ISSN: 0970-938X (Print) | 0976-1683 (Electronic)

An International Journal of Medical Sciences

Research Article - Biomedical Research (2020) Volume 31, Issue 1

^{1}Department of Electrical & Electronics Engineering, Birla Institute of Technology, Jharkhand, India

^{2}Department of Electrical & Electronics Engineering, IIT (ISM), Jharkhand, India

^{3}Department of Bio-Engineering, Birla Institute of Technology, Jharkhand, India

- *Corresponding Author:
- Rakesh Kumar Sinha

Department of Bio-Engineering

Birla Institute of Technology Jharkhand

India

**Accepted Date:** June 17, 2019

Electroencephalography (EEG) is an electrophysiological monitoring technique to capture the brains

electrical activity. It is a noninvasive recording technique in which electrodes are placed over the scalp.

EEG records the variations in voltage resulting from ionic current inside the brain neurons. In a clinical

perspective, EEG corresponds to the recording of the brain's impulsive electrical activity during a given

time period. EEG is used to diagnose epilepsy, sleep disorders, encephalopathies, etc. Hence, EEG

signals are very useful in detecting abnormalities in the human brain. But the main problem in the

analysis of these signals is due to the noise that gets added to them. These artefacts arise due to various

reasons such as due to power line disturbance (50 or 60 Hz) or due to other natural rhythms of the body

like the heartbeat, muscle movement, blinking of eyes etc. These signals get added as noise while

recording of the EEG signal and pose difficulty in correct clinical analysis. Therefore, it is necessary to

develop methods that are efficient in removing noise from these signals. Several methods such as those

based on time and frequency have been earlier utilized but failed due to their inability to remove lowfrequency

noise. In this work, several pre-processing filters have been tested on EEG data. An attempt

has been made to find the best pre-processing technique that can be used for effective cleaning of EEG

signals. From the results obtained it can be concluded that the proposed modified self-filter shows the

best results when compared with other filtering techniques such as Kalman filter, recurrent quantum

neural network (RQNN) filter, moving average (MA) filter, modified self-filter, Savitzky Golay (SG)

filter and Weiner filter.

Electroencephalography (EEG), Modified self-filter, Savitzky Golay (SG) filter, Weiner filter, Recurrent quantum neural network (RQNN) filter, Moving average (MA) filter.

**Motivation and Incitement**

The human brain is the most complex yet the most fascinating organ. Methods to decode its neuronal functions or dysfunctions are yet to be entirely definitized so far. Several neuroimaging techniques such as fMRI (functional magnetic resonance imagining), SPECT (single photon resonance imaging tomography), PET (positron emission tomography) and EEG (electroencephalography) are vastly applied in the analysis of brain functions as these are highly effective in providing the cerebral metabolic information that can easily be visualized [1]. With the advent of these techniques, it has become easier to understand the various processes occurring in the brain and their quantification has become much simpler. Amongst all the available neuroimaging techniques EEG is widely used because of its ease of acquisition, reliability, high temporal resolution, easy portability and less risk to the users [2]. The spatial resolution and specificity of the EEG recordings are low because of the volume conduction effects occurring in the brain but still, this technique has managed to outperform other methodologies for determining the kaleidoscopic brain functions and understanding the how, where, what and when functional modalities of the brain. These signals are extensively being used in cognitive science, neurophysiological studies, and clinical research applications for identification and cure of diseases such as epilepsy and sleep disorders along with the development of rehabilitation systems [3-5].

EEG signals are recorded non-invasively using an electrode cap which consists of 16, 32, 64 or more recording electrodes or using headbands or head gear that consists of dry electrodes and wireless systems. Though special precautions are taken while recording the EEG signals, these signals still get contaminated with what is called as artefacts [6]. Artefacts are unnecessary and unwanted noise signals that get mixed with the original EEG signals and distort the relevant neuronal information provided by them and makes their analysis difficult. They hide as actual EEG components and mix with the original EEG signals and hence cause an incongruity between the motivation of research and realization for actual system implementation. Moreover, the wrong diagnosis by the medics may lead to the loss of someone’s life or any other permanent damage. Also, the recorded signals have low signal to noise ratio (SNR), usually of the order 0.067-0.0954 [7]. Having such low SNR causes hindrance in the removal of noisy signals because the noise signals correspond to very low frequency. Therefore, methods that focus on both high and low-frequency noise removal have been chosen in order to cover the maximum bandwidth of EEG signals (4-50 Hz). These artefacts may arise from various environmental and biological sources such as the powerline sources used for the recording devices, a change in impedance of the recording devices, blinking of the eye, unwanted muscle movements, muscle contractions, cardiac activity, breathing, sweating, swallowing [8].

Any discrepancy in the original EEG signal indirectly or directly has an effect on the application for which these signals are being used. In clinical applications the inaccurate interpretation of EEG signals may lead to the wrong diagnosis of the disease and hence wrong medication to the patient may prove to be fatal. It is therefore very important to deal with them before further processing or analysis of these signals. It is easier to get rid of technical artefacts by improvement in recording techniques, but biological artefacts pose to be a problem. Also, in countries like India where healthcare equipment’s and facilities are not of very good quality and get corrupted with noises the need for the development of filtering techniques that are software based and do not require any extra hardware installation is necessary.

**Related work**

Many artefact rejection techniques have been designed and being implemented not only to make the signals noise free but be able to preserve the true nature of the EEG signal. Some conventional artefact removal techniques include principal component analysis (PCA), independent component analysis (ICA), common spatial patterns (CSP) filtering, blind source separation (BSS), regression and filtering as reviewed by Kanoga et al. [9]. Artoni et al. [10] implemented the decomposition techniques based on PCA and ICA for noise elimination from EEG signals recorded during visual memory experiment and computed that these are more suitable for offline analysis. However, the disadvantage of using PCA is that it becomes difficult to reconstruct the overall signals using the linear combinations of the principal components because of the ignorance of signals with small amplitudes and irregular changes. On the other hand, ICA faces the difficulty of detecting signal components if Gaussian noise is contaminated in the manner that noise spreads over in an undesirable way into the signal components. BSS technique for rejection of muscle and ocular artefacts was implemented by Mowla et al. [11] on EEG signals recorded from healthy males sitting idle. But decomposition using this technique prove to be tedious, time-consuming and computationally complex. In the mid-1990’s regression techniques for this purpose were widely used for non-stationary EEG data as for example by Kenemans et al. [12]. Sanjana and Patel [13] presented a technique, to categorise Ocular Artefact region and create reference signal, in which Discrete Wavelet Transform (DWT) is applied with Adaptive method. The problem in using wavelet signals is that the disintegration of contaminated signals could not be distinguished from EEG substitutes having more ocular artefacts. Chavez et al. [14] discussed a novel surrogate-based artefact removal (SuBAR) for automatic eradication of artefact from single-channel EEG. The limitation of this method, however, was as the spectrum of noisy EEG was similar to the stationary process, this method was unable to find the long and stubborn muscular artefacts. Most of the research is either focused on the improvement of existing techniques or the development of hybrid techniques that can be used for this purpose [15]. Limited literature is available on the comparison of different techniques used for artefact rejection. A common methodology that can be utilized to perfectly remove artefacts has still not been defined.

**Contributions**

Methods based on digital filtering such as Kalman filter [16], Savitzky Golay (SG), recurrent quantum neural network (RQNN) [17], self-filtering and moving average (MA) filter have been tried and tested upon in this paper to detect the best filter for artefact removal. Further modifications in self filter has been done to enhance its efficiency for artefact removal. Kalman filter has been used to remove the uncorrelated noise in time. SG and MA filters are commonly used for signal smoothing. RQNN filters rely on quantum mechanics and Schrodinger wave equation for improving the SNR ratio. The advantage of using time domain filters is that the raw data can directly be applied to the filter and the output is obtained, unlike frequency domain filtering techniques which require computation of root mean square value and Fourier transform of the signal which has a high latency rate and delay. Also, they are found to be more efficient in removing the Gaussian noise, random noise and pink noise which occur due to different sources as mentioned before [18]. Although these filters have consistently been used for noise removal from EEG signals, in this paper slight modifications have been done in the existing methods to improve their performance. The aforementioned filters are used for data smoothing and removal of noise. Their filtering capabilities are tested on EEG data. A known amount of machine generated noises are added to these signals and the comparison of filters is done based on various parameters such as signal correlation and mean square error. Hence, the scope of the work proposed is concentrated on the optimal selection of time domain-based filter that are robust to variations in real-time implementation.

**Kalman filter**

This algorithm finds a wide application in removing noise from time series data. The main advantages of these filters are their small computational time and requirements, sophisticated recursive properties and its ability as an estimator for one dimensional linear system embedded with Gaussian noise. To make estimations it uses the past and present observations because of its recursive nature [19]. Estimation of the state of the system at a given time ‘T’ is computed from the previous state obtained at ‘T-1’, described with the help of stochastic linear differential equation given as:

Here, *X _{T}* represents the state vector,

The measured signal is given as follows:

Here, *Z _{T}* is the measurement vector,

This algorithm is used for removing the noise from the data with the help of a two-layer network of prediction and measurement stage. An autoregressive model of order 3 is utilized for parameter estimation [20].

**Savitzky-Golay filter**

Savitzky-Golay (SG) algorithm is a digital FIR smoothing polynomial filter used for noise removal in low frequency data. Smoothing is done based on the least squares fitting of polynomials to frames of noisy data segments. This is achieved by fitting consecutive subsets of end-to-end data points using a lower degree polynomial with the help of least squares. The filter parameters are chosen using experimental procedure and a frame length of 41 and polynomial of order 3 is chosen for the SG filter [21]. It is known to maintain the original morphology of the signal while simultaneously giving the smallest peak distortion and an increased signal to noise ratio for non-stationary signals like EEG.

**Moving average filter**

This is also a kind of low pass finite impulse response filter (FIR) used for data smoothing applications of short-term fluctuations occurring in time series data. It analyses the data points by decomposing the whole dataset into smaller subsets also known as windows and taking their average. The subsets are so chosen such that they are equal in number from either side of the central value [22]. In our study a window of length 6 is taken for which the moving average can be defined as:

here *X(n)* is the original signal.

**Recurrent Quantum Neural Network (RQNN) filter**

Gandhi et al. proposed RQNN architecture in which a noisy signal is used to excite the neural lattice making the topology stable [23]. Here the output of the probability density function act as a feedback to the kernel function. The error generated here is weighted to evaluate the potential function V(x,t) expressed as:

Where is scaling factor used to activate the potential function. W (x, t) is weight matrix and g (x, t) is the Gaussian kernel function which is given as:

Where *y(t)* is raw signal and is the estimated signal x
position of the particle in the neural lattice, t is the time and p
(x, t) is the pdf. The potential function V (x, t) modulates the
Schrodinger Wave equation (SWE) which can be expressed in
terms of wave function ψ (x, t) as:

Where h is planks constant taken as 1 and m mass of particle. The estimated signal can be found through maximum likelihood function (MLE) which is given as:

Here is the pdf of the signal and E [.] is expected vector. The synaptic weight can be updated by following rule:

is the de-learning rate which is used to forget the previous value of the weight matrix since EEG signal is nonstationary signal and λ is learning rate which is used to update the weight matrix. The de-learning rate is used to limit the weight matrix from going to infinite as the rightmost term is positive. The SWE is evaluated by Crank-Nicolson method [24]. The parameters of RQNN m, λ and ζ is evaluated by using particle swarm optimization.

**Self-filtering**

For the development of transfer function Stockwell transform (ST) [25] and modified ST (MoST) has been used. The transfer function TF for self-filtering is given as:

Where S (t, f) is the ST or MoST of the EEG signal. The S transform S (t, f) of a signal x (t) is given as:

Where g(t-τ,σ) is Gaussian function is given

Where τ is translational in time domain t and σ is dilation in frequency domain. The standard ST cannot handle the noise in the EEG signal therefore MoST introduced by Zhang et al. [26] has been employed here which increases the time and frequency domain resolution. The Gaussian window used for MoST is given as:

After evaluating the transfer function of SF from (10), the filter is realized by following equation

The filtered signal y(t) has been reconstructed is given as:

It is to be noted that SF deemphasizes the low amplitude feature on S spectrum compared to the large amplitude therefor the random noise feature, which has low amplitude is attenuated.

*Implementation on EEG signal*

EEG signals are widely used in detection of various diseases as well as psychophysiological disorders and hence need to be free of noise so as to avoid incorrect diagnosis. The correct pre-processing methods play an important role which most importantly maintains the original signal structure. Keeping this in mind and taking into account the complex nature of EEG signals different filtering techniques is tested upon complex EEG data.

*Dataset description*

The dataset used in this paper is the BCI Competition IV 2012 Dataset 2b which is comprised of 2 classes of motor imagery (http://www.bbci.de/competition/iv/#dataset2a) [27].

These signals are then added with a known amount of noise. The final signal embedded with noise can be described as:

Where *EEG(t) _{c}* the contaminated is EEG signal,

The EEG signals are given as an input to different filters and their performance is tested.

*Performance evaluation*

Performance evaluation is done to validate the goodness of a filter in removing the noise from the EEG signals. The true EEG signals are embedded either with 0 dB random noise, 5 dB or 15 dB white Gaussian noise and 5 dB and 15 dB pink noise. Efficiency of the filters is tested using different filter evaluation parameters as discussed henceforth.

**Evaluation parameters: **The different parameters used for
evaluation of filters are as follows:

**Correlation:** It is the measure of dependence between two
variables. It is calculated using:

Here and *Y _{j}* are the signals being compared with mean X andX.

A perfect correlation is achieved between the filtered and pure EEG signal if the correlation coefficient is 1 [31].

**Coherence: **Coherence is the measure of similarity between
two signals, that is how well a signal x corresponds to another
signal y at different frequencies. Its values are bounded
between 0 and 1. 0 indicates that the two signals *X _{j}* are linearly
independent and the value 1 corresponds to linearly dependent
signals. Coherence of two signals x and y is calculated as
follows:

Here *P _{xy}* is the cross PSD of signals x and y and

**Signal to noise ratio (SNR):** Signal-to-noise ratio (abbreviated
SNR) is a measure that compares the level of a desired signal
to the level of background noise. SNR is defined as the ratio of
signal power to the noise power, often expressed in decibels. A
ratio higher than 1:1 (greater than 0 dB) indicates more signal
than noise.

**Power spectral density estimation:** It determines the
distribution of signal power over the entire frequency range. It
is an important measure in determining the effectiveness of the
filter. Maximum the difference between the PSDs of a signal
before and after the filtration, the better is the filter quality. It is
an indicator of the amount of other frequency components
present in a signal apart from those in the desired frequency
range [33,34]. Lesser the value of PSD lesser are the other
unwanted signals present. PSD here is obtained using the Fast
Fourier Transform with the help of the following equation:

Here, *N* represents the number of samples, *f _{s}* is the sampling
frequency and

**Mean Square Error (MSE):** It is obtained by calculating the
difference between true EEG signals and filtered EEG signals.

Here *K* represents the number of samples.

The noisy EEG signals are denoised using different filters one by one and their efficiency is tested based on the filter parameters. The EEG signals are added to each of the different type of noises. All the noisy signals are filtered using the filters and an attempt has been made to find the most suitable filter for a given type of signal. The different filter parameters used for developing the filters are discussed as follows.

SG a finite impulse response smoothing filter is designed
having an order of 3 with a frame length of 31. A SG filter
performs much better than other conventional filters if correct
frame length and order are chosen. The parameters chosen are
as presented by [31]. The plot obtained after filtering the EEG
signal embedded with random noise of 0 dB is shown in **Figure
1**. Similarly, for MA smoothing filter a frame length of 6 was
chosen and the filtering plot obtained using this signal for EEG
wave filtration embedded with 5 dB white Gaussian noise is as
shown in **Figure 2**. For filtration using RQNN filters a number
of tuning parameters are taken into consideration, which needs
to be tuned appropriately. These parameters are chosen with
the help of PSO. For EEG signals the chosen value of m,
lambda and zeta are 0.5, 0.9 and 2, respectively. Similarly,
parameters of self-filter and modified self-filter are also tuned
to obtain the best results. **Figure 3** represents the filtering plot
for RQNN filter for EEG wave embedded with 15 dB Gaussian
noise. The filtering plots obtained for EEG waves embedded
with 5 dB pink noise and 15 dB white Gaussian noise are as
shown in **Figures 4 and 5** for SF and modified **Figure 6** shows
the plot for filtering using Kalman for 0 dB random noise for
EEG wave. The noisy signal and filtered signal are both plotted
in the same graph for all the cases. As stated, before the
classification of best filter was done based on different
evaluation parameters discussed before. **Table 1** discuses
correlation, PSD and SNR values obtained using different
filters for class 1 signal of dataset 2b. **Table 2** illustrates the
result for coherence and MSE values after filtration for the
same signal. From the results as seen in **Tables 1 and 2** it can
be observed that all the filters show a correlation value of
almost 0.9 for all the filters between the raw EEG and filtered
EEG. This indicates that all the filters apart from removing
noise also retain the original signal effectively. Therefore,
choosing the best filter based on just this parameter is difficult.
The coherence values lie between the range of 0.2 and 0.7 for
all the filtering techniques used while mostly being on the
lower side. The lower the coherence value the more likely it is
for the two signals to be related to each other. The MSE value
obtained is found to be the least in case of SG filter, almost
nearer to 0 for all the types of added noise. Kalman filter also
exhibits a very low MSE of 0.159 for random noise addition.
SNR ideally should be as high as possible because more the
SNR more is the signal content. All the filters exhibit a SNR
value of 22-24 dB for random noise signals. PSD is the
measure of how the signal is distributed with respect to
frequency. It determines the distribution of signal power over
the entire frequency range. It is an important measure in
determining the effectiveness of the filter. Maximum the
difference between the PSDs of a signal before and after the
filtration, the better is the filter quality. It is an indicator of the
amount of other frequency components present in a signal
apart from those in the desired frequency range. The PSD before filtration was -11.64 dB/Hz and it varied between
-13.178 to -30.3015 dB/Hz.

Filter\Type of Noise | Random Noise | White Noise (5 dB) | White Noise (15 dB) | Pink Noise(5 dB) | Pink Noise(15 dB) | ||||||||||
---|---|---|---|---|---|---|---|---|---|---|---|---|---|---|---|

Corr. | SNR | PSD | Corr. | SNR | PSD | Corr. | SNR | PSD | Corr. | SNR | PSD | Corr. | SNR | PSD | |

M.A. | 0.963 | 22.92 | -17.7 | 0.974 | 5.29 | -17.4 | 0.691 | 1.6 | 1.98 | 0.953 | 9.2 | -18.1 | 0.863 | 8.1 | -17.1 |

S. G. | 0.985 | 24.83 | -16.6 | 0.978 | 5.73 | -17 | 0.944 | 3.15 | -13.1 | 0.969 | 11.3 | -17.7 | 0.799 | 1023 | -18.3 |

S. F. | 0.941 | 21 | -13.3 | 0.92 | 2.66 | -19.5 | 0.487 | 5.22 | -12.8 | 0.944 | 7.62 | -26.3 | 0.784 | 6.2 | -16.2 |

Modified S. F. | 0.924 | 22.3 | -27 | 0.915 | 3.77 | -22.5 | 0.829 | 5.49 | -15 | 0.895 | 7.98 | -25.5 | 0.915 | 8.8 | -35.6 |

RQNN | 0.824 | 21.7 | -28 | 0.953 | 4.79 | -23.5 | 0.979 | 5.89 | -17 | 0.995 | 9.98 | -28.5 | 0.978 | 6.8 | -18.3 |

Kalman | 0.996 | 24.4 | -12.2 | 0.901 | 6.8 | -1.43 | 0.552 | 28.6 | -7.57 | 0.959 | 10.59 | -8.74 | 0.853 | 11.29 | -9.4 |

**Table 1.** Evaluation parameters (corr, SNR, PSD) for class 1 EEG wave embedded with different types of noise.

Filter\Type of Noise | Random Noise | White Noise (5 dB) | White Noise (15 dB) | Pink Noise(5 dB) | Pink Noise (15dB) | |||||
---|---|---|---|---|---|---|---|---|---|---|

Coherence | MSE | Coherence | MSE | Coherence | MSE | Coherence | MSE | Coherence | MSE | |

M.A. | 0.272 | 1.245 | 0.25 | 0.818 | 0.176 | 1.542 | 0.24 | 1.595 | 0.31 | 0.52 |

S. G. | 0.262 | 0.404 | 0.233 | 0.59 | 0.2 | 1.537 | 0.235 | 0.801 | 0.33 | 0.9 |

S. F. | 0.345 | 2.847 | 0.213 | 2.922 | 0.145 | 2.492 | 0.312 | 2.573 | 0.12 | 3.2 |

Modified S. F. | 0.257 | 2.508 | 0.229 | 2.581 | 0.184 | 1.415 | 0.26 | 3.24 | 0.29 | 4.4 |

RQNN | 0.24 | 1.308 | 0.329 | 0.585 | 0.194 | 0.425 | 0.32 | 0.23 | 0.22 | 0.13 |

Kalman | 0.776 | 0.159 | 0.255 | 2.789 | 0.198 | 0.975 | 0.388 | 1.068 | 0.28 | 2.1 |

**Table 2. **Evaluation parameters (Coherence, MSE) for class 1 EEG wave embedded with different types of noise.

The correlation and coherence values indicate the difference between pure and impure EEG signals. It can be observed that modified self-filter has correlation and coherence values, which clearly indicate its efficiency in filtration. The signal to artefact ratio and MSE obtained using modified self-filter is also low, which corresponds to very less artefacts in filtered signals.

The plot for MSE for EEG signals added with random noise is
as shown in **Figures 7, 8**. x-axis indicates the different filters. 1
stands for SG, 2 for MA, 3 for SF, 4 for modified SF, 5 for
RQNN and 6 for Kalman filter.

Taking into consideration all signals and all the filtering techniques it cannot be stated that one filter is superior to others. Choice of filter depends mainly on signal to be filtered and the quantity and type of noise added in it. According to the feasible filter orders suggested by Xian et al. [35] to obtain best filtration using SG filter, further analysis was also conducted on filter of order 2 and 4 and according to the results obtained it was concluded that filter of order 3 was found to be most suitable. Similarly, MA filter with varying window lengths were also tested, ranging from 4-7 and window length of 6 was found to be most efficient. Parameters for RQNN were chosen using PSO hence, hence obtained filter is most optimized.

The different adaptive filters are designed and applied for EEG signals. The design parameters of the filter are varied in a certain feasible range and all the possible combinations are evaluated using dataset 2b. The parameters corresponding to the highest correlation coefficient are the optimal design parameters of the filter. The designed filter is tested successfully on noisy EEG signal for different values of SNR. It is revealed that the modified SF filter removes the noise as well as the original shape of the signal is, maintained. The technique proves to be computationally simple, fast and efficient. Further, the method can also be used for other signals such as ECG, EMG, EOG, and EGG. In this article, the authors presented consistent comparison of the most popular methods of EEG signal pre-processing to facilitate subsequent EEG classification process. Automatic algorithms such as: Self- Filtering, Weiner Filtering (in the task of EEG artefact removing) and combinations of these algorithms were implemented and tested. Experiments show that the best results (classification accuracy improvement) was obtained for modified self-filtering. The developed pre-processing algorithms that use self-filtering are more difficult to implement on-line. While the modified self-filtering algorithm can be used without any problem in any BCI. In addition, it was observed that the sophisticated pre-processing methods improved classification results particularly.

The authors would like to acknowledge with much obligation the crucial role of Graz University and the team who involves in EEG signal recordings and make it available online for new findings and analysis. Authors are also very thankful for the help received from Mr. Subhojit Ghosh faculty member Department of Electrical Engineering, National Institute of Technology, Raipur in the completion of this work in present form.

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