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A neuron, with axon, dendrites and the cell body (soma). 

A neuron, with axon, dendrites and the cell body (soma). 

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... neuron has a very simple computational capability in itself, but by working together in vast neural networks they together form the complex system that is the human brain. The neuron generally has several different incoming connections, called dendrites, and one outgoing connection, called an axon ( Figure 1). The axon of a neuron usually connects to dendrites of other neurons through synapses. ...
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... the case of classifying patterns, the threshold in the one-dimensional case becomes a hyperplane in an N-dimensional space, where N is the number of features used to describe the signal. This is exemplified in Figure 10 for the cases of two and three dimensions. ...
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... ML classifier was implemented by using training data to estimate the pdfs by e.g. calculating and smoothing the histograms for the two classes ( Figure 11). The areas of the histograms were then normalized to one. ...
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... S-shape gives the functions the property that they act linearly around the origin, while large inputs are squeezed into the interval zero to one. In the implementation used in this project, the hyperbolic tangent function was used (Figure 12). The neuron can graphically be visualized as in Figure 13. ...
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... the implementation used in this project, the hyperbolic tangent function was used (Figure 12). The neuron can graphically be visualized as in Figure 13. In this example, it has three inputs and one output, but the model allows for any number of inputs. ...
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... S-shape inside the neuron illustrates the sigmoid activation function that is applied to the output. The multilayer perceptron (Figure 14) consists of any number of layers of neurons, although two (or three, if inputs are considered to be neurons) is the most common. The outputs from the first layer are connected to the inputs of the next layer in a strictly forward manner, hence the designation "feed- forward" network. ...
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... was avoided by using early stopping, meaning that the error on the evaluation set was monitored and a training length that resulted in a reasonable trade-off for all different patients was chosen. Figure 15 shows an example of how the sensitivity, specificity and AUC evolve during training. Initially, all samples are classified as suppression, resulting in 100% specificity and zero sensitivity. ...
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... contradiction between the gradual increase in sensitivity and the very quick increase in AUC arises because the AUC calculation does not depend on a specific threshold value. Figure 16 shows a visualization of the network weights. These determine how large an influence the inputs have on each hidden neuron, and how much influence each hidden neuron has on the final summation in the output neuron. ...
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... Maximizing the margin of classification In short, the first part means that the SVM uses a function to transform the problem nonlinearly and then construct a nonlinear decision boundary using linear techniques. The second part means that while a classifier such as an ANN settles for any boundary that separates two classes in the training data from each other, the SVM finds the one that maximizes the margin ( Figure 17), a property that often will increase the generalization ability of the classifier. The SVM also has the property that only the samples near the decision boundary are involved in the computations. ...
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... the ANN is trained by updating its weights with an amount proportional to any randomly chosen misclassified training sample, the SVM can be trained by choosing the current worst-classified pattern. When the training is finished, these patterns would be the support vectors, the patterns on the margins that define the optimal separating hyperplane (Figure 18). This method of training the SVM, however, is feasible only for very small datasets, because it would mean that all training samples have to be searched in each iteration in order to find the worst-classified sample. ...
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... performance values varied significantly for the different patients, so the final values were chosen to give decent performance for all cases, rather than selecting a parameter setting that would have given almost perfect performance in some cases and zero performance in others. Figure 19 shows an example of AUC values plotted in a grid of parameter values. Note that the surfaces for the different patients are located at different heights, and that the gradients for increasing performance point in different directions. ...
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... results depend on what parameters are chosen when training the classifier, as described in the previous chapters concerning the different classification methods. Figure 21 shows the same type of example as Figure 20, but is based on the feature data in Figure 8, from another patient. In this case there is one burst that is completely missed, and there are two artifacts that are classified as bursts. ...

Citations

... All the EEG records are bandpass-filtered to 1-40 Hz as the signals below 1 Hz and above 40 Hz in EEG are generally unreliable due to low signal-to-noise ratio [23] and the conventional EEG bands of our research interest i.e., delta (1-4 Hz), theta (4-8 Hz), alpha (8)(9)(10)(11)(12)(13), beta (13)(14)(15)(16)(17)(18)(19)(20)(21)(22)(23)(24)(25)(26)(27)(28)(29)(30) and gamma (30)(31)(32)(33)(34)(35)(36)(37)(38)(39)(40) lie in this range [24]. The records are re-referenced to Common Average Reference (CAR) montage to approximate a reference-free recording condition, to minimize the artifacts, to make channel records independent i.e., to make channel records to represent local activities [25], to provide high reliability over quantitative EEG features [26]. ...
... All the EEG records are bandpass-filtered to 1-40 Hz as the signals below 1 Hz and above 40 Hz in EEG are generally unreliable due to low signal-to-noise ratio [23] and the conventional EEG bands of our research interest i.e., delta (1-4 Hz), theta (4-8 Hz), alpha (8)(9)(10)(11)(12)(13), beta (13)(14)(15)(16)(17)(18)(19)(20)(21)(22)(23)(24)(25)(26)(27)(28)(29)(30) and gamma (30)(31)(32)(33)(34)(35)(36)(37)(38)(39)(40) lie in this range [24]. The records are re-referenced to Common Average Reference (CAR) montage to approximate a reference-free recording condition, to minimize the artifacts, to make channel records independent i.e., to make channel records to represent local activities [25], to provide high reliability over quantitative EEG features [26]. In spite of proper recording conditions to eliminate any unwanted information, the Electrooculogram (EOG) and Electrocardiogram (ECG) artifacts are found to be still present in the records. ...
Article
Full-text available
Measurement of features from the chaos theory or as popularly known, the concept of nonlinear dynamics, as indicatives of several pathological conditions and cognition states using the electroencephalography (EEG) signal is very popular. In this paper, the analysis of scalp EEG signals of normal subjects and brain tumour patients using the nonlinear dynamic features has been presented. The nonlinear dynamic features that represent the dimensional and waveform complexities of the signal being analyzed have been considered. The statistical analysis of the selected nonlinear dynamic features has been presented. The results show that the nonlinear dynamic features significantly discriminate the brain tumour group from the normal group.
... All EEG records were then bandpass-filtered to 1-40 Hz as the signals below 1 Hz and above 40 Hz in EEG are generally unreliable due to low signal-to-noise ratio [22], [23]. The records were rereferenced to common average reference to approximate a reference-free recording condition [23], to minimize the artifacts [24], [25], to make channel records independent i.e., to make channel records to represent local activities [24], [26], and to provide high reliability over quantitative EEG features [27]. Finally a 10-minute, artifact-free epoch from each EEG record was retained for the analysis. ...
... All EEG records were then bandpass-filtered to 1-40 Hz as the signals below 1 Hz and above 40 Hz in EEG are generally unreliable due to low signal-to-noise ratio [22], [23]. The records were rereferenced to common average reference to approximate a reference-free recording condition [23], to minimize the artifacts [24], [25], to make channel records independent i.e., to make channel records to represent local activities [24], [26], and to provide high reliability over quantitative EEG features [27]. Finally a 10-minute, artifact-free epoch from each EEG record was retained for the analysis. ...
Article
Full-text available
The scalp electroencephalography (EEG) signal is an important clinical tool for the diagnosis of several brain disorders. The objective of the presented work is to analyze the feasibility of the spectral features extracted from the scalp EEG signals in detecting brain tumors. A set of 16 candidate features from frequency domain is considered. The significance on the mean values of these features between 100 brain tumor patients and 102 normal subjects is statistically evaluated. Nine of the candidate features significantly discriminate the brain tumor case from the normal one. The results encourage the use of (quantitative) scalp EEG for the diagnosis of brain tumors