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Search Results (1,612)

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Keywords = electroencephalography

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8 pages, 1897 KiB  
Article
Effect of Earthing Mats on Sleep Quality in Rats
by Minsook Ye, Woojin Jeong, Hyo-jeong Yu, Kyu-ri Kim, Sung Ja Rhie, Yongsuk Kim, Jiyoun Kim and Insop Shim
Int. J. Mol. Sci. 2024, 25(18), 9791; https://doi.org/10.3390/ijms25189791 - 10 Sep 2024
Viewed by 139
Abstract
Grounding, a therapeutic technique involving direct contact with the earth, has been proposed by various studies to potentially have beneficial effects on pressure, sleep quality, stress, inflammation, and mood. However, the scientific evidence supporting its sedative effects remains incomplete. This study examined the [...] Read more.
Grounding, a therapeutic technique involving direct contact with the earth, has been proposed by various studies to potentially have beneficial effects on pressure, sleep quality, stress, inflammation, and mood. However, the scientific evidence supporting its sedative effects remains incomplete. This study examined the sedative effectiveness of an earthing mat on sleep quality and investigated the underlying neural mechanisms using electroencephalography (EEG) analysis in rodents, focusing on orexin and superoxide dismutase (SOD) levels in the brain. Rats were randomly assigned to four groups: the naïve normal group (Nor), the group exposed to an earthing mat for 7 days (A-7D), the group exposed to an earthing mat for 21 days (A-21D), and the group exposed to an electronic blanket for 21 days (EM). EEG results revealed that the A-21D group exhibited significantly reduced wake time and increased rapid eye movement (REM), non-rapid eye movement (NREM), and total sleep time compared to the Nor group (p < 0.05). Moreover, the A-21D group demonstrated a significant increase in NREM sleep (p < 0.001), REM sleep (p < 0.01), and total sleep time (p < 0.001), along with a decrease in wake time compared to the EM group (p < 0.001). The orexin level in the A-21D group was significantly lower compared to the Nor group (p < 0.01), while SOD1 expression was markedly elevated in the A-21D group compared to the Nor group (p < 0.001). These results suggest that the earthing mat may represent a promising new method for promoting sleep quality and could serve as an effective therapeutic technique. Full article
(This article belongs to the Section Molecular Pathology, Diagnostics, and Therapeutics)
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<p>Effect of earthing mat on sleep architecture. Changes in the percentage of wake time (<b>A</b>), REM sleep (<b>B</b>), NREM sleep (<b>C</b>), and total sleep (<b>D</b>) during the dark phase are depicted in the earthing mat-exposed groups. The data represent the mean ± SEM of the percentage of time spent in the sleep–wake state. *** <span class="html-italic">p</span> &lt; 0.001, * <span class="html-italic">p</span> &lt; 0.05 vs. Nor, ### <span class="html-italic">p</span> &lt; 0.001, ## <span class="html-italic">p</span> &lt; 0.01 vs. A21-D; one-way ANOVA followed by Tukey. ● Nor, ■ A-7D,▲ A-21D,▼EM.</p>
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<p>Impact of earthing mat on orexin-positive cells in the LH. (<b>A</b>) Photomicrographs illustrating orexin-positive cells in the LH. The dashed circles indicate the LH region. (<b>B</b>) Quantification of orexin-positive cells in the LH. *** <span class="html-italic">p</span> &lt; 0.01 vs. Nor; ### <span class="html-italic">p</span> &lt; 0.05 vs. A-21D; one-way ANOVA followed by Tukey’s test.</p>
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<p>Impact of earthing mat on SOD-positive cells in the LH. (<b>A</b>) Photomicrographs illustrating orexin-positive cells in the LH. (<b>B</b>) Quantification of SOD-positive cells in the LH. *** <span class="html-italic">p</span> &lt; 0.01 vs. Nor; one-way ANOVA followed by Tukey’s test.</p>
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<p>Animal groups and treatments in the experimental design of this study.</p>
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20 pages, 3560 KiB  
Article
Resting-State EEG Alterations of Practice-Related Spectral Activity and Connectivity Patterns in Depression
by Elisa Tatti, Alessandra Cinti, Anna Serbina, Adalgisa Luciani, Giordano D’Urso, Alberto Cacciola, Angelo Quartarone and Maria Felice Ghilardi
Biomedicines 2024, 12(9), 2054; https://doi.org/10.3390/biomedicines12092054 - 10 Sep 2024
Viewed by 213
Abstract
Background: Depression presents with altered energy regulation and neural plasticity. Previous electroencephalography (EEG) studies showed that practice in learning tasks increases power in beta range (13–30 Hz) in healthy subjects but not in those with impaired plasticity. Here, we ascertain whether depression presents [...] Read more.
Background: Depression presents with altered energy regulation and neural plasticity. Previous electroencephalography (EEG) studies showed that practice in learning tasks increases power in beta range (13–30 Hz) in healthy subjects but not in those with impaired plasticity. Here, we ascertain whether depression presents with alterations of spectral activity and connectivity before and after a learning task. Methods: We used publicly available resting-state EEG recordings (64 electrodes) from 122 subjects. Based on Beck Depression Inventory (BDI) scores, they were assigned to either a high BDI (hBDI, BDI > 13, N = 46) or a control (CTL, BDI < 7, N = 75) group. We analyzed spectral activity, theta–beta, and theta–gamma phase–amplitude coupling (PAC) of EEG recorded at rest before and after a learning task. Results: At baseline, compared to CTL, hBDI exhibited greater power in beta over fronto-parietal regions and in gamma over the right parieto-occipital area. At post task, power increased in all frequency ranges only in CTL. Theta–beta and theta–gamma PAC were greater in hBDI at baseline but not after the task. Conclusions: The lack of substantial post-task growth of beta power in depressed subjects likely represents power saturation due to greater baseline values. We speculate that inhibitory/excitatory imbalance, altered plasticity mechanisms, and energy dysregulation present in depression may contribute to this phenomenon. Full article
(This article belongs to the Section Neurobiology and Clinical Neuroscience)
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<p>Scalp topographies displaying the <span class="html-italic">t</span>-values for group comparisons (hBDI vs. CLT) before the task, at baseline for the original, oscillatory, and fractal components for each frequency band. White dots indicate electrodes with significant group differences after cluster correction for multiple comparisons.</p>
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<p>EEG Power-Law Exponent (PLE) for the hBDI group (orange) and CTL group (green) before (<b>A</b>) and after the task (<b>B</b>), with individual data points, box plots, and density plots to visualize data distribution. Topographic plots depict the <span class="html-italic">t</span>-values of cluster-based permutation statistics (right). Electrodes within significant clusters are represented as white dots.</p>
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<p>Group differences (hBDI vs. CTL) for theta–beta (<b>A</b>) and theta–gamma (<b>B</b>) PAC. Topographic plots depict the results of cluster-based permutation <span class="html-italic">t</span>-statistics. PRE, in the top line, represents the group comparison at baseline, before task performance. POST (bottom line) refers to group comparison after the task execution. White dots represent electrodes within significant clusters.</p>
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<p>Scalp topographical <span class="html-italic">t</span>-maps of group comparisons (hBDI vs. CLT) in the post-task resting-state EEG for the original, oscillatory, and fractal components. White dots indicate electrodes with significant group differences after cluster correction for multiple comparisons.</p>
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<p>Scalp topographical <span class="html-italic">t</span>-values maps for post-pre task comparisons (post-task vs. pre-task EEG) in the CTL (<b>A</b>) and hBDI (<b>B</b>) groups. Results for the original, oscillatory, and fractal components are presented for each frequency band. White dots indicate electrodes with significant group differences after cluster correction for multiple comparisons.</p>
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<p>Post-task/pre-task differences for theta–beta (<b>A</b>) and theta–gamma (<b>B</b>) PAC in the CTL (first line) and hBDI (bottom line) groups. Topographic plots depict the results of cluster-based permutation <span class="html-italic">t</span>-statistics. White dots represent electrodes within significant clusters.</p>
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10 pages, 1121 KiB  
Article
Subthreshold Cannabidiol Potentiates Levetiracetam in the Kainic Acid Model of Temporal Lobe Epilepsy: A Pilot Study
by Chiara Lucchi, Mattia Marcucci, Kawther Ameen Muhammed Saeed Aledresi, Anna-Maria Costa, Giuseppe Cannazza and Giuseppe Biagini
Pharmaceuticals 2024, 17(9), 1187; https://doi.org/10.3390/ph17091187 - 10 Sep 2024
Viewed by 168
Abstract
Refractoriness to antiseizure medications is still a major concern in the pharmacotherapy of epilepsy. For this reason, we decided to evaluate the combination of levetiracetam and cannabidiol, administered at a subthreshold dose, to limit the possible adverse effects of this phytocannabinoid. We administered [...] Read more.
Refractoriness to antiseizure medications is still a major concern in the pharmacotherapy of epilepsy. For this reason, we decided to evaluate the combination of levetiracetam and cannabidiol, administered at a subthreshold dose, to limit the possible adverse effects of this phytocannabinoid. We administered levetiracetam (300 mg/kg/day, via osmotic minipumps), cannabidiol (120 mg/kg/day, injected once a day subcutaneously), or their combination for one week in epileptic rats. Saline-treated epileptic rats were the control group. Animals were monitored with video electroencephalography the week before and after the treatment. No changes were found in the controls. Levetiracetam did not significantly reduce the total seizure number or the overall seizure duration. Still, the overall number of seizures (p < 0.001, Duncan’s new multiple range test) and their total duration (p < 0.01) increased in the week following treatment withdrawal. Cannabidiol did not change seizures when administered as a single drug. Instead, levetiracetam combined with cannabidiol resulted in a significant reduction in the overall number and duration of seizures (p < 0.05), when comparing values measured during treatment with both pre- and post-treatment values. These findings depended on changes in convulsive seizures, while non-convulsive seizures were stable. These results suggest that cannabidiol determined a remarkable potentiation of levetiracetam antiseizure effects at a subthreshold dose. Full article
(This article belongs to the Special Issue Targeted Therapies for Epilepsy)
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<p>Weekly occurrence of spontaneous recurrent seizures (SRSs) in epileptic rats treated with saline subcutaneously (s.c., via osmotic minipumps [<a href="#B15-pharmaceuticals-17-01187" class="html-bibr">15</a>]) (<b>a</b>), saline (s.c.) and levetiracetam (LEV, s.c. via osmotic minipumps [<a href="#B15-pharmaceuticals-17-01187" class="html-bibr">15</a>]) (<b>b</b>), saline (s.c., via osmotic minipumps) and cannabidiol (CBD, 120 mg/kg s.c. [<a href="#B13-pharmaceuticals-17-01187" class="html-bibr">13</a>]) (<b>c</b>), and cannabidiol + levetiracetam (CBD + LEV; CBD s.c., LEV s.c. via osmotic minipumps) (<b>d</b>). In (<b>a</b>), the overall number of seizures in rats receiving saline treatment did not change across treatment conditions. In (<b>b</b>), after the removal of minipumps, rats treated with levetiracetam presented a significant increase (** <span class="html-italic">p</span> &lt; 0.01) in the occurrence of all SRSs. Conversely, cannabidiol treatment (<b>c</b>) did not affect the total number of SRSs during the different treatment conditions. In (<b>d</b>), the combined treatment of LEV and CBD significantly reduced (° <span class="html-italic">p</span> &lt; 0.05) the number of total SRSs in comparison to the pretreatment period. Subsequently, the rapid stop-removal of the treatment led to a significant increase (* <span class="html-italic">p</span> &lt; 0.05) in the weekly frequency of SRSs in the post-treatment phase. ** <span class="html-italic">p</span> &lt; 0.01, Duncan’s method, TREAT vs. POST in LEV; ° <span class="html-italic">p</span> &lt; 0.05 PRE vs. TREAT in CBD + LEV, * <span class="html-italic">p</span> &lt; 0.05 TREAT vs. POST in CBD + LEV, Duncan’s new multiple range test.</p>
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<p>Weekly occurrence of nonconvulsive (stages, st. 0–3 of the Racine’s scale [<a href="#B16-pharmaceuticals-17-01187" class="html-bibr">16</a>]) and convulsive (st. 4–5) spontaneous recurrent seizures (SRSs) in epileptic rats treated with levetiracetam (LEV s.c., via osmotic minipumps) (<b>a</b>,<b>b</b>) and cannabidiol + levetiracetam (CBD + LEV; CBD s.c., LEV s.c. via osmotic minipumps) (<b>c</b>,<b>d</b>). As shown in (<b>a</b>,<b>b</b>), levetiracetam did not significantly reduce the number of both nonconvulsive and convulsive seizures. The removal of minipumps (<b>b</b>) resulted in a significant increase (*** <span class="html-italic">p</span> &lt; 0.01) in the occurrence of convulsive tonic–clonic seizures in comparison to the treatment period. In (<b>d</b>), the combined administration of cannabidiol and levetiracetam significantly affected (° <span class="html-italic">p</span> &lt; 0.05) the number of convulsive seizures, in comparison to the pretreatment period. Moreover, the weekly frequency of tonic–clonic SRSs increased significantly (* <span class="html-italic">p</span> &lt; 0.05) in the post-treatment phase as a result of the treatment’s quick stop-removal. The number of nonconvulsive seizures remained unchanged. *** <span class="html-italic">p</span> &lt; 0.01, Duncan’s new multiple range test (MRT), TREAT vs. POST in LEV; ° <span class="html-italic">p</span> &lt; 0.05 PRE vs. TREAT in CBD + LEV, * <span class="html-italic">p</span> &lt; 0.05 TREAT vs. POST in CBD + LEV; MRT.</p>
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<p>Overall duration of spontaneous recurrent seizures (SRSs) in epileptic rats treated with saline subcutaneously (s.c., via osmotic minipumps [<a href="#B14-pharmaceuticals-17-01187" class="html-bibr">14</a>]) (<b>a</b>), saline (s.c.) and levetiracetam (LEV, s.c. via osmotic minipumps [<a href="#B15-pharmaceuticals-17-01187" class="html-bibr">15</a>]) (<b>b</b>), saline (s.c., via osmotic minipumps) and cannabidiol (CBD, 120 mg/kg s.c. [<a href="#B12-pharmaceuticals-17-01187" class="html-bibr">12</a>]) (<b>c</b>), and cannabidiol + levetiracetam (CBD + LEV; CBD s.c., LEV s.c. via osmotic minipumps) (<b>d</b>). In (<b>a</b>), note that the total seizure duration in rats receiving saline treatment did not change across treatment conditions. In (<b>b</b>), the rapid discontinuation of levetiracetam administration induced a significant increase (** <span class="html-italic">p</span> &lt; 0.01) in the overall duration of SRSs, measured during the week. Cannabidiol treatment (<b>c</b>) reduced the total seizure duration without reaching a statistical difference. In (<b>d</b>), cannabidiol and levetiracetam combination resulted in a beneficial effect on the total duration of SRSs, when compared to pretreatment period (° <span class="html-italic">p</span> &lt; 0.05). The cessation of combined treatment subsequently led to a significant increase (* <span class="html-italic">p</span> &lt; 0.05) in the overall duration of the SRSs. ** <span class="html-italic">p</span> &lt; 0.01, Duncan’s new multiple range test (MRT), TREAT vs. POST in LEV; ° <span class="html-italic">p</span> &lt; 0.05 PRE vs. TREAT in CBD + LEV, * <span class="html-italic">p</span> &lt; 0.05 TREAT vs. POST in CBD + LEV, MRT.</p>
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<p>Mean duration of spontaneous recurrent seizures (SRSs) in epileptic rats treated with saline subcutaneously (s.c., via osmotic minipumps) (<b>a</b>), saline (s.c.) and levetiracetam (LEV, s.c. via osmotic minipumps [<a href="#B15-pharmaceuticals-17-01187" class="html-bibr">15</a>]) (<b>b</b>), saline (s.c., via osmotic minipumps) and cannabidiol (CBD, 120 mg/kg s.c. [<a href="#B13-pharmaceuticals-17-01187" class="html-bibr">13</a>]) (<b>c</b>), and cannabidiol + levetiracetam (CBD + LEV; CBD s.c., LEV s.c. via osmotic minipumps) (<b>d</b>). A reduction in the mean duration of SRSs was evident in all groups of treatment with minipumps, but the two-way (treatment × time interval) repeated measures ANOVA did not reveal any statistical differences.</p>
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12 pages, 1198 KiB  
Article
Visual Deprivation’s Impact on Dynamic Posture Control of Trunk: A Comprehensive Sensing Information Analysis of Neurophysiological Mechanisms
by Anna Sasaki, Honoka Nagae, Yukio Furusaka, Kei Yasukawa, Hayato Shigetoh, Takayuki Kodama and Junya Miyazaki
Sensors 2024, 24(17), 5849; https://doi.org/10.3390/s24175849 - 9 Sep 2024
Viewed by 196
Abstract
Visual information affects static postural control, but how it affects dynamic postural control still needs to be fully understood. This study investigated the effect of proprioception weighting, influenced by the presence or absence of visual information, on dynamic posture control during voluntary trunk [...] Read more.
Visual information affects static postural control, but how it affects dynamic postural control still needs to be fully understood. This study investigated the effect of proprioception weighting, influenced by the presence or absence of visual information, on dynamic posture control during voluntary trunk movements. We recorded trunk movement angle and angular velocity, center of pressure (COP), electromyographic, and electroencephalography signals from 35 healthy young adults performing a standing trunk flexion–extension task under two conditions (Vision and No-Vision). A random forest analysis identified the 10 most important variables for classifying the conditions, followed by a Wilcoxon signed-rank test. The results showed lower maximum forward COP displacement and trunk flexion angle, and faster maximum flexion angular velocity in the No-Vision condition. Additionally, the alpha/beta ratio of the POz during the switch phase was higher in the No-Vision condition. These findings suggest that visual deprivation affects cognitive- and sensory-integration-related brain regions during movement phases, indicating that sensory re-weighting due to visual deprivation impacts motor control. The effects of visual deprivation on motor control may be used for evaluation and therapeutic interventions in the future. Full article
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<p>Experimental Environment Setup: (<b>A</b>) Research equipment and attachment locations. The two green rectangles represent the two arms of the electronic goniometer. (<b>B</b>) Condition setup. In the No-Vision condition, participants wore an eye mask to deprive vision. (<b>C</b>) The curves are from one repetition of one subject’s movement tasks and a time series of measurement indicators. The APA, flexion, switch, and extension phases are classified based on angular velocity and COP-AP baseline values to analyze each measurement indicator. EEG: electroencephalography; EMG: electromyography (Fp1: left side prefrontal, Fp2: right side prefrontal, Cz: center of the parietal, POz: back center of the parietal); RA: rectus abdominis; ES: erector spinae; COP: center of pressure; AP: anterior–posterior; APA: anticipatory postural adjustments.</p>
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<p>Variable importance for classifying conditions with and without visual information. Max: maximum; APA: anticipatory postural adjustments; COP: center of pressure; RA: rectus abdominis; ES: erector spinae; CCI: co-contraction index.</p>
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<p>Scalograms of EEG for each channel in the Vision and No-vision conditions. The scalograms are from one repetition of one subject’s movement tasks. The Fp panels indicate the average of Fp1 and Fp2. The closer the color is to red, the higher the power value in the frequency band; the closer to blue, the lower the power value in the frequency band. Black lines in the figure indicate APA offset (flexion onset), flexion offset, and extension onset, from left to right.</p>
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12 pages, 1345 KiB  
Case Report
Neuropsychological Characteristics and Quantitative Electroencephalography in Skogholt’s Disease—A Rare Neurodegenerative Disease in a Norwegian Family
by Knut A. Hestad, Jan O. Aaseth and Juri D. Kropotov
Brain Sci. 2024, 14(9), 905; https://doi.org/10.3390/brainsci14090905 - 6 Sep 2024
Viewed by 315
Abstract
Members of three generations of a Norwegian family (N = 9) with a rare demyelinating disease were studied. Neuropsychological testing was performed using the Mini Mental Status Examination (MMSE), Wechsler Intelligence Scale-III (WAIS-III), and Hopkins Verbal Learning Test-Revised (HVLT-R). EEGs were recorded with [...] Read more.
Members of three generations of a Norwegian family (N = 9) with a rare demyelinating disease were studied. Neuropsychological testing was performed using the Mini Mental Status Examination (MMSE), Wechsler Intelligence Scale-III (WAIS-III), and Hopkins Verbal Learning Test-Revised (HVLT-R). EEGs were recorded with grand averaging spectrograms and event-related potentials (ERPs) in rest and cued GO/NOGO task conditions. The results were within the normal range on the MMSE. Full-scale WAIS-III results were in the range of 69–113, with lower scores in verbal understanding than in perceptual organization, and low scores also in indications of working memory and processing speed difficulties. The HVLT-R showed impairment of both immediate and delayed recall. Quantitative EEG showed an increase in low alpha (around 7.5 Hz) activity in the temporofrontal areas, mostly on the left side. There was a deviation in the late (>300 ms) component in response to the NOGO stimuli. A strong correlation (r = 0.78, p = 0.01) between the Hopkins Verbal Learning Test (delayed recall) and the amplitude of the NOGO ERP component was observed. The EEG spectra showed deviations from the healthy controls, especially at frontotemporal deviations. Deviations in the ERP component of the NOGO trials were related to delayed recall in the Hopkins Verbal learning test. Full article
(This article belongs to the Special Issue Genetics of Neurodegenerative Diseases: Retrospect and Prospect)
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<p>EEG power vs. frequency plots for three electrodes (F7, T3, and T5) for the patient group (<b>left</b>) and healthy controls (<b>right</b>) of the corresponding age selected from the HBI database (N = 50) with the maps taken at 7.6 and 9.0 Hz, respectively. EEG was recorded during 20 min of the cued GO/NOGO task. Note the asymmetrical lower alpha power at the left frontal–temporal areas of the patient group. <span class="html-italic">Y</span>-axis—EEG power in µV<sup>2</sup>. <span class="html-italic">X</span>-axis—frequency in Hz from 0 to 30 Hz.</p>
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<p>The difference waves (patient group–healthy group) of EEG spectra for three conditions: (<b>left column</b>)—eyes open, (<b>middle column</b>)—eyes closed, and (<b>right column</b>)—cued GO/NOGO task. <span class="html-italic">Y</span>-axis—relative EEG power in %. <span class="html-italic">X</span>-axis—frequency in Hz from 0 to 30 Hz. Vertical bars below the curves indicate the confidence level of statistical significance of the difference (small bars—<span class="html-italic">p</span> &lt; 0.05, larger bars—<span class="html-italic">p</span> &lt; 0.01).</p>
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<p>(<b>Top</b>): ERPs for NOGO trials (<b>left</b>), GO trials (<b>middle</b>), and Ignore trials (<b>right</b>) averaged over patients (thick lines) and healthy controls (thin lines) for Cz, Pz, and O1 electrodes, respectively. (<b>Bottom</b>): Maps of ERPS in NOGO trials (at 340 ms), GO trials (at 330 ms), and Ignore trials (at 100 ms) for the patient and healthy groups. On the plots: Y- axis—averaged potential in µV. X-axis—time after stimulus onset, vertical dotted line—stimulus offset.</p>
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<p>Amplitude of NOGO ERP component at Cz for each patient against T-scores for delayed recall in Hopkins Verbal Learning test-revised. Each patient represented with a black dot.</p>
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18 pages, 3355 KiB  
Article
Improved Dipole Source Localization from Simultaneous MEG-EEG Data by Combining a Global Optimization Algorithm with a Local Parameter Search: A Brain Phantom Study
by Subrat Bastola, Saeed Jahromi, Rupesh Chikara, Steven M. Stufflebeam, Mark P. Ottensmeyer, Gianluca De Novi, Christos Papadelis and George Alexandrakis
Bioengineering 2024, 11(9), 897; https://doi.org/10.3390/bioengineering11090897 - 6 Sep 2024
Viewed by 449
Abstract
Dipole localization, a fundamental challenge in electromagnetic source imaging, inherently constitutes an optimization problem aimed at solving the inverse problem of electric current source estimation within the human brain. The accuracy of dipole localization algorithms is contingent upon the complexity of the forward [...] Read more.
Dipole localization, a fundamental challenge in electromagnetic source imaging, inherently constitutes an optimization problem aimed at solving the inverse problem of electric current source estimation within the human brain. The accuracy of dipole localization algorithms is contingent upon the complexity of the forward model, often referred to as the head model, and the signal-to-noise ratio (SNR) of measurements. In scenarios characterized by low SNR, often corresponding to deep-seated sources, existing optimization techniques struggle to converge to global minima, thereby leading to the localization of dipoles at erroneous positions, far from their true locations. This study presents a novel hybrid algorithm that combines simulated annealing with the traditional quasi-Newton optimization method, tailored to address the inherent limitations of dipole localization under low-SNR conditions. Using a realistic head model for both electroencephalography (EEG) and magnetoencephalography (MEG), it is demonstrated that this novel hybrid algorithm enables significant improvements of up to 45% in dipole localization accuracy compared to the often-used dipole scanning and gradient descent techniques. Localization improvements are not only found for single dipoles but also in two-dipole-source scenarios, where sources are proximal to each other. The novel methodology presented in this work could be useful in various applications of clinical neuroimaging, particularly in cases where recordings are noisy or sources are located deep within the brain. Full article
(This article belongs to the Section Biosignal Processing)
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Graphical abstract

Graphical abstract
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<p>(<b>a</b>–<b>c</b>) Coronal, sagittal, axial views, respectively, of the dipole sources inside the phantom model. Green represents the sources on the left hemisphere and red represents the sources in the right hemisphere, six per hemisphere. (<b>d</b>,<b>e</b>) EEG and MEG sensor arrangements, respectively, for the phantom measurements. (<b>f</b>) A realistic BEM-based head model for projecting the dipole sources onto the scalp surface.</p>
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<p>(<b>a</b>–<b>c</b>) Coronal, sagittal, axial views, respectively, of the simulated sources inside the phantom model with blue spheres representing the locations of the simulated sources.</p>
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<p>Goodness of fit (GOF) for the localization of an EEG dipole source as a function of source location across an axial plane of the phantom ((<b>a</b>) z<sub>1</sub> = 33 mm, (<b>b</b>) z<sub>2</sub> = 29 mm).</p>
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<p>Comparison of the three localization techniques, hybrid-SA, DS, and GD, for (<b>a</b>) localization error versus SNR, and (<b>b</b>) localization errors versus dipole depth, when using EEG data only. Simulated and experimental data are plotted together, but with different symbols. (<span style="color:red">*</span> representing statistically significant difference between hybrid-SA and GD, <span style="color:#538135">*</span> representing statistically significant difference between hybrid-SA and DS, for <span class="html-italic">p</span> &lt; 0.05).</p>
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<p>Comparison of the three localization techniques, hybrid-SA, DS, and GD, for (<b>a</b>) localization error versus SNR, and (<b>b</b>) localization errors versus dipole depth, when using MEG data only. Simulated and experimental data are plotted together, but with different symbols. (<span style="color:#C00000">*</span> representing statistically significant difference between hybrid-SA and GD, <span style="color:#538135">*</span> representing statistically significant difference between hybrid-SA and DS, <span style="color:#FFC000">*</span> representing statistically significant difference between GD and DS for <span class="html-italic">p</span> &lt; 0.05).</p>
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<p>Comparison of the three localization techniques, hybrid-SA, DS, and GD, for (<b>a</b>) localization error versus SNR, and (<b>b</b>) localization errors versus dipole depth, when using the combined MEG-EEG data. Simulated and experimental data are plotted together, but with different symbols. (<span style="color:red">*</span> representing statistically significant difference between hybrid-SA and GD, <span style="color:#538135">*</span> representing statistically significant difference between hybrid-SA and DS, for <span class="html-italic">p</span> &lt; 0.05).</p>
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<p>Comparison between the three localization techniques, hybrid-SA, DS, and GD for the simultaneous localization two dipoles for (<b>a</b>) EEG-only, (<b>b</b>) MEG-only, and (<b>c</b>) combined EEG-MEG data, versus SNR. (<span style="color:red">*</span> representing statistically significant difference between hybrid-SA and GD, <span style="color:#538135">*</span> representing statistically significant difference between hybrid-SA and DS, for <span class="html-italic">p</span> &lt; 0.05).</p>
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<p>Comparison between the three algorithms, hybrid-SA, DS, and GD for (<b>a</b>) dipole phi (azimuthal) angle error, and (<b>b</b>) dipole theta (polar) angle error versus SNR. (<span style="color:red">*</span> representing statistically significant difference between hybrid-SA and GD, <span style="color:#538135">*</span> representing statistically significant difference between hybrid-SA and DS, for <span class="html-italic">p</span> &lt; 0.05).</p>
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21 pages, 5042 KiB  
Article
Low-Cost Dynamometer for Measuring and Regulating Wrist Extension and Flexion Motor Tasks in Electroencephalography Experiments
by Abdul-Khaaliq Mohamed, Muhammed Aswat and Vered Aharonson
Sensors 2024, 24(17), 5801; https://doi.org/10.3390/s24175801 - 6 Sep 2024
Viewed by 237
Abstract
A brain–computer interface could control a bionic hand by interpreting electroencephalographic (EEG) signals associated with wrist extension (WE) and wrist flexion (WF) movements. Misinterpretations of the EEG may stem from variations in the force, speed and range of these movements. To address this, [...] Read more.
A brain–computer interface could control a bionic hand by interpreting electroencephalographic (EEG) signals associated with wrist extension (WE) and wrist flexion (WF) movements. Misinterpretations of the EEG may stem from variations in the force, speed and range of these movements. To address this, we designed, constructed and tested a novel dynamometer, the IsoReg, which regulates WE and WF movements during EEG recording experiments. The IsoReg restricts hand movements to isometric WE and WF, controlling their speed and range of motion. It measures movement force using a dual-load cell system that calculates the percentage of maximum voluntary contraction and displays it to help users control movement force. Linearity and measurement accuracy were tested, and the IsoReg’s performance was evaluated under typical EEG experimental conditions with 14 participants. The IsoReg demonstrated consistent linearity between applied and measured forces across the required force range, with a mean accuracy of 97% across all participants. The visual force gauge provided normalised force measurements with a mean accuracy exceeding 98.66% across all participants. All participants successfully controlled the motor tasks at the correct relative forces (with a mean accuracy of 89.90%) using the IsoReg, eliminating the impact of inherent force differences between typical WE and WF movements on the EEG analysis. The IsoReg offers a low-cost method for measuring and regulating movements in future neuromuscular studies, potentially leading to improved neural signal interpretation. Full article
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<p>Typical dimensions of the human hand [<a href="#B30-sensors-24-05801" class="html-bibr">30</a>,<a href="#B31-sensors-24-05801" class="html-bibr">31</a>,<a href="#B32-sensors-24-05801" class="html-bibr">32</a>,<a href="#B33-sensors-24-05801" class="html-bibr">33</a>,<a href="#B34-sensors-24-05801" class="html-bibr">34</a>,<a href="#B35-sensors-24-05801" class="html-bibr">35</a>].</p>
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<p>Major components and main measurements of the IsoReg shown from different views. (<b>a</b>) shows the top view, (<b>b</b>) shows the view of the left side and (<b>c</b>) shows the view from the underside/bottom of the IsoReg. (<b>d</b>) describes the labels A–U.</p>
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<p>Block diagram of force measurement system.</p>
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<p>Demonstrating the mechanism of force measurement using RH WF as an example.</p>
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<p>Circuit diagram of IsoReg electronics.</p>
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<p>Third and main software routine to capture, calculate and display MVC-normalised real-time force data.</p>
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<p>Second software routine for calculating the zero-force-offset values for each participant’s hand.</p>
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<p>First software routine for calculating the WE and WF MVCs for each participant’s hand.</p>
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<p>The experimental setup for Test 1 and Test 2 for the right cylindrical rod. The left cylindrical rod was tested in a similar manner.</p>
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<p>Depictions of how a participant was seated in the lab with all the surrounding equipment for EEG recording. (<b>a</b>) shows the view from the side. (<b>b</b>) shows the view from the front. (<b>c</b>) shows the top view of the hand strapped to the base of the IsoReg. (<b>d</b>) shows the front view of a seated participant, showing the position of the shoulders and upper arm.</p>
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<p>Timing diagram of a single trial and the related changes in MVC-normalised wrist force. Visual cues are shown in orange text. During S2, the participant tried to obtain the relative force of either WE or WF up to 15% as fast as possible. During S3, the participant tried to sustain the isometric movement at 15%, but maintaining a relative force between 13% and 17% was deemed acceptable.</p>
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<p>Testing method applied to determine the degree of force normalisation. <span class="html-italic">F<sub>N</sub></span>(<span class="html-italic">t</span>) for participant 1 for three repetitions of WE with the RH is shown as an example (blue line). Ideally, all <span class="html-italic">F<sub>N</sub></span> values during the periods of S3 (green strips) should lie between the dotted green lines. This method was used for all RH WE and WF repetitions and for all LH WE and WF repetitions.</p>
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<p>The measured forces vs. the force applied for the right cylindrical force rod (<b>a</b>) and the left cylindrical force rod (<b>b</b>).</p>
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<p>Picture 1 of IsoReg.</p>
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<p>Picture 2 of IsoReg.</p>
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22 pages, 3614 KiB  
Article
Tai Chi Practice Buffers Aging Effects in Functional Brain Connectivity
by Jonathan Cerna, Prakhar Gupta, Maxine He, Liran Ziegelman, Yang Hu and Manuel E. Hernandez
Brain Sci. 2024, 14(9), 901; https://doi.org/10.3390/brainsci14090901 - 6 Sep 2024
Viewed by 575
Abstract
Tai Chi (TC) practice has been shown to improve both cognitive and physical function in older adults. However, the neural mechanisms underlying the benefits of TC remain unclear. Our primary aims are to explore whether distinct age-related and TC-practice-related relationships can be identified [...] Read more.
Tai Chi (TC) practice has been shown to improve both cognitive and physical function in older adults. However, the neural mechanisms underlying the benefits of TC remain unclear. Our primary aims are to explore whether distinct age-related and TC-practice-related relationships can be identified with respect to either temporal or spatial (within/between-network connectivity) differences. This cross-sectional study examined recurrent neural network dynamics, employing an adaptive, data-driven thresholding approach to source-localized resting-state EEG data in order to identify meaningful connections across time-varying graphs, using both temporal and spatial features derived from a hidden Markov model (HMM). Mann–Whitney U tests assessed between-group differences in temporal and spatial features by age and TC practice using either healthy younger adult controls (YACs, n = 15), healthy older adult controls (OACs, n = 15), or Tai Chi older adult practitioners (TCOAs, n = 15). Our results showed that aging is associated with decreased within-network and between-network functional connectivity (FC) across most brain networks. Conversely, TC practice appears to mitigate these age-related declines, showing increased FC within and between networks in older adults who practice TC compared to non-practicing older adults. These findings suggest that TC practice may abate age-related declines in neural network efficiency and stability, highlighting its potential as a non-pharmacological intervention for promoting healthy brain aging. This study furthers the triple-network model, showing that a balancing and reorientation of attention might be engaged not only through higher-order and top-down mechanisms (i.e., FPN/DAN) but also via the coupling of bottom-up, sensory–motor (i.e., SMN/VIN) networks. Full article
(This article belongs to the Special Issue Advances of AI in Neuroimaging)
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<p>A summary of the processing pipeline used. Panel (<b>A</b>) depicts the process through which raw data were pre-processed and prepared for source localization; Panel (<b>B</b>) displays the MRI template used for source localization, and it summarizes the processes through which the EEG signal underwent source reconstruction/localization; Panel (<b>C</b>) shows a hidden Markov model from which temporal and spatial features were extracted. WN = within network; BN = between network; FC = functional connectivity.</p>
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<p>Thresholded functional connectivity matrices for younger adult controls (YACs), older adult controls (OACs), and Tai Chi older adult practitioners (TCOAs). Red indicates positive correlations, and blue indicates negative correlations (z-scored values displayed). Compared to YACs, OACs show reduced negative correlations and increased positive correlations, indicating age-related declines in network specialization. TCOAs exhibit a pattern between YACs and OACs, suggesting that Tai Chi practice may help preserve functional connectivity, maintaining a more balanced network organization despite aging. Networks visualized include visual (VIN), somatomotor (SMN), dorsal attention (DAN), ventral attention (VAN), limbic (LIN), frontoparietal (FPN), and default mode network (DMN).</p>
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18 pages, 5224 KiB  
Article
Variational Mode Decomposition Analysis of Electroencephalograms during General Anesthesia: Using the Grey Wolf Optimizer to Determine Hyperparameters
by Kosuke Kushimoto, Yurie Obata, Tomomi Yamada, Mao Kinoshita, Koichi Akiyama and Teiji Sawa
Sensors 2024, 24(17), 5749; https://doi.org/10.3390/s24175749 - 4 Sep 2024
Viewed by 314
Abstract
Frequency analysis via electroencephalography (EEG) during general anesthesia is used to develop techniques for measuring anesthesia depth. Variational mode decomposition (VMD) enables mathematical optimization methods to decompose EEG signals into natural number intrinsic mode functions with distinct narrow bands. However, the analysis requires [...] Read more.
Frequency analysis via electroencephalography (EEG) during general anesthesia is used to develop techniques for measuring anesthesia depth. Variational mode decomposition (VMD) enables mathematical optimization methods to decompose EEG signals into natural number intrinsic mode functions with distinct narrow bands. However, the analysis requires the a priori determination of hyperparameters, including the decomposition number (K) and the penalty factor (PF). In the VMD analysis of EEGs derived from a noninterventional and noninvasive retrospective observational study, we adapted the grey wolf optimizer (GWO) to determine the K and PF hyperparameters of the VMD. As a metric for optimization, we calculated the envelope function of the IMF decomposed via the VMD method and used its envelope entropy as the fitness function. The K and PF values varied in each epoch, with one epoch being the analytical unit of EEG; however, the fitness values showed convergence at an early stage in the GWO algorithm. The K value was set to 2 to capture the α wave enhancement observed during the maintenance phase of general anesthesia in intrinsic mode function 2 (IMF-2). This study suggests that using the GWO to optimize VMD hyperparameters enables the construction of a robust analytical model for examining the EEG frequency characteristics involved in the effects of general anesthesia. Full article
(This article belongs to the Section Biomedical Sensors)
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<p>Flowchart of grey wolf optimization (GWO) for variational mode decomposition (VMD).</p>
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<p>Position updating algorithm for the wolves in the grey wolf optimizer. Three leader/subleader wolves, α, β, and δ, surround the prey, and the position of the prey is inferred from the positions of these three leader wolves, assuming that they surround it. Vectors A and C are coefficient vectors and are calculated for each coordinate. The other wolves in the pack, ω, locate the leader wolves’ positions, which are initially adjusted with a coefficient C and then gradually adjusted in each loop to better approximate the leader wolves’ positions. A random coefficient D is then applied to their distance, allowing them to approach the leader wolves within a range of −1 to +1. As a result, wolves that are closer to the prey than the leader wolves may replace them as the new leaders, enabling the pack to surround the prey more closely. The algorithm specifies three leader wolves and divides the obtained average position by the number of leaders. If the positions of α, β, and δ are 6, 8, and 3, respectively, then the position of the prey would be the midpoint, calculated as (6 + 8 + 3)/3 = 5.7, and the integer 5 becomes the updated position for the prey. The new position of the ω<sub>1</sub> wolf is adjusted according to the leaders’ positions, taking into account its current position.</p>
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<p>The relationship between the hyperparameters K and PF of VMD and the envelope entropy of each IMF. VMD is applied to a synthetic cosine wave composed of three known frequency components (2, 12, and 36 Hz). <math display="inline"><semantics> <mrow> <mi>y</mi> <mo>=</mo> <mi mathvariant="normal">c</mi> <mi mathvariant="normal">o</mi> <mi mathvariant="normal">s</mi> <mo>(</mo> <mn>2</mn> <mo>×</mo> <mn>2</mn> <mi mathvariant="sans-serif">π</mi> <mi>t</mi> <mo>)</mo> <mo>+</mo> <mstyle scriptlevel="0" displaystyle="true"> <mfrac> <mrow> <mn>1</mn> </mrow> <mrow> <mn>2</mn> </mrow> </mfrac> </mstyle> <mi mathvariant="normal">c</mi> <mi mathvariant="normal">o</mi> <mi mathvariant="normal">s</mi> <mo>(</mo> <mn>12</mn> <mo>×</mo> <mn>2</mn> <mi mathvariant="sans-serif">π</mi> <mi>t</mi> <mo>)</mo> <mo>+</mo> <mstyle scriptlevel="0" displaystyle="true"> <mfrac> <mrow> <mn>1</mn> </mrow> <mrow> <mn>4</mn> </mrow> </mfrac> </mstyle> <mi mathvariant="normal">c</mi> <mi mathvariant="normal">o</mi> <mi mathvariant="normal">s</mi> <mo>(</mo> <mn>36</mn> <mo>×</mo> <mn>2</mn> <mi mathvariant="sans-serif">π</mi> <mi>t</mi> <mo>)</mo> </mrow> </semantics></math> (1024 data points). (<b>A</b>) The synthetic cosine wave, its envelope function, and the envelope entropy. (<b>B</b>) The three cosine waves, their envelope functions, and envelope entropies. (<b>C</b>) Decomposition of the synthetic cosine wave into three IMFs using the GWO algorithm with optimized values of K = 3 and PF = 4984, and calculation of each IMF’s envelope function and envelope entropy. (<b>D</b>) Application of VMD with K = 3 and PF = 10, and determination of IMFs, their envelope functions, and envelope entropies. (<b>E</b>) Application of VMD with K = 3 and PF = 70, and analysis of IMFs and their envelope functions, and envelope entropies. (<b>F</b>) Application of VMD with K = 2 and PF = 4984, and evaluation of the IMFs and their envelope functions, and envelope entropy. (<b>G</b>) Application of VMD with K = 4 and PF = 4984, and analysis of the IMFs and their envelope functions, and envelope entropies. K: decomposition number; PF: penalty factor; fitness: fitness value of VMD = the maximum envelope entropy of the IMF.</p>
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<p>Optimization process for the hyperparameters K and PF of VMD using the GWO algorithm. Twenty wolves and 20 optimization loops, observed over one epoch (8 s, 1024 data points) of EEG during the maintenance phase of GA (obtained through continuous intravenous propofol administration) in three patients. This process involved monitoring the position of each wolf during two-dimensional wolf hunting. (<b>A</b>) EEG (8 s). (<b>B</b>) The optimization of K. (<b>C</b>) The optimization of PF. (<b>D</b>) The optimization of fitness. α wolf: red line; β wolf: orange line; δ wolf: yellow line; ω wolves: black lines. K: decomposition number; PF: penalty factor; fitness: fitness value of VMD = the maximum envelope entropy of the IMF.</p>
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<p>Grey wolf optimization in the VMD of EEGs obtained from three patients of GA induced by continuous intravenous propofol. (<b>A</b>) The optimal solutions for K and PF were determined through fitness function optimization using the GWO algorithm. Twenty wolves and 20 optimization loops for all 73 epochs. Each epoch lasted for 8 s (128 Hz, 1024 data points) of the 10-minute period before and after awakening from GA. Additionally, K was set in the range of 2 to 6 (in increments of 1), and the PF values ranged from 10 to 5000 (in increments of 10). (<b>B</b>) The spectrogram for the 10-minute interval was obtained using the multitaper method and is displayed in <a href="#sensors-24-05749-f004" class="html-fig">Figure 4</a>B. (<b>C</b>) Using VMD with K = 2 or 3 and PF = 2000, the signal was decomposed into IMFs and a Hilbert spectrogram was obtained. The gradient color bar shows the relative power value of the signal. K: decomposition number; PF: penalty factor; fitness: fitness value of VMD = the maximum envelope entropy of the IMF.</p>
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<p>Analysis of 8 s EEG segments during the (1) maintenance, (2) transition, and (3) emergence phases of general anesthesia induced by propofol. (<b>A</b>) Original EEG (8 s, 128 Hz, 1024 data points). (<b>B</b>) The power spectrum obtained through Fourier analysis. (<b>C</b>) Hilbert spectrum. To optimize K and PF, GWO analysis was conducted with 20 wolves, 20 repetitions, and settings of K = 2 to 6 (in increments of 1) and PF = 10 to 5000 (in increments of 10). (<b>D</b>) Decomposed intrinsic mode functions (IMFs). (<b>E</b>) The power spectrogram for a 64 s period was determined using the multitaper method. The first 8 s were the subject of the VMD analysis. The gradient color bar shows the relative power value of the signal. K: decomposition number; PF: penalty factor; fitness: fitness value of VMD = the maximum envelope entropy of the IMF.</p>
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12 pages, 3240 KiB  
Article
Physiological Responses Related to Sitting Comfort Due to Changes in Seat Parameters
by Jongseong Gwak, Kazuyoshi Arata, Takumi Yamakawa, Hideo Tobata, Motoki Shino and Yoshihiro Suda
Appl. Sci. 2024, 14(17), 7870; https://doi.org/10.3390/app14177870 - 4 Sep 2024
Viewed by 335
Abstract
The design of vehicle cabin seats is crucial in transportation, as it directly affects the safety and comfort of both drivers and passengers. To design seat parameters that enhance sitting comfort, a quantitative evaluation of sitting comfort involving an understanding of users’ physiological [...] Read more.
The design of vehicle cabin seats is crucial in transportation, as it directly affects the safety and comfort of both drivers and passengers. To design seat parameters that enhance sitting comfort, a quantitative evaluation of sitting comfort involving an understanding of users’ physiological responses is necessary. This study aimed to assess users’ physiological responses to relaxation induced by changes in seat parameters using electroencephalography and electrocardiography. We examined the physiological responses and subjective evaluations of relaxation in fifteen participants, focusing on the effects of reclining, ottoman, and slab. The results demonstrated an improvement in the subjective level of relaxation with changes in all seat parameters set here. However, central nervous system responses and autonomic nervous system reactions varied based on alterations in posture angles and seat pressure distributions. This underscores the importance of physiological markers, encompassing indicators of autonomic and central nervous system responses, in evaluating relaxation in relation to changes in posture angles and seat pressure distribution. Full article
(This article belongs to the Special Issue Seating Comfort and Biomechanical Application)
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<p>The flow of the physiological response process during sitting. (Adapted from with permission from Ref. [<a href="#B19-applsci-14-07870" class="html-bibr">19</a>]. 2021, Elsevier).</p>
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<p>Experimental conditions of seat.</p>
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<p>Segmentation of the measurement area.</p>
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<p>An example of a visual analog scale to evaluate the feeling of relaxation (range of 0 to 1). If the participant marked a point with the red checkmark in the figure, the value of 0.67 is determined based on the ratio of the length on the scale from 0 to 1.</p>
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<p>Experimental procedure.</p>
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<p>An example of the process to calculate the difference in physiological indices: Xi indicates the value calculated from the measurement data in each trial, such as (<span class="html-italic">θ</span> + <span class="html-italic">α</span>)/<span class="html-italic">β</span>, the average of RRI, the value of LF/HF, or the subjective evaluation value of the relaxation, etc.</p>
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<p>Differences in peak pressure of backrest and seat pan in each part. The upper graph represents the results for the backrest, while the lower graph represents those for the seat pan. Asterisks indicate significances: ✝, *, **, and *** for <span class="html-italic">p</span> &lt; 0.10, 0.05, 0.01, and 0.001, respectively.</p>
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<p>Differences in contact area of backrest and seat pan in each part. The upper graph represents the results for the backrest, while the lower graph represents those for the seat pan. Asterisks indicate significances: ✝, *, **, and *** for <span class="html-italic">p</span> &lt; 0.10, 0.05, 0.01, and 0.001, respectively.</p>
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<p>Differences in relaxation value in each part. Asterisks indicate significances: ** for <span class="html-italic">p</span> &lt; 0.01.</p>
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63 pages, 37102 KiB  
Article
BLUE SABINO: Development of a BiLateral Upper-Limb Exoskeleton for Simultaneous Assessment of Biomechanical and Neuromuscular Output
by Christopher K. Bitikofer, Sebastian Rueda Parra, Rene Maura, Eric T. Wolbrecht and Joel C. Perry
Machines 2024, 12(9), 617; https://doi.org/10.3390/machines12090617 - 3 Sep 2024
Viewed by 425
Abstract
Arm and hand function play a critical role in the successful completion of everyday tasks. Lost function due to neurological impairment impacts millions of lives worldwide. Despite improvements in the ability to assess and rehabilitate arm deficits, knowledge about underlying sources of impairment [...] Read more.
Arm and hand function play a critical role in the successful completion of everyday tasks. Lost function due to neurological impairment impacts millions of lives worldwide. Despite improvements in the ability to assess and rehabilitate arm deficits, knowledge about underlying sources of impairment and related sequela remains limited. The comprehensive assessment of function requires the measurement of both biomechanics and neuromuscular contributors to performance during the completion of tasks that often use multiple joints and span three-dimensional workspaces. To our knowledge, the complexity of movement and diversity of measures required are beyond the capabilities of existing assessment systems. To bridge current gaps in assessment capability, a new exoskeleton instrument is developed with comprehensive bilateral assessment in mind. The development of the BiLateral Upper-limb Exoskeleton for Simultaneous Assessment of Biomechanical and Neuromuscular Output (BLUE SABINO) expands on prior iterations toward full-arm assessment during reach-and-grasp tasks through the development of a dual-arm and dual-hand system, with 9 active degrees of freedom per arm and 12 degrees of freedom (six active, six passive) per hand. Joints are powered by electric motors driven by a real-time control system with input from force and force/torque sensors located at all attachment points between the user and exoskeleton. Biosignals from electromyography and electroencephalography can be simultaneously measured to provide insight into neurological performance during unimanual or bimanual tasks involving arm reach and grasp. Design trade-offs achieve near-human performance in exoskeleton speed and strength, with positional measurement at the wrist having an error of less than 2 mm and supporting a range of motion approximately equivalent to the 50th-percentile human. The system adjustability in seat height, shoulder width, arm length, and orthosis width accommodate subjects from approximately the 5th-percentile female to the 95th-percentile male. Integration between precision actuation, human–robot-interaction force-torque sensing, and biosignal acquisition systems successfully provide the simultaneous measurement of human movement and neurological function. The bilateral design enables use with left- or right-side impairments as well as intra-subject performance comparisons. With the resulting instrument, the authors plan to investigate underlying neural and physiological correlates of arm function, impairment, learning, and recovery. Full article
(This article belongs to the Special Issue Advances in Assistive Robotics)
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<p>Bilateral exoskeleton predecessors to the BLUE SABINO: (<b>LEFT</b>) the EXO-UL7 and (<b>RIGHT</b>) the EXO-UL8.</p>
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<p>The BLUE SABINO instrument design is composed of a width-adjustable base, height-adjustable chair, length-adjustable upper arm and forearm segments, size-adjustable HRA attachments, remote-center four-bar mechanisms, two-DOF shoulder modules (PRISM), and optional 12-DOF hand modules.</p>
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<p>The kinematics of the human arm from the shoulder to the wrist can be represented by nine degrees of freedom. (<b>A</b>) Joints J<sub>1</sub>–J<sub>9</sub> and their corresponding anatomical axes (indicated by red dashed arrows oriented along the axes of rotation). (<b>B</b>) The kinematics of BLUE SABINO accommodate these nine degrees of freedom per arm (here, red arrows indicate the selected positive orientation of each joint’s rotation axis).</p>
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<p>BLUE SABINO rigid body links. The right-side rigid links of the right BLUE SABINO arm are shown in an exploded view ((<b>top left</b>) and (<b>center</b>)). Three of the links form movable assemblies composed of various parallel link mechanisms. The upper-arm (<b>top right</b>) and forearm (<b>bottom left</b>) remote-center mechanisms are composed of five primary links and an additional link for arm-length adjustment. PRISM (<b>bottom right</b>) is constructed with ten links, nine moving, and one stationary base.</p>
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<p>Anthropomorphic arm modeling for human–robot attachments (HRAs). Elliptical profiles for proximal and distal ends of the (<b>A</b>) upper arm and (<b>B</b>) forearm, and (<b>C</b>) lofted bend-U-shaped profile for the hand.</p>
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<p>Adjustable HRA orthotic designs and exploded assembly views. (<b>A</b>) The upper-arm orthosis. (<b>B</b>) The forearm orthosis. (<b>C</b>) The hand orthosis.</p>
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<p>Definition of manipulator points (q), axes (ω), and force sensor body frames.</p>
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<p>BLUE SABINO 18-DOF bilateral electromechanical system.</p>
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<p>Anticipated torque distributions per joint during ADL tasks (adapted from [<a href="#B75-machines-12-00617" class="html-bibr">75</a>]) used to select motors and gears for Joints 1–6.</p>
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<p>Layout for BLUE SABINO power and communication distribution.</p>
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<p>BLUE SABINO system startup sequence.</p>
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<p>Automatic and manual safety systems are integrated into the BLUE SABINO control architecture. Automatic systems provide fast and dependable safety responses, while the manual system allows the user and operator to stop the system manually, if needed.</p>
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<p>Admittance control scheme for BLUE SABINO. (1) User-applied forces are converted to human joint torques, <math display="inline"><semantics> <mrow> <msub> <mi mathvariant="sans-serif">τ</mi> <mi mathvariant="normal">h</mi> </msub> </mrow> </semantics></math>. (2) The admittance-control loop uses <math display="inline"><semantics> <mrow> <msub> <mi mathvariant="sans-serif">τ</mi> <mi mathvariant="normal">h</mi> </msub> </mrow> </semantics></math> to set target states. (3) Joint-level admittance models, including inertia, m<sub>a</sub> velocity damping, b<sub>v</sub>, and velocity error damping, <math display="inline"><semantics> <mrow> <msub> <mi mathvariant="normal">b</mi> <mrow> <mi>ve</mi> </mrow> </msub> </mrow> </semantics></math>, to set the inner-loop trajectory targets. (4) The trajectory-control loop computes proportional-derivative (PD) admittance-state tracking control torques, <math display="inline"><semantics> <mrow> <msub> <mi mathvariant="sans-serif">τ</mi> <mrow> <mi>PD</mi> </mrow> </msub> </mrow> </semantics></math>. (5) Model-based compensation for friction and gravity is added to the control torque, resulting in <math display="inline"><semantics> <mrow> <msub> <mi mathvariant="sans-serif">τ</mi> <mi mathvariant="normal">u</mi> </msub> </mrow> </semantics></math><math display="inline"><semantics> <mrow> <mo>.</mo> </mrow> </semantics></math> (6) Safety limits are enforced on human–robot interaction forces and joint range of motion. Control-state monitoring disables control torque throughput if any safety limits are exceeded or network/device faults are detected.</p>
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<p>System integration phases: (<b>A</b>) An initial two-DOF version supported elbow flexion/extension and forearm pronosupination. (<b>B</b>) The five-DOF version added three orthogonal joints to the shoulder. (<b>C</b>) The future 18-DOF bilateral version adds two joints at the wrist and two joints at the base of the shoulder.</p>
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<p>Motion-capture setup and predefined robot trajectories. (<b>Top</b>) The motion of the right-side seven-DOF BLUE SABINO arm is recorded simultaneously using a set of five Flex 13 IR motion-capture cameras. The cameras track the spatial positions of retroreflective markers on a special wrist-mounted motion-capture end-effector part. Optitrack software fits a rigid body in real time to the markerset to define the position and orientation of <math display="inline"><semantics> <mrow> <msub> <mi mathvariant="normal">P</mi> <mi mathvariant="normal">c</mi> </msub> </mrow> </semantics></math>. (<b>Bottom</b>) Three-dimensional views of the upper-arm section of BLUE SABINO (with orthosis components removed for clarity) are shown in relation to the predefined trajectories traced out for motion-capture experiments. The path is traced by the end-effector point <math display="inline"><semantics> <mrow> <msub> <mi mathvariant="normal">P</mi> <mi mathvariant="normal">c</mi> </msub> </mrow> </semantics></math>, whose initial position is indicated by the purple sphere and represents the centroid of the rigid body tracked by the motion-capture system.</p>
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<p>Sinusoid tracking inputs. The input position (red)- and velocity (blue)-state target signals are shown for an experiment using joint J<sub>5</sub>. The PD control torque <math display="inline"><semantics> <mrow> <msub> <mi mathvariant="sans-serif">τ</mi> <mrow> <mi>PD</mi> </mrow> </msub> </mrow> </semantics></math> (purple) and gravity/friction compensation torque <math display="inline"><semantics> <mrow> <msub> <mrow> <mo> </mo> <mover> <mi mathvariant="sans-serif">τ</mi> <mo stretchy="false">^</mo> </mover> </mrow> <mi mathvariant="normal">g</mi> </msub> <msub> <mrow> <mrow> <mo>+</mo> <mover> <mi mathvariant="sans-serif">τ</mi> <mo stretchy="false">^</mo> </mover> </mrow> </mrow> <mi mathvariant="normal">f</mi> </msub> </mrow> </semantics></math> (orange) are combined to generate the control input torque <math display="inline"><semantics> <mrow> <msub> <mi mathvariant="sans-serif">τ</mi> <mi mathvariant="normal">u</mi> </msub> </mrow> </semantics></math>.</p>
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<p>Logarithmic-ramping chirp-state inputs. The input position (red) and velocity (blue) state target signals, and the instantaneous command frequency (black) are shown for the first half of the experiment with chirp ramping up between 0.1 and 2 Hz.</p>
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<p>Biosignal acquisition validation task. The user begins the task with the fingertips touching the start target (tennis ball) located in the lower front part of the workspace. After hearing an audio cue, the user reaches to the second target (tennis ball) in the upper right part of their workspace, touches it, and returns their hand to touch the start target. An example trajectory for a single motion is illustrated in pink (<b>left</b>) in context of a virtual robot model. Pink arrows overlaid on the experimental setup (<b>center</b>) represent the movement from one target to the next and back. The transparent grey scatter (<b>right</b>) illustrates the area traveled in all repetitions on the same virtual robot charts.</p>
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<p>Topographical layout of EEG montage with reference electrode at A2 (blue) and ground at Afz (red).</p>
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<p>EMG montage and target muscles of the upper limb. Five EMG locations were placed on the skin over the shown target muscles. Bipolar electrodes were placed in pairs to enable differential measurement for improved noise rejection.</p>
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<p>BLUE SABINO exoskeleton: (<b>A</b>) Seven-DOF bilateral arm configuration with task display screen, operator console, control tower, and shoulder-width adjustment mechanism; (<b>B</b>) Experimental chair with footrest and control-enable footswitch; (<b>C</b>) Overhead and (<b>D</b>) front views with subject wearing right-hand three-fingered OTHER Hand module.</p>
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<p>OTHER Hand on the BLUE SABINO System.</p>
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<p>Animation of BLUE SABINO joints via kinematics-driven MATLAB script.</p>
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<p>Results of motion capture for a segment of the UofI I trajectory illustrate the high agreement between end-effector position measured by motion capture (blue) vs. encoder position (red). The absolute difference (purple) remains low, indicating that the robot is able to accurately measure its true position within 0.4 mm on average for the task.</p>
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<p>Mean tracking error per shape. The means of the distance error between the end-effector point <math display="inline"><semantics> <mrow> <msub> <mi>p</mi> <mi>c</mi> </msub> </mrow> </semantics></math> and the target position are shown on the left and center charts. The left chart shows errors reported by forward kinematics according to joint position measurements. The center chart shows the error according to motion capture. The rightmost chart displays mean absolute difference between the forward kinematic and motion capture measurements. Error bars display 95% confidence intervals of the means. Blue bars indicate statistics computed over individual actions (five repetitions each), while orange bars show statistics over all motions and repetitions (20 repetitions total).</p>
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<p>The adjustments supporting 5th to 95th percentile users in BLUE SABINO are included in its custom chair, base structure, length-adjustable arms, and the size-adjustable orthotic components forming the human–machine attachments (HMAs) and adjustment mechanisms.</p>
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<p>Range of motion comparison between healthy male and female ROM reported in [<a href="#B62-machines-12-00617" class="html-bibr">62</a>,<a href="#B63-machines-12-00617" class="html-bibr">63</a>,<a href="#B103-machines-12-00617" class="html-bibr">103</a>,<a href="#B104-machines-12-00617" class="html-bibr">104</a>,<a href="#B105-machines-12-00617" class="html-bibr">105</a>], healthy movements measured by motion capture during ADL tasks [<a href="#B64-machines-12-00617" class="html-bibr">64</a>,<a href="#B106-machines-12-00617" class="html-bibr">106</a>,<a href="#B107-machines-12-00617" class="html-bibr">107</a>], and BLUE SABINO’s achieved ROM. BLUE SABINO’s ROM encompasses approximately 95% of the ADL motion range for all joints combined. It also covers between 83% and 89% of healthy 50th-percentile ROM on all joints.</p>
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<p>Sinusoid tracking-state accuracy. (<b>Top</b>) Position- and velocity-state tracking accuracy is shown for each of the joints of BLUE SABINO 5-DOF-RIGHT. Progression between states moves clockwise around each circle with the position and velocity states shown in red, and the error shown in blue. Only the portion of the input with full 10-degree amplitude (between 20 and 80 s in <a href="#machines-12-00617-f016" class="html-fig">Figure 16</a>) is shown. (<b>Bottom</b>) An enlarged view of the J<sub>7</sub> state chart shows the cyclical tracking error present in detail. Sixty wave cycles are shown with measured state line colors progressing from red to yellow to blue to highlight the variation of tracking accuracy between cycles.</p>
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<p>Sinusoid tracking phase magnitude characterization. A single sine-wave input and position/velocity response is shown for J<sub>7</sub>. The velocity-state measurement is filtered using a noncausal low-pass filter with a 10 Hz cutoff that smooths the signal, making it easier to identify the response peak time. The state time delay <math display="inline"><semantics> <mi mathvariant="sans-serif">β</mi> </semantics></math> is extracted as the time distance between peaks of the target and measured position states. The state-magnitude ratios are computed via the measurement and target state values at the identified peak times.</p>
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<p>RMS chirp-trajectory state-tracking error vs. frequency.</p>
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<p>Chirp-trajectory state-tracking-error variance vs. frequency.</p>
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<p>Logarithmic-ramping chirp-tracking time-series results. The input position (red)- and velocity (blue)-state targets signals and the instantaneous command frequency (dashed black) are shown in the first four columns. Command torque signals are shown on the fifth and sixth columns, overlaid with each actuator’s continuous and peak torque output band.</p>
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<p>Ensemble-averaging robotic measures. (<b>Top</b>) Hand displacement in x (red), y (blue), z (green), and absolute displacement (purple); (<b>Middle</b>) Hand-velocity ensemble average (red) of all measurements (grey); (<b>Bottom</b>) Required shoulder torque to complete each reach trajectory and the ensemble-average torque profile (purple). Individual trajectories from all reach movements and shoulder torques required to drive the exoskeleton are displayed in grey.</p>
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<p>Trial average EEG, EMG, and robot kinematics. The ensemble-averaged biosignal including contralateral low-beta EEG at C3, EMG from three shoulder muscles, and robotic measurements, including the displacement and velocity of the right hand, and the absolute summed magnitude of interaction torque between the user and robot’s shoulder joints.</p>
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<p>Topographical progression of EEG power: The top portion of the plot shows Lβ power and μ power at C3, as well as shoulder torque from robot joints (RJ) 3–5, from 1000 ms before the cue presentation to 4000 ms after the cue. On the same timescale along the bottom are topographical heat maps showing the percent change in Lβ power with respect to baseline.</p>
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<p>Adjustable HRA based on ellipse-fit forearm model. (<b>Left</b>) Three-piece HRA design. (<b>Right</b>) Ellipse size range with enlarged view of potential range of alignment errors. Colored dots represent the center location of each ellipse when the adjustment is fully contracted (cyan), centered (yellow), and fully expanded (green). Red axes represent the model coordinate system which was built around the 50th-percentile arm.</p>
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<p>A triple-pivot four-par mechanism is similar to a standard four-bar mechanism (<b>A</b>), with two intermediate links operated in parallel (<b>B</b>), and with both intermediate links extended beyond the output link pivot to a remote center (RC) output link (<b>C</b>).</p>
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<p>Remote-center mechanisms. (<b>A</b>) Remote-center mechanisms at the upper arm and forearm allow the placement of actuators for internal/external rotation and pronation/supination away from the anatomical centers of rotation. (<b>B</b>) The mechanisms use ball bearing pairs that are spaced apart to reduce angular play resulting from each bearing experiencing radial play in opposite directions. Precision shims ensure a snug fit at each bearing interface. The shims and compression preload applied by the precision shoulder bolts reduce both axial and radial play.</p>
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<p>Experimental mean and standard deviation measurements vs. optimal-fit and relaxed-Coulombic-fit models show the torque required to overcome friction in each system motor. The sigmoid model of Equation (18) with parameters fit using FMINCON optimization best fits the experimentally measured torque–velocity profiles. However, the relaxed model reduces activation in the low-velocity region, improving chatter rejection.</p>
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<p>The effect of the friction model using relaxed-fit vs. optimal-fit friction parameters is illustrated. Friction torque compensation for a white noise-corrupted 1 Hz velocity signal is computed using the proposed sigmoid friction model with both sets of parameters. The relaxed-fit model effectively reduces the effect of discontinuous chatter as velocity passes through 0.</p>
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15 pages, 1650 KiB  
Article
Acute Effects of Transcranial Direct Current Stimulation Combined with High-Load Resistance Exercises on Repetitive Vertical Jump Performance and EEG Characteristics in Healthy Men
by Yuping Zhou, Haiting Zhai and Hongwen Wei
Life 2024, 14(9), 1106; https://doi.org/10.3390/life14091106 - 3 Sep 2024
Viewed by 400
Abstract
Background: Transcranial direct current stimulation (tDCS) is a non-invasive technique known to enhance athletic performance metrics such as vertical jump and lower limb strength. However, it remains unclear whether combining tDCS with the post-activation effects of high-load resistance training can further improve lower [...] Read more.
Background: Transcranial direct current stimulation (tDCS) is a non-invasive technique known to enhance athletic performance metrics such as vertical jump and lower limb strength. However, it remains unclear whether combining tDCS with the post-activation effects of high-load resistance training can further improve lower limb performance. Objective: This study investigated the synergistic effects of tDCS and high-load resistance training, using electroencephalography to explore changes in the motor cortex and vertical jump dynamics. Methods: Four experiments were conducted involving 29 participants. Each experiment included tDCS, high-load resistance training, tDCS combined with high-load resistance training, and a control condition. During the tDCS session, participants received 20 min of central stimulation using a Halo Sport 2 headset, while the high-load resistance training session comprised five repetitions of a 90% one-repetition maximum weighted half squat. No intervention was administered in the control group. Electroencephalography tests were conducted before and after each intervention, along with the vertical jump test. Results: The combination of tDCS and high-load resistance training significantly increased jump height (p < 0.05) compared to tDCS or high-load resistance training alone. As for electroencephalography power, tDCS combined with high-load resistance training significantly impacted the percentage of α-wave power in the frontal lobe area (F3) of the left hemisphere (F = 6.33, p < 0.05). In the temporal lobe area (T3) of the left hemisphere, tDCS combined with high-load resistance training showed a significant interaction effect (F = 6.33, p < 0.05). For β-wave power, tDCS showed a significant main effect in the frontal pole area (Fp1) of the left hemisphere (F = 17.65, p < 0.01). In the frontal lobe area (F3) of the left hemisphere, tDCS combined with high-load resistance training showed a significant interaction effect (F = 7.53, p < 0.05). The tDCS combined with high-load resistance training intervention also resulted in higher β-wave power in the parietal lobe area (P4) and the temporal lobe area (T4) (p < 0.05). Conclusions: The findings suggest that combining transcranial direct current stimulation (tDCS) and high-load resistance training significantly enhances vertical jump performance compared to either intervention alone. This improvement is associated with changes in the α-wave and β-wave power in specific brain regions, such as the frontal and temporal lobes. Further research is needed to explore the mechanisms and long-term effects of this combined intervention. Full article
(This article belongs to the Special Issue Focus on Exercise Physiology and Sports Performance)
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<p>Flow chart of the experiment.</p>
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<p>Halo Sport 2 headset.</p>
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<p>EEG electrode placement diagram. (<b>A</b>) Lateral view, (<b>B</b>) Top view.</p>
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<p>α-wave EEG power. *: Indicates a significant difference compared to CON. #: Indicates a significant difference compared to tDCS + HRT.</p>
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<p>Left hemisphere β-wave EEG power. *: Indicates a significant difference compared to CON.</p>
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<p>Right hemisphere β-wave EEG power. *: Indicates a significant difference compared to CON.</p>
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24 pages, 4425 KiB  
Brief Report
Transcranial Magnetic Stimulation Facilitates Neural Speech Decoding
by Lindy Comstock, Vinícius Rezende Carvalho, Claudia Lainscsek, Aria Fallah and Terrence J. Sejnowski
Brain Sci. 2024, 14(9), 895; https://doi.org/10.3390/brainsci14090895 - 2 Sep 2024
Viewed by 492
Abstract
Transcranial magnetic stimulation (TMS) has been widely used to study the mechanisms that underlie motor output. Yet, the extent to which TMS acts upon the cortical neurons implicated in volitional motor commands and the focal limitations of TMS remain subject to debate. Previous [...] Read more.
Transcranial magnetic stimulation (TMS) has been widely used to study the mechanisms that underlie motor output. Yet, the extent to which TMS acts upon the cortical neurons implicated in volitional motor commands and the focal limitations of TMS remain subject to debate. Previous research links TMS to improved subject performance in behavioral tasks, including a bias in phoneme discrimination. Our study replicates this result, which implies a causal relationship between electro-magnetic stimulation and psychomotor activity, and tests whether TMS-facilitated psychomotor activity recorded via electroencephalography (EEG) may thus serve as a superior input for neural decoding. First, we illustrate that site-specific TMS elicits a double dissociation in discrimination ability for two phoneme categories. Next, we perform a classification analysis on the EEG signals recorded during TMS and find a dissociation between the stimulation site and decoding accuracy that parallels the behavioral results. We observe weak to moderate evidence for the alternative hypothesis in a Bayesian analysis of group means, with more robust results upon stimulation to a brain region governing multiple phoneme features. Overall, task accuracy was a significant predictor of decoding accuracy for phoneme categories (F(1,135) = 11.51, p < 0.0009) and individual phonemes (F(1,119) = 13.56, p < 0.0003), providing new evidence for a causal link between TMS, neural function, and behavior. Full article
(This article belongs to the Special Issue Language, Communication and the Brain)
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<p>Phoneme Classes and Their Cortical Representation. (<b>A</b>) The phonemes included in this study (/b/, /p/, /d/, /t/) differ according to the place in the oral cavity where they are articulated (bilabial and alveolar—columns) and the degree to which they involve vocal cord movement (voiced and unvoiced—rows). (<b>B</b>) Vocal cord vibrations, represented by blue lines overlying the waveform, are generated via the phonemes /b/ and /d/ (waveforms are taken from the audio stimuli). After vowels, which are always voiced, vibrations perseverate into post-vocalic consonants. Differences in the waveforms and the degree of preseveration are observable among bilabial (blue) and alveolar (orange) phonemes. (<b>C</b>) The experimental paradigm stimulates sites in the motor cortex associated with phoneme articulation. Each site was taken from neuroimaging studies that reported the mean MNI coordinates corresponding to the peak motor cortex activation probability during a specific articulatory process (lip: −56, −8, 46; tongue: −60, −10, 25; voicing: −60, −15, 18) [<a href="#B35-brainsci-14-00895" class="html-bibr">35</a>,<a href="#B36-brainsci-14-00895" class="html-bibr">36</a>]. The site associated with voicing is adjacent to the tongue target and receives the same maximum stimulation intensity from the TMS coil. (<b>D</b>) Participants listened to stimuli items immersed in 500 ms of white noise to avoid performance at the ceiling in the phoneme discrimination task. Two TMS pulses were administered 50 ms prior to the phoneme onset with a 50-ms inter-pulse interval to replicate the excitatory paradigm in our reference study [<a href="#B31-brainsci-14-00895" class="html-bibr">31</a>].</p>
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<p>Experimental Paradigm. (<b>A</b>) Participants listened to phoneme stimuli presented via computer-based experiment-presentation software. Concurrently, EEG signals were recorded as participants identified the phoneme they heard with a button-press response input on a computer keyboard. The task was performed with TMS under experimental conditions and without TMS under the control condition. After data collection, a classification analysis was conducted on the EEG signals, and accuracy was computed for the aggregate task-response data. (<b>B</b>) The task was administered in two blocks in 2019 and in four blocks in 2021; both CV and VC phoneme pairs were presented in 2019, and only CV phoneme pairs were presented in 2021. The presentation order of blocks and stimuli lists was counterbalanced across participants. EEG data were obtained for 8 participants in 2019 and 16 participants in 2021. Task-response data were obtained from 8 participants in 2019 and 2021.</p>
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<p>Phoneme Category Discrimination. (<b>A</b>) 2019 CV results for (<b>i</b>) relative accuracy, and parameter estimation for (<b>ii</b>) bilabial phonemes and (<b>iii</b>) alveolar phonemes. (<b>B</b>) 2021 CV results for (<b>i</b>) relative accuracy, and parameter estimation for (<b>ii</b>) bilabial phonemes and (<b>iii</b>) alveolar phonemes. (<b>C</b>) 2019 VC results for (<b>i</b>) relative accuracy and parameter estimation for (<b>ii</b>) bilabial phonemes and (<b>iii</b>) alveolar phonemes. Error bars represent the 95% confidence intervals.</p>
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<p>Individual Phoneme Discrimination. (<b>A</b>) 2021 CV results for (<b>i</b>) relative accuracy, and robustness parameters for (<b>ii</b>) /b/, (<b>iii</b>) /p/, (<b>iv</b>) /d/, and (<b>v</b>) /t/. (<b>B</b>) 2019 VC results for (<b>i</b>) relative accuracy, and robustness parameters for (<b>ii</b>) /b/, (<b>iii</b>) /p/, (<b>iv</b>) /d/, and (<b>v</b>) /t/. Error bars represent the 95% confidence intervals.</p>
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<p>Neural Category Decoding. (<b>A</b>) 2019 CV results for (<b>i</b>) relative accuracy and (<b>ii</b>) bilabial and (<b>iii</b>) alveolar parameter estimation. (<b>B</b>) 2021 CV results for (<b>i</b>) relative accuracy and (<b>ii</b>) bilabial and (<b>iii</b>) alveolar parameter estimation. (<b>C</b>) 2019 VC results for (<b>i</b>) relative accuracy and (<b>ii</b>) bilabial and (<b>iii</b>) alveolar parameter estimation. Error bars represent the 95% confidence intervals.</p>
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<p>Neural Category Decoding. (<b>A</b>) 2021 CV results for (<b>i</b>) relative accuracy and robustness parameters for (<b>ii</b>) /b/, (<b>iii</b>) /p/, (<b>iv</b>) /d/, and (<b>v</b>) /t/. (<b>B</b>) 2019 VC results for (<b>i</b>) relative accuracy and robustness parameters for (<b>ii</b>) /b/, (<b>iii</b>) /p/, (<b>iv</b>) /d/, and (<b>v</b>) /t/. Error bars represent the 95% confidence intervals.</p>
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15 pages, 2870 KiB  
Article
Towards Prosthesis Control: Identification of Locomotion Activities through EEG-Based Measurements
by Saqib Zafar, Hafiz Farhan Maqbool, Muhammad Imran Ashraf, Danial Javaid Malik, Zain ul Abdeen, Wahab Ali, Juri Taborri and Stefano Rossi
Robotics 2024, 13(9), 133; https://doi.org/10.3390/robotics13090133 - 1 Sep 2024
Viewed by 482
Abstract
The integration of advanced control systems in prostheses necessitates the accurate identification of human locomotion activities, a task that can significantly benefit from EEG-based measurements combined with machine learning techniques. The main contribution of this study is the development of a novel framework [...] Read more.
The integration of advanced control systems in prostheses necessitates the accurate identification of human locomotion activities, a task that can significantly benefit from EEG-based measurements combined with machine learning techniques. The main contribution of this study is the development of a novel framework for the recognition and classification of locomotion activities using electroencephalography (EEG) data by comparing the performance of different machine learning algorithms. Data of the lower limb movements during level ground walking as well as going up stairs, down stairs, up ramps, and down ramps were collected from 10 healthy volunteers. Time- and frequency-domain features were extracted by applying independent component analysis (ICA). Successively, they were used to train and test random forest and k-nearest neighbors (kNN) algorithms. For the classification, random forest revealed itself as the best-performing one, achieving an overall accuracy up to 92%. The findings of this study contribute to the field of assistive robotics by confirming that EEG-based measurements, when combined with appropriate machine learning models, can serve as robust inputs for prosthesis control systems. Full article
(This article belongs to the Special Issue AI for Robotic Exoskeletons and Prostheses)
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<p>(<b>a</b>) The hardware of EMOTIV Epoc headset, (<b>b</b>) the position of the 14 electrodes.</p>
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<p>Flowchart of the data processing and analysis.</p>
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<p>Frequency response of different filters in the EEGLAB toolbox.</p>
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<p>EEG signals (<b>Left</b>) and independent components (<b>Right</b>) (<span class="html-italic">x</span>-axis represents the time in seconds, while the <span class="html-italic">y</span>-axis represents the micro voltage measured by each electrode and ICs).</p>
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<p>(<b>a</b>) Example of informax ICA results related to ascending stairs, (<b>b</b>) example of ADJUST results related to descending stairs. The number on the scalp stands for the specific components found by the independent component analysis, whereas the percentage indicates the confidence associated with the type of identified component. The colors on the scalp represent different levels of voltage, with warmer colors indicating higher levels of electrical potential, whereas blue and green indicate lower levels of activity. Black curves indicate isopotential lines, closer lines indicate steeper gradients of electrical potential, whereas widely spaced lines indicate more gradual changes.</p>
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16 pages, 6475 KiB  
Article
Exploring Inner Speech Recognition via Cross-Perception Approach in EEG and fMRI
by Jiahao Qin, Lu Zong and Feng Liu
Appl. Sci. 2024, 14(17), 7720; https://doi.org/10.3390/app14177720 - 1 Sep 2024
Viewed by 621
Abstract
Multimodal brain signal analysis has shown great potential in decoding complex cognitive processes, particularly in the challenging task of inner speech recognition. This paper introduces an innovative I nner Speech Recognition via Cross-Perception (ISRCP) approach that significantly enhances accuracy by fusing electroencephalography (EEG) [...] Read more.
Multimodal brain signal analysis has shown great potential in decoding complex cognitive processes, particularly in the challenging task of inner speech recognition. This paper introduces an innovative I nner Speech Recognition via Cross-Perception (ISRCP) approach that significantly enhances accuracy by fusing electroencephalography (EEG) and functional magnetic resonance imaging (fMRI) data. Our approach comprises three core components: (1) multigranularity encoders that separately process EEG time series, EEG Markov Transition Fields, and fMRI spatial data; (2) a cross-perception expert structure that learns both modality-specific and shared representations; and (3) an attention-based adaptive fusion strategy that dynamically adjusts the contributions of different modalities based on task relevance. Extensive experiments on the Bimodal Dataset on Inner Speech demonstrate that our model outperforms existing methods across accuracy and F1 score. Full article
(This article belongs to the Section Electrical, Electronics and Communications Engineering)
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<p>Inner speech using EEG and FMRI data.</p>
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<p>The process of transforming EEG signals into MTF images.</p>
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<p>Visualization of EEG data for 8 classes.</p>
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<p>Visualization of EEG data for 2 classes.</p>
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<p>Visualization of fMRI data for 8 classes.</p>
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<p>Visualization of fMRI data for 2 classes.</p>
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