 freely available
 reusable
Sensors 2013, 13(9), 1243112466; doi:10.3390/s130912431
Published: 17 September 2013
Abstract
: Electromyography (EMG) signals are becoming increasingly important in many applications, including clinical/biomedical, prosthesis or rehabilitation devices, human machine interactions, and more. However, noisy EMG signals are the major hurdles to be overcome in order to achieve improved performance in the above applications. Detection, processing and classification analysis in electromyography (EMG) is very desirable because it allows a more standardized and precise evaluation of the neurophysiological, rehabitational and assistive technological findings. This paper reviews two prominent areas; first: the preprocessing method for eliminating possible artifacts via appropriate preparation at the time of recording EMG signals, and second: a brief explanation of the different methods for processing and classifying EMG signals. This study then compares the numerous methods of analyzing EMG signals, in terms of their performance. The crux of this paper is to review the most recent developments and research studies related to the issues mentioned above.1. Introduction
Electromyograpy (EMG) refers to the collective electric signal from muscles, which is controlled by the nervous system and produced during muscle contraction. The signal represents the anatomical and physiological properties of muscles; in fact, an EMG signal is the electrical activity of a muscle's motor units, which consist of two types: surface EMG, and intramuscular EMG [1]. Surface EMG and intramuscular EMG signals are recorded by noninvasive electrodes and invasive electrodes, respectively. These days, surfacedetected signals are preferably used to obtain information about the time or intensity of superficial muscle activation [2]. Electromyography (EMG) signals are considered most useful as electrophysiological signals in both medical and engineering fields. The basic method for understanding the human body's behaviors under normal and pathological conditions is provided by the recording of EMG signals. Whenever an EMG signal is being recorded from the muscle, various types of noises contaminate it. Therefore, analyzing and classifying the EMG signals is very difficult because of the complicated pattern of the EMG, especially when EMG motion occurs [3]. EMG signals can be used to generate device control commands for rehabilitation equipment such as robotic prostheses and in generic manmachine interfaces for Human Computer Interface (HCI). They have also been deployed in many clinical and industrial applications [4]. Processing and classifying EMG signals requires using the Electromyographic Control technique. Control systems based on the classification of EMG signals are usually known as Myoelectric Control Systems (MCSs); powered upperlimb prostheses and electricpowered wheelchairs are two of the main potential applications of MCSs [5]. However, to use these applications effectively, an accurate EMG signal acquisition is a prerequisite. When acquiring an EMG signal, various background noises are received due to the presence of electronic equipment and physiological factors. Section 1 of this paper provides an overview of these various noises and mentions ways to overcome them (when the acquisition of an EMG signal is completed). Nevertheless, it remains very difficult for the noise to be removed clearly. Therefore, that EMG signal is processed and analyzed to get the required information. Many researchers have used different kinds of advanced methodologies, including wavelet transform, WignerVille Distribution, Independent component analysis, Empirical mode decomposition, and higherorder statistics for analyzing the EMG signal appropriately. The second section of this paper contains EMG signal classification methods.
2. Noise Sources in EMG Signals
The identity of an actual EMG signal that originates in the muscle is lost due to the mixing of various noise signals or artifacts. The attributes of the EMG signal depend on the internal structure of the subject, including the individual skin formation, blood flow velocity, measured skin temperatures, the tissue structure (muscle, fat, etc.), the measuring site, and more. These attributes produce different types of noise signals that can be found within the EMG signals. This may have an effect on the result of feature extraction and hence affect the diagnosis of the EMG signals. Various methods of noise elimination have been proposed during the EMG signal acquisition, and the subject continues to be a popular one among practitioners. The main challenges in analyzing the EMG signals are explained below.
2.1. Inherent Noise in the Electrode
All types of electronic equipment generate electrical noise, otherwise known as “inherent noise”. This noise has frequency components that range from 0 Hz to several thousand Hz. Two kinds of EMG signals in widespread use include surface EMG, and intramuscular (needle and finewire) EMG. To perform intramuscular EMG, a needle electrode or a needle containing two finewire electrodes is placed within the muscle of interest (invasive electrode). However, the use of surface electrodes has become more accepted in clinical and physiological applications [6]. The advantage of surface electrodes is that they are noninvasive, and the patient need not be anesthetized before placing the electrode. The operation is simple and painless.
For recording the EMG, the noninvasive electrodes are applied to the skin of the subject. For recording purposes, electrodes made of silver/silver chloride (10 × 1 mm) have been found to give adequate signaltonoise ratio and are electrically very steady. For this reason, they are widely used as surface electrodes [7]. When the electrode size enlarges, the impedance decreases. However, electrode size should not be very large. On the other hand, high electrode impendence effectively reduces the signal quality and gives low signaltonoise ratio. Therefore, both parameters should be taken into consideration. Researchers are allowed to use high electrode impedances for experiments in which statistical power is high or in which large numbers of electrodes are necessary, but tend to switch to low electrode impedances for experiments in which statistical power would otherwise be too low [8]. This noise can be eliminated by using intelligent circuit design and high quality instruments.
2.2. Movement Artifact
Movement of the cable connecting the electrode to the amplifier and the interface between the detection surface of the electrode and the skin creates motion artifacts. Muscle fibers generate electric activity whenever muscles are active [9]. EMG signals are recorded by placing electrodes close to the muscle groups. When the muscle is activated, the length of the muscle decreases and the muscle, skin and electrodes move with respect to one another. At that time, the electrodes will show some movement artifacts. The frequency range of the motion noise is usually 1–10 Hz and has a voltage comparable to the amplitude of the EMG. Recessed electrodes can remove the movement artifact significantly, in which a conductive gel layer is used between the skin surface and the electrodeelectrolyte interface. Another type of movement artifact occurs due to the potential difference between skin layers. Recessed electrodes cannot remove this artifact. However, this type of artifact is attenuated by reducing the skin impedance [10]. Tam and Webster [11] found that scratching the skin reduces these artifacts. Burbank and Webster [12] showed that low skin impedance could be achieved by using the puncture technique, thus reducing the artifacts. Conforto et al. [13] tested four filtering procedures to reject the motion artifact from an EMG signal during dynamic contractions. These procedures include the eighth order Chebyshev high pass filters with corner frequency at 20 Hz; the moving average filter; the moving median filter; and the adaptive filter, which is based on orthogonal Meyer wavelets. They found that the wavelet procedure maintains all the information and detects the time more precisely than the other methods. The virtual movement between skin surface electrodes and the innervations zone(s) of the underlying motor units can cause another type of motion artifact. Mesin et al. discovered that the outcome of the innervations zone (IZ) on amplitude, frequency and conduction velocity can be calculated from the EMG and the effect of electrodes placed close to IZ. At the same time, they showed that the interelectrode distance must be thin with respect to the distance between the IZ and the tendon, and that no electrode should go beyond this zone [14].
2.3. Electromagnetic Noise
The human body behaves like an antenna—the surface of the body is continuously inundated with electric and magnetic radiation, which is the source of electromagnetic noise. Electromagnetic sources from the environment superimpose the unwanted signal, or cancel the signal being recorded from a muscle. The amplitude of the ambient noise (electromagnetic radiation) is sometimes one to three times greater than the EMG signal of interest.
The human body's surface continuously emits electromagnetic radiation, and avoiding exposure to ambient noise on the surface of the Earth is impracticable [15]. The dominant concern for the ambient noise arises from the 60 Hz (or 50 Hz) radiation from power sources, which is also called PowerLine Interference (PLI). This is caused by differences in the electrode impedances and in stray currents through the patient and the cables. However, in order to remove the recorded artifact, offline processing is necessary [10]. A high pass filter can remove the interference if the frequency of this interference is high. However, if the frequency content of PLI is within the EMG signal then it is very essential to recognize the nature of the EMG signal. 50 Hz PLI and its four harmonics (e.g., 100, 200, 300 and 400 Hz) are constructed mathematically by the equation [16]:
Figure 1 illustrates the general model for the PLI cancellation system. A number of adaptive filter techniques have been proposed for the attenuation of the PLI noise, such as adaptive FIR notch filter, adaptive IIR notch filter, adaptive notch filter using Fourier transform and so forth. An efficient Laguerre filter can eliminate powerline interference from EMG signals successfully; in fact, it has been shown to be more effective than other adaptive algorithms. This filter can increase the SNR of an EMG signal significantly without using any information from the powerline interference [16].
2.4. Cross Talk
An undesired EMG signal from a muscle group that is not commonly monitored is called “crosstalk”. Crosstalk contaminates the signal and can cause an incorrect interpretation of the signal information [17]. Crosstalk depends on the many physiological parameters [18,19], and can be minimized by choosing electrode size and interelectrode distances (typically 1–2 cm or the radius of the electrode) carefully. Electrodes with a smaller surface area reduce bipolar spacing and mathematical differentiation, and the combination of these three methods reduces the potential crosstalk effectively [20]. Crosstalk increases with increasing subcutaneous fat thickness. Lowery et al. showed that the distance from the active fibers increases the decay rate of the crosscorrelation function, and acts faster than crosstalk. The crosscorrelation between two EMG signals is neither a qualitative nor a quantitative measure of crosstalk [19]. The main causal factor of crosstalk is the generation of the nonpropagating signal components due to loss of the intracellular action potentials at the tendons. Thus, crosstalk has a different shape with respect to the signals detected directly over an active muscle and has a broader bandwidth than these signals. The crosscorrelation coefficient analysis and high pass filtering method have no effect on crosstalk and are not reliable for reducing it [21]. Selectivity of EMG electrodes depends on their interspacing, their conductive area, and axis direction with respect to the direction of the underlying muscular fibers. Minimal crosstalk area (MCA) is defined as a surface where crosstalk versus cocontraction of muscles is minimal. The precise location and measurements of the distance between two bony landmarks are the keys to finding the “minimal crosstalk area” of the targeted muscle. MCA helps to limit or avoid crosstalk from neighboring muscles [22].
Mezzarane et al. presented the mathematical relationship (see Equation (2) below) between the target muscle EMG and crosstalk [23]:
2.5. Internal Noise
Anatomical, biochemical and physiological factors take place due to the number of muscle fibers per unit, depth and location of active fibers, and amount of tissue. These factors are called internal noise and directly affect EMG signal quality. Conventionally, physical capacitive effects are assumed negligible when analyzing the EMG signals. However, these assumptions might not be valid f or muscle tissue. Both muscle conductivity and permittivity are frequencydependent (dispersive). Furthermore, skin has a relatively low conductivity and high permittivity such that capacitive effects would be expected to be significant and the dispersive effects of permittivity will be more pronounced [24]. Therefore, the capacitive effects also act as an internal noise for an EMG signal. The amount of the tissue between contracting muscles and electrodes, along with their thickness, affect the amplitude of the EMG signal. Hemingway et al. showed that if the thickness of the subcutaneous tissue between the surface electrode and active muscles increases, then the electromyographic activity decreases [25]. They observed the effect by examining 20 normal subjects who contracted their muscle force for 45 s. It should be mentioned that all the subjects had varying amounts of subcutaneous tissue. The amount of excess body fat is considered as an internal noise for EMG because it increases the separation between the active muscle fibers and the detection sites. Under the recording sites, surgical fat layer reduction increases surface EMG signal amplitude [26]. These effects can be partly reduced by using high pass spatial filters [27].
2.6. Inherent Instability of the Signal
The amplitude of the EMG signal is quasirandom in nature. The frequency components between 0 and 20 Hz are mostly unstable because they are affected by the firing rate of the motor units. The firing rate of the motor units is quasirandom in nature. Because of the unstable nature of these components of the signal, it is considered as unwanted noise. The numbers of active motor units, motor firing rate and mechanical interaction between muscle fibers can change the behavior of the information in the EMG signal [15].
2.7. Electrocardiographic (ECG) Artifacts
The electrical activity of the heart is the foremost interfering component for surface electromyography (sEMG) in the shoulder girdle, which is called an “electrocardiogram (ECG) artifact” [28]. Cardiac activity (ECG artifact) often contaminates EMG signals, especially in trunk muscle electromyography [29]. The placement of EMG electrodes, which is conducted by a selection of the pathological muscle group, often decides the level of ECG contamination in EMGs. ECG contamination in EMGs may be kept at a minimal level by commonmode rejection at the recording site, by the careful placement of bipolar recording electrodes along the heart's axis if possible [30]. Due to an overlap of frequency spectra by ECG and EMG signals and their relative characteristics, such as nonstationarity and varied temporal shape, it is very difficult to remove the ECG artifacts from the EMG signal [31]. ECG contamination is only visually identifiable below 25% maximum voluntary contraction (MVC) of EMG activation. However, Hu et al. suggested that the level of corruption by ECG artifacts on sEMG parameters is more serious and prominent under static sEMG measurements [32]. Highpass filtering at 100 Hz essentially removed the effect of ECG interference. Whenever subjects are maintaining constant force contraction, repetitive fluctuation occurs in the intensity of surface EMG signals due to the ECG artifact. Highpass filter is a very effective method to eliminate this oscillation caused by the ECG artifact [33].
3. EMG Signal Processing
In the field of clinical diagnosis and biomedics, the analysis of EMG signals with powerful and advanced methodologies is becoming more and more a required tool for healthcare providers. This overview covers recent advances in the field of EMG signal processing.
3.1. Wavelet Analysis
The timefrequency plane is one of the most fundamental concepts in signal analysis. The Wignerville distribution (WVD) is one timefrequency representation method, which is used for analyzing the EMG signal. In 1992, Ricamato et al. showed that it is possible to present the frequency ranges of the motor unit by WVD [34]. WVD is highly concentrated in the instantaneous frequency and time of the signal, which is an excellent localization property of this method. It has a crossterm effect and is very noisy. Therefore, it is not well suited for analyzing a multicomponent signal like EMG.
Wavelets have been growing in popularity as an alternative to the usual Fourier transform method. The wavelet transform can essentially be divided into discrete and continuous forms. It efficiently transforms the signals with a flexible resolution in both time and frequencydomains. The time taken for processing the signal using Discrete Wavelet Transform (DWT) method is low. However, in Continuous Wavelet Transform (CWT), it is more consistent and less timeconsuming due to the absence of down sampling. The DWT method has been successful in analyzing nonstationary signals, such as surface EMG (sEMG) signals, but it yields a highdimensional feature vector [35].
The basic analytical expression for CWT is presented in Equation (3) below. In a wavelet transform, the wavelet corresponding to scale a and time location b is given by:
Successive lowpass and high pass filtering in the discretetime domain computes the DWT. The general equation of DWT (Equation (4)), is given below:
Daubechies analyzed the time series that contained nonstationary power at many different frequencies, by using wavelet transform [36]. The different types of wavelets have different timefrequency structures. There are several factors that should be considered when choosing the wavelet function [37]. Guglielminotti and Merletti theorized that wavelet transform exhibits very good energy localization in the timescale plane when the shape of the MUAP is matched with wavelet shape [38], in the order that the wavelets are generally chosen, whose shapes are similar to those of the MUAP. In 1997, Laterza and Olmo explained that wavelet transform was developed as an alternative approach to other time frequency representations to overcome the resolution problem. Moreover, WT is not affected by cross terms, which is particularly relevant when dealing with multicomponent signals [39]. The WT is principally useful for MUAP detection in the presence of additive white noise. Mexican hat wavelet and the Morlet wavelet are the most popular continuous wavelets. One of the disadvantages in this approach is that the Mexican hat wavelet does not accurately match the MUAP shape. The major problem of fast and short term Fourier transform (SFT and FFT) is that the signals are considered to be stationary signals [40]. Therefore, to overcome this problem Pattichis and Pattichis processed the signal at different resolution levels by using the continuous wavelet transform [41].
The preprocessing stage based on a wavelet denoising algorithm for sEMG upper and lowerlimb movement recognitions has been a huge success over the past few years [42,43]. Removing the interference of random noises from EMG signals (for example, white Gaussian noise (WGN)) using filtering procedures is difficult. Wavelet denoising algorithms can effectively remove these noises [44]. Phinyomark et al. provided the basic idea of a waveletbased denoising procedure. The application of this algorithm needs the selection of five processing parameters, including: (1) the type of wavelet basis function; (2) the scale; (3) the threshold selection rule; (4) the threshold rescaling method, and (5) the thresholding function [44]. Selecting the right wavelet function is the most crucial part of wavelet denoising, which in turn depends on a number of factors, such as the type of application and characteristics of the signal. Phinyomark et al. studied five wavelet functions (db2, db5, sym5, sym8 and coif5) for denoising the sEMG signal for multifunction myoelectric control. They analyzed the processed sEMG by measuring the mean square error (MSE) parameter and showed that the scale level 4 provides the better performance when compared with other scale levels. They also showed that the fifth order of Coiflet provides the perfect reconstruction for sEMG signal [45]. Where the signals contain discontinuities and sharp spikes, the wavelet transform denoising method finely preserved the maximum signal character [46]. The selection of suitable wavelet functions from three twentyfour wavelet function and decomposition levels is very important for EMG signal from a denoising viewpoint. Jiang and Kuo assessed four classical threshold estimation functions and concluded that EMG signals are insensitive to the selection of threshold estimation functions [47]. In 2003, Kumar et al. determined muscle failure by using the Symlet function (Sym4 and Sym5) with decomposition level 8 and 9 (out of 10 levels) [48]. Hossain and Mamun proved that WF db45 shows the best contrast when they analyzed the sEMG signal using both power spectrum and bispectrum compared to the other four WFs (Haar, db2 sym4 and sym5) within the range 50 to 70 Hz [49]. In 2012 Wei et al. proposed a new waveletbased algorithm that analyzed surface EMG signals in three steps [50]. For denoising EMG, they applied a Maximal Overlap Discrete Wavelet Transform (MODWT) algorithm and decomposed EMG data into different frequency band oscillations. For this algorithm they used the wavelet function db4 at decomposition level 5. It was an easy, simple and inexpensive process.
The benefit of using a wavelet basic function is that it has continuous derivatives, which allows it to decompose a continuous function more efficiently. It also avoids unwanted signals. Daubechies's wavelets provide better energy concentration with longlength filters than those with shortlength filters [51]. Table 1 displays the different types of wavelet functions with their families.
By investigating and analyzing various research studies on wavelet transform, the author has concluded that analyzing sEMG signals using Daubechies's function renders successful results. For obtaining better results from a sEMG analysis on different applications, the author recommends to use the db function (db2, db4, db6, db44 and db45) at decomposition level 4. In case of high and low noises in sEMG, the db function at decomposition level 4 can be used as a compromise level. The author simulated the raw sEMG signal by using the above wavelet functions. Figure 2 represents the raw sEMG signal from the right rectus femoris muscle during maximum walking speed and its denoised version using a different wavelet function, such as db2, db4, db6, db44 and db45 at decomposition level 4.
3.2. Higher Order Statistics (HOS)
Higher order spectra are defined as spectral representations of higher order cumulants of a random process. Let x (k) be a real, discrete time and nthorder stationary random process. Moreover, let w = [w1, w2…wn] T and x = [x(k + τ_{1}),……,x(k + τ_{n}_{−1})]^{T}. Then the nthorder moment of x (k), ${\mathit{\text{M}}}_{\mathit{\text{n}}}^{\mathit{\text{x}}}=\left({\tau}_{1},{\tau}_{2}\cdots {\tau}_{n1}\right)$ is defined as the coefficient in the Taylor expansion of the moment generating function in Equation (5):
In practice, the nthorder moment can be equivalently calculated by taking an probability over the process multiplied by (n−1) lagged versions of itself. Higher order spectra are often estimated directly in the spectral domain as expected values of higher order periodograms. The spectral representation of Higher Order Statistics (HOS), such as moments and cumulants of the third order and above, are known as polyspectra or higher order spectra. For efficient processing of the EMG signal, HOS is applicable due to its unique properties. HOS can identify deviations from linearity, stationarity or Gaussianity in the signal [52]. HOS is important for a quality neuromuscular diagnosis to obtain information on innervation pulse trains and MotorUnit Action Potentials (MUAPs) characteristics. Kanosue et al. developed a statistical signal processing method that can determine the amplitude and number of recruited MUAPs [53]. The spectral moments (second and fourth order) with a parametric model are used in this method. Secondorder statistics (SOS) provide low order models and present the real data that is parsimonious with the particle dimension. Within the past few decades, there has been considerable interest in using higher order statistics (HOS) technique [15]. HOS was introduced in the 1960s, and Giannakis and Tsatsanis applied HOS for EMG signal analysis in 1991. The advantage of HOS is that accurate phase reconstruction is possible in the HOS domain, but SOS is phaseblind [54]. Moreover, HOS is useful for modelling nonGaussian and nonlinear processes. Kalpanis et al. gave the theory using HOS, which characterizes the Gaussianity of the sEMG signal by using the bicoherence index. sEMG signal distribution is highly nonGaussian at low and high levels of force, whereas the distribution has its maximum Gaussianity at the midlevel of maximum voluntary contraction (MVC). They used the HOS technique in their sEMG signal analysis in order to extract a new parameter (power spectrum median frequency) that could enhance the diagnostic character of sEMG [55]. In probability theory and statistics, the skewness (measure of third order cumulants) measures asymmetry and kurtosis (measure of fourth order cumulants) measures peakness of the probability distribution. Cumulants and moments are particularly convenient; this is why cumulants and moments are successfully used in the higher order statistics technique. In an earlier stage, Yana et al. used HOSbased approaches to recover MUAPs from the sEMG signal [56]. However, this approach was only applied to simulated sEMG signals. Shahid et al. applied HOS to the EMG signal and proposed the ‘Bispectrum of Linear Systems’ to characterize the motor unit action potential due to its advantages of HOS over SOS [57]. The EMG processing method based on the first and second order moments and cumulants (SOS) cannot suppress white Gaussian noise from the signal where HOS (bispectrum or third order spectrum) can eliminate this noise. The mathematical model of the EMG signal is of the output of a Linear Time Invariant (LTI) system whose input is nonGaussian white noise. Using the convolution theorem for the LTI system, the output x (n) can be expressed as:
Whenever a signalprocessing technique is applied on the diagnosis of neuromuscular disorders, some parameters, such as amplitude, number of phases, spike duration, number of turns, etc. should be taken into consideration. The HOS method characterizes and detects the nonlinearity of the sEMG signal. This method is also able to estimate both the amplitude and phase information successfully. From the above analysis of various research works on the HOS technique, the author concluded that this method is more useful for analyzing the sEMG signal in case of diagnosing neuromuscular disorder.
3.3. Empirical Mode Decomposition (EMD)
EMD is a moderately new, datadriven adaptive technique for the analysis of nonstationary and nonlinear signals. EMD is a method to analyze the underlying notion of instantaneous frequency, and provides insight into the timefrequency signal features. The EMD method was first introduced by Huang et al. [58], and is used as a sifting process that estimates intrinsic mode functions (IMFs).
EMD aims to decompose a multicomponent signal, x(t) into a number of virtually monocomponent IMFs, h(t) plus a nonzeromean value of the residual component, r(t):
Each one of the IMFs; e.g., h(k + 1), is obtained by applying a process called sifting to the residual multicomponent signal as in the following Equation (8):
The sifting process is an iterative procedure which aims to achieve improved estimates of hk(t) in each iteration. More specifically, during the (n + 1) th sifting iteration, the temporal estimate of the IMF hnk(t), is obtained in the previous sifting iteration. This process is repeated until the designated IMF fulfills the following criteria:
 (1)
The number of extrema and the number of zero crossings must either equal one another, or differ at most by one.
 (2)
The mean value of the upper envelope and lower envelope is zero at any point of the whole time series.
When the IMF component is a monotonic function, the process is finalized and the original signal is reconstructed by adding all the IMF components along with the mean of final residue, m_{final}. Final residue is obtained by the difference between S(t) and the sum of all IMFs. The reconstructed signal, S(t) can be represented as in the following Equation (9):
During the signal processing, EMG signals use the EMD for background activity attenuation. EMD is very effective for noise reduction because it is a nonlinear method that can deal with nonstationary data. This procedure makes no assumptions about the input timeseries where the wavelet procedure depends on the basic mother wavelet function. Andrade et al. showed that the EMD method provides better results for the attenuation of EMG background activity (noise) when compared with different wavelet prototypes (db2, db3 and db4). However, computing IMFs takes a lot of time, which can be disadvantageous when compared to wavelets [59]. Figure 4 illustrates the raw EMG data from the right vastus medialis muscle during maximum walking speeds; EMD decomposes it into a finite number of intrinsic mode functions, which is shown in Figure 5.
The major drawback of the EMD method is that it is more sensitive to the presence of noise, and has a modemixing problem. The EMD method is also a timeconsuming process. Therefore, a more robust, noiseassisted version of the EMD algorithm, called Ensemble EMD (EEMD) is used [60]. Ensemble EMD (EEMD) was introduced to remove the modemixing effect. The EEMD bypasses the modemixing problem of the original EMD by adding white noise into the targeted signal repeatedly. It also provides physically unique decompositions when it is applied to data with mixed and intermittent scales. Zhang et al. showed that different types of noises [powerline interference (PLI), white Gaussian noise (WGN), and baseline wandering (BW)] could be adaptively removed based on an IMF filtering where an EMD/EEMDbased IMF filtering framework achieved improved performance than the conventional digital filters (IIR causal and IIR noncausal filters). It has been found that with a low level of SNR of the processed signal, the EEMD method provided the best surface EMG denoising performance compared to all other methods [61].
By studying the sEMG signal analysis using the empirical mode decomposition technique, the author has come to the conclusion that the EEMD method offers the most successful results for the attenuation of specific noises of sEMG signals. This method is more robust and the filtering procedure is able to directly extract signal components, which overlap significantly in time and frequency. EEMD achieved best surface EMG denoising performance for attenuating noises, especially in cases of powerline noises (PLI), white Gaussian noise (WGN), baseline wandering (BW) and ECG artifacts.
3.4. Artificial Neural Network (ANN)
The Neural Network (NN) approach is suitable for modeling nonlinear data and is able to cover distinctions among different conditions. The requirements for designing an ANN for a given application include: (i) determining the network architecture; (ii) defining the total number of layers, the number of hidden units in the middle layers and number of units in the input and output layers; and (iii) the training algorithm used during the learning phase [62]. The back propagation neural network (BPNN) is a popular learning algorithm to train selflearning feedforward neural networks. However, some drawbacks of this method exist, in that NN requires a huge quantity of training data, the network architecture is quite rigid and NN takes too many learning iterations [63]. Another neural network, called Cascade Correlation Network (CCN), can overcome the limitations of BPNN. It reduces the Mean Square value of the required signal and the convergence time, while increasing the SNR. CCN is an architecture that uses a supervised learning algorithm for artificial neural networks [64]. CCN offers several advantages, such as: no need to guess the size, depth and connectivity pattern of the network in advance; it learns approximately 50 times faster than a standard backpropagation algorithm; and it is very appropriate for large training sets. However, a maximum correlation criterion systematically pushes the hidden layers to their saturated excessive values in place of an active layer, so the error surface becomes rough. This is the main disadvantage of CCN [65]. Mankar and Ghatol mentioned that a radial basis function (RBF) neural network efficiently removes artifacts from the EMG signal, when compared to other types of neural networks. Table 2 demonstrates the comparison of performance parameters; i.e., Mean Square Error (MSE) and correlation coefficient, among several neural network methods for EMG noise reduction [66,67]. In this case, a single, hidden layer of processing elements belongs to the RBF network which uses Gaussian transfer functions, rather than the standard sigmoidal functions employed by Multilayer Perceptron (MLP).
Table 2 represents the performance comparison of various neural networks. All the neural networks were trained to reduce the noises in the EMG signal using the training data. In addition, cross validation data were used to compare the efficiency of the learning ANN models in terms of solving the problem at hand.
Among these models, it compared: MultiLayer Perceptron NN (MLP), Generalized Feed Forward NN (Gen FF), Modular NN (Mod NN), Jordan/Elman NN, and Recurrent Neural Network. The RBF network possesses several distinctive features, which makes it unique from other networks.
The general Equation (10), of this network is given below [68]:
Here, ϕ(‖x−c_{i}‖) is the radial basis function of the hidden layer; W_{ij} is the weight between ith hidden layer and jth output; ci = center vector; Yj and βj are the output of the network and bias value of the output jth neuron; and N = Number of nodes in the hidden layer.
Determining the number of neurons in the hidden layer is very crucial because the data learning capability in the RBF neural networks depends on its sufficiency [69]. Kale and Dudul demonstrated that a Focused TimeLagged Recurrent Neural Network (FTLRNN)based filter with a single, hidden layer elegantly removes noise from the EMG signal and gives reasonable accuracy [70]. According to their experimental study, Table 3 shows that compared to RBF NN and MLP, the FTLRNN model needs more time for training. However, the results of the Mean Square Error (MSE) and corelation coefficient (r), and the visual inspection of modeling characteristics prove the FTLRNN model to be superior to the other two NNs. Here, the number of epochs is constant (1,000) for all three NNs. From the table, it can be observed that the FTLRNN model provides very low MSE and the high correlation coefficient. Therefore, FTLRNN is the best neural network to remove noise from an EMG signal.
An Artificial Neural Network is not a very common method for sEMG signal processing for noise reduction. However, in recent years several researchers have applied the different approaches of the ANN method to sEMG noise removal. By analyzing all of the approaches, the author recommends to use Jordan/Elman NN as a sEMG noise reduction approach. The advantage of the Jordan/Elman NN is that it is simple, speedy and is capable of generalization.
3.5. Independent Component Analysis (ICA)
The ICA algorithm has rapidly become one of the most prominent signal processing techniques. The ICA is a statistical method, which can assume the original signal from the mixture signal. P. Comon first proposed this method [71] and it is used for transforming an experimental multivariate random vector into components that are statistically independent from each other. In ICA there is no order of magnitude associated with each component, and the extracted components are invariant to the sign of the sources. Using this vectormatrix notation, the above mixing model is written as:
Equation (11) represents an ICA model. Where X = [x_{1}, x_{2}…x_{m}]^{T} is an m vector of linear mixtures, S = [s_{1}, s_{2},…,s_{n}]^{T} is an ndimensional random vector of independent source signals, and A is fullrank m × n scalar linearly mixing matrix (n × m). Without knowing the source signals and the mixing matrix, a signal copy of the statistically independent sources s will be estimated from observed mixtures x. Figure 6 shows that the block diagram of the blind source separation technique.
In this figure s (t) are the sources. X (t) are the recordings sˆ (t) are the estimated sources, A is the mixing matrix, and W is the unmixing matrix. Without nonGaussianity, the estimation of the ICA model is not possible. ICA yields improvements above Principal Component Analysis (PCA), when signals do not display a Gaussian distribution [72]. It is suitable to separate the EMG signals from different sources when the assumptions below are fulfilled:
 (i)
Sources are independent at each time instant
 (ii)
Mixing matrix is linear and propagation delays of it are negligible
 (iii)
The sources are stationary and do not change with time
 (iv)
The signals are nonGaussian
 (v)
The electromyographic (EMG) artifacts are statistically and mutually independent.
Consequently, ICA is a feasible method for source separation and decomposition of an EMG signal. Nowadays it is widely used to separate and remove noise sources from EMG and to decompose EMG signals into a maximum number of independent components. There are different types of ICA algorithms; some of them are used for processing the EMG signal, such as the Fast ICA algorithm, the Joint Approximate Diagonalization of Eigenmatrices (JADE), and the Infomax Estimation or maximum likelihood algorithm. The Fast ICA algorithm is a very popular method due to its simplicity, fast convergence and satisfactory results.
Hyvarinen introduced new contrast (or objective) functions for ICA based on the minimization of mutual information first [73]. There are two types of fast ICA algorithms: Fixedpoint algorithm for one unit, and Fixedpoint algorithm for several units. The Fast ICA algorithm could be performed at the beginning of each iteration, in order to solve overlaps and cancellations between MUAPs. It solves the low signaltonoise ratio, which is the main complication in surface EMG signal decomposition [74]. Nakamura et al. reported that ICA is a very useful technique for decomposing sEMG signals into MotorUnit Action Potentials (MUAPs) originating from different muscle sources. Fast ICA could provide much better discrimination of the properties of MotorUnit Action Potential Trains (MUAPTs) for sEMG signal decomposition (i.e., waveforms, discharge intervals, etc.) than PCA [75]. Fast ICA is a type of algorithm that successfully isolates powerline components from EMG signals. However, the performance of Fast ICA fluctuates quickly and few components obtained by ICA decomposition are inverted—a major problem when automatically decomposing EMG signals. Cardoso firstly proposed the JADE algorithm [76], which is more effective than Fast ICA for decomposing sEMG signals [73]. The JADE algorithm is based on the principle of computing several cumulant tensors, which are a generalization of matrices [77]. Firstly, Zhou et al. examined the feasibility of ICA based on an Information maximization (Infomax) algorithm for obtaining more information of the active motor units. Infomax ICA was unable to isolate all the MUAP trains due to time delays and the variances in shape between the surface action potentials detected at the different electrode locations. Furthermore, blind source separation techniques addressing a more complex convoluted mixing model are required for obtaining accurate firing rate information [78]. Bell and Sejnowski first introduced the Maximum Likelihood (ML) algorithm by using the stochastic gradient method [79]. The estimation of this algorithm is based on the fact that no prior information is available. Furthermore, Garcia et al. demonstrated that the JADE ICA could be used successfully for solving overlaps of MUAPs. In each iteration of the algorithm, the action potentials of one motor unit (MU) could generally be separated from the others. They showed that the JADE algorithm is more efficient than Fast ICA. JADE's performance is not strongly affected by added noise. However, interchannel delay is the main drawback of this method [80].
In this section, the authors have reviewed some of the more prevalent approaches to ICA along with their potential benefits when applying them to EMG signals. The author has concluded that the ICAbased filtering procedure provides successful results in removing ECG artifacts and powerline noise (PLI), due to its largely independent signaltonoise ratio, and because of its subtle effects on frequency content.
4. EMG Features
Because of the various noises and artifacts detected among EMG signals, required information remains an amalgam inside the raw EMG signals. However, if these raw signals are used as an input in sEMG classification, the efficiency of the classifier decreases. To improve the performance of the classifier, researchers have been using different types of EMG features as an input to the classifier. To achieve optimal classification performance, the properties of EMG feature space (e.g., Maximum Class separability, robustness, and the computational complexity) should be taken into consideration [81]. There are three types of EMG features in different domains: time domain, frequency domain and timefrequency domain features. Hudgins et al. developed time domain features of the sEMG. They used mean absolute value (MAV), mean absolute value slope, slope sign changes (SSC), waveform lengths (WL) and zero crossings (ZC) for representing myoelectric patterns [82–84]. These features are termed as ‘the Hudgins feature’. A carefully selected set of input features provides a higher classification rate than the raw signal [85,86]. In the quest to improve, the accuracy of myoelectric signal pattern classification Englehart et al. compared time domain (TD) features used by Hudgins [82] with the time frequency domain features (TFD) [87]. Based on the results of the classification error, they showed that feature based on Wavelet packet transform (WPT) was the most effective method. Timefrequency domain features are effective feature sets especially for transient myoelectric signal pattern classification. Due to the high dimensionality and highresolution problem of timefrequency representation, dimensionality reduction is often a necessary complement to feature extraction [88]. Features based on Mean Frequency (MNF), Median Frequency (MDF), Mean Peak Frequency (PKF), Mean Power (MNP), Timetopeak Force (TTP), Spectral Moments, Frequency Ratio (FR), Power Spectrum Ratio (PSR), and Variance of Central Frequency (VCF) are not good in EMG signal classification [89]. Table 4 shows the commonly used sEMG feature extraction method.
5. Classification
An efficient means of classifying electromyography (EMG) signal patterns has been the interest of many researchers in the modern era. There are different types of classifiers, which are effectively used for different EMG applications, such as Artificial Neural Network (ANN), fuzzy classifier, Linear Discriminant Analysis (LDA), SelfOrganizing Map (SOM) and Support Vector Machines (SVM) [89]. The raw EMG signal is represented as a feature vector in the feature extraction process, which is used as an input to the classifier. Because raw EMG signals directly feed to the classifier, they are not practical due to the randomness of the EMG signal. To avoid overloading the classifier, features were reduced in the dimension, using different dimension reduction methods. Dimensional reduction methods decrease the burden of the classifier and computational time. PCA is a more wellknown method than other methods of dimension reduction [90]. Waveletbased feature set reduced in dimension by principal components analysis greatly improves the classification accuracy in myoelectriccontrolled prosthesis applicaion [91]. However, Chu et al. proposed a linearnonlinear feature projection method by combining PCA with SelfOrganizing Feature Map (SOFM). This method simplifies the structure of the classifier and provides greater classification performance compared to using only PCA [92]. In the dimension reduction method, the PCA and the Linear Discriminant Analysis (LDA) are well known. However, this method takes more computational time for solving the eigenvalue problem. The estimation method of LDA is a Simple Fisher Linear Discriminant Analysis (SimpleFLDA) that also can be used for the dimension reduction method. This algorithm takes less time to calculate the eigenvector because it does not use a matrix [93]. The amalgamation of TD features set with FLDA technique provides a good balance between robustness of the algorithm and computational efficiency. Accurate classification of EMG signal has great advantage on prosthetic control, which improves the quality of life of persons with limb deficiency. SVM and LDA classifiers are currently very popular amongst the researcher for the prosthetic control application due to their simple implementation and ease of training [94,95]. Figure 7 represents the main components of the EMG pattern recognition or classification method.
The success of the electromyogram classification system highly depends on the quality of the selected and extracted features [96]. Feature extraction step in the classification system increase information density of the signal [94]. Moreover, assessing and developing efficient dimensionality reduction and classifier methods are suggested for perfect EMG pattern recognition.
Many researchers have highlighted the neural network classifier in EMG pattern recognition because it can represent both linear and nonlinear relationships taken from data being modeled. ANNs are nonlinear statistical data modeling tools that are inspired by the structure of biological neural networks and that are able to process an EMG signal. Del and Park suggested that ANN is a suitable technique for realtime applications of EMG [97]. ANN can precisely recognize the myoelectric (MES) signal. Data obtained by this unsupervised learning technique are then automatically targeted and presented to a Multilayer Perceptrontype Neural Network (MLP NN) [98]. The output of the neural network approach represents a quantity of preferred enervated muscle stimulation over a synergy [13]. In 1993, Tsuji et al. proposed an error back propagationtype neural network for the classification of sixforearm motions by using entropy [99]. Motion classification from the EMG signals is useful in fields such as control of multifunctional powered prosthesis, humanassisting robots or rehabilitation devices, and virtual reality.
A new EMG pattern discrimination method, called the Recurrent LogLinearized Gaussian Mixture Network (RLLGMN), and based on the Hidden Markov Model (HMM), was proposed by Bu et al. [100]. For prosthetic control, they used this method and showed successful forearm motion (Figure 8) discrimination capability and accuracy, which was better than LLGMN and back propagation ANN (BPNN). As depicted in Table 5, they showed that the most excellent discrimination rate and approximately 0 standard deviation is obtained by using the RLLGMN method among all three methods.
Moreover, Wei et al. classified three EMG steady patterns—the normal (NR) pattern, the eye closing (EC) pattern, and the rhythmic jaw movement (RJM) pattern—by using BPANN with the LevenbergMarquardt algorithm [101]. They used this classifier to generate five control commands for a simulated Intelligent Wheelchair. Figure 9 shows the block diagram of this algorithm.
On the other hand, ICA is a feasible method for source separation and decomposition of surface electromyogram (sEMG). Naik et al. examined four algorithms, Fast ICA, JADEICA, InfomaxICA and Temporal Décorrelation Source Separation (TDSEP) ICA, for identifying subtle wrist actions. Table 6 represents the comparison between the various types of ICA algorithms [102].
TDSEP is an ICA algorithm based on the simultaneous diagonalization of several timedelayed correlation matrices. From the table it is observed that it provided the best performance and gave an overall efficiency of 97%. Use of ICA alone is not suitable for sEMG due to the nature of sEMG distribution and order ambiguity. Naik et al. proposed a novel method (Multi Run ICA) which is a combination of the mixing matrix and network weights to classify the sEMG recordings. This approach is able to overcome the ambiguity problems [103].
Fuzzy logic systems have more advantages for biosignal classification. Due to such biological signal characteristics as nonrepeatable and stochastic, fuzzy logic is an advantageous technique in biomedical signal classification. Fuzzy logic methods are superior to neural networkbased approaches because of their simplicity and insensitivity to overtraining. The insufficient number of patterns interferes with the current sEMG, which repeatedly deepens by the inaccuracy of the instrumentation and analytical system. In order to resolve these difficulties, Khezri et al. suggested an Adaptive NeuroFuzzy Inference System (ANFIS) to detect hand gestures [104]. The fuzzy system initially fuzzifies the inputs to values at interval [0, 1], using a set of membership functions (MF's) [105–107]. Then, by using the IFTHEN rule it is derived by using fuzzy logic. The fuzzy rules can be represented Equation (12) as Ri: If x1 is MFi1 and/or x2 is MFi2 and/or … xj is MFj, then zi is:
Based on the level of complexity and the change in hand movement and rate of precision, the ANFIS proves to be better than ANN. Table 7 shows the percentage of specificity and sensitivity measured in both ANFIS and ANNbased methods [104].
The classification of electromyography (EMG) signals is also very important for detecting diseases. In clinical diagnosis, the simplicity, speed and reliability of classification are essential. The EMG signals from disabled patients or patients with different neurological diseases such as Parkinson's, Huntington's, Amyotrophic Lateral Sclerosis, etc. are very different from healthy EMG signals. All these types of patients have neurologic movement disorders and they could have different muscle structures. Therefore, many researchers have been working on EMG signals from these types of patients’ muscle tissue, recognizing it for monitoring the progression of the various diseases. Several research studies are also being carried out on neuromuscular fatigue (muscles that are not able to generate force or power) EMG. Furthermore, an accurate and computationally efficient means of classifying fatigue electromyographic signal patterns has been the subject of considerable research in recent years, which is most applicable in sports science.
Subasi et al. developed two classifier Feedforward Error Backpropagation Artificial Neural Networks (FEBANN) and Wavelet Neural Networks (WNN) for diagnosing EMG patterns [108]. WNN is a neural network where a discrete wavelet function is used as a node activation function in a hidden layer. They used an autoregressive spectrum of EMG as an input to the input layer of FBANN with three discrete outputs representing normal, myopathic or neurogenic disorder. These three EMG patterns are shown in Figure 11.
In 2012, Christodouloua et al. used three classifiers, namely the statistical KNearest Neighbor (KNN), the SelfOrganizing Map (SOM) and the Support Vector Machine (SVM) for classifying neuromuscular disorders (20 normal, 11 myopathy and nine neuropathy subjects) [109]. They first used multiscale amplitude modulationfrequency modulation (AMFM) features as an input to these classifiers. In their study, Gaussian Radial Basis Function was used in the SVM classifier. They proved that SVM provided the best diagnostic performance among all three classifiers. However, the learning speed of SVM was slow [110].
Subasi and Kiymik used the timefrequency methods such as STFT, WignerVille Distribution (WVD) and Continuous Wavelet Transform (CWT), which have been used as preprocessing techniques. ICA was also used to reduce the dimension of feature vectors. Then, the extracted features of the EMG signal were used as an input to the Multilayer Perceptron Neural Network (MLPNN), which could be used to detect muscle fatigue. They showed that ANN with ICA separates EMG signals from healthy and fatigued muscles. By avoiding the spectral estimation, the problems of the conventional Fourier spectral variables deriving method is overcome by this method. Timefrequency methods do not assume quasistationarity or linearity in the order for this method to be appropriate for nonstationary signals. Muscle fatigue is automatically detected by this method [111].
Moreover, for classifying EMG signals, Sezgin used higher order spectra [112]. A bispectrum analysis (which belongs to the higher order spectra class) extracts the phase information from an EMG signal, which is called Quadratic Phase Coupling (QPC). These QPCs were fed into the Extreme Learning Machine (ELM) algorithm in order to separate abnormal activities from normal activities. The main advantage of ELM over the traditional learning methods is that it is capable of training and testing data fast and with a high accuracy. Therefore, this method may also be useful and applicable for a disease monitoring system. Table 8 represents the performance comparison among machine learning classification methods, such as ELM, Support Vector Machine (SVM), Logistic Regression (LR), Linear Discriminant Analysis (LDA) and Artificial Neural Network (ANN). A summary of electromyography pattern recognition techniques in different applications is presented in Table 9.
6. Discussion
This study showed that several undesired signal sources (extrinsic factors, inherent noise in electronic equipment, motion artifacts, ambient noise) can be attenuated to a great extent by using an active electrode. However, this basic technique is not sufficient for the abovementioned noise elimination problem. Researchers have used different types of processing techniques for canceling these noises. Proper use of these techniques can increase EMG signal quality to where the signal becomes much more accurate, simple, reliable and steady. Based on the studies reviewed, the wavelet transform and higher order spectra employed in the processing (noise reduction and significant information extract) method are optimal.
The study also described the use of the electromyography pattern recognition method, which is very important in different applications, such as rehabilitation devices, prosthetic arm/leg control, assistive technology, symptom detection for neuromuscular disorder, and so on.
In case of a disease monitoring system, two major criteria are applicable—one is robustness and reliability, and another is accuracy of diagnosis. Based on these criteria, the SVM classifier (where multiscale Amplitude Modulation and Frequency Modulation (AMFM) histogram features are used as an input) is suggested for classifying electromyography signals. AMFM features can capture instantaneous variations in amplitude, frequency and phase of the electromyography signal. For realtime control of a robotic arm or leg, surface electromyographic (EMG) signal classification is also an important issue. On the other hand, if the number of EMG channels and features increases, the number of control commands of the classifier also increases. A large number of features (especially time domain and time scale feature vector) which extract the significant but different types of information from electromyography also provide improved classification results. Dimensionality reduction methods, Principle Component Analysis (PCA), and Linear Discriminant Analysis (LDA) methods are recommended if a huge number of features are used as input to the classifier. The main advantage of using the method is that the computational complexity of classifiers is allayed greatly. Dimensionality reduction methods should transform the data to a space vector with low dimensions and keep maximum information of the signal.
Furthermore, for increasing the classification accuracy, a combination of processing methods and pattern recognition techniques is strongly recommended. This combination method may be helpful to increase the classification accuracy without having to use too many muscle positions. The findings of this study are tabularized in Table 10, below.
7. Conclusions
A raw EMG signal contains more important information regarding the nervous system in useless form. The aim of this paper was to give detailed information about clearing up commonly associated noises and artifacts from EMG signals, and to explore the various methodologies for analyzing the signals. This study emphasized the algorithms and methodologies used for detecting, processing and classifying EMG signals, and discussed their advantages and disadvantages. This comparison of methodologies will help researchers encounter the perfect method for analyzing EMG signals, which is required in medical and physiological applications, such as diagnosis of neurological problems, biomedical and biochemical research, prosthetic arm control and enduser applications. It is the hope of this study to derive a clear and concise view of EMG processing methods for removing noise and to initiate improvements on current pattern recognition techniques.
The author would like to thank and acknowledge the medical services of Teknologi Kasihatan dan Perubatan Research Group. This study was supported by the University Kebangsaan, Malaysia, under the Malaysia Research Fund through the MSc. Program (Grant No. 030102SF0703).
Conflicts of Interest
The authors declare no conflict of interest.
References
 Farina, D.; Negro, F. Accessing the neural drive to muscle and translation to neurorehabilitation Technologies. IEEE Rev. Biomed. Eng. 2012, 5, 3–14. [Google Scholar]
 Merletti, R.; de Luca, C.J. New Techniques in Surface Electromyography. In Computer Aided Electromyography and Expert Systems; Desmedt, J.E., Ed.; Elsevier: Amsterdam, The Netherlands; New York, NY, USA; Oxford, UK, 1989; volume 2, Chapter 9 (Section 3). pp. 115–124. [Google Scholar]
 Alkan, A.; Günay, M. Identification of EMG signals using discriminant analysis and SVM classifier. Expert Syst. Appl. 2012, 39, 44–47. [Google Scholar]
 De la Rosa, R.; Alonso, A.; Carrera, A.; Durán, R.; Fernández, P. Manmachine interface system for neuromuscular training and evaluation based on EMG and MMG signals. Sensors 2010, 10, 11100–11125. [Google Scholar]
 Phinyomark, A.; Hu, H.; Phukpattaranont, P.; Limsakul, C. Application of linear discriminant analysis in dimensionality reduction for hand motion classification. Meas. Sci. Rev. 2012, 12, 82–89. [Google Scholar]
 Cavalcanti, G.M.A.; Vieira, T.M.M. Surface electromyography: Why, when and how to use it. Rev. Andal. Med. Deport. 2011, 4, 17–28. [Google Scholar]
 Navarro, X.; Krueger, T.B.; Lago, N.; Micera, S.; Stieglitz, T.; Dario, P. A critical review of interfaces with the peripheral nervous system for the control of neuroprostheses and hybrid bionic systems. J. Peripher. Nerv. Syst. 2005, 10, 229–258. [Google Scholar]
 Kappenman, E.S.; Luck, S.J. The effects of electrode impedance on data quality and Statistical significance in ERP recordings. Psychophysiology 2010, 47, 888–904. [Google Scholar]
 De Luca, C.J. Electromyography. In Encyclopaedia of Medical Devices and Instrumentation; Webster, J.G., Ed.; Wiley: New York, NY, USA, 1988; pp. 1111–1120. [Google Scholar]
 Clancy, E.A.; Morin, E.L.; Merletti, R. Sampling, noisereduction and amplitude estimation issues in surface electromyography. J. Electromyogr. Kinesiol. 2002, 12, 1–16. [Google Scholar]
 Tam, H.W.; Webster, J.G. Minimizing electrode motion artefact by skin abrasion. IEEE Trans. Biomed. Eng. 1977, 24, 134–139. [Google Scholar]
 Burbank, D.P.; Webster, J.G. Reducing skin potential motion artifact by skin abrasion. Med. Biol. Eng. Comput. 1978, 16, 31–38. [Google Scholar]
 Conforto, S.; D'Alessio, T.D.; Pignatelli, S. Optimal rejection of movement artefacts from myoelectric signals by means of a wavelet filtering procedure. J. Electromyogr. Kinesiol. 1999, 9, 47–57. [Google Scholar]
 Mesin, L.; Merletti, R.; Rainoldi, A. Surface EMG: The issue of electrode location. J. Electromyogr. Kinesiol. 2009, 19, 719–726. [Google Scholar]
 Reaz, M.B.I.; Hussain, M.S.; MohdYasin, F. Techniques of EMG signal analysis: Detection, processing, classification and Applications. Biol. Proced. Online 2006, 8, 11–35. [Google Scholar]
 Malboubi, M.; Razzazi, F.; Aliyari, S.M. Elimination of Power Line Noise from EMG Signals Using an Efficient Adaptive Laguerre Filter. Proceedings of the International Conference on Signals and Electronic Systems, Gliwice, Poland, 7–10 September 2010; pp. 49–52.
 Gerdle, B.; Karlsson, S.; Day, S.; Djupsjöbacka, M. Acquisition, Processing and Analysis of the Surface Electromyogram. In Modern Techniques in Neuroscience; Windhorst, U., Johansson, H., Eds.; Springer Verlag: Berlin, Germany, 1999; Chapter 26. pp. 705–755. [Google Scholar]
 Viljoen, S.; Hanekom, T.; Farina, D. Effect of characteristics of dynamic muscle contraction on crosstalk in surface electromyography recordings. S. Afr. Inst. Electr. Eng. 2007, 98, 18–28. [Google Scholar]
 Lowery, M.M.; Stoykov, N.S.; Kuiken, T.A. A simulation study to examine the use of crosscorrelation as an estimate of surface EMG cross talk. J. Appl. Physiol. 2003, 94, 1324–1334. [Google Scholar]
 Winter, D.A.; Fuglevand, A.J.; Archer, S.E. Crosstalk in surface electromyography: Theoretical and practical estimates. J. Electromyogr. Kinesiol. 1994, 4, 15–26. [Google Scholar]
 Farina, D.; Merletti, R.; Indino, B.; GravenNielsen, T. Surface EMG crosstalk evaluated from experimental recordings and simulated signals. Reflections on crosstalk interpretation, quantification and reduction. Methods Inf. Med. 2004, 43, 30–35. [Google Scholar]
 Blanc, Y.; Dimanico, U. Electrode placement in surface electromyography (sEMG) Minimal Crosstalk Area (MCA). Open Rehabil. J. 2010, 3, 110–126. [Google Scholar]
 Mezzarane, R.A.; Kohn, A.F. A method to estimate EMG crosstalk between two muscles based on the silent period following an Hreflex. Med. Eng. Phys. 2009, 31, 1331–1336. [Google Scholar]
 Stoykov, N.S.; Lowery, M.M.; Taflove, A.; Kuiken, T.A. A Finite Element Analysis of Muscle Tissue Capacitive Effects and Dispersion in EMG. Proceedings of the 23rd Annual EMBS International Conference, Istanbul, Turkey, 25–28 October 2001; pp. 1044–1047.
 Hemingway, M.A; Biedermann, H.J.; Inglis, J. Electromyographic recordings of paraspinal muscles: Variations related to subcutaneous tissue thickness. Biofeedback Selfregul. 1995, 20, 39–49. [Google Scholar]
 Kuiken, T.A.; Lowery, M.M.; Stoykov, N.S. The effect of subcutaneous fat on myoelectric signal amplitude and crosstalk. Prosthet. Orthot. Int. 2003, 27, 48–54. [Google Scholar]
 Farina, D.; Rainoldi, A. Compensation of the effect of subcutaneous tissue layers on surface EMG: A simulation study. Med. Eng. Phys. 1999, 21, 487–497. [Google Scholar]
 Taelman, J.; Mijovic, B.; Huffel, S.V. ECG Artifact Removal from Surface EMG Signals by Combining Empirical Mode Decomposition and Independent Component Analysis. Proceedings of the International Conference on BioInspired Systems and Signal Processing, Subconference of the 4th International Joint Conference on Biomedical Engineering Systems and Technologies (BIOSTEC 2011), Rome, Italy, 26–29 January 2011; pp. 421–424.
 Willigenburg, N.W.; Daffertshofer, A.; Kingma, I.; van Dieën, J.H. Removing ECG contamination from EMG recordings: A comparison of ICAbased and other filtering procedures. J. Electromyogr. Kinesiol. 2012, 22, 485–493. [Google Scholar]
 Lu, G.; Brittain, J.S.; Holland, P.; Yianni, J.L.; Green, A.; Stein, J.F.; Aziz, T.Z.; Wang, S. Removing ECG noise from surface EMG signals using adaptive filtering. Neurosci. Lett. 2009, 462, 14–19. [Google Scholar]
 Mak, J.N.F.; Hu, Y.; Luk, K.D.K. An automated ECGartifact removal method for trunk muscle surface EMG recordings. Med. Eng. Phys. 2010, 32, 840–848. [Google Scholar]
 Hu, Y.; Mak, J.N.F.; Luk, K.D.K. Effect of electrocardiographic contamination on surface electromyography assessment of back muscles. J. Electromyogr. Kinesiol. 2009, 19, 145–156. [Google Scholar]
 Hargrove, L.; Zhou, P.; Englehart, K.; Kuiken, T.A. The effect of ECG interference on patternrecognitionbased myoelectric control for targeted muscle reinnervated patients. IEEE Trans. Bio Med. Eng. 2009, 56, 2197–2201. [Google Scholar]
 Ricamato, A.L.; Absher, R.G.; Moffroid, M.T.; Tranowski, J.P. A TimeFrequency Approach to Evaluate Electromyographic Recordings. Proceedings of the Fifth Annual IEEE Symposium on ComputerBased Medical Systems, Durham, NC, USA, 14–17 June 1992; pp. 520–527.
 Chu, J.U.; Moon, I.; Lee, Y.J.; Kim, S.K.; Mun, M.S. A supervised featureprojectionbased realtime EMG pattern recognition for multifunction myoelectric hand control. IEEE/ASME Trans. Mechatron. 2007, 12, 282–290. [Google Scholar]
 Daubechies, I. The wavelet transforms timefrequency localization and signal analysis. IEEE Trans. Inform. Theory 1990, 36, 961–1004. [Google Scholar]
 Farge, M. Wavelet transforms and their applications to turbulence. Annu. Rev. Fluid Mech. 1992, 24, 395–457. [Google Scholar]
 Guglielminotti, P.; Merletti, R. Effect of Electrode Location on Surface Myoelectric Signal Variables: A Simulation Study. In Studies in Health technology and Informatics Volume 5: Electrophysiological Kinesiology; IOS Press: Amsterdam, The Netherlands.
 Laterza, F.; Olmo, G. Analysis of EMG signals by means of the matched wavelet transform. Electron. Lett. 1997, 33, 357–359. [Google Scholar]
 Ismail, A.R.; Asfour, S.S. Continuous Wavelet Transform Application to EMG Signals during Human Gait. Proceedings of the 32nd Asilomar Conference on Signals, Systems & Computers, Pacific Grove, CA, USA, 1–4 November 1998; Volume 1, pp. 325–329.
 Pattichis, C.S.; Pattichis, M.S. Timescale analysis of motor unit action potentials. IEEE Trans. Biomed. Eng. 1999, 46, 1320–1329. [Google Scholar]
 Hussain, M.S.; Reaz, M.B.I.; Yasin, F.M.; Ibrahimy, M.I. Electromyography signal analysis using wavelet transform and higher order statistics to determine muscle contraction. Expert Syst. 2009, 26, 35–48. [Google Scholar]
 Khezri, M.; Jahed, M. Surface Electromyogram Signal Estimation Based on Wavelet Thresholding Technique. Proceedings of the EMB 30th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, Vancouver, BC, Canada, 20–24 August 2008; pp. 4752–4755.
 Phinyomark, A.; Limsakul, C.; Phukpattaranont, P. A Comparative Study of Wavelet Denoising for Multifunction Myoelectric Control. Proceedings of the International Conference on Computer and Automation Engineering (ICCAE ′09), Bangkok, Thailand, 8–10 March 2009; pp. 21–25.
 Phinyomark, A.; Limsakul, C.; Phukpattaranont, P. Optimal Wavelet Functions in Wavelet Denoising for Multifunction Myoelectric Control. Proceedings of the Electrical Engineering/Electronics, Computer, Telecommunications and Information Technology, Pattaya, Chonburi, 6–9 May 2009; pp. 1098–1101.
 Zhang, X.; Wang, Y.; Han, R.P.S. Wavelet Transform Theory and Its Application in EMG Signal Processing. Proceedings of the Seventh International Conference on Fuzzy Systems and Knowledge Discovery (FSKD), Yantai, China, 10–12 August 2010; Volume 5, pp. 2234–2238.
 Jiang, C.F.; Kuo, S.L. A Comparative Study of Wavelet Denoising of Surface Electromyographic Signals. Proceedings of the 29th Annual International Conference of the IEEE Engineering in Medicine and Biology Society (EMBS 2007), Lyon, France, 23–26 August 2007; pp. 1868–1871.
 Kumar, D.K.; Pah, N.D.; Bradley, A. Wavelet analysis of surface electromyography to determine muscle fatigue. IEEE Trans. Neural Syst. Rehabil. Eng. 2003, 11, 400–406. [Google Scholar]
 Hussain, M.S.; Mamun, M. Effectiveness of the wavelet transform on the surface EMG to understand the muscle fatigue during walk. Meas. Sci. Rev. 2012, 12, 28–33. [Google Scholar]
 Wei, G.; Tian, F.; Tang, G.; Wang, C. A waveletbased method to predict muscle forces from surface electromyography signals in weightlifting. J. Bionic Eng. 2012, 9, 48–58. [Google Scholar]
 Rafiee, J.; Rafiee, M.A.; Prause, N.; Schoen, M.P. Wavelet basis functions in biomedical signal processing. Expert Syst. Appl. 2010, 38, 6190–6201. [Google Scholar]
 Chua, K.; Chandran, V.; Rajendra, A.U.; Min, L.C. Application of higher order statistics/spectra in biomedical signals—A review. Med. Eng. Phys. 2010, 32, 679–689. [Google Scholar]
 Kanosue, K.; Yoshida, M.; Akazawa, K.; Fujii, K. The number of active motor units and their firing rates in voluntary contraction of human brachialiis muscle. Jpn. J. Physiol. 1979, 29, 427–443. [Google Scholar]
 Giannakis, G.B.; Tsatsanis, M.K. HOS or SOS for Parametric Modeling? Proceedings of the IEEEthe International Conference on Acoustics, Speech, and Signal Processing, Toronto, ON, Canada, 14–17 April 1991; pp. 3097–3100.
 Kaplanis, P.A.; Pattichis, C.S.; Hadjileontiadis, L.J.; Panas, S.M. Bispectral Analysis of Surface EMG. Proceedings of the 10th Mediterranean Electrotechnical Conference, Lemesos, Cypras, 29–31 May 2000; pp. 770–773.
 Yana, K.; Marushima, H.; Mino, H.; Takeuchi, N. Bispectral Analysis of Filtered Impulse Processes with Applications to the Analysis of Bioelectric Phenomena. Proceedings of the Workshop on HigherOrder Spectral Analysis, Vail, CO, USA, 28–30 June 1989; pp. 140–145.
 Shahid, S. Higher Order Statistics Techniques Applied to EMG Signal Analysis and Characterization. Ph.D. Thesis, University of Limerick, Limerick, Ireland, 2004. [Google Scholar]
 Huang, N.E.; Shen, Z.; Long, S.R.; Wu, M.C.; Shih, H.H.; Zheng, Q.; Yen, N.C.; Tung, C.C.; Liu, H.H. The empirical mode decomposition and the Hilbert spectrum for nonlinear and nonstationary time series analysis. Proc. R. Soc. A 1998, 454, 903–995. [Google Scholar]
 Andrade, O.A.; Nasuto, S.; Kyberd, P.; SweeneyReed, C.M.; van Kanijn, F.R. EMG signal filtering based on Empirical Mode Decomposition. Biomed. Signal Process. Control 2006, 1, 44–55. [Google Scholar]
 Wu, Z.; Huang, N.E. Ensemble empirical mode decomposition: A noiseassisted data analysis method. Adv. Adapt. Data Anal. 2009, 1, 1–41. [Google Scholar]
 Zhang, X.; Zhou, P. Filtering of surface EMG using ensemble empirical mode decomposition. Med. Eng. Phys. 2013, 35, 537–542. [Google Scholar]
 Badri, L. Development of neural networks for noise reduction. Int. Arab J. Inf. Technol. 2010, 7, 289–294. [Google Scholar]
 Ito, K.; Tsuji, T.; Kato, A.; Ito, M. LimbFunction Discrimination Using EMG Signals by Neural Network and Application to Prosthetic Forearm Control. Proceedings of the 1991 IEEE International Joint Conference on Neural Networks, Singapore, 18–21 November 1991; pp. 1214–1219.
 Fahlaman, S.E.; Liebiere, C. The CascadedCorrelation Learning Architecture. In Advances in Neural Information Processing Systems II; Touretzky, D.S., San, M.C.A., Eds.; Morgan Kaufmann Publishers Inc.: San Francisco, CA, USA, 1990; pp. 524–532. [Google Scholar]
 Selva, V.C.K.; Kanagasabapathy, P.; Kumar, E.S. A survey of interference cancellation in biosignals. Int. J. Rev. Comput. 2011, 7, 64–83. [Google Scholar]
 Mankar, V.R.; Ghatol, A. Use of RBF neural network in EMG signal noise removal. Wseas Trans. Circuits Syst. 2008, 7, 259–265. [Google Scholar]
 Haselsteiner, E.; Pfurtscheller, G. Using timedependent neural networks for EEG classification. IEEE Trans. Rehab. Eng. 2000, 8, 457–463. [Google Scholar]
 Wang, S.; Gao, Y.; Zhao, J.; Yang, T.; Zhu, Y. Prediction of sEMGBased Tremor Joint Angle Using the RBF Neural Network. Proceedings of 2012 IEEE International Conference on Mechatronics and Automation, Chengdu, China, 5–8 August 2012; pp. 2103–2108.
 Kurban, T.; Beşdok, E. A comparison of RBF neural network training algorithms for inertial sensor based terrain classification. Sensors 2009, 9, 6312–6329. [Google Scholar]
 Kale, S.N.; Dudul, S.V. Intelligent noise removal from EMG signal using focused timelagged recurrent neural network. Appl. Comput. Intell. Soft Comput. 2009, 2009, 1–12. [Google Scholar]
 Comon, P. Independent component analysis—A new concept? Signal Process 1994, 36, 287–314. [Google Scholar]
 Staudenmann, D.; Daffertshofer, A.; Kingma, I.; Stegeman, D.F.; van Dieen, J.H. Independent component analysis of highdensity electromyography in muscle force estimation. IEEE Trans. Biomed. Eng. 2007, 54, 751–754. [Google Scholar]
 Hyverinen, A. Fast and robust fixed point algorithms for independent component analysis. IEEE Trans. Neural Netw. 1999, 10, 626–634. [Google Scholar]
 Garcia, G.A.; Maekawa, K.; Akazawa, K. Decomposition of synthetic multichannel surfaceelectromyogram using independent component analysis. Lect. Notes Comput. Sci. 2004, 3195, 985–992. [Google Scholar]
 Nakamura, H.; Yoshida, M.; Kotani, M.; Akazawa, K.; Moritani, T. The application of independent component analysis to the multichannel surface electromyographic signals for separation of motor unit action potential trains: Part I—Measuring techniques. J. Electromyogr. Kinesiol. 2004, 14, 433–441. [Google Scholar]
 Cardoso, J.F.; Souloumiaac, A. Blind beam forming for NonGaussian signals. IEEE Proc. F 1993, 140, 362–370. [Google Scholar]
 Acharaya, D.P.; Panda, G. A review of independent component analysis techniques and their applications. IETE Tech. Rev. 2008, 25, 320–332. [Google Scholar]
 Zhou, P.; Madeleine, M.; Lowery, W; Rymer, Z. Extracting motor unit firing information by independent component analysis of surface electromyogram: A preliminary study using a simulation approach. Int. J. Comput. Syst. Signal. 2006, 7, 19–28. [Google Scholar]
 Bell, A.J.; Sejnowski, T.J. An information maximization approach to blind separation and blind deconvolution. Neural Comput. 1995, 7, 1129–1159. [Google Scholar]
 García, G.A.; Okuno, R.; Akazawa, K. A decomposition algorithm for surface electrodearray electromyogram A noninvasive, threestep approach to analyze surface EMG signals. IEEE Eng. Med. Biol. Mag. 2005, 24, 63–72. [Google Scholar]
 ZardoshtiKermani, M.; Wheeler, B.C.; Badie, K.; Hashemi, R.M. EMG feature evaluation for movement control of upper extremity prostheses. IEEE Trans. Rehabil. Eng. 1995, 3, 324–333. [Google Scholar]
 Hudgins, B.; Parker, P.; Scott, R.N. A new strategy for multifunction myoelectric control. IEEE Trans. Biomed. Eng. 1993, 40, 82–94. [Google Scholar]
 Englehart, K.; Hugdins, B.; Parker, P. Multifunction Control of Prostheses Using the Myoelectric Signal. In Intelligent Systems and Technologies in Rehabilitation Engineering; Teodorescu, H.N.L., Jain, L.C., Eds.; CRC Press: New York, NY, USA, 2000. [Google Scholar]
 Englehart, K.; Hudgins, B. A robust, realtime control scheme for multifunction myoelectric control. IEEE Trans. Biomed. Eng. 2003, 50, 848–854. [Google Scholar]
 Ibrahimy, M.I.; Khalifa, O.O.; Ahsan, M.R. EMG Motion Pattern Classification through Design and Optimization of Neural Network. Proceedings of the International Conference on Biomedical Engineering (ICoBE), Kuala Lumpur, Malaysia, 27–28 February 2012; pp. 175–179.
 Rajesh, V.; Kumar, P.R.; Reddy, D.V. SEMG Based Human Machine Interface for Controlling Wheel Chair by Using ANN. Proceedings of the International Conference of Control, Automation, Communication and Energy Conservation, Perundurai, Tamilnadu, India, 4–6 June 2009; pp. 1–6.
 Englehart, K.; Hudgins, B.; Parker, P.A.; Stevenson, M. Classification of the myoelectric signal using timefrequency based representations. Med. Eng. Phys. 1999, 21, 431–438. [Google Scholar]
 Hargrove, L.J.; Li, G.; Englehart, K.B.; Hudgins, B.S. Principal components analysis preprocessing for improved classification accuracies in patternrecognitionbased myoelectric control. IEEE Trans. Biomed. Eng. 2009, 56, 1407–1414. [Google Scholar]
 Phinyomark, A.; Phukpattaranont, P.; Limsakul, C. Feature reduction and selection for EMG signal classification. Expert Syst. Appl. 2012, 39, 7420–7431. [Google Scholar]
 Asghari, O.M.; Hu, H. Myoelectric control systems—A survey. Biomed. Signal Process. Control 2007, 2, 275–294. [Google Scholar]
 Englehart, K.; Hudgin, B.; Parker, P. A wavelet based continuous classification scheme for multifunction myoelectric control. IEEE Trans. Biomed. Eng. 2001, 48, 302–311. [Google Scholar]
 Chu, J.U.; Moon, I.; Mun, M.S. A realtime EMG pattern recognition system based on linearnonlinear feature projection for a multifunction myoelectric hand. IEEE Trans. Biomed. Eng. 2006, 53, 2232–2239. [Google Scholar]
 Oyama, T.; Mitsukura, Y. Wrist EMG Signals Identification Using Neural Network, Industrial Electronics. Proceedings of the 35th Annual Conference of IEEE (IECON '09), Porto, Portugal, 3–5 November 2009; pp. 4286–4290.
 Scheme, E.; Englehart, K. Electromyogram pattern recognition for control of powered upperlimb prostheses: State of the art and challenges for clinical use. J. Rehabil. Res. Dev. 2011, 48, 643–659. [Google Scholar]
 Jiang, N.; Dosen, S.; Muller, K.R.; Farina, D. Myoelectric control of artificial limbs—Is there a need to change focus? IEEE Signal Process. Mag. 2012, 29, 152–150. [Google Scholar]
 Chan, F.; Yang, Y.S.; Lam, F.; Zhang, Y.T.; Parker, P. Fuzzy EMG classification for prosthesis control. IEEE Trans. Rehabil. Eng. 2000, 8, 305–311. [Google Scholar]
 AlMulla, M.R.; Sepulveda, F.; Colley, M. A review of noninvasive techniques to detect and predict localised muscle fatigue. Sensors 2011, 11, 3545–3594. [Google Scholar]
 Boca, A.D.; Park, D.C. Myoelectric Signal Recognition Using Fuzzy Clustering and Artificial Neural Networks in Real Time, Proceedings of the IEEE International Conference on Neural Networks and IEEE World Congress on Computational Intelligence, Orlando, FL, USA, 27 June–2 July 1994; pp. 3098–3103.
 Tsuji, T.; Ichinobe, H.; Ito, K.; Nagamachi, M. Discrimination of forearm motions from EMG signals by error back propagation typed neural network using entropy. Trans. Soc. Instrum. Control Eng. 1993, 29, 1213–1220. [Google Scholar]
 Nan, B.; Fukuda, O.; Tsuji, T. EMGbased motion discrimination using a novel recurrent neural network. J. Intell. Inf. Syst. 2003, 21, 113–126. [Google Scholar]
 Lai, W.; Hu, H.; Yuan, K. Use of Forehead BioSignals for Controlling an Intelligent Wheelchair. Proceedings of the 2008 IEEE International Conference on Robotics and Biomimetics, Bangkok, Thailand, 21–26 February 2009; pp. 108–113.
 Naik, G.R.; Kumar, D.K.; Weghorn, H. A comparison of ICA algorithms in surface EMG signal processing. Int. J. Biomed. Eng. Technol. 2011, 6, 363–374. [Google Scholar]
 Naik, G.R.; Kumar, D.K.; Palaniswami, M. Multi Run ICA and Surface EMG Based Signal Processing System for Recognising Hand Gestures. Proceedings of the IEEE International Conference on Computer and Information Technology (CIT 2008), Sydney, Australia, 8–11 July 2008; pp. 700–705.
 Khezri, M.; Jahed, M. A neuro–fuzzy inference system for semgbased identification of hand motion commands. IEEE Trans. Ind. Electron. 2011, 58, 1952–1960. [Google Scholar]
 Liu, Y.H. Recognition of electromyographic signals using cascaded kernel learning machine. IEEE/ASME Trans. Mechatron. 2007, 12, 253–264. [Google Scholar]
 Uchida, M.; Ide, H. The control method for the robot hand based on the fuzzy theory. J. Robot. Mechatron. 1992, 4, 262–267. [Google Scholar]
 Shenoy, P.; Miller, K.J.; Crawford, B.; Rao, R.N. Online electromyographic control of a robotic prosthesis. IEEE Trans. Biomed. Eng. 2008, 55, 1128–1135. [Google Scholar]
 Subasi, A.; Yilmaz, M.; Ozcalik, H.R. Classification of EMG signals using wavelet neural network. J. Neurosci. Meth. 2006, 156, 360–367. [Google Scholar]
 Christodoulou, C.I.; Kaplanis, P.A.; Murray, V.; Pattichis, M.S.; Pattichis, C.S.; Kyriakides, T. Multiscale AMFM analysis for the classification of surface electromyographic signals. Biomed. Signal Process. Control 2012, 7, 265–269. [Google Scholar]
 Güler, N.F.; Koçer, S. Use of support vector machines and neural network in diagnosis of neuromuscular disorders. J. Med. Syst. 2005, 29, 271–284. [Google Scholar]
 Subasi, A.; Kemal, K.M. Muscle fatigue detection in emg using timefrequency methods, ICA and neural networks. J. Med. Syst. 2010, 34, 777–785. [Google Scholar]
 Sezgin, N. Analysis of EMG signals in aggressive and normal activities by using higherorder spectra. Sci. World J. 2012, 2012. [Google Scholar] [CrossRef]
Table 1. List of 324 wavelet functions from 15 wavelet families. 
Wavelet Family  Wavelet Subtypes  No 

Haar  db1  1 
Daubechies  db2db45  2–45 
Coiflet  coif1coif5  46–50 
Morlet  morl  51 
Complex Morlet  cmor  52–147 
Discrete Meyer  dmey  148 
Meyer  meyr  149 
Mexican Hat  mexh  150 
Shannon  shan  151–200 
Frequency Bspline  fbsp  201–260 
Gaussian  gaus  261–267 
Complex Gaussian  cgaus  268–275 
Biorthogonal  bior  276–290 
Reverse Biorthogonal  rbio  291–305 
Symlet  sym  306–324 
Table 2. Comparison of different types of Neural network [66]. 
Sr no  Type of ANN  Hidden Layer Configuration  Correlation Coefficient(r)  Minimum MSE Criterion  

Training  Crossvalidation  Testing  
01  MLP  05,05,07  0.627751035  0.0100858  0.02468346  0.00336508 
02  Gen FF  05,05,07  0.636240018  0.0095010  0.01897900  0.00467948 
03  Mod NN  05,05,07  0.636114324  0.0115398  0.02638402  0.00299289 
04  Jor/elman NN  05,05,07  0.627025792  0.00994905  0.025520535  0.003213602 
05  Recurrent NN  05,05,07  0.616395357  0.00997408  0.024154242  0.003366557 
06  RBF network  05,05,07  0.634935685  0.00996188  0.025991453  0.003341636 
Table 3. Comparison of all the NN architectures on test dataset [70]. 
NN Model  Transfer Function in Output Layer  Learning Rule  Mean Square Error (MSE)  Correlation Coefficient (r)  Epochs  Time Elapsed (μs)  %Error 

MLP  Tanh  Momentum  0.02501 (noise)  0.78114 (noise)  1,000  19.16  253 
0.02482 (EMG)  0.58433 (EMG)  
FTLRNN  Linear  Momentum  0.000067 (noise)  0.99950 (noise)  1,000  14  10 
0.000048 (EMG)  0.99939 (EMG)  
RBF  Linear  Levenberg Marquardt (LM)  0.02470 (noise)  0.78414 (noise)  1,000  8.3  293 
0.02482 (EMG)  0.58509 (EMG) 
Table 4. Mathematical representation of widely used sEMG feature extraction methods. 
Feature Extraction  Mathematical Equation 

Integrated EMG(IEMG)  $\mathit{\text{IEMG}}=\sum _{n=1}^{N}\left{x}_{n}\right$ 
Here N denotes the length of the signal and x_{n} represents the sEMG signal in a segment.  
Mean Absolute Value (MAV)  $\mathit{\text{MAV}}=\frac{1}{N}\sum _{n=1}^{N}\left{x}_{n}\right$ 
Modified Mean Absolute Value 1 (MMAV1)  $\mathit{\text{MMAV}}1=\frac{1}{N}\sum _{n=1}^{N}{w}_{n}\left{x}_{n}\right$ 
${w}_{n}=\{\begin{array}{cc}1,\hfill & \mathit{\text{if}}\phantom{\rule{0.2em}{0ex}}0.25N\le n\le 0.75N\hfill \\ 0.5,\hfill & \hfill \mathit{\text{otherwise}}\end{array}$  
Modified Mean Absolute Value 2 (MMAV2)  $\mathit{\text{MMAV}}2=\frac{1}{N}\sum _{n=1}^{N}{w}_{n}\left{x}_{n}\right$ 
${w}_{n}=\{\begin{array}{c}1,\phantom{\rule{0.8em}{0ex}}\mathit{\text{if}}\phantom{\rule{0.2em}{0ex}}0.25N\le n\le 75N\\ \frac{4n}{n},\phantom{\rule{2.0em}{0ex}}\mathit{\text{if}}\phantom{\rule{0.2em}{0ex}}0.25N\le n\hfill \\ \frac{4\left(nN\right)}{n},\phantom{\rule{0.8em}{0ex}}\mathit{\text{if}}\phantom{\rule{0.2em}{0ex}}0.75N\le n\end{array}$  
Simple Square Integral(SSI)  $\mathit{\text{SSI}}=\sum _{n=1}^{N}\left{x}_{n}\right^2$ 
Variance of EMG (VAR)  $\mathit{\text{VAR}}=\frac{1}{N1}\sum _{n=1}^{N}{x}_{n}^2$ 
Root Mean Square (RMS)  $\mathit{\text{RMS}}=\sqrt{\frac{1}{N}\sum _{n=1}^{N}{x}_{n}^2}$ 
Waveform Length (WL)  $WL=\sum _{n=1}^{N}\left{x}_{n+1}{x}_{n}\right$ 
Willison Amplitude (WAMP)  $\mathit{\text{WAMP}}=\sum _{n=1}^{N}f\left{x}_{n+1}{x}_{n}\right$ 
$f\left(x\right)=\{\begin{array}{c}1,\phantom{\rule{0.8em}{0ex}}\mathit{\text{if}}\phantom{\rule{0.2em}{0ex}}\text{x}\ge \mathit{\text{threshold}}\\ 0,\phantom{\rule{0.8em}{0ex}}\mathit{\text{otherwise}}\end{array}$  
Log detector (LOG)  $\mathit{\text{LOG}}={e}^{\frac{1}{N}\sum _{n=1}^{N}\mathit{\text{log}}\left{x}_{n}\right}$ 
Slope Sign Change (SSC)  $\mathit{\text{SSC}}=\sum _{n=2}^{N}f\left[\left({x}_{n}{x}_{n1}\right)\times ({x}_{n}{x}_{n+1})\right]$ 
$f\left(x\right)=\{\begin{array}{c}1,\phantom{\rule{0.8em}{0ex}}\mathit{\text{if}}\phantom{\rule{0.2em}{0ex}}\text{x}\ge \mathit{\text{threshold}}\\ 0,\phantom{\rule{0.8em}{0ex}}\mathit{\text{otherwise}}\end{array}$  
Zero crossing (ZC)  $ZC=\sum _{n=1}^{N1}[\mathit{\text{sgn}}({x}_{n}\times {x}_{n+1}){\cap}^{}\left{x}_{n}{x}_{n+1}\right\ge \mathit{\text{threshold}}]$ 
$\mathit{\text{sgn}}=\{\begin{array}{c}1,\phantom{\rule{0.8em}{0ex}}\mathit{\text{if}}\phantom{\rule{0.2em}{0ex}}\text{x}\ge \mathit{\text{threshold}}\\ 0,\phantom{\rule{0.6em}{0ex}}\mathit{\text{otherwise}}\end{array}$  
Multiscale amplitude modulation–frequency modulation (AM–FM)  $f\left(k\right)=\sum _{n=1}^{M}{a}_{n}\left(k\right)\mathit{\text{cos}}{\varnothing}_{n}(k)$ 
Here n = 1, 2,…M indexes the AM–FM components, a_{n} represents the nth instantaneous amplitude, and ϕ_{n} represents the nth instantaneous phase. Here, AM–FM components are extracted over a dyadic filter bank. 
Table 5. Discrimination results of five subjects (A, B, C, D and E) [100]. 
Subject  A  B  C  D  E 

RLLGMN Mean ± SD (%)  99.06 ± 0.00  89.32 ± 0.37  93.04 ± 0.11  93.49 ± 0.00  92.75 ± 0.00 
LLGMN (Mean ± SD (%))  94.00 ± 5.50  82.83 ± 0.00  88.50 ± 0.04  88.67 ± 0.15  89.26 ± 0.14 
BPNN (Mean ± SD (%))  73.41 ± 7.86  46.52 ± 12.3  44.20 ± 10.4  69.79 ± 9.97  69.17 ± 7.00 
Table 6. Performance of four types ICA algorithm (percentage) for isometric hand gesture Identification [102]. 
Number of Participants  Middle and Index Finger Flexion  Little and Ring Finger Flexion  All Finger Flexion  Finger and Wrist Flexion Together 

Raw EMG  60%  60%  60%  60% 
Infomax  80%  80%  80%  80% 
JADE  85%  85%  85%  85% 
Fast ICA  90%  90%  90%  90% 
TDESP  97%  97%  97%  97% 
Table 7. Performance comparison between ANFIS and ANNbased methods [104]. 
Classifier  Specificity  Sensitivity 

ANFIS  92%  94.67% 
ANN  86.6%  92.2% 
Table 8. Performances of the ANN, SVM, LR, LDA and ELM learning machines [112]. 
Model  Training Process Time (s)  Testing Process Time (s)  Accuracy (%) 

ANN  32.25  1.18  98.20 
SVM  1.80  0.20  96.15 
LR  0.10  0.05  97.50 
LDA  0.09  0.04  97.25 
ELM  0.07  0.005  99.75 
Table 9. Summary of different EMG classification system. 
Feature  Classifier  Classfication Type  Electrode Sensor Placement  Correctness  Reference 

FFT  NN (Feature dimensionality reduction by (SimpleFLDA)  Recognize Wrist motion  FCR & FCU (Four electrode)  94%  Oyama and Mitsukura [93] 
MAV, SSCs, and AR model coefficients of the signal, ZC  Adaptive Neurofuzzy interference system (ANFIS)  Six classes of hand movement  Extensor digitorum, ECR, PL and FCU  92%  Khezri & Jahed [104] 
MAV,RMS, VAR, SD, ZC, SSC & WL  BPANN with LevenbergMarquardt training algorithm  Hand motion pattern  Hand  89.2%  Ahsan et al. [85] 
WPT  MLP(Feature dimensionality reduction by SOFM + PCA)  Multifunction myoelectric hand control  Extensor digitorum, Extensor carpi radialis, PL and FCU (Four channel)  97%  Chu, J.U et al. [92] 
FFT  Fuzzy interference system (FIS)  Hand motion recognition for controlling Robot hand  Hand  90%  Uchida et al. [106] 
RMS  SVM  Eight classes of hand movement for realtime control of a robotic arm.  Flexor carpi radialis, FCU, Pronator teres, Bracioradialis, ECD, Anconius, Pronator quadrates  92–98%  Shenoy et al. [107] 
RMS,Entropy  BPANN (Gradientdescent algorithm)  Four hand gestures recognition for humancomputer interaction  Forearm, Abductor Pollicies longus (four channel)  97.5%  Rajesh et al. [86] 
ARM and EMG histogram  CKLM  Control of a multidegreesoffreedom prosthetic hand.  PL, EDC,FCU, FDS,FDP  93.54%  YiHung [105] 
Entropy  Error backpropagation type neural networks  Six Motion discrimination  Forearm (four paired electrode)  90%  Tsuji et al. [99] 
Force information FEMG, Entropy  RLLGMN  Six motion discrimination  Forearm (six channel)    Nan Bu et al. [100] 
RMS  BPANN  Classify six different hand gestures  Flexor carpi radialis, FCU, FDS, Bracioradialis (Four electrode channels)  99%  Naik et al. [103] 
AMFM  KNN  Classified neuromuscular disorder  Biceps brachii muscle  58%  Christodouloua et al. [109] 
SOM  60%  
SVM  78%  
AR  WNN  Classified neuromuscular disorder  Biceps brachii muscle  90.7%  Subasi et al. [108] 
FEBANN  88%  
Vector elements extracted by STFT  MLPNN with LevenbergMarquardt (LM) and gradient descent (GDA) algorithms (Feature dimensionality reduction by ICA).  Muscle fatigue detection  Right biceps brachii muscle  88.5%  Subasi A. et al. [111] 
SPWVD  90%  
CWT  91%  
Quadratic phase coupling (QPC)  Extreme Learning Machine Algorithm (ELM)  Classify the EMG signals (an aggressive action or a normal action)  Right biceps & triceps, Left biceps & triceps, right & left thigh, right & left hamstring (8 channel)  99.75%  Sezgin, N. [112] 
AR  SVM  Diagnosis of neuromuscular diseases  Biceps and Hypothenar eminence    Güler et al. [110] 
IEMGIntegrated EMG, WPTWavelet packet Transform, FFTFastFourier Transform, STFTShort time Fourier Transform, SPWVDSmoothed PseudoWignerVille Distribution, CWT Continuous wavelet transform, ARAutoregressive analysis, MAVMean amplitude value, RMSRoot mean square, VARVariance value, SDStandard deviation, ZCZero crossing, SSCSlope Sign Changes, WLWave length, RECRecurrent Rate, PaccPower, WmaxWavelet coefficient, Samp EnEntropy, ARMAutoregressive model, FMNFrequency mean, FMDFrequency median, FRFrequency ratio, PLPalmaris longus, EDCExtensor digitorum communis, FCUFlexor carpi ulnaris, FDSFlexor digitorum superficialis, FDPFlexor digitorum profundus, FEBANNFeed forward error backpropagation artificial neural networks, WNNwavelet neural networks, BPNNBack propagation neural network
Table 10. Summary of most important methods. 
Methods  Characteristics  

WignerVille Distribution (WVD) 
 
Wavelet Transform (WT) 
 
Artificial Neural Network (ANN) 
 
Higher order statistics (HOS) 
 
Empirical Mode Decomposition (EMD) 
 
Independent Component Analysis (ICA) 
 
Fuzzy Logic 

© 2013 by the authors; licensee MDPI, Basel, Switzerland. This article is an open access article distributed under the terms and conditions of the Creative Commons Attribution license (http://creativecommons.org/licenses/by/3.0/).