is significant in understanding the potential mechanism in the motor-control system and could be helpful to evaluate the motion function for rehabilitation.

Figure 1 .
Figure 1.Experimental setup.(A) Schematic diagram of EMG signal acquisition experiment showed the position of elbow flexion and electrodes placement; (B) 100 ˝intermediate state; (C) 180 ˝of elbow extension; (D) 40 ˝of elbow flexion.

Figure 2 .
Figure 2. The WPE and frequency band local-energy of EMG signal under three action states (40°, 100° and 180°of elbow flexion).(a) is WPE calculated by the WPT method.(b) shows the frequency band local-energy.

Figure 2 .
Figure 2. The WPE and frequency band local-energy of EMG signal under three action states (40 ˝, 100 and 180 ˝of elbow flexion).(a) is WPE calculated by the WPT method.(b) shows the frequency band local-energy.
The same color indicated the WP-LBSE values for the same subject, and the same shape showed the WP-LBSE values for the same patterns.In each pattern, there were three same marks.Visualization of the discrimination among groups was provided by plotting the individual vectors for three patterns.The vector distributions under 40 ˝(full elbow flexion), 100 ˝(intermediate reference position) and 180 ˝(full elbow extension) were [1.65-1.85,1.60-1.80],[1.45-1.80,1.35-1.55]and [1.40-1.75,1.00-1.30],respectively.The mean values of the vector distributions under 40 ˝were significantly higher than that under 100 ˝(p = 0.0093) and 180 ˝(p = 0.0067).Entropy 2016, 18, 41 6 of 10 The same color indicated the WP-LBSE values for the same subject, and the same shape showed the WP-LBSE values for the same patterns.In each pattern, there were three same marks.Visualization of the discrimination among groups was provided by plotting the individual vectors for three patterns.The vector distributions under 40° (full elbow flexion), 100° (intermediate reference position) and 180° (full elbow extension) were [1.65-1.85,1.60-1.80],[1.45-1.80,1.35-1.55]and [1.40-1.75,1.00-1.30],respectively.The mean values of the vector distributions under 40° were significantly higher than that under 100° (p = 0.0093) and 180° (p = 0.0067).

Figure 3 .
Figure 3. Scatter diagram of WP-LBSE of EMG signals in BB muscle and TB muscle under three motor patterns (40°, 100° and 180°of elbow flexion).
Figure 4 intuitively depicts a more rapid decline and shows significant differences among the three states (t = 10.31,p < 0.01), especially the WP-LBSE of the EMG signals in TB muscle.

Figure 4 .
Figure 4.The tendency graphs of WP-LBSE in BB muscle and TB muscle in three time intervals were showed respectively.The WP-LBSEs of each subject were showed under three joint angles (40°, 100° and 180° of elbow flexion).

Figure 3 .
Figure 3. Scatter diagram of WP-LBSE of EMG signals in BB muscle and TB muscle under three motor patterns (40 ˝, 100 ˝and 180 ˝of elbow flexion).
Figure 4 intuitively depicts a more rapid decline and shows significant differences among the three states (t = 10.31,p < 0.01), especially the WP-LBSE of the EMG signals in TB muscle.The same color indicated the WP-LBSE values for the same subject, and the same shape showed the WP-LBSE values for the same patterns.In each pattern, there were three same marks.Visualization of the discrimination among groups was provided by plotting the individual vectors for three patterns.The vector distributions under 40° (full elbow flexion), 100° (intermediate reference position) and 180° (full elbow extension) were [1.65-1.85,1.60-1.80],[1.45-1.80,1.35-1.55]and [1.40-1.75,1.00-1.30],respectively.The mean values of the vector distributions under 40° were significantly higher than that under 100° (p = 0.0093) and 180° (p = 0.0067).

Figure 3 .
Figure 3. Scatter diagram of WP-LBSE of EMG signals in BB muscle and TB muscle under three motor patterns (40°, 100° and 180°of elbow flexion).
Figure 4 intuitively depicts a more rapid decline and shows significant differences among the three states (t = 10.31,p < 0.01), especially the WP-LBSE of the EMG signals in TB muscle.

Figure 4 .
Figure 4.The tendency graphs of WP-LBSE in BB muscle and TB muscle in three time intervals were showed respectively.The WP-LBSEs of each subject were showed under three joint angles (40°, 100° and 180° of elbow flexion).

Figure 4 .
Figure 4.The tendency graphs of WP-LBSE in BB muscle and TB muscle in three time intervals were showed respectively.The WP-LBSEs of each subject were showed under three joint angles (40 ˝, 100 and

Figure 5 .
Figure 5. Correlation between the mean WP-LBSE values and the angles.(a) Error bar of the average WP-LBSE values across all subjects in three time intervals under three angles; (b) Line graph of the mean WP-LBSE values across all subjects in three time intervals under three angles.

Figure
Figure Correlation between the mean WP-LBSE values and the angles.(a) Error bar of the average WP-LBSE values across all subjects in three time intervals under three angles; (b) Line graph of the mean WP-LBSE values across all subjects in three time intervals under three angles.