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EEG Classification using Support Vector Machine
Homri Ines, Yacoub Slim and Ellouze Noureddine
Laboratoire Signal Image et Technologie de l'Information,(SITI),
Université Tunis El Manar, ENIT
Tunis, Tunisia
[email protected], [email protected], [email protected]
Abstract—EEG data of motor imagery of left and right hand
movement are analyzed; different wavelet functions are applied
to EEG segments for features extraction. Support vector
machine is utilized for right and left hand movement imagination
classification, than, the obtained results are compared with
neural networks and linear discriminant analysis classification
results .
Index Terms—EEG, Wavelet function, support vector
machine.
I. INTRODUCTION
Brain computer interfaces BCI offer new possibilities for
EEG signals exploitation , EEG signals of motor imagery can
be seen as a new way of communication for persons suffering
from severe physical handicaps [1]. Actually, analysis and
interpretation of EEG signals are useful to distingue limbs
movement imagination [2].The classification of EEG signals
include primarily their preprocessing which can be
accomplished by several methods, such as independent
component analysis (ICA) [3], Principal component analysis
(PCA) [4]; then the features extraction which can be
performed using different techniques such as; fast Fourier
transform FFT [5], band power [6, 7], common spatial pattern
(CSP) [8], the autoregressive model AR [9] or multivariate
autoregressive model MVAR [10], the wavelet transform for
time-frequency analysis [11, 12, 13, 14, 15]; allowing the
creation of features vectors. Next, the classification can be
achieved by several classifiers such as Linear discriminant
analysis LDA, neural networks , support vector machine SVM
. In this paper, EEG signals for left and right hand movement
imagery are utilized. Signals are filtered between 0.5 and 30
HZ. Features extraction is performed using different wavelet
functions, and support vector machine is used in the
classification.
II. METHODS
A. EEG Data Description
EEG motor imagery data utilized in this study is dataset III
available in BCI competition II (2003) [16]. EEG signals are
sampled with 128Hz and filtered between 0.5 and 30Hz.
Dataset consists of 140 trials of training data and 140 test trials,
each trial of 9s contains records acquired by electrodes C3, CZ
Fig. 1. Electrodes positions ( top) and timing scheme (bottom) [16].
and C4 according to the international 10-20 system of
electrode placement. In each trial, subject imagined left or
right hand movement between 3s and 9s. Dataset contain three
records:
x-train contains 140 training trials
x-test contains 140 test trials
y-train contains trials labels {1, 2}, respectively for
left and right hand movement, saved in x_train.
B. EEG Temporal Windowing
EEG dataset is composed of a train set and a test set
including each 140 trials of 9s length. Each trial is segmented
with sliding windows of 256 samples corresponding to 2
seconds with a shift of one point. In this way each trial is
composed of 385 EEG segments.
C. Wavelet Transform for Features Extraction
EEG signals recorded from channels C3 and C4, over
sensory-motor cortices; activated during movement
imagination; are analysed in order to assess sensory-motor
SSD'13 1569682619
1
2013 10th International Multi-Conference on Systems, Signals & Devices (SSD) Hammamet, Tunisia, March 18-21, 2013
978-1-4673-6457-7/13/$31.00 ©2013 IEEE
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rhythms mu [8 13] HZ [17] and beta [13 30] HZ located in the
centro-temporal region of the scalp. Indeed, the preparation or
imagination of movement is accompanied by a decrease of
power, named Event-Related De-synchronization (ERD) in mu
and beta rhythms, and an increase in power is observed in
these frequency bands after the end of movement called ERS
(Event Related Synchronization) [18]. In BCI, these events are
utilized to describe hand movements imagination [19].
In order to extract characteristics of EEG signals, different
wavelet families; Daubechies, Symmlet and Coiflet; are
utilized for EEG segment decomposition into frequency sub-
bands. Several wavelet functions are tested to find the
appropriate one for EEG decomposition [20, 21] as following:
1. Daubechies4, Daubechies6, Daubechies8,
Daubechies10, and Daubechies12
2. Coiflet2, Coiflet4, and Coiflet5
3. Symmlet5, Symmlet6, Symmlet7, Symmlet8,
Symmlet9, and Symmlet10.
EEG sampled at 128 HZ are decomposed into three levels,
three details sub-bands D1 - D3 and one final approximation
A3. Since relevant characteristics of hand movement
imagination exist in mu and Beta bands, Wavelet coefficients
of details D2 and D3 are considered and following statistical
parameters are created in order to reduce the size of features
vectors [20]:
1. P1: Mean of the absolute values of wavelet
coefficients of detail sub-bands { 2D, 3D
}
recorded from channels { 3C, 4C
}.
2. P2: Standard deviation of wavelet coefficients
3. P3: Average power of wavelet coefficients.
Parameters P1 and P3 provide information related to the
power spectrum of the signal, and parameter P2 presents the
variation in the power spectrum over time.
Each EEG segment is described by a vector of twelve
features representing statistical parameters computed from
wavelet coefficients of detail sub-bands { 2D, 3D
} recorded
from channels { 3C, 4C
}.
EEG segments of all trials are grouped into subsets
according to their occurrence in each trial, for example all
segments having occurrence number 1 and obtained from trials
number 1 to 140 are grouped into subset number 1. So, to
generalize segments having occurrence number k and obtained
from 140 trials are grouped into a subset number k, where k is
an integer from 1 to N, and N=385 is the total segments
number in one EEG trial.
Each one of the 385 EEG subsets, is described by a
features matrix composed of 140 rows corresponding to total
trials number and twelve columns corresponding to features
number. In this way, 385 features matrices are created for
train and test datasets as illustrated in Fig. 2.
Fig. 2. EEG trials segmentation and features extraction .
D. Support Vector Machine SVM
SVM is a strong binary supervised learning classifier, with
a high capacity of generalization . SVM is based on a general
linear model. In the presence of nonlinear trends in the data, a
kernel method is applied to map the data to a high-dimensional
kernel induced feature space. The maximization of margin
separating the chosen support vectors from the two classes, in
the training data, generate a decision boundary. The kernel was
chosen to be a nonlinear radial-basis function RBF kernel
with a penalty parameter c of 6 and a parameter of 0.5. We
use the LIBSVM program provided by Chang and Lin [22].
Each features matrix is converted to LIBSVM input data
format. The desired target output was set to {-1, 1}
respectively for right and left hand movement. Patterns from
140 trials are used in training session and 140 trials are
EEG subset n°1 EEG subset
n°385
EEG Trial segmentation
EEG segment n°
1
EEG segments (of 256
samples) numerated from 1 to
385
140 times for ALL EEG trials
Creation of EEG subsets
numerated from 1 to 385
EEG segment
n°1 from trial 1
................
EEG segment
n°1 from trial
140
EEG segment
n°385 from trial 1
................
EEG segment n°385 from trial
140
features matrix
n°1
features matrix
n°385
Features Extraction
2
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reserved for test. For each features matrix presented as input to
the classifier, SVM performance is estimated in terms of
classification accuracy based on the percentage of correct
recognition rate of hand movement classes, calculated as
following:
Accuracy= (number of correctly classified patterns / total
number of tested patterns)*100.
Moving average classification accuracy of 10 past segments
is employed to create curves showing the classification results
in figure 3, 4 and 5, as following:
ki
ki
iAccuracykaccuracyMav
9
))((*10/1)( (1)
III. RESULTS AND DISCUSSION
Table 1 illustrates highest classification results obtained for
different wavelet families and the corresponding optimal EEG
segments achieving these results.
Considering classification results achieved by SVM
classifier in table 1, among Daubechies wavelet functions
(DB4, DB6, DB8, DB10, and DB12), DB10 reached the
highest accuracy of 89.30% in segment (504- 760 samples); for
Coiflet wavelet functions (Coiflet2, Coiflet4 and Coiflet5)
highest accuracy of 89.30% is accomplished via Coiflet5 in
segment (466- 722 samples), and for Symmlet wavelet
functions (Symmlet5, Symmlet6, Symmlet7, Symmlet8,
Symmlet9 and Symmlet10) highest accuracy is 90% in EEG
segment (478- 734 samples ) using Symmlet5.
As seen in table 1, DB10, Coiflet5 and Symmlet5 wavelet
functions achieved highest classification accuracies via SVM
classifier, results accomplished via DB10, Coiflet5, and
Symmlet5 are illustrated respectively in Fig. 3, Fig. 4 and
Figure 5; where The x -axis represents the starting point of
EEG segments of size 256 samples; the y-axis represents the
moving average classification accuracy.
SVM classification results illustrated in Fig. 3, Fig. 4 and
Figure 5 show that immediately after announcing the
movement to imagine, the classification accuracy grows. It
peaks at the time of the actual movement imagination, and it
remains 2 s after.
TABLE I. HIGHEST CLASSIFICATION RESULTS OBTAINED FOR DIFFERENT
WAVELET FAMILIES USING SVM CLASSIFIER
Wavelet
family
Wavelet
function
Optimal EEG
segment
Highest
Classification
accuracy
Daubechies DB10 504-760 samples 89.30%
Coiflet Coiflet5 466-722 samples 89.30%
Symmlet Symmlet5 478-734 samples 90%
TABLE II. COMPARISON OF HIGHEST CLASSIFICATION RESULTS
OBTAINED FOR DIFFERENT WAVELET FAMILIES USING SVM CLASSIFIER, NEURAL NETWORKS MLP, AND LDA CLASSIFIER.
Classifier Wavelet
function
Optimal EEG
segment
Highest
Classification
accuracy
SVM Symmlet5 478-734 samples 90 %
MLP Coiflet5 544-800 samples 89.30%
LDA Symmlet10 482-738 samples 87.86 %
Fig. 3. Moving average classification accuracy achieved via DB10 wavelet
function and SVM Classifier.
Fig. 4. Moving average classification accuracy achieved via Coiflet5 wavelet
function and SVM Classifier
Fig. 5. Moving average classification accuracy achieved via Symmlet5
wavelet function and SVM Classifier
3
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In table 2, there is a comparison between the accomplished
highest results of SVM classifier and highest results achieved
by neural network multilayer perceptron MLP and linear
discriminant analysis LDA classifiers we obtained in a
previous study [23].
Considering LDA results accomplished by different
wavelet functions , highest result of 87.88% is reached by
Symmlet10.
For MLP neural network classifier, highest results of
89.30% is achieved by Coiflet5 . SVM classifier results
reached 90% using Symmlet5 wavelet function.
Comparing results in table 1 and table 2 , shows that SVM,
MLP and LDA results differ slightly, also based on previous
results [23], DB10 and Coiflet5 wavelets attain good
accuracies using either SVM, LDA and MLP classifiers.
IV. CONCLUSION
In this paper, EEG trials are segmented and prepared for
features extraction by temporal windowing of 256 samples
corresponding to 2s with a shift of one point. Features
extraction techniques based on different wavelet functions, are
applied in order to compare their effects on the classification
accuracy using SVM classifier, among them; Symmlet5
wavelet function reach a classification rate of 90%.
Comparison of SVM with MLP and LDA classification
results, show a slight difference in the achieved highest
accuracies. Tests achieved to find the appropriate wavelet
function for features extraction, the variation of classification
accuracies in time in different EEG segments indicated that
classification results depended on individual subject
concentration over time.
REFERENCES
J.R. Wolpaw, T.M. Vaughan and E. Donchin, “EEG based
communication prospects and problems,” IEEE Transactions on
Rehab. Engineering, vol.04, pp. 425-430, 1996.
Z.A. Keirn, and J.I Aunon, “A new mode of communication between
man and his Surroundings, ” IEEE Transactions on Biomed.
Eng, vol.37, pp.1209-1214, 1990.
S .Makeig, AJ. Bell, T-P . Jung, and TJ. Sejnowski, “Independent
component analysis of Electroencephalographic data, ”
Advances in Neural Information Processing Systems, vol.08,
pp. 145-151, 1996.
T-P .Jung, C. Humphries, TW .Lee, S. Makeig, MJ. McKeown, V.
Iragui, and TJ .Sejnowski, “Removing Electroencephalographic
Artifacts : Comparison between ICA and PCA,” Neural
Networks for Signal Processing VIII, pp. 63-72,1998.
P. Mark, K. Aleksandar, “Feature Extraction in development of
brain-computer interface: a case study, ” Proceedings of the
20th Annual International Conference of the IEEE Engineering
in Medicine and Biology Society, 2003.
R. Palaniappan, “Brain computer interface design using band powers
extracted during mental tasks, ” Proceedings of the 2
International IEEE EMBS Conference on Neural Engineering,
Arlington, Virginia, March 16 - 19, 2005.
N. Brodu, F. Lotte, and A. Lécuyer, “Comparative Study of Band-
Power Extraction Techniques for Motor Imagery
Classification,” IEEE Symposium on Computational
Intelligence, Cognitive Algorithms, Mind, and Brain (SSCI'2011
CCMB), pp. 1-6, 2011.
H. Ramoser, J. Muller-Gerking and G. Pfurtscheller, “Optimal spatial
filtering of single –trial EEG during imagined hand
movements,” IEEE Trans. Neural Syst. Rehabil. Eng, vol.08,
no.4, pp.441-446, 2000.
C.W. Anderson, E. Stolz, and S. Shamsunder, “ Discriminating
mental tasks using EEG represented by AR models, ” in IEEE
17th Annual Conference Engineering in Medicine and biology
Society, vol.02 , 1995.
C.W. Anderson, E.A. Stolz, S. Shamsunder, “ Multivariate
autoregressive models for classification of spontaneous
electroencephalographic signals,” IEEE Trans. Biomed. Eng,
vol.45, pp.277–286, 2004.
H. Adeli, Z. Zhou, and N. Dadmehr, “ Analysis of EEG records in an
epileptic patient using wavelet transform, ” J. Neurosci.
Methods, vol.123, no.1, pp. 69-87, Feb 2003.
M. Akay, “ Wavelet in biomedical engineering, ” Journal of Annals
of Biomedical Engineering., vol.23, pp. 529-530, 1995.
V. J. Samar, A. Bopardikar, R. Rao, K. Swartz, “Wavelet Analysis of
Neuroelectric Waveforms: A Conceptual Tutorial, ” Brain and
Language, pp.66: 7–60, 1999.
X. Zhang , L. Yin, W.Wang, “ Wavelet Time-frequency Analysis of
Electro-encephalogram (EEG) Processing, ” (IJACSA)
International Journal of Advanced Computer Science and
Applications, vol.01, no.5 , November 2010.
Lei Qin., “A wavelet-based time–frequency analysis approach for
classification of motor imagery for brain–computer interface
applications, ” J. Neural Eng, vol.02, pp. 65–72, 2005.
http://www.bbci.de/competition/ii/
G. Pfurtscheller, C. Neuper, A. Schlogl, and Lugger K.,
“Separability of EEG signals recorded during right and left
motor imagery using adaptive auto regressive parameters ”,
IEEE Transactions on Rehabilitation Engineering, vol.06,
pp.316-325, 1998.
G. Pfurtscheller, A. Stancfik Jr., G. Edlinger, “On the existence of
different types of central beta rhythms below 30 Hz”, Journal of
Electroencephalography and clinical Neurophysiology, vol.102,
pp. 316-325, 1997.
G. Pfurtscheller, C. Neuper, D. Flotzinger, and M. Pregenzer, “EEG
based discrimination between imagination of right and left
hand movement”, Electroenceph clin Neurophysiol, vol.103,
pp. 642-651, 1997.
P. Jahankhani , V. Kodogiannis, K. Revett, “ EEG signal
classification using wavelet feature extraction and neural
networks , ” IEEE John Vincent Atanasoff 2006 International
Symposium on Modern Computing, pp.52-57, 2006.
Y. Slim, K. Raoof, “Removal of ECG interference from surface
respiratory electromyography”, Innovation et Recherche
Biologique et Médicale IRBM, vol.31, no4, pp.209-220, 2010.
Chang C-C, Lin C-J, “LIB-SVM: a library for support vector
machines”, 2001. Software available at
http://www.csie.ntu.edu.tw/cjlin/libsvm
I. Homri, S. Yacoub, N. Ellouze, “EEG signal classification for
motor imagery", International Journal of Advancements in
Computing Technology. IJACT., in press.
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