158 research outputs found

    Determination and classification of human stress index using nonparametric analysis of EEG signals / Norizam Sulaiman

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    Regardless of type of stress, either mental stress, emotional stress or physical stress, it definitely affects human lifestyle and work performance. There are two prominent methods in assessing stress which are psychological assessment (qualitative method) and physiological assessment (quantitative method). This research proposes a new stress index based on Electroencephalogram (EEG) signals and non-parametric analysis of the signals. In non-parametric method, the EEG features that might relate to stress are extracted in term of Asymmetry Ratio (AR), Relative Energy Ratio (RER), Spectral Centroids (SC) and Spectral Entropy (SE). The selected features are fed to the k-Nearest Neighbor (k- NN) classifier to identify the stressed group among the four experimental groups being tested. The classification results are based on accuracy, sensitivity and specificity. To support the classification results using k-NN classifier, the clustering techniques using Fuzzy C-Means (FCM) and Fuzzy K-Means (FKM) are implemented. To ensure the robustness of the classifier, the cross-validation technique using k-fold and leave-oneout is performed to the classifier

    Determination and classification of human stress index using nonparametric analysis of EEG signals / Norizam Sulaiman

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    Regardless of type of stress, either mental stress, emotional stress or physical stress, it definitely affects human lifestyle and work performance. There are two prominent methods in assessing stress which are psychological assessment (qualitative method) and physiological assessment (quantitative method). This research proposes a new stress index based on Electroencephalogram (EEG) signals and non-parametric analysis of the signals. In non-parametric method, the EEG features that might relate to stress are extracted in term of Asymmetry Ratio (AR), Relative Energy Ratio (RER), Spectral Centroids (SC) and Spectral Entropy (SE). The selected features are fed to the k-Nearest Neighbor (k-NN) classifier to identify the stressed group among the four experimental groups being tested. The classification results are based on accuracy, sensitivity and specificity. To support the classification results using k-NN classifier, the clustering techniques using Fuzzy C-Means (FCM) and Fuzzy K-Means (FKM) are implemented. To ensure the robustness of the classifier, the cross validation technique using k-fold and leave-one-out is performed to the classifier. The assignment of the stress index is verified by applying Z-score technique to the selected EEG features. The experiments established a 3-level index (Index 1, Index 2 and Index 3) which represents the stress levels of low stress, moderate stress and high stress at overall classification accuracy of 88.89%, classification sensitivity of 86.67 % and classification specificity of 100%. The outcome of the research suggests that the stress level of human can be determined accurately by applying SC on the ratio of the Energy Spectral Density (ESD) of Beta and Alpha bands of the brain signals. The experimental results of this study also confirm that human stress level can be determined and classified precisely using physiological signal through the proposed stress index. The high accuracy, sensitivity and specificity of the classifier might also indicate the robustness of the proposed method

    Learning Style Classification via EEG Sub-band Spectral Centroid Frequency Features

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    Kolbโ€™s Experiential Learning Theory postulates that in learning, knowledge is created by the learnersโ€™ ability to absorb and transform experience. Many studies have previously suggested that at rest, the brain emits signatures that can be associated with cognitive and behavioural patterns. Hence, the study attempts to characterise and classify learning styles from EEG using the spectral centroid frequency features. Initially, learning style of 68 university students has been assessed using Kolbโ€™s Learning Style Inventory. Resting EEG is then recorded from the prefrontal cortex. Next, the EEG is pre-processed and filtered into alpha and theta sub-bands in which the spectral centroid frequencies are computed from the corresponding power spectral densities. The dataset is further enhanced to 160 samples via synthetic EEG. The obtained features are then used as input to the k-nearest neighbour classifier that is incorporated with k-fold cross-validation. Feature classification via k-nearest neighbour has attained five-fold mean training and testing accuracies of 100% and 97.5%, respectively. Hence, results show that the alpha and theta spectral centroid frequencies represent distinct and stable EEG signature to distinguish learning styles from the resting brain.DOI:http://dx.doi.org/10.11591/ijece.v4i6.683

    Development of Smart Security System for Building or Laboratory Entrance based on humanโ€™s brain (EEG) and Voice Signals

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    The drastic increment in cyber-crimes and violent attacks involving our properties and lives made the world become much vigilant towards ill-intentioned peoples. Thus, it leads to the booming of smart security system industry which relies heavily on biometrics technology. However, due to certain circumstances, some users may find the existing biometrics technologies such as fingerprint, palm, iris and face recognition are unable to detect the necessary data precisely due to the physical injuries of the users. Furthermore, the fact that these biometrics technologies are easily retrieved from the user and be used as counterfeit to access to the security system undetected. Thus, in this research, in order to enhance the existing security system based on the biometric technologies, the combination of the human physiological signals such as brain and voice signals will be employed in order to unlock the magnetic door entrance to the laboratory, building or office. This research has utilized mobile Electroencephalogram (EEG) headset and voice recognizer to capture humanโ€™s brain and voice signals respectively. The extracted features from the captured signals then are analyzed, classified and translated to determine the device command for the microcontroller to control the door entranceโ€™s locking system. The high rate of classification results of the selected features of EEG and voice signals at 96.7% and 99.3% respectively show that selected features can be translated to command parameters to control device

    K-NN Classification of Brain Dominance

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    The brain dominance is referred to right brain and left brain. The brain dominance can be observed with an Electroencephalogram (EEG) signal to identify different types of electrical pattern in the brain and will form the foundation of oneโ€™s personality. The objective of this project is to analyze brain dominance by using Wavelet analysis. The Wavelet analysis is done in 2-D Gabor Wavelet and the result of 2-D Gabor Wavelet is validated with an establish brain dominance questionnaire. Twenty-one samples from University Malaysia Pahang (UMP) student are required to answer the establish brain dominance questionnaire has been collected in this experiment. Then, brainwave signal will record using Emotiv device. The threshold value is used to remove the artifact and noise from data collected to acquire a smoother signal. Next, the Band-pass filter is applied to the signal to extract the sub-band frequency components from Delta, Theta, Alpha, and Beta. After that, it will extract the energy of the signal from image feature extraction process. Next the features were classified by using K-Nearest Neighbor (K-NN) in two ratios which 70:30 and 80:20 that are training set and testing set (training: testing). The ratio of 70:30 gave the highest percentage of 83% accuracy while a ratio of 80:20 gave 100% accuracy. The result shows that 2-D Gabor Wavelet was able to classify brain dominance with accuracy 83% to 100%

    Biometric identification and recognition for IRIS using Failure Rejection Rate (FRR) / Musab Ahmed Mohammed Ali Al-Rawi

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    Iris recognition is reckoned as one of the most reliable biometrics for identification purpose in terms of reliability and accuracy. Hence, the objectives of this research are new algorithms development significantly for iris segmentation specifically the proposed Fusion of Profile and Mask Technique (FPM) specifically in getting the actual center of the pupil with high level of accuracy prior to iris localization task, followed by a particular enhancement in iris normalization that is the application of quarter size of an iris image (instead of processing a whole or half size of an iris image) and for better precision and faster recognition with the robust Support Vector Machine (SVM) as classifier. Further aim of this research is the integration of cancelable biometrics feature in the proposed iris recognition technique via non-invertible transformation which determines the feature transformation-based template protection techniques security. Therefore, it is significant to formulate the noninvertibility measure to circumvent the possibility of adversary having the capability in guessing the original biometric providing that the transformed template is obtained. At any process of recognition stage, the biometric data is protected and also whenever there is a compromise to any information in the database it will be on the cancelable biometric template merely without affecting the original biometric information

    K-NN classification of brain dominance

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    The brain dominance is referred to right brain and left brain. The brain dominance can be observed with an Electroencephalogram (EEG) signal to identify different types of electrical pattern in the brain and will form the foundation of oneโ€™s personality. The objective of this project is to analyze brain dominance by using Wavelet analysis. The Wavelet analysis is done in 2-D Gabor Wavelet and the result of 2-D Gabor Wavelet is validated with an establish brain dominance questionnaire. Twenty one samples from University Malaysia Pahang (UMP) student are required to answer the establish brain dominance questionnaire has been collected in this experiment. Then, brainwave signal will record using Emotiv device. The threshold value is used to remove the artifact and noise from data collected to acquire a smoother signal. Next, the Band-pass filter is applied to the signal to extract the sub-band frequency components from Delta, Theta, Alpha, and Beta. After that, it will extract the energy of the signal from image feature extraction process. Next the features were classified by using K-Nearest Neighbor (K-NN) in two ratios which 70:30 and 80:20 that are training set and testing set (training: testing). The ratio of 70:30 gave the highest percentage of 83% accuracy while a ratio of 80:20 gave 100% accuracy. The result shows that 2-D Gabor Wavelet was able to classify brain dominance with accuracy 83% to 100%

    Optimizing parameters and algorithms of multivariate pattern classification for hypothesis testing in high-density EEG

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    Multivariate pattern analysis (MVPA) has come into widespread use for analysis of neuroimaging data in recent years and is gaining further momentum. Given the task of detecting a generalizable pattern in neural activity, MVPA allows to detect fine multidimensional spatiotemporal contrasts between two or more conditions and is thus able to take the full advantage of multivariate information encoded in the data. In particular, MVPA based approaches lend themselves very well to the analysis of electroencephalogram (EEG) data because, unlike the widely-used averaging methods, they consider the signal in its entirety and are thus less susceptible to the confounding effects of single points with abnormal amplitudes. However, using MVPA for hypothesis testing purposes in high-density EEG data has remained a challenging issue. Although MVPA is getting more and more mainstream to detect information in neural activity, its behavior is not well understood, yet. EEG data are high dimensional, yet sample size is usually low in comparison. Moreover, due to the low signal-to-noise ratio, the effect size is small and differences between classes are hard to detect. In such cases, MVPA behaves unexpectedly which makes the overall accuracy of the classifier difficult to interpret. In addition, because MVPA is sensitive to any kind of structure in the data, confounding factors or additional variance within data can bias accuracy. Such complexities warrant extra caution when interpreting classification results, thereby requiring further investigation and guidelines. On the other hand, MVPA literature is mainly dominated by methods suited for fMRI data and most of the dedicated EEG methodology is developed for brain computer interfaces (BCI) or single trial analysis of event-related potentials. Specifically, decoding continuous EEG increasingly suffers from the curse of dimensionality because of the lack of clear prior knowledge on which frequency bands and time points carry relevant information, or an onset where the effect of stimulation can be expected. In this thesis, we addressed the aforementioned challenges involved in using MVPA for decoding EEG data. Chapter 2 describes the statistical properties of MVPA in realistic neuroimaging data and provides important guidelines to interpret classification results. We show that the probability distribution of classification accuracies does not follow any known parametric distribution and can be strongly biased and skewed. We describe unexpected properties of the distribution of classification rates which forbid their use as estimates of the size of experimental effects. Importantly, we scrutinize the finding of below chance level classification rates, which often occur in low sample size, low effect size data and their implications on the shape of classification rates distribution. Next, in chapter 3, we investigate neuroimaging data that, next to a main effect of class, additionally contains a nested subclass structure. We show that in these data sets, correct classification ratios are systematically biased from chance even in absence of class effect. We propose a nonparametric permutation algorithm which can detect the subclass bias and account for its effect by adjusting permutation tests to consider the subclass structure of the data, using subclass-level randomization. Finally, in chapter 4, we used MVPA to decode continuous high-density EEG across subjects. We developed a classification framework along with a specific preprocessing procedure that is optimized for three purposes: 1) to increase signal-to-noise ratio, 2) to reduce the dimensionality of the data, and 3) to adapt the signal better to between-subject classification. Our algorithm uses a two-step classification procedure based on ensemble of linear support vector machines (SVM) which learns the spatial and temporal components of neural activity separately and then aggregates the two components of information to build a classification hyperplane using another linear SVM. We then use this method to see whether human sleep EEG contains any information about what has been learned before sleep

    ๋น„์นจ์Šต์  ๋‡ŒํŒŒ ์‹ ํ˜ธ๋ฅผ ์ด์šฉํ•œ ์‘๊ธ‰ํ™˜์ž์˜ ์ƒ์ฒด๋ฐ˜์‘ ๋ชจ๋‹ˆํ„ฐ๋ง ๊ธฐ๋ฒ•

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    ํ•™์œ„๋…ผ๋ฌธ (๋ฐ•์‚ฌ) -- ์„œ์šธ๋Œ€ํ•™๊ต ๋Œ€ํ•™์› : ๊ณต๊ณผ๋Œ€ํ•™ ํ˜‘๋™๊ณผ์ • ๋ฐ”์ด์˜ค์—”์ง€๋‹ˆ์–ด๋ง์ „๊ณต, 2021. 2. ๊น€ํฌ์ฐฌ.๋‡ŒํŒŒ๋Š” ๋Œ€๋‡Œํ”ผ์งˆ์ด๋‚˜ ๋‘ํ”ผ์˜ ์ „๊ทน์„ ํ†ตํ•ด์„œ ๋‡Œ์˜ ์ „๊ธฐ์  ์‹ ํ˜ธ๋ฅผ ๊ธฐ๋กํ•œ ๊ฒƒ์„ ์˜๋ฏธํ•œ๋‹ค. ๋‡Œ ๊ธฐ๋Šฅ ๊ด€์ฐฐ์„ ์œ„ํ•œ ์ง„๋‹จ๋„๊ตฌ๋กœ์จ ๋‡ŒํŒŒ๋Š” ๋‡Œ์ „์ฆ์ด๋‚˜ ์น˜๋งค ์ง„๋‹จ ๋“ฑ์˜ ๋ชฉ์ ์œผ๋กœ ํ™œ์šฉ๋˜๊ณ  ์žˆ๋‹ค. ๋ณธ ๋…ผ๋ฌธ์—์„œ๋Š” ๋น„์นจ์Šต์  ๋‡ŒํŒŒ๋ฅผ ์ด์šฉํ•˜์—ฌ ์‘๊ธ‰ํ™˜์ž์˜ ์ฃผ์š” ์ƒ๋ฆฌํ•™์  ์ง€ํ‘œ๋ฅผ ๋ชจ๋‹ˆํ„ฐ๋งํ•˜๋Š” ๊ธฐ์ˆ ์„ ๊ฐœ๋ฐœํ•˜์˜€๋‹ค. ์ฒ˜์Œ ๋‘ ์—ฐ๊ตฌ์—์„œ ์‹ฌํ์†Œ์ƒ์ˆ ์˜ ํšจ๊ณผ๋ฅผ ํ‰๊ฐ€ํ•˜๊ธฐ ์œ„ํ•œ ์‹ฌ์ •์ง€ ๋ผ์ง€์‹คํ—˜๋ชจ๋ธ์„ ๊ณ ์•ˆํ•˜์˜€๋‹ค. ํ˜„์žฌ์˜ ์‹ฌํ์†Œ์ƒ์ˆ  ์ง€์นจ์€ ์ฒด์ˆœํ™˜ ํ‰๊ฐ€๋ฅผ ์œ„ํ•ด ๊ธฐ๋„์‚ฝ๊ด€์„ ํ†ตํ•œ ํ˜ธ๊ธฐ๋ง ์ด์‚ฐํ™”ํƒ„์†Œ ๋ถ„์••์˜ ์ธก์ •์„ ๊ถŒ๊ณ ํ•œ๋‹ค. ํ•˜์ง€๋งŒ, ์ •ํ™•ํ•œ ๊ธฐ๋„์‚ฝ๊ด€์ด ํŠนํžˆ ๋ณ‘์› ๋ฐ– ์ƒํ™ฉ์—์„œ ์–ด๋ ค์šธ ์ˆ˜ ์žˆ๋‹ค. ๋”ฐ๋ผ์„œ, ๊ฐ„ํŽธํžˆ ์ธก์ •ํ•  ์ˆ˜ ์žˆ๊ณ  ์†Œ์ƒ ํ™˜์ž์˜ ์‹ ๊ฒฝํ•™์  ์˜ˆํ›„๋ฅผ ์ง„๋‹จํ•˜๋Š”๋ฐ ์‚ฌ์šฉ๋˜๋Š” ๋‡ŒํŒŒ๋ฅผ ์ด์šฉํ•œ ์˜ˆ์ธก ๊ธฐ์ˆ ์ด ์‹ฌํ์†Œ์ƒ์ˆ  ํ’ˆ์งˆํ‰๊ฐ€์ง€ํ‘œ์˜ ๋Œ€์•ˆ์œผ๋กœ ์ œ์•ˆ๋˜์—ˆ๋‹ค. ์ฒซ ๋ฒˆ์งธ ์‹คํ—˜์—์„œ๋Š” ๊ณ ํ’ˆ์งˆ๊ณผ ์ €ํ’ˆ์งˆ ๊ธฐ๋ณธ์‹ฌํ์†Œ์ƒ์ˆ ์„ 10ํšŒ ๋ฐ˜๋ณตํ•˜๋ฉด์„œ ์ธก์ •๋œ ๋‡ŒํŒŒ๋ฅผ ๋ถ„์„ํ•˜์˜€๋‹ค. ์‹ฌํ์†Œ์ƒ์ˆ ์˜ ํ’ˆ์งˆ์— ๋”ฐ๋ฅธ ๋‡ŒํŒŒ์˜ ๋ณ€ํ™”๋ฅผ ์ด์šฉํ•˜์—ฌ ์ฒด์ˆœํ™˜ ํ‰๊ฐ€๋ฅผ ์œ„ํ•œ EEG-based Brain Resuscitation Index (EBRI) ๋ชจ๋ธ์„ ๋„์ถœํ•˜์˜€๋‹ค. EBRI ๋ชจ๋ธ์—์„œ ํš๋“ํ•œ ํ˜ธ๊ธฐ๋ง ์ด์‚ฐํ™”ํƒ„์†Œ ๋ถ„์•• ์˜ˆ์ธก์น˜๋Š” ์‹ค์ œ ๊ฐ’๊ณผ ์–‘์˜ ์ƒ๊ด€๊ด€๊ณ„๋ฅผ ๋ณด์ด๋ฉฐ, ๋ณ‘์› ๋ฐ– ์ƒํ™ฉ์—์„œ์˜ ํ™œ์šฉ ๊ฐ€๋Šฅ์„ฑ์„ ๋ณด์˜€๋‹ค. ๋‘ ๋ฒˆ์งธ ์‹คํ—˜์—์„œ๋Š” ๋‘ ๊ฐ€์ง€ ์‹ฌํ์†Œ์ƒ์ˆ (๊ธฐ๋ณธ์‹ฌํ์†Œ์ƒ์ˆ , ์ „๋ฌธ์‹ฌํ์†Œ์ƒ์ˆ )์ด ์ˆ˜ํ–‰๋˜์—ˆ๋‹ค. ์ œ์„ธ๋™ ์ง์ „์— ์ˆ˜์ง‘๋œ ๋‡ŒํŒŒ๋Š” ์‹ฌํ์†Œ์ƒ์ˆ  ๋„์ค‘ ๊ฒฝ๋™๋งฅํ˜ˆ๋ฅ˜์˜ ํšŒ๋ณต๋ฅ ๊ณผ ํ•จ๊ป˜ ๋ถ„์„๋˜์—ˆ๋‹ค. ์‹ฌํ์†Œ์ƒ์ˆ  ๋„์ค‘ ๊ฒฝ๋™๋งฅํ˜ˆ๋ฅ˜์˜ ํšŒ๋ณต๋ฅ ์„ ๋ฐ˜์˜ํ•˜๋Š” ๋‡ŒํŒŒ ๋ณ€์ˆ˜๋ฅผ ๊ทœ๋ช…ํ•œ ํ›„, ์ด๋ฅผ ์ด์šฉํ•˜์—ฌ ๋†’์€ ํšŒ๋ณต๋ฅ (30% ์ด์ƒ)๊ณผ ๋‚ฎ์€ ํšŒ๋ณต๋ฅ (30% ๋ฏธ๋งŒ)์„ ๊ตฌ๋ถ„ํ•˜๋Š” ๊ธฐ๊ณ„ํ•™์Šต ๊ธฐ๋ฐ˜ ์ด์ง„๋ถ„๋ฅ˜๋ชจ๋ธ์„ ๋„์ถœํ•˜์˜€๋‹ค. ์„œํฌํŠธ ๋ฒกํ„ฐ ๋จธ์‹  ๊ธฐ๋ฐ˜์˜ ์˜ˆ์ธก๋ชจ๋ธ์ด 0.853์˜ ์ •ํ™•๋„์™€ 0.909์˜ ๊ณก์„ ํ•˜๋ฉด์ ์„ ๋ณด์ด๋ฉฐ ๊ฐ€์žฅ ์šฐ์ˆ˜ํ•œ ์„ฑ๋Šฅ์„ ๋ณด์˜€๋‹ค. ์ด๋Ÿฌํ•œ ์˜ˆ์ธก๋ชจ๋ธ์€ ์‹ฌ์ •์ง€ ํ™˜์ž์˜ ๋‡Œ ์†Œ์ƒ์„ ํ–ฅ์ƒ์‹œ์ผœ ๋น ๋ฅธ ๋‡Œ ๊ธฐ๋Šฅ ํšŒ๋ณต์„ ๊ฐ€๋Šฅํ•˜๊ฒŒ ํ•  ๊ฒƒ์œผ๋กœ ๊ธฐ๋Œ€๋œ๋‹ค. ์„ธ ๋ฒˆ์งธ ์—ฐ๊ตฌ์—์„œ ๋น„์นจ์Šต์  ๋‡ŒํŒŒ๋ฅผ ์ด์šฉํ•˜์—ฌ ๋‘๊ฐœ๋‚ด์••์„ ์˜ˆ์ธกํ•˜๋Š” ๋ชจ๋ธ์„ ๊ฐœ๋ฐœํ•˜๊ธฐ ์œ„ํ•œ ์™ธ์ƒ์„ฑ ๋‡Œ์†์ƒ ๋ผ์ง€์‹คํ—˜๋ชจ๋ธ์ด ๊ณ ์•ˆ๋˜์—ˆ๋‹ค. ์™ธ์ƒ์„ฑ ๋‡Œ์†์ƒ์€ ๋ฌผ๋ฆฌ์  ์ถฉ๊ฒฉ์— ์˜ํ•ด ์ •์ƒ์ ์ธ ๋‡Œ ๊ธฐ๋Šฅ์ด ์ค‘๋‹จ๋œ ์ƒํƒœ๋ฅผ ์˜๋ฏธํ•˜๋ฉฐ, ์ด ๋•Œ์˜ ๋‘๊ฐœ๋‚ด์•• ์ƒ์Šน๊ณผ ๊ด€๋ฅ˜์ €ํ•˜๊ฐ€ ๋‡ŒํŒŒ์— ์˜ํ–ฅ์„ ๋ผ์น  ์ˆ˜ ์žˆ๋‹ค. ๋”ฐ๋ผ์„œ, ์šฐ๋ฆฌ๋Š” ๋‡ŒํŒŒ ๊ธฐ๋ฐ˜ ๋‘๊ฐœ๋‚ด์•• ์˜ˆ์ธก๋ชจ๋ธ์„ ๊ฐœ๋ฐœํ•˜์˜€๋‹ค. ํด๋ฆฌ์นดํ…Œํ„ฐ๋กœ ์‹คํ—˜๋™๋ฌผ์˜ ๋‘๊ฐœ๋‚ด์••์„ ๋ณ€๊ฒฝํ•˜๋ฉด์„œ ๋‡ŒํŒŒ๋ฅผ ํš๋“ํ•˜์˜€๋‹ค. ๋‘๊ฐœ๋‚ด์••์˜ ์ •์ƒ๊ตฌ๊ฐ„(25 mmHg ๋ฏธ๋งŒ)๊ณผ ์œ„ํ—˜๊ตฌ๊ฐ„(25 mmHg ์ด์ƒ)์„ ์œ ์˜๋ฏธํ•˜๊ฒŒ ๊ตฌ๋ถ„ํ•˜๋Š” ๋‡ŒํŒŒ ๋ณ€์ˆ˜๋ฅผ ๊ทœ๋ช…ํ•œ ํ›„ ๊ธฐ๊ณ„ํ•™์Šต ๊ธฐ๋ฐ˜ ์ด์ง„๋ถ„๋ฅ˜๋ชจ๋ธ์„ ๋„์ถœํ•˜์˜€๋‹ค. ๋‹ค์ธต ํผ์…‰ํŠธ๋ก  ๊ธฐ๋ฐ˜์˜ ์˜ˆ์ธก๋ชจ๋ธ์ด 0.686์˜ ์ •ํ™•๋„์™€ 0.754์˜ ๊ณก์„ ํ•˜๋ฉด์ ์„ ๋ณด์ด๋ฉฐ ๊ฐ€์žฅ ์šฐ์ˆ˜ํ•œ ์„ฑ๋Šฅ์„ ๋ณด์˜€๋‹ค. ๋˜๋‹ค๋ฅธ ๋น„์นจ์Šต ๋ฐ์ดํ„ฐ์ธ ์‹ฌ๋ฐ•์ˆ˜ ์ •๋ณด์™€ ํ•จ๊ป˜ ์‚ฌ์šฉํ•˜์˜€์„ ๋•Œ ์ •ํ™•๋„์™€ ๊ณก์„ ํ•˜๋ฉด์ ์€ ๊ฐ๊ฐ 0.760๊ณผ 0.834๋กœ ํ–ฅ์ƒ๋˜์—ˆ๋‹ค. ์ œ์•ˆ๋œ ์˜ˆ์ธก๋ชจ๋ธ์€ ์‘๊ธ‰์ƒํ™ฉ์—์„œ ๋น„์นจ์Šต์ ์œผ๋กœ ๋‘๊ฐœ๋‚ด์••์„ ๊ด€์ฐฐํ•˜์—ฌ ์ •์ƒ ์ˆ˜์ค€์˜ ๋‘๊ฐœ๋‚ด์••์„ ์œ ์ง€ํ•˜๋Š”๋ฐ ๋„์›€์„ ์ค„ ๊ฒƒ์œผ๋กœ ๊ธฐ๋Œ€๋œ๋‹ค. ๋ณธ ๋…ผ๋ฌธ์€ ์‘๊ธ‰ํ™˜์ž์˜ ์ฃผ์š” ์ƒ๋ฆฌํ•™์  ์ง€ํ‘œ๋ฅผ ๋น„์นจ์Šต์  ๋‡ŒํŒŒ๋ฅผ ์ด์šฉํ•˜์—ฌ ๊ด€์ฐฐํ•˜๋Š” ์˜ˆ์ธก๋ชจ๋ธ์„ ์ œ์•ˆํ•˜๊ณ  ์„ฑ๋Šฅ์„ ๊ฒ€์ฆํ•˜์˜€๋‹ค. ๋ณธ ์—ฐ๊ตฌ์—์„œ๋Š” ๋‡ŒํŒŒ๋ฅผ ์ด์šฉํ•˜์—ฌ ์ฆ‰๊ฐ์ ์ธ ํ˜ธ๊ธฐ๋ง ์ด์‚ฐํ™”ํƒ„์†Œ ๋ถ„์••, ๊ฒฝ๋™๋งฅํ˜ˆ๋ฅ˜, ๋‘๊ฐœ๋‚ด์••์„ ์ถ”์ •ํ•˜๊ธฐ ์œ„ํ•œ ์˜ˆ์ธก๋ชจ๋ธ์„ ์ˆ˜๋ฆฝํ•˜์˜€๋‹ค. ํ•˜์ง€๋งŒ, ๋‡ŒํŒŒ ๋ฐ์ดํ„ฐ๋Š” ์žฅ๊ธฐ๊ฐ„์˜ ์‹ ๊ฒฝํ•™์ , ๊ธฐ๋Šฅ์  ํšŒ๋ณต๊ณผ ํ•จ๊ป˜ ํ‰๊ฐ€๋˜์–ด์•ผ ํ•œ๋‹ค. ๋ณธ ๋…ผ๋ฌธ์—์„œ ๊ฐœ๋ฐœํ•œ ์˜ˆ์ธก๋ชจ๋ธ์˜ ์„ฑ๋Šฅ๊ณผ ์ ์šฉ ๊ฐ€๋Šฅ์„ฑ์€ ํ–ฅํ›„ ๋‹ค์–‘ํ•œ ์ž„์ƒ์—ฐ๊ตฌ๋ฅผ ํ†ตํ•ด cerebral performance category์™€ modified Rankin scale ๋“ฑ์˜ ์‹ ๊ฒฝํ•™์  ํ‰๊ฐ€์ง€ํ‘œ์™€ ํ•จ๊ป˜ ๋ถ„์„, ๊ฐœ์„ ๋˜์–ด์•ผ ํ•  ๊ฒƒ์ด๋‹ค.Electroencephalogram (EEG) is a recording of the electrical activity of the brain, measured using electrodes attached to the cerebrum cortex or the scalp. As a diagnostic tool for brain disorders, EEG has been widely used for clinical purposes such as epilepsy- and dementia diagnosis. This study develops an EEG-based noninvasive critical care monitoring method for emergency patients. In the first two studies, ventricular fibrillation swine models were designed to develop EEG-based monitoring methods for evaluating the effectiveness of cardiopulmonary resuscitation (CPR). The CPR guidelines recommend measuring end-tidal carbon dioxide (ETCO2) via endotracheal intubation to assess systemic circulation. However, accurate insertion of the endotracheal tube might be difficult in an out-of-hospital setting (OOHS). Therefore, an easily measurable EEG, which has been used to predict resuscitated patients neurologic prognosis, was suggested as a surrogate indicator for CPR feedback. In the first experimental setup, the high- and low quality CPRs were altered 10 times repeatedly, and the EEG parameters were analyzed. Linear regression of an EEG-based brain resuscitation index (EBRI) was used to estimate ETCO2 levels as a novel feedback indicator of systemic circulation during CPR. A positive correlation was found between the EBRI and the real ETCO2, which indicates the feasibility of EBRI in OOHSs. In the second experimental setup, two types of CPR mode were performed: basic life support and advanced cardiovascular life support. EEG signals that were measured between chest compressions and defibrillation shocks were analyzed to monitor the cerebral circulation with respect to the recovery of carotid blood flow (CaBF) during CPR. Significant EEG parameters were identified to represent the CaBF recovery, and machine learning (ML)-based classification models were established to differentiate between the higher (โ‰ฅ 30%) and lower (< 30%) CaBF recovery. The prediction model based on the support vector machine (SVM) showed the best performance, with an accuracy of 0.853 and an area under the curve (AUC) of 0.909. The proposed models are expected to guide better cerebral resuscitation and enable early recovery of brain function. In the third study, a swine model of traumatic brain injury (TBI) was designed to develop an EEG-based prediction model of an elevated intracranial pressure (ICP). TBI is defined as the disruption of normal brain function due to physical impact. This can increase ICP, and the resulting hypoperfusion can affect the cerebral electrical activity. Thus, we developed EEG-based prediction models to monitor ICP levels. During the experiments, EEG was measured while the ICP was adjusted with the Foley balloon catheter. Significant EEG parameters were determined to differentiate between the normal (< 25 mmHg) and dangerous (โ‰ฅ 25 mmHg) ICP levels and ML-based binary classifiers were established to distinguish between these two groups. The multilayer perceptron model showed the best performance with an accuracy of 0.686 and an AUC of 0.754, which were improved to 0.760 and 0.834, respectively, when a noninvasive heart rate was also used as an input. The proposed prediction models are expected to instantly treat an elevated ICP (โ‰ฅ 25 mmHg) in emergency settings. This study presents a new EEG-based noninvasive monitoring method of the physiologic parameters of emergency patients, especially in an OOHS, and evaluates the performance of the proposed models. In this study, EEG was analyzed to predict immediate ETCO2, CaBF, and ICP. The prediction models demonstrate that a noninvasive EEG can yield clinically important predictive outcomes. Eventually, the EEG parameters should be investigated with regard to the long-term neurological and functional outcomes. Further clinical trials are warranted to improve and evaluate the feasibility of the proposed method with respect to the neurological evaluation scores, such as the cerebral performance category and modified Rankin scale.Abstract i Contents iv List of Tables viii List of Figures x List of Abbreviations xii Chapter 1 General Introduction 1 1.1 Electroencephalogram 1 1.2 Clinical use of spontaneous EEG 5 1.3 EEG and cerebral hemodynamics 7 1.4 EEG use in emergency settings 9 1.5 Noninvasive CPR assessment 10 1.6 Noninvasive traumatic brain injury assessment 16 1.7 Thesis objectives 21 Chapter 2 EEG-based Brain Resuscitation Index for Monitoring Systemic Circulation During CPR 23 2.1 Introduction 23 2.2 Methods 25 2.2.1 Ethical statement 25 2.2.2 Study design and setting 25 2.2.3 Experimental animals and housing 27 2.2.4 Surgical preparation and hemodynamic measurements 27 2.2.5 EEG measurement 29 2.2.6 Data analysis 32 2.2.7 EBRI calculation 33 2.2.8 Delta-EBRI calculation 34 2.3 Results 36 2.3.1 Hemodynamic parameters 36 2.3.2 Changes in EEG parameters 37 2.3.3 EBRI calculation 39 2.3.4 Delta-EBRI calculation 41 2.4 Discussion 42 2.4.1 Accomplishment 42 2.4.2 Limitations 45 2.5 Conclusion 46 Chapter 3 EEG-based Prediction Model of the Recovery of Carotid Blood Flow for Monitoring Cerebral Circulation During CPR 47 3.1 Introduction 47 3.2 Methods 50 3.2.1 Ethical statement 50 3.2.2 Study design and setting 50 3.2.3 Experimental animals and housing 52 3.2.4 Surgical preparation and hemodynamic measurements 54 3.2.5 EEG measurement 55 3.2.6 Data processing 57 3.2.7 Data analysis 58 3.2.8 Development of machine-learning based prediction model 59 3.3 Results 63 3.3.1 Results of CPR process 63 3.3.2 EEG changes with the recovery of CaBF 66 3.3.3 Changes in EEG parameters depending on four CaBF groups 68 3.3.4 Changes in EEG parameters depending on two CaBF groups 69 3.3.5 EEG parameters for prediction models 70 3.3.6 Performances of prediction models 73 3.4 Discussion 76 3.4.1 Accomplishment 76 3.4.2 Limitations 78 3.5 Conclusion 80 Chapter 4 EEG-based Prediction Model of an Increased Intra-Cranial Pressure for TBI patients 81 4.1 Introduction 81 4.2 Methods 83 4.2.1 Ethical statement 83 4.2.2 Study design and setting 83 4.2.3 Experimental animals and housing 85 4.2.4 Surgical preparation and hemodynamic measurements 86 4.2.5 EEG measurement 88 4.2.6 Data processing 90 4.2.7 Data analysis 90 4.2.8 Development of machine-learning based prediction model 91 4.3 Results 92 4.3.1 Hemodynamic changes during brain injury phase 92 4.3.2 EEG changes with an increase of ICP 93 4.3.3 EEG parameters for prediction models 94 4.3.4 Performances for prediction models 95 4.4 Discussion 100 4.4.1 Accomplishment 100 4.4.2 Limitations 104 4.5 Conclusion 104 Chapter 5 Summary and Future works 105 5.1 Thesis summary and contributions 105 5.2 Future direction 108 Bibilography 113 Abstract in Korean 135Docto

    Brain Computer Interfaces and Emotional Involvement: Theory, Research, and Applications

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    This reprint is dedicated to the study of brain activity related to emotional and attentional involvement as measured by Brainโ€“computer interface (BCI) systems designed for different purposes. A BCI system can translate brain signals (e.g., electric or hemodynamic brain activity indicators) into a command to execute an action in the BCI application (e.g., a wheelchair, the cursor on the screen, a spelling device or a game). These tools have the advantage of having real-time access to the ongoing brain activity of the individual, which can provide insight into the userโ€™s emotional and attentional states by training a classification algorithm to recognize mental states. The success of BCI systems in contemporary neuroscientific research relies on the fact that they allow one to โ€œthink outside the labโ€. The integration of technological solutions, artificial intelligence and cognitive science allowed and will allow researchers to envision more and more applications for the future. The clinical and everyday uses are described with the aim to invite readers to open their minds to imagine potential further developments
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