 Research
 Open Access
Feature ranking and rank aggregation for automatic sleep stage classification: a comparative study
 Shirin Najdi†^{1, 2}Email author,
 Ali Abdollahi Gharbali†^{1, 2} and
 José Manuel Fonseca^{1, 2}
https://doi.org/10.1186/s1293801703583
© The Author(s) 2017
 Published: 18 August 2017
Abstract
Background
Nowadays, sleep quality is one of the most important measures of healthy life, especially considering the huge number of sleeprelated disorders. Identifying sleep stages using polysomnographic (PSG) signals is the traditional way of assessing sleep quality. However, the manual process of sleep stage classification is timeconsuming, subjective and costly. Therefore, in order to improve the accuracy and efficiency of the sleep stage classification, researchers have been trying to develop automatic classification algorithms. Automatic sleep stage classification mainly consists of three steps: preprocessing, feature extraction and classification. Since classification accuracy is deeply affected by the extracted features, a poor feature vector will adversely affect the classifier and eventually lead to low classification accuracy. Therefore, special attention should be given to the feature extraction and selection process.
Methods
In this paper the performance of seven feature selection methods, as well as two feature rank aggregation methods, were compared. PzOz EEG, horizontal EOG and submental chin EMG recordings of 22 healthy males and females were used. A comprehensive feature set including 49 features was extracted from these recordings. The extracted features are among the most common and effective features used in sleep stage classification from temporal, spectral, entropybased and nonlinear categories. The feature selection methods were evaluated and compared using three criteria: classification accuracy, stability, and similarity.
Results
Simulation results show that MRMRMID achieves the highest classification performance while Fisher method provides the most stable ranking. In our simulations, the performance of the aggregation methods was in the average level, although they are known to generate more stable results and better accuracy.
Conclusions
The Borda and RRA rank aggregation methods could not outperform significantly the conventional feature ranking methods. Among conventional methods, some of them slightly performed better than others, although the choice of a suitable technique is dependent on the computational complexity and accuracy requirements of the user.
Keywords
 Sleep stage classification
 Feature selection
 Rank aggregation
 Feature ranking
 Polysomnography
 Biomedical signal processing
 kNN
 Neural network
Background
Sleep occupies a significant part of human life. Therefore, the accurate diagnose of sleeprelated disorders is of great importance in sleep research. Sleep is a particular condition of the nervous system with noticeable features and brain activity phases. Although most people think that sleep is a passive and constant process, as a matter of fact, sleep is an active state. Human bodies move frequently during the night and the human brain is sometimes even more active than in the waking state [1]. Normal human sleep generally consists of two distinct stages with independent functions known as nonrapid eye movement (NREM) and rapid eye movement (REM) sleep. In their ideal situation, NREM and REM states alternate regularly, each cycle lasting 90 min on average. According to the American Academy of Sleep Medicine (AASM) [2], NREM is subdivided into three stages: stage 1 or light sleep, stage 2 and stage 3 or slow wave sleep (SWS). The evolution of sleep stages is complemented by gradual changes in many behavioral and physiological occurrences. Sleep stages are commonly classified using multiple simultaneous physiologic parameters during sleep named Polysomnography (PSG) in a clinic or hospital environment. A collection of rules has been identified in the AASM to guide the practitioners. However, the visual process of sleep stage classification is timeconsuming, subjective and costly. In order to improve the accuracy and efficiency of the sleep stage classification, researchers have been trying to develop automatic classification algorithms. The automatic sleep stage classification mainly consists of three steps: preprocessing, feature extraction and classification [3]. In the feature extraction stage, several temporal, spectral and nonlinear features are extracted from PSG signals. Nevertheless, some of these features may be irrelevant or have high mutual correlation increasing the complexity of the model without any real benefit. To face this challenge, feature selection and dimensionality reduction methods have been utilized.
In principle, a feature selection method has been used with the aim of selecting a subset of features in a way that the classifier can distinguish the differences between various classes of input data more effectively. The advantages of using feature selection methods make it an essential requirement for many classification applications. Reaching a more compact and simple model is the most important advantage offered by the feature selection process, that can reduce the necessary computational time for the classifier. Also, enhancing the generalization ability, increasing the classification power through reduced overfitting level, less storage memory and simplified visualization are further benefits of feature selection in classification tasks. Several different types of feature selection methods exist in the literature. Among them, the most common methods are divided into three main categories: filter, wrapper and embedded methods. Filter methods perform feature selection by considering some intrinsic characteristics of the data and usually provide a rank or a score for each feature. Low scored features will be removed experimentally or according to a predefined threshold. Filter methods, besides being simple and fast, are independent of the classifier.
Wrapper methods on the other hand, embed a search algorithm in the space of possible features subsets. Then, various subsets are produced and evaluated by training and testing with the specific classification algorithm. Since, the number of possible subsets grows exponentially with the number of features, heuristic search algorithms are used for finding the optimal feature subset. The high computational complexity and the risk of over fitting are its main disadvantages. The main benefits of wrapper methods over filter methods are taking into account feature dependencies and interaction between the selected subset and the specific classification method.
Embedded methods integrate the optimal feature subset selection with the classification algorithm. They have less computational complexity compared to wrapper methods. The results of both wrapper methods and embedded methods are classifierspecific.
In sleep stage classification, filter methods are more common than wrapper and embedded methods. Among the filter methods fast correlation based filter (FCBF), Fisher score, ReliefF, Chi square (Chi2), information gain (IG), conditional mutual information maximization (CMIM), minimum redundancy maximum relevance (MRMR) algorithms and Rsquare [4–7] are the most preferred ones. In addition to the traditional methods, a new filter method called ‘Mahal’ is proposed in [8] for facing the challenge of feature selection in small datasets with a large number of features for sleep stage classification. On the other hand, sequential feature selection algorithms including sequential forward selection (SFS) and sequential backward selection (SBS) are the most common wrapper methods used in the automatic sleep stage classification [9, 10]. Statistical hypothesis testing methods are also used in sleep stage classification applications for feature selection and dimensionality reduction. Examples of these methods are t test, ANOVA and Kruksal–Wallis test which are used for three different purposes: dimensionality reduction, feature selection and assessment of the discriminative capability of the selected feature set. To the best of our knowledge, there are no studies for comparing the performance of various feature selection methods from the same category in sleep stage classification. The studies done so far usually choose feature selection methods from different categories. For example in [11], one filter and three wrapper methods are used and the results are compared. Therefore, there is a need for comprehensive comparison of feature selection methods from the same category.
As mentioned before, feature ranking techniques provide a ranked list of features. Different feature ranking techniques may produce different rankings according to their specific criteria for assessing features and there is no universal ranking algorithm that considers all the measures. Therefore, motivated by ensemble methods in supervised learning [12], rank aggregation methods are proposed to combine different feature ranking methods and achieve more stable ranked feature lists with similar or even higher classification performance [13, 14]. In order to perform ensemble feature selection, one needs to decide on the method to aggregate the results from different ranking methods. There are many rank aggregation approaches from the very simple ones to some more complex [14]. To the best of our knowledge, there are no studies done on feature selection based on rank aggregation methods in the sleep stage classification area.
 1.
A comprehensive feature set including Itakura Spectral Distance (ISD) [15] was extracted from PSG signals,
 2.
Similarity and stability of different feature ranking and rank aggregation methods were assessed,
 3.
Classification performance of different feature ranking and rank aggregation methods was compared.
In this work, we present the extension of the results published in [4]. The paper is organized as follows: In the next section (“Methods”) the database, preprocessing, extracted features, feature selection techniques and classification algorithms will be described. In the following section related results will be shown. Discussion of the obtained results will be presented in the next section. On the last section, the conclusions and future work directions are presented.
Methods
Data
The data used in this study was obtained from Physionet SleepEDF Expanded Database [15]. The collection of data in this database comes from two studies. PSG recordings of the first study are named SC files (SC = Sleep Cassette). PSG recordings of the second study are named ST files (ST = Sleep Telemetry). In our simulations, we didn’t use SC files, since EMG data for first study was a zeroamplitude or nodata recording. Therefore, we used ST files which are a collection of 22 PSG signals recorded in the hospital during two nights for about 9 h. Except for slight difficulty in falling asleep, subjects were healthy without any sleep related medication. The data were segmented into 30s epochs and all epochs were scored according to R&K guidelines for human sleep staging. These recordings include EEG (FpzCz and PzOz), EOG (horizontal), submental chin EMG, together with the corresponding hypnograms.

Lack of stage 4 (according to R&K guidelines),

Artifacts such as severe movement or sensor misconnection,

Unsynchronized EEG data and hypnogram,

Lack of stage 3 epochs,

Severely corrupted EEG data.
Summary of the data provided by six selected subjects
Wake  REM  S1  S2  SWS  

Subject #1  146  122  101  527  136 
Subject #2  41  159  71  351  284 
Subject #3  85  226  120  392  180 
Subject #4  40  143  47  266  152 
Subject #5  149  80  102  428  218 
Subject #6  131  142  135  378  198 
Preprocessing
Artifact free data is necessary for guaranteeing the reliability of sleep stage classification algorithms. In this work, the epochs with zeroenergy were automatically detected and removed. The zeroenergy epochs can appear due to the possible failure of recording device. Then, the EEG and EOG signals were bandpass filtered in the frequency interval of 0.3–35 Hz. This interval was selected according to the recommendations of AASM. For filtering, wavelet multilevel decomposition and reconstruction was used. This filtering technique has a high fidelity to the original wideband signal in contrast to the Butterworth filtering that produces a highly distorted “valley” shape [16].
Feature extraction and normalization
Summary of the features extracted from PSG recordings
Signal  Category  Feature name 

EEG  Time domain (F1 to F12)  Statistical features (minimum value, maximum value, arithmetic mean, standard deviation, variance, skewness, kurtosis, median), zerocrossing rate, Hjorth parameters (activity, mobility and complexity) [32] 
Time–frequency domain (F13 to F26)  Features extracted from wavelet packet coefficients including energy of α, δ, β1, β2, θ and spindle bands, total energy of all bands, energy ratio of (\( \frac{\alpha }{\delta + \theta } \), \( \frac{\delta }{\alpha + \theta } \), \( \frac{\theta }{\alpha + \delta } \), \( \frac{\delta }{\theta } \), \( \frac{\alpha }{\theta } \)), statistical features (mean and standard deviation of coefficients in all of the bands)  
Entropy (F27 to F30)  Spectral entropy, Rényi entropy, approximate entropy, permutation entropy [32]  
Nonlinear (F31 to F36)  Petrosian fractal dimension, teager energy, energy, mean curve length, hurst exponent [32], ISD  
EOG  Time domain (F37 to F41)  Mean, maximum, standard deviation, skewness, kurtosis [58] 
Nonlinear (F42)  Energy [58]  
EMG  Frequency domain (F43 to F46)  Total power in the EMG frequency spectrum, statistical features of EMG frequency spectrum (maximum, mean, standard deviation) [58] 
Nonlinear (F47 to F49)  Energy, ratio of the EMG Signal energy for the current epoch and previous epoch, ratio of the EMG signal energy for the current epoch and next epoch [58] 

Statistical features (F1 to F8, F37 to F41, and F44 to F46): Understanding the evolution of PSG signals as stochastic processes can provide valuable information regarding the sleep stage classification. In this study, the simple and most common statistical features [17] including mean, median, maximum and minimum values, skewness and kurtosis of each EEG, EOG and EMG epoch are used according to Table 2.

Zero crossing rate (F9): Zero crossing rate (ZCR) is simple and at the same time very effective feature especially in sleep stage classification. ZCR counts the signals signchange points on a segment of a signal. In this paper, the length of this segment is 30 s.

Hjorth parameters (F10 to F12): In 1960, Bo Hjorth [18] proposed normalized slope detectors (NSD) as indicators of statistical properties of a signal in time domain. NSDs include three features: activity, mobility and complexity. These features are widely used in the analysis and characterization of EEG. Hjorth’s NSD are calculated as shown in Table 3 with σ _{0} representing the variance of the signal, σ _{1} the variance of the first derivate and σ _{2} the variance of the second derivate of the signal.Table 3
Hjorth parameters
Feature name
Formula
Hjorth activity
σ _{0} ^{2}
Hjorth mobility
σ _{1}/σ _{1}
Hjorth Complexity
\( \sqrt {({{\sigma_{2} } \mathord{\left/ {\vphantom {{\sigma_{2} } {\sigma_{1} )^{2} }}} \right. \kern0pt} {\sigma_{1} )^{2} }}}  \left( {{{\sigma_{1} } \mathord{\left/ {\vphantom {{\sigma_{1} } {\sigma_{0} }}} \right. \kern0pt} {\sigma_{0} }}} \right)^{2} \)

Wavelet based features (F13 to F26): In order to analyze the stochastic nature of EEG, we chose the wavelet packet (WP) analysis since it provides a valuable joint time–frequency domain analysis. In clinical applications, four main brain rhythms are associated with different states of sleep, including Delta (0–3.99 Hz), Theta (4–7.99 Hz), Alpha (8–13 Hz) and Beta (>13 Hz) [2]. According to the scheme proposed in [19], a WP tree with 7 decomposition levels was suitable to estimate the necessary frequency bands of EEG rhythms with adequate accuracy. Then, features F13 to F26 were extracted from the corresponding WP coefficients according to descriptions in Table 2.

Spectral entropy (F27): Spectral entropy, as a technique for measuring the irregularity of EEG, is calculated by the entropy of the power spectrum. Suppose P is the normalized power spectrum of EEG in a predefined frequency range, [f _{1}, f _{2}] and \( \sum {P_{i} = 1} \), the spectral entropy is calculated as:
$$ H_{sp} =  \sum\limits_{{f_{1} }}^{{f_{2} }} {P_{i} \log P_{i} } $$(1)In this study, H _{ sp } is used in the following normalized form:

Rényi entropy (F28): In 1960, Alfréd Rényi introduced Rényi’s general notion of entropy [22]. Since, Rényi Entropy unites several distinct entropy measures, it turned out to be theoretically interesting and found many applications in various research areas such as pattern recognition [23] and biomedicine [24]. Suppose P _{ x }(X) is probability distribution of random variable X. The Rényi entropy of order α for X is defined as:
$$ H_{\alpha } (X) = \frac{1}{1  \alpha }\log \sum\limits_{x} {P_{x} (X)^{\alpha } } $$(3) 
Approximate entropy (F29): Approximate entropy is regarded as a measure of the randomness or equivalently regularity of a time series. Considering that time series with repetitive patterns are more predictable than those without repetitive patterns, approximate entropy reflects the likelihood that similar patterns existing in a time series will not be followed by more patterns from the same type [25, 26].
For calculating approximate entropy two parameters need to be predefined: first the pattern length m and second the similarity threshold r. Given the time series \( \,\left\{ {x_{i} } \right\}_{i = 1 \ldots N} \), a sequence of vectors \( {\mathbf{x}}\left( 1 \right) \) through \( {\mathbf{x}}(N  m + 1) \) is formed in which \( \,{\mathbf{x}}(i) = [x(t), \ldots ,x(t + m  1)] \). Two vectors \( {\mathbf{x}}(i) \) and \( {\mathbf{x}}(j) \) are similar if their distance is less than r. The distance between two patterns is defined as the maximum difference between their corresponding components. Then, \( C_{i}^{m} (r) \) is defined as:
where \( C_{i}^{m} (r) \) expresses the patterns regularity of length m with a threshold value of r. Finally, approximate entropy is defined as [27]:$$ \begin{aligned} C_{i}^{m} (r) = \frac{{{\text{No}} . {\text{ of }}j \le N  m + 1}}{N  m + 1} \hfill \\ \quad \quad \quad \,{\text{for }}d[x(i),x(j)] \le r \hfill \\ \end{aligned} $$(4)$$ \begin{aligned} ApEn(m,r,N) = \frac{1}{N  m + 1}\sum\limits_{i = 1}^{N  m + 1} {\ln (C_{i}^{m} )} \hfill \\ \quad \quad \quad \quad \quad \quad \quad  \frac{1}{N  m}\sum\limits_{i = 1}^{N  m} {\ln (C_{i}^{m} )} \hfill \\ \end{aligned} $$(5) 
Permutation entropy (F30): Permutation entropy was proposed by Bandt et al. [28] and is a simple complexity measure, that can be applied to any type of time series including regular, chaotic, noisy and time series from reality. In mathematical terms, consider that a time series is \( \left\{ {x_{t} } \right\}_{t = 1 \ldots T} \). Through an embedding procedure, a set of vectors \( {\mathbf{X}}_{t} = [x_{t} ,x_{t + 1} , \ldots ,x_{t + m} ] \) with the embedding dimension m is formed. Then, X _{ t } is arranged in an increasing order. There will be \( m! \) different order patternsπ, also called permutations. If \( f(\pi ) \) denotes the frequency of permutation in the time series, then its relative frequency would be:
$$ p(\pi ) = \frac{f(\pi )}{T  (m  1)} $$(6)Therefore, the permutation entropy is defined as:

Petrosian fractal dimension (F31): The fractal dimension has been widely used in the characterization of nonstationary biomedical signals like EEG for several applications in order to measure the complexity of sleep EEG. Petrosian algorithm can be used for a fast computation of fractal dimension by means of transforming the signal into a binary sequence [30]. Petrosian fractal dimension is calculated using the following formula:
$$ FD_{Petrosian} = \frac{{\log_{10} N}}{{\log_{10} N + \log_{10} (\frac{N}{{N + 0.4N_{\Delta } }})}} $$(8)In which N is the length of the EEG signal and N _{Δ} is the number of sign changes in the derivative of the signal.

Teager energy (F32): Teager energy operator has been proved to be very useful in analysing signals from the energy point of view. It is defined as:
in continuous form, where \( \dot{x}(t) \) is the first derivative and \( \ddot{x}(t) \) is the second derivative of x. The discrete form of Teager energy is [31]:$$ \Psi (x(t)) = \dot{x}^{2} (t)  x(t)\ddot{x}(t) $$(9)$$ \Psi \left( {x[n]} \right) = x^{2} [n]  x[n  1]x[n + 1] $$(10) 
Energy (F33, F42, and F47 to F49): Energy is calculated as the average sum of the squares of all samples in a signal segment. Energy value of a signal increases with the increase of activity in the signal [32]. According to Table 2, both energy and energy ratio of different epochs of PSG recordings were used in this work.

Mean curve length (F34): Mean curve length was proposed with the purpose of reducing the complexity of Katz fractal dimension algorithm and provides results almost equivalent to it [33]. It is commonly used for identification of EEG activity, including amplitude and frequency changes and also its dimensionality [34]. Mean curve length, in its discrete form, is calculated using the following formula:
considering x as the EEG data, n the epoch number and N the epoch length in samples.$$ CL[n] = \sum\limits_{i = 1 + (n  1)N}^{nN} {\left {x(i)  x(i  1)} \right} $$(11) 
Hurst exponent (F35): Hurst exponent, introduced by Harold Edwin Hurst [35], is a measure for long range statistical dependence of time series. Hurst exponent has a value in the range between 0 and 1 and is defined as:
where T is the duration of signal sample and \( {\raise0.7ex\hbox{$R$} \!\mathord{\left/ {\vphantom {R S}}\right.\kern0pt} \!\lower0.7ex\hbox{$S$}} \) is the value of rescaled range.$$ H = \frac{{\log \left( {{\raise0.7ex\hbox{$R$} \!\mathord{\left/ {\vphantom {R S}}\right.\kern0pt} \!\lower0.7ex\hbox{$S$}}} \right)}}{\log (T)} $$(12) 
Itakura Spectral Distance (F36): The Itakura Spectral Distance (ISD) is broadly used in speech processing applications to measure the distance (similarity) between two auto regressive coefficients (AR) processes [36, 37]. ISD was also used in automatic sleep classification to find the relation between EEG and EOG signals during different epochs of sleep stages over the night [38]. In this paper, the ISD of sleep stages of EEG was measured. In order to calculate the distances, the AR coefficients were extracted from 50% of the wake epochs of each subject. Then, by getting the mean of the AR coefficients a representative model of the wake epoch was generated and the ISD between this model and the W (remaining 50%), S1, S2, SWS and REM epochs was calculated.

Spectral power (F43): Power spectrum density (PSD) represents the distribution of signal’s power as a function of frequency. The spectral power of a signal in a frequency band is obtained by integrating PSD over the signal’s frequency range.
Feature ranking methods
In this paper, to select a subset of features containing most of the original feature set information, we used seven different feature ranking methods: ReliefF, minimum redundancymaximum relevance (MRMRMID and MRMRMIQ), Fisher score, Chi Square (Chi2), information gain (IG) and conditional mutual information maximization (CMIM). We have also implemented two different rank aggregation methods, Borda and robust rank aggregation (RRA), to evaluate their ability to produce better feature rankings compared to conventional feature ranking methods. A brief description of the used feature ranking methods is provided below:
ReliefF
In 1992, Kira and Rendell [39] proposed an instance based method, Relief, for estimating features quality. In this method, for a randomly selected sample, two nearest neighbors were considered: one from the same class (nearest hit) and other from a different class (nearest miss). The quality estimated for each feature is updated according to the randomly selected sample’s distance from the nearest hit and miss. The Relief method is restricted to twoclass problems and is highly sensitive to noisy and incomplete data. An extension of Relief, called ReliefF [40], was proposed improving the original method by estimating the probabilities more reliably and extending the algorithm to multiclass problems. The ReliefF algorithm uses knearest hits and knearest misses for updating the quality estimation for each feature.
Minimum redundancymaximum relevance
MRMR [41] is a feature selection method which selects a subset of features with maximum relevance for the target class and, at the same time, minimum redundancy between the selected features. In the MRMR method, the redundancy (R) and relevance (D) are expressed in terms of mutual information. In order to select the final feature set, an objective function φ(D, R) is maximized. The φ(D, R) can be defined either as the mutual information difference (MID), DR, or the mutual information quotient (MIQ), D/R.
Fisher score
This method is one of the most efficient and widely used feature ranking methods. The key idea is to find a subset of the feature matrix with maximum distance between the data points from different classes and minimum distance between the data points of the same class in the feature space [42].
Chi square
Chi2 is another very common class sensitive feature selection method which ranks the features according to their Chi2 statistics without taking into account the interactions between features. Originally proposed exclusively for categorical data, this method was later extended to the continuous case [43]. For calculating the Chi2 statistics of each feature, the range of the numerical feature should be discretized into intervals.
Information gain
Ross Quinlan proposed an algorithm for generating decision trees from a set of training data [44]. In this algorithm, information gain (IG) is the measure for selecting the effective feature at each node. Generally, IG can be described as the change in the marginal entropy of a feature set taking into account the conditional entropy of that feature set with the given class set.
Conditional mutual information maximization
This method [45] is based on mutual information in such a way that all the selected features are informative and have twobytwo weak dependency. A feature is added to the selected feature subset if it contains information about the specific class and this information is not contained on any other previously selected feature.
Borda
Robust rank aggregation
This method, proposed by Kolde et al. [46], is another rank aggregation method that compares the results from several feature ranking methods with a randomly ranked feature list. The RRA first looks how a specific feature is ranked by the various methods and lists the corresponding values in a socalled rank order, from best to worst. It is clear that, if a feature has high quality, the dominance of ranks in the rank order will be towards smaller numbers. The probability of the random list producing better ranking than the values seen in the actual rank order for that specific feature is determined. The features with the small probability are selected as the better ones [47].
Classification
The process of labeling the data into relevant classes is called classification. The first step in the classification process is the identification of the features or characteristics that will enable the highest discrimination between the different groups of data. A classification model is developed in such a way that it provides the structure for how the classification processes’ actions will be realized. Ideally, this model should be chosen to optimize the performance of the classification system, although it may need to be revised as the classifier design progresses. A classifier is then implemented and “trained” to recognize the chosen features in the data, or to determine the best inputtooutput mapping. Once the system has trained and learned, it is ready to classify specific inputs. Then, the system can be tested and evaluated with such metrics as speed of computation and accuracy of classification [48].
In this study, we selected two simple and widely used classifiers: knearest neighbor (kNN) and multilayer feedforward neural network (MLFN) to discriminate five sleep stages W, S1, S2, SWS and REM. By selecting k = 1, nearest neighbor (NN) was utilized. The NN classifier is the simplest nonparametric classifier and assigns a pattern to a specific class based on its nearest neighbor’s class. In spite of its simplicity, in [49] it has been proved that, if the utilized database is fairly large, the error bound for nearest neighbor rule is quite tight, i.e. equal or less than twice the Bayes error. Also, neural networks are known to be very powerful computing models that can learn from training examples. Neural networks have been successfully used in a broad range of data mining applications including classification [50].
Performance evaluation
In this paper three main criteria namely stability, accuracy and similarity are considered for evaluating and comparing the different feature selection techniques.
Stability
The S _{ s } takes values in the range of [0 1], with 0 meaning there is no overlap or similarity between two rankings and 1 meaning that the two rankings are identical. Then N subsets of the original training set are drawn using a random resampling technique such as cross validation or bootstrapping. Each specific ranking algorithm produces a feature preference list for each N subsets. The similarity between all possible pairs is calculated. The stability of that specific feature ranking algorithm is simply the average of the similarities over all possible pairs, i.e. \( \frac{N(N  1)}{2} \) pairs.
Similarity
The stability measure used for assessing the internal stability of a feature selection technique can also be used in a different context to measure the similarity of different feature selection techniques. The similarity measure provides information about the consistency and diversity of different feature selection algorithms. The similarity between two feature subsets s and \( s^{\prime} \) can be calculated using Eq. (15) with a slight difference in the definition of s and \( s^{\prime} \). Instead of two lists of features produced by a specific feature selection technique from different subsets of the training set, they are now two lists produced by two different feature selection techniques derived from the complete training set [51].
Accuracy
Experimental setup
Six subjects were selected from the Physionet database for evaluating and comparing the feature ranking and rank aggregation methods. For filtering EEG and EOG signals, Daubechies order 20 (db20) was used as the mother wavelet. The filtered data was segmented into 30second epochs. From each epoch, a feature vector containing 49 features was extracted. After feature standardization, the feature vectors were fed into seven feature ranking methods. Then, in order to aggregate the results, the outputs of these seven feature ranking methods were used by Borda and RRA, producing two additional ranked lists of features.
For sleep stage classification, the parameters of the classifiers are set as follows. The Euclidean distance was chosen as the distance metric for the NN classifier. For the threelayer neural network classifier 12 hidden neurons and a sigmoid transfer function were selected in our simulations. The Levenberg–Marquardt training algorithm was adopted for minimizing the cost function because of its fast and stable convergence. In contrast with conventional approaches in the literature, which imports all the existing epochs to the classifier, we used a quantity of epochs selected out of each subject. In this method, selected epochs from each subject have two characteristics. Firstly, the number of epochs are the same for all the subjects. Second, the number of epochs for each stage is dependent on the number of occurrences of that stage for each subject. This method is suitable for large databases helping on the computational complexity reduction of the classifier training stage.
Results
Mean stability for selected features
ReliefF  Fisher  Chi2  IG  CMIM  MRMRMID  MRMRMIQ  Borda  RRA  

Mean stability up to 5th feature  0.50  0.80  0.79  0.73  0.20  0.72  0.82  0.39  0.65 
Mean stability up to 13th feature  0.66  0.99  0.95  0.92  0.21  0.79  0.82  0.68  0.78 
Mean stability up to 29th feature  0.69  0.86  0.86  0.94  0.24  0.75  0.77  0.70  0.70 
Similarity of the feature selection techniques
ReliefF  Fisher  Chi2  IG  CMIM  MRMRMID  MRMRMIQ  Borda  RRA  

ReliefF  1  0.26  0.18  0.18  0.35  0.40  0.40  0.31  0.31 
Fisher  1  0.58  0.52  0.11  0.58  0.65  0.72  0.65  
Chi2  1  0.90  0.15  0.35  0.35  0.52  0.52  
IG  1  0.18  0.35  0.35  0.46  0.46  
CMIM  1  0.22  0.22  0.22  0.22  
MRMRMID  1  0.90  0.72  0.65  
MRMRMIQ  1  0.72  0.65  
Borda  1  0.72  
RRA  1 
Top 10 features selected by each method and the optimum number selected by Kneedle algorithm (corresponding accuracy)
ReliefF  Fisher  Chi2  IG  CMIM  MRMRMID  MRMRMIQ  Borda  RRA  

Top 10 features  F28  F36  F35  F9  F15  F35  F35  F36  F36 
F36  F35  F9  F35  F36  F39  F42  F35  F35  
F7  F31  F11  F11  F9  F36  F15  F9  F9  
F49  F9  F31  F31  F8  F22  F36  F31  F31  
F41  F29  F36  F36  F1  F15  F22  F22  F27  
F27  F11  F27  F4  F34  F31  F23  F27  F22  
F20  F25  F26  F27  F35  F29  F31  F29  F17  
F23  F27  F4  F26  F28  F23  F38  F11  F29  
F6  F12  F25  F25  F6  F9  F29  F15  F11  
F22  F22  F14  F29  F48  F38  F9  F20  F20  
MLFN  7 (0.75)  5 (0.76)  7 (0.76)  7 (0.76)  3 (0.74)  5 (0.76)  5 (0.76)  5 (0.76)  7 (0.77) 
kNN  7 (0.69)  5 (0.71)  9 (0.73)  9 (0.73)  3 (0.68)  7 (0.75)  11 (0.75)  9 (0.74)  7 (0.73) 
Discussion
According to Fig. 2, Fisher method seems to have the highest stability and the CMIM method comes out to be the least stable one. Also, the stability of Chi2 and IG methods seems very convergent.
There exists a huge reduction in stability for MRMR_MID, MRMR_MIQ and ReliefF for threefeature subset, although after that stability increases slightly by each additional feature. Both MRMR methods are always 100% stable in selecting the first feature which is Hurst Exponent. It means that the Hurst Exponent has the highest discrimination ability from MRMR methods point of view. Also, the Fisher method has 100% stability for threefeature and fivefeature subsets (ID, Hurst exponent, Petrosian fractal dimension as threefeature group and ID, Hurst exponent, Petrosian fractal dimension, zerocrossing rate and approximate entropy as fivefeature group).
According to Table 4, MRMRMIQ has the highest mean stability up to five features. Meanwhile, Fisher and Chi2 methods have almost the same stability value. Considering thirteen features, Fisher method is almost totally stable (99.92%). Finally, considering twentynine features, IG outperforms other methods from mean stability point of view.
According to Table 5, Chi2 and IG pair and MRMRMID and MRMRMIQ pair generate highly similar results. The similarity of MRMR methods can be explained by their similar theoretical background. On the contrary, CMIM and Fisher methods give the most dissimilar results. The average similarity of Borda and RRA methods is approximately 0.5 with the other methods. Regarding the aggregation characteristics it was predictable.
Table 6 illustrates the top 10 features selected by each method. ISD (F36) always appears in the top 10 for all the methods. In spite of the fact that different feature ranking methods have their own specific criteria for ranking the features, observing ISD in the top 10 list, means that ISD is a preferable feature for all the feature selection methods. In addition to ISD, there are some other features that can be considered most preferable according to Table 6. EEG ZCR (F9) is a simple, yet effective feature that is listed in top 10 by all of the methods except ReliefF. Following ZCR, Petrosian fractal dimension (F31), Hurst exponent (F35), WP feature (F22), approximate entropy (F29), spectral entropy (F27), and Hjorth mobility parameter (F11) are selected by at least five ranking methods to be included in top 10 list. On the other hand, features that are not in this list or are just selected by one method can be categorized as the least preferred features. EMG energy and energy ratio features (F47 to F49) and some of WP features are examples of least preferred features. The optimum number of features for each method, which is selected by the Kneedle algorithm, is shown in Table 6. For MLFN and kNN classifiers, a slight difference exists in the optimum number. Considering the maximum accuracy that the methods reach in their optimum points, the MRMRMID method using kNN classifier outperforms all the others with seven selected features. Also, both MRMR methods using MLFN classifier outperform all the other methods with five features.
The CMIM method reaches its best accuracy with the first 3 features on both the classifiers. Considering Fig. 3, its accuracy is equal or less than the MRMRMID method’s accuracy at that point. Unanticipatedly, none of the aggregation methods outperformed the rest of the feature ranking methods. One possible reason for this is that the aggregation methods, especially Borda, are affected by the performance of all the methods from best to worst.
Conclusions and future works
In this paper we compared the performance of seven feature ranking methods for sleep stage classification. Feature selection based on filtering techniques has several advantages such as being fast, easily scalable to highdimensional datasets, decrease computational complexity and work independently of the classifiers. Also, rank aggregation methods are supposed to be robust when used with a broad variety of classifiers and produce comparable classification accuracy to the individual feature selection methods. In this work, two rank aggregation methods were also applied to evaluate the performance on sleep stage classification. The Physionet SleepEDF Expanded Database was used to assess the impact of these methods on the classification accuracy of kNN and MLFN. In addition, the stability and similarity of different feature selection methods were also evaluated. The results indicate that the MRMRMID method slightly outperforms the other feature selection methods from the accuracy point of view. Considering that the CMIM produces the most unstable rankings, generally Fisher method produces the most stable results. When a small group of features (5–13) was required, the RRA aggregation method slightly outperformed the Borda. In our simulations, the performance of the aggregation methods was in the average level, although they are known to generate more stable results and better accuracy. It should be considered that the results presented in this paper are obtained through using Physionet SleepEDF Expanded Database which is already used in several previous sleep studies [19, 54–56] and can be supposed as verified enough to be used in such a comparative study. Nevertheless, generalizing these results to all future sleep studies requires further study and analysis by using other sleep databases as well. Also, in this paper for evaluating the generalization ability of classifiers we used repeated random subsampling validation. In [57], it is mentioned that due to the data subdivision dependency resulted from validation methods that are based on random subsampling, patient cross validation was preferred. Therefore, future steps will involve verifying the results with different databases, applying and comparing more rank aggregation methods and also using patient cross validation and comparing the results with common validation methods.
Notes
Declarations
Declarations
Authors’ contributions Simulations: SN, AAG. Drafting: all authors. Analysis and interpretation of results: all authors. Critical revision: all authors. All authors read and approved the final manuscript.
Acknowledgements
Not applicable.
Competing interests
The authors declare that they have no competing interests.
Availability of data and materials
All of the datasets supporting the conclusions of this article are freely available at http://physionet.org/physiobank/database/sleepedfx/.
Funding
This work was partially funded by FCT Strategic Program UID/EEA/00066/203 of UNINOVA, CTS and INCENTIVO/EEI/UI0066/2014 of UNINOVA. Publication costs were funded by FCT Strategic Program UID/EEA/00066/203 of UNINOVA, CTS.
About this supplement
This article has been published as part of BioMedical Engineering OnLine Volume 16 Supplement 1, 2017: Selected articles from the 4th International WorkConference on Bioinformatics and Biomedical EngineeringIWBBIO 2016. The full contents of the supplement are available online at https://biomedicalengineeringonline.biomedcentral.com/articles/supplements/volume16supplement1.
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References
 Migotina D, Calapez A, Rosa A. Automatic artifacts detection and classification in sleep EEG Signals using descriptive statistics and histogram analysis: comparison of two detectors. In Engineering and technology, 2012 Spring Congress. IEEE; 2012. p. 1–6.Google Scholar
 Berry RB, Brooks R, Gamaldo CE, Harding SM, Lioyd RM, Marcus CL, et al. AASM—manual for the scoring of sleep and associated events version 2.1; 2014.Google Scholar
 Chokroverty S. sleep disorders medicine: basic science, technical considerations, and clinical aspects. New York: Saunders, Elsevier; 2009.Google Scholar
 Najdi S, Gharbali AA, Fonseca JM. A comparison of feature ranking and rank aggregation techniques in automatic sleep stage classification based on polysomnographic signals. In 4th International Conference IWBBIO. Granada: Springer International Publishing; 2016. p. 230–41.Google Scholar
 Rathore SS, Gupta A. A comparative study of featureranking and featuresubset selection techniques for improved fault prediction. In Proceedings of the 7th India Software Engineering Conference—ISEC’14. New York: ACM Press; 2014. p. 1–10.Google Scholar
 Simões H, Pires G, Nunes U, Silva V. Feature extraction and selection for automatic sleep staging using EEG. In ICINCO; 2010. p. 128–33.Google Scholar
 Khalighi S, Sousa T, Nunes U. Adaptive automatic sleep stage classification under covariate shift. In Engineering in medicine and biological society, 2012 annual international conference. IEEE; 2012. p. 2259–62.Google Scholar
 Foussier J, Fonseca P, Long X, Leonhardt S. Automatic feature selection for sleep/wake classification with small data sets. 6th International conference on bioinformatics models, methods and algorithms; 2013. p. 1–7.Google Scholar
 Chapotot F, Becq G. Automated sleepwake staging combining robust feature extraction, artificial neural network classification, and flexible decision rules. Int J Adapt Control Signal Process. 2009;24:409–23.MathSciNetMATHGoogle Scholar
 Zoubek L, Charbonnier S, Lesecq S, Buguet A, Chapotot F. Feature selection for sleep/wake stages classification using data driven methods. Biomed Signal Process Control. 2007;2:171–9.View ArticleGoogle Scholar
 Khalighi S, Sousa T, Pires G, Nunes U. Automatic sleep staging: a computer assisted approach for optimal combination of features and polysomnographic channels. Expert Syst Appl. 2013;40:7046–59.View ArticleGoogle Scholar
 Seni G, Elder J. Ensemble methods in data mining improving accuracy through combining predictions. Synth Lect Data Min Knowl Discov. 2010;2:1–26.View ArticleGoogle Scholar
 Prati RC. Combining feature ranking algorithms through rrank aggregation. 2012 international joint conference neural networks. IEEE; 2012. p. 1–8.Google Scholar
 Dwork C, Kumar R, Naor M, Sivakumar D. Rank aggregation methods for the web. 10th Proceeding International Conference World Wide Web—WWW’01. New York: ACM Press; 2001. p. 613–22.Google Scholar
 The SleepEDF Database. https://physionet.org/physiobank/database/sleepedfx/. Accessed 1 Feb 2017.
 Wiltschko AB, Gage GJ, Berke JD. Wavelet filtering before spike detection preserves waveform shape and enhances singleunit discrimination. J Neurosci Methods. 2008;173:34–40.View ArticleGoogle Scholar
 Hamida STB, Ahmed B. Computer based sleep staging: challenges for the future. 2013 7th IEEE GCC conference and exhibition. IEEE; 2013. p. 280–5.Google Scholar
 Hjorth B. EEG analysis based on time domain properties. Electroencephalogr Clin Neurophysiol. 1970;29:306–10.View ArticleGoogle Scholar
 Ebrahimi F, Mikaeili M, Estrada E, Nazeran H. Automatic sleep stage classification based on EEG signals by using neural networks and wavelet packet coefficients. In Engineering in medicine and biological society, 2008 30th annual international conference. IEEE; 2008. p. 1151–4.Google Scholar
 Inouye T, Shinosaki K, Sakamoto H, Toi S, Ukai S, Iyama A, et al. Quantification of EEG irregularity by use of the entropy of the power spectrum. Electroencephalogr Clin Neurophysiol. 1991;79:204–10.View ArticleGoogle Scholar
 Sabeti M, Katebi S, Boostani R. Entropy and complexity Measures for EEG signal classification of schizophrenic and control participants. Artif Intell Med. 2009;47:263–74.View ArticleGoogle Scholar
 Renyi A. On measures of entropy and information. In Proceeding of the fourth Berkeley symposium on mathematical statistics and probability, volume 1: contributions to the theory of statistics, California. University of California Press; 1961. p. 547–61.Google Scholar
 Jenssen R, Hild KE, Erdogmus D, Principe JC, Eltoft T. Clustering using Renyi’s entropy. Proceedings of International Joint Conference on Neural Networks, 2003. IEEE; 2003. p. 523–8.Google Scholar
 Lake D. Renyi entropy measures of heart rate gaussianity. IEEE Trans Biomed Eng. 2006;53:21–7.View ArticleGoogle Scholar
 Pincus SM, Gladstone IM, Ehrenkranz RA. A regularity statistic for medical data analysis. J Clin Monit Comput. 1991;7:335–45.View ArticleGoogle Scholar
 Ho KK, Moody GB, Peng CK, Mietus JE, Larson MG, Levy D, et al. Predicting survival in heart failure case and control subjects by use of fully automated methods for deriving nonlinear and conventional indices of heart rate dynamics. Circulation. 1997;96:842–8.View ArticleGoogle Scholar
 Pincus SM, Goldberger AL. Physiological timeseries analysis: what does regularity quantify? Am J Physiol. 1994;266:H1643–56.Google Scholar
 Bandt C, Pompe B. Permutation entropy: a natural complexity measure for time series. Phys Rev Lett. 2002;88:174102.View ArticleGoogle Scholar
 Li D, Li X, Liang Z, Voss LJ, Sleigh JW, et al. Multiscale permutation entropy analysis of eeg recordings during sevoflurane anesthesia. J Neural Eng. 2010;7:46010.View ArticleGoogle Scholar
 Petrosian A. Kolmogorov complexity of finite sequences and recognition of different preictal EEG patterns. Proceedings of the eighth IEEE symposium computer based medical systems. IEEE Computer Society Press; 1995. p. 212–7.Google Scholar
 Kaiser JF. Some useful properties of teager’s energy operators. IEEE international conference on acoustics, speech, and signal processing. IEEE; 1993. p. 149–52.Google Scholar
 Şen B, Peker M, Çavuşoğlu A, Çelebi FV. A comparative study on classification of sleep stage based on EEG signals using feature selection and classification algorithms. J Med Syst. 2014;38:18.View ArticleGoogle Scholar
 Katz MJ. Fractals and the Analysis of Waveforms. Comput Biol Med. 1988;18:145–56.View ArticleGoogle Scholar
 D’Alessandro M, Esteller R, Vachtsevanos G, Hinson A, Echauz J, Litt B. Epileptic seizure prediction using hybrid feature selection over multiple intracranial EEG electrode contacts: a report of four patients. IEEE Trans Biomed Eng. 2003;50:603–15.View ArticleGoogle Scholar
 Hurst HE. The problem of longterm storage in reservoirs. Int Assoc Sci Hydrol Bull. 1956;1:13–27.View ArticleGoogle Scholar
 Zhang Y, Zhao Y. Real and imaginary modulation spectral subtraction for speech enhancement. Speech Commun. 2013;55:509–22.View ArticleGoogle Scholar
 Taşmaz H, Erçelebi E. Speech enhancement based on undecimated wavelet packetperceptual filterbanks and MMSE–STSA estimation in various noise environments. Digit Signal Process. 2008;18:797–812.View ArticleGoogle Scholar
 Estrada E, Nava P, Nazeran H, Behbehani K, Burk J, Lucas E. Itakura Distance: a useful similarity measure between EEG and EOG signals in computeraided classification of sleep stages. In Conference proceedings, IEEE engineering medical biology society; 2005. p. 1189–92.Google Scholar
 Kira K, Rendell LA. The feature selection problem: traditional methods and a new algorithm. In: Swartout WR, editor. Proceeding 10th national conference on artificial intelligence. San Jose, CA, July 12–16, 1992; 1992. p. 129–34.Google Scholar
 RobnikŠikonja M, Kononenko I. Theoretical and empirical analysis of ReliefF and RReliefF. Mach Learn. 2003;53:23–69.View ArticleMATHGoogle Scholar
 Ding C, Peng H. minimum redundancy feature selection from microarray gene expression data. IEEE proceedings of computational systems bioinformatics conference—CSB2003. IEEE Computer Society Press; 2005. p. 523–8.Google Scholar
 Gu Q, Li Z, Han J. Generalized Fisher score for feature selection. CoRR; 2012.Google Scholar
 Huan Liu, Setiono R. Chi2: feature selection and discretization of numeric attributes. In proceedings of the 7th IEEE international conference on tools with artificial intelligence IEEE Computer Society Press; 1995. p. 388–91.Google Scholar
 Quinlan JR. C4.5: Programs for machine learning. Morgan Kaufmann Publishers Inc.; 1993.Google Scholar
 Fleuret F. Fast binary feature selection with conditional mutual information. J Mach Learn Res. 2004;5:1531–55.MathSciNetMATHGoogle Scholar
 Kolde R, Laur S, Adler P, Vilo J. Robust rank aggregation for gene list integration and metaanalysis. Bioinformatics. 2012;28:573–80.View ArticleGoogle Scholar
 Wald R, Khoshgoftaar TM, Dittman D. Mean aggregation versus robust rank aggregation for ensemble gene selection. 2012 11th international conference on machine learning and application. IEEE; 2012. p. 63–9.Google Scholar
 Hastie T, Tibshirani R, Friedman J. The elements of statistical learning. New York: Springer; 2009.View ArticleMATHGoogle Scholar
 Duda RO, Hart PE, Stork DG. Pattern classification. New York: Wiley; 2012.MATHGoogle Scholar
 Zhang G, Eddy Patuwo B, Hu YM. Forecasting with artificial neural networks. Int J Forecast. 1998;14:35–62.View ArticleGoogle Scholar
 Kalousis A, Prados J, Hilario M. Stability of feature selection algorithms: a study on highdimensional spaces. Knowl Inf Syst. 2007;12:95–116.View ArticleGoogle Scholar
 Imtiaz SA, RodriguezVillegas E. Recommendations for performance assessment of automatic sleep staging algorithms. 2014 36th annual international conference of the IEEE engineering in medicine and biological society. IEEE; 2014. p. 5044–7.Google Scholar
 Satopaa V, Albrecht J, Irwin D, Raghavan B. Finding a “Kneedle” in a haystack: detecting knee points in system behavior. 2011 31st international conference on distributed computing systems workshop. IEEE; 2011. p. 166–71.Google Scholar
 Bajaj V, Pachori RB. Automatic classification of sleep stages based on the timefrequency image of EEG signals. Comput Methods Programs Biomed. 2013;112:320–8.View ArticleGoogle Scholar
 Zhou J, Wu X, Zeng W. Automatic detection of sleep apnea based on EEG detrended fluctuation analysis and support vector machine. J Clin Monit Comput. 2015;29:767–72.View ArticleGoogle Scholar
 RodríguezSotelo J, OsorioForero A, JiménezRodríguez A, CuestaFrau D, CirugedaRoldán E, Peluffo D. Automatic sleep stages classification using eeg entropy features and unsupervised pattern analysis techniques. Entropy. 2014;16:6573–89.View ArticleGoogle Scholar
 Herrera LJ, Fernandes CM, Mora AM, Migotina D, Largo R, Guillen A, et al. Combination of heterogeneous EEG feature extraction methods and stacked sequential learning for sleep stage classification. Int J Neural Syst. 2013;23:1350012.View ArticleGoogle Scholar
 Dursun M, Gunes S, Ozsen S, Yosunkaya S. Comparison of artificial immune clustering with Fuzzy Cmeans Clustering in the sleep stage classification problem. 2012 international symposium on innovations in intelligent systems and applications. IEEE; 2012. p. 1–4.Google Scholar