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17 pages, 924 KiB  
Article
Legendre Polynomial Fitting-Based Permutation Entropy Offers New Insights into the Influence of Fatigue on Surface Electromyography (sEMG) Signal Complexity
by Meryem Jabloun, Olivier Buttelli and Philippe Ravier
Entropy 2024, 26(10), 831; https://doi.org/10.3390/e26100831 - 30 Sep 2024
Abstract
In a recently published work, we introduced local Legendre polynomial fitting-based permutation entropy (LPPE) as a new complexity measure for quantifying disorder or randomness in time series. LPPE benefits from the ordinal pattern (OP) concept and incorporates a natural, aliasing-free multiscaling effect by [...] Read more.
In a recently published work, we introduced local Legendre polynomial fitting-based permutation entropy (LPPE) as a new complexity measure for quantifying disorder or randomness in time series. LPPE benefits from the ordinal pattern (OP) concept and incorporates a natural, aliasing-free multiscaling effect by design. The current work extends our previous study by investigating LPPE’s capability to assess fatigue levels using both synthetic and real surface electromyography (sEMG) signals. Real sEMG signals were recorded during biceps brachii fatiguing exercise maintained at 70% of maximal voluntary contraction (MVC) until exhaustion and were divided into four consecutive temporal segments reflecting sequential stages of exhaustion. As fatigue levels rise, LPPE values can increase or decrease significantly depending on the selection of embedding dimensions. Our analysis reveals two key insights. First, using LPPE with limited embedding dimensions shows consistency with the literature. Specifically, fatigue induces a decrease in sEMG complexity measures. This observation is supported by a comparison with the existing multiscale permutation entropy (MPE) variant, that is, the refined composite downsampling (rcDPE). Second, given a fixed OP length, higher embedding dimensions increase LPPE’s sensitivity to low-frequency components, which are notably present under fatigue conditions. Consequently, specific higher embedding dimensions appear to enhance the discrimination of fatigue levels. Thus, LPPE, as the only MPE variant that allows a practical exploration of higher embedding dimensions, offers a new perspective on fatigue’s impact on sEMG complexity, complementing existing MPE approaches. Full article
(This article belongs to the Special Issue Ordinal Pattern-Based Entropies: New Ideas and Challenges)
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<p>Normalised sEMG PSDs: (<b>a</b>) Simulated PSDs calculated using (<a href="#FD6-entropy-26-00831" class="html-disp-formula">6</a>) and parameter pairs <math display="inline"><semantics> <mrow> <mo>(</mo> <msub> <mi>f</mi> <mi>l</mi> </msub> <mo>;</mo> <msub> <mi>f</mi> <mi>h</mi> </msub> <mo>)</mo> </mrow> </semantics></math> in Hz: (49;146.5) denoted as <math display="inline"><semantics> <msub> <mi>w</mi> <mn>1</mn> </msub> </semantics></math>, (49;117) as <math display="inline"><semantics> <msub> <mi>w</mi> <mn>2</mn> </msub> </semantics></math>, (39;98) as <math display="inline"><semantics> <msub> <mi>w</mi> <mn>3</mn> </msub> </semantics></math>, and (29;58.5) as <math display="inline"><semantics> <msub> <mi>w</mi> <mn>4</mn> </msub> </semantics></math>; 50 Monte Carlo realisations of synthetic sEMG signals based on filtered white Gaussian noise are generated for each parameter pair. (<b>b</b>) Average normalised PSD estimates of sEMG signals acquired under fatigue conditions <math display="inline"><semantics> <msub> <mi>W</mi> <mn>1</mn> </msub> </semantics></math> to <math display="inline"><semantics> <msub> <mi>W</mi> <mn>4</mn> </msub> </semantics></math>, as described in <a href="#sec3dot2-entropy-26-00831" class="html-sec">Section 3.2</a>, and subsampled by a factor of 10. (<b>c</b>) Average normalised PSD estimates of these same sEMG signals after mean removal. All PSD estimates were calculated using an AR model of order 30 [<a href="#B55-entropy-26-00831" class="html-bibr">55</a>].</p>
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<p>LPPE with (<b>a</b>) <math display="inline"><semantics> <mrow> <mi>d</mi> <mo>=</mo> <mn>4</mn> </mrow> </semantics></math> and (<b>b</b>) <math display="inline"><semantics> <mrow> <mi>d</mi> <mo>=</mo> <mn>5</mn> </mrow> </semantics></math>, applied to synthetic sEMG signals generated as described in <a href="#sec3dot1-entropy-26-00831" class="html-sec">Section 3.1</a>. (<b>c</b>,<b>d</b>) show a zoom performed on (<b>a</b>) and (<b>b</b>), respectively. The sampling frequency is 1000 Hz.</p>
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<p>Mean rcDPE with (<b>a</b>) <math display="inline"><semantics> <mrow> <mi>d</mi> <mo>=</mo> <mn>4</mn> </mrow> </semantics></math> and (<b>b</b>) <math display="inline"><semantics> <mrow> <mi>d</mi> <mo>=</mo> <mn>5</mn> </mrow> </semantics></math> applied to real sEMG signals acquired as described in <a href="#sec3dot2-entropy-26-00831" class="html-sec">Section 3.2</a>. The rcDPE is insensitive to the mean removal of the acquired sEMG signals.</p>
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<p>LPPE with <math display="inline"><semantics> <mrow> <mi>d</mi> <mo>=</mo> <mn>5</mn> </mrow> </semantics></math> applied to real sEMG signals, acquired under fatigue condition from 10 subjects as described in <a href="#sec3dot2-entropy-26-00831" class="html-sec">Section 3.2</a> and subsampled by a factor <math display="inline"><semantics> <mrow> <mi>M</mi> <mo>=</mo> <mn>10</mn> </mrow> </semantics></math>. The sampling frequency is <math display="inline"><semantics> <msub> <mi>F</mi> <mi>s</mi> </msub> </semantics></math> = 1000 Hz.</p>
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<p>LPPE with <span class="html-italic">d</span> = 5 applied to centred (mean removal) real sEMG signals acquired under fatigue condition from 10 subjects as described in <a href="#sec3dot2-entropy-26-00831" class="html-sec">Section 3.2</a>. The sampling frequency is <math display="inline"><semantics> <msub> <mi>F</mi> <mi>s</mi> </msub> </semantics></math> = 1000 Hz.</p>
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<p>Mean LPPE with (<b>a</b>) <span class="html-italic">d</span> = 4 and (<b>b</b>) <span class="html-italic">d</span> = 5 using the 10 real sEMG signals acquired as described in <a href="#sec3dot2-entropy-26-00831" class="html-sec">Section 3.2</a>, after mean removal and subsampling by <span class="html-italic">M</span> = 10. (<b>c</b>,<b>d</b>) are a zoom of (<b>a</b>) and (<b>b</b>), respectively. The sampling frequency is <math display="inline"><semantics> <msub> <mi>F</mi> <mi>s</mi> </msub> </semantics></math> = 1000 Hz.</p>
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<p>Oscillations in detrended LPPE of real sEMG signals obtained using the data-driven decomposition method, VMD, and their respective spectra with <span class="html-italic">d</span> = 4. The sampling frequency is <math display="inline"><semantics> <msub> <mi>F</mi> <mi>s</mi> </msub> </semantics></math> = 1000 Hz.</p>
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<p>Relative absolute difference of (<b>a</b>) LPPEs and (<b>b</b>) rcDPE of real sEMG signals using pairwise comparisons of the fatigue steps <math display="inline"><semantics> <msub> <mi>W</mi> <mn>1</mn> </msub> </semantics></math>-<math display="inline"><semantics> <msub> <mi>W</mi> <mn>2</mn> </msub> </semantics></math>, <math display="inline"><semantics> <msub> <mi>W</mi> <mn>2</mn> </msub> </semantics></math>-<math display="inline"><semantics> <msub> <mi>W</mi> <mn>3</mn> </msub> </semantics></math>, and <math display="inline"><semantics> <msub> <mi>W</mi> <mn>3</mn> </msub> </semantics></math>-<math display="inline"><semantics> <msub> <mi>W</mi> <mn>4</mn> </msub> </semantics></math>. The sampling frequency is 1000 Hz. The relative absolute difference is calculated using <math display="inline"><semantics> <mrow> <mn>100</mn> <mo>×</mo> <mstyle scriptlevel="0" displaystyle="true"> <mfrac> <mrow> <mrow> <mo>|</mo> </mrow> <msub> <mi>y</mi> <mi>i</mi> </msub> <mo>−</mo> <msub> <mi>y</mi> <mi>j</mi> </msub> <mrow> <mo>|</mo> </mrow> </mrow> <mrow> <mrow> <mo>|</mo> </mrow> <msub> <mi>y</mi> <mi>i</mi> </msub> <mo>+</mo> <msub> <mi>y</mi> <mi>j</mi> </msub> <mrow> <mo>|</mo> </mrow> </mrow> </mfrac> </mstyle> </mrow> </semantics></math>, where <math display="inline"><semantics> <msub> <mi>y</mi> <mi>i</mi> </msub> </semantics></math> is LPPE or rcDPE of step <math display="inline"><semantics> <msub> <mi>W</mi> <mi>i</mi> </msub> </semantics></math>.</p>
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<p>LPPE of pure tones: (<b>a</b>) LPPE shapes are shown for two sinusoids of frequencies 20 Hz and 110 Hz, with <span class="html-italic">d</span> = 5. (<b>b</b>) Segment length <span class="html-italic">L</span> corresponding to LPPE maxima represented as a function of the frequency of the pure tone. Two additional curves are provided: (-.) the inverse of the frequency, and (:) this curve scaled by a factor of 0.57 as an approximation. The sampling frequency is 1000 Hz.</p>
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<p>LPPE of sinusoids embedded in an additive Gaussian noise: (<b>a</b>) rcDPE and (<b>b</b>) LPPE with SNR = 0 dB. (<b>c</b>,<b>d</b>) are LPPE plotted as a function of embedding dimension × the sinusoid frequency at SNR 0 and 5 dB.</p>
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16 pages, 3196 KiB  
Article
Transferable Deep Learning Models for Accurate Ankle Joint Moment Estimation during Gait Using Electromyography
by Amged Elsheikh Abdelgadir Ali, Dai Owaki and Mitsuhiro Hayashibe
Appl. Sci. 2024, 14(19), 8795; https://doi.org/10.3390/app14198795 (registering DOI) - 30 Sep 2024
Abstract
The joint moment is a key measurement in locomotion analysis. Transferable prediction across different subjects is advantageous for calibration-free, practical clinical applications. However, even for similar gait motions, intersubject variance presents a significant challenge in maintaining reliable prediction performance. The optimal deep learning [...] Read more.
The joint moment is a key measurement in locomotion analysis. Transferable prediction across different subjects is advantageous for calibration-free, practical clinical applications. However, even for similar gait motions, intersubject variance presents a significant challenge in maintaining reliable prediction performance. The optimal deep learning models for ankle moment prediction during dynamic gait motions remain underexplored for both intrasubject and intersubject usage. This study evaluates the feasibility of different deep-learning models for estimating ankle moments using sEMG data to find an optimal intrasubject model against the inverse dynamic approach. We verified and compared the performance of 1302 intrasubject models per subject on 597 steps from seven subjects using various architectures and feature sets. The best-performing intrasubject models were recurrent convolutional neural networks trained using signal energy features. They were then transferred to realize intersubject ankle moment estimation. Full article
(This article belongs to the Special Issue Advances in Foot Biomechanics and Gait Analysis)
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<p>Anatomical (red) and tracking (white) markers.</p>
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<p>Time-series dataset inputs/outputs illustration.</p>
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<p>sEMG intrasubject models results. (<b>a</b>) boxplots illustrate the distribution of <math display="inline"><semantics> <msup> <mi>R</mi> <mn>2</mn> </msup> </semantics></math> values for models trained on various combinations of autoregressive model (AR) coefficients and zero crossing count (ZC) features. (<b>b</b>) illustrates the distribution of <math display="inline"><semantics> <msup> <mi>R</mi> <mn>2</mn> </msup> </semantics></math> values for models trained on Signal Power features: root mean square (RMS), mean absolute value (MAV), and waveform length (WL). (<b>c</b>) shows the distribution of <math display="inline"><semantics> <msup> <mi>R</mi> <mn>2</mn> </msup> </semantics></math> values for models for tibialis anterior (TA), soleus (SOL), gastrocnemius medialis (GM), and peroneus brevis (PB) muscles groups when using Signal Power features. The outliers observed in (<b>b</b>) are primarily attributed to the TA+PB muscle group, which exhibited lower estimation performance than other muscle groups.</p>
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<p>This figure compares the estimated S1 (first volunteer) ankle moments from the inverse dynamic (ID) Equation (<a href="#FD7-applsci-14-08795" class="html-disp-formula">7</a>) against intrasubject models (MLP, RCNN, LSTM) using the mean absolute value (MAV) and waveform length (WL) features extracted from tibialis anterior (TA), soleus (SOL), gastrocnemius medialis (GM), and peroneus brevis (PB) sEMG signals. The x-axis represents the normalized gait cycle, starting from the swing phase and ending with the subsequent swing phase. The y-axis shows the normalized ankle moment. Positive values indicate plantar flexion, while negative values indicate dorsiflexion. The shaded areas represent the standard deviation of the estimations across subjects.</p>
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<p>DEMG intrasubject models results. (<b>a</b>) boxplots illustrate the distribution of <math display="inline"><semantics> <msup> <mi>R</mi> <mn>2</mn> </msup> </semantics></math> values for models trained on various combinations of autoregressive model (AR) coefficients and zero crossing count (ZC) features. (<b>b</b>) illustrates the distribution of <math display="inline"><semantics> <msup> <mi>R</mi> <mn>2</mn> </msup> </semantics></math> values for models trained on Signal Power features: root mean square (RMS), mean absolute value (MAV), and waveform length (WL). (<b>c</b>) shows the distribution of <math display="inline"><semantics> <msup> <mi>R</mi> <mn>2</mn> </msup> </semantics></math> values for models for tibialis anterior (TA), soleus (SOL), gastrocnemius medialis (GM), and peroneus brevis (PB) muscles groups when using signal power features.</p>
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<p>This figure compares the three intersubject models against their corresponding ankle moments from the inverse dynamic (ID) Equation (<a href="#FD7-applsci-14-08795" class="html-disp-formula">7</a>). The x-axis represents the normalized gait cycle, starting from the swing phase and ending with the subsequent swing phase. The y-axis shows the normalized ankle moment. Positive values indicate plantar flexion, while negative values indicate dorsiflexion. The shaded areas represent the standard deviation of the estimations across subjects. S6 and S7 refer to volunteers number 6 and 7, respectively, tibialis anterior (TA), soleus (SOL), gastrocnemius medialis (GM), and peroneus brevis (PB) muscles.</p>
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17 pages, 7529 KiB  
Article
Effects of the Acoustic-Visual Indoor Environment on Relieving Mental Stress Based on Facial Electromyography and Micro-Expression Recognition
by Guodan Liu, Pengcheng Hu, Huiyang Zhong, Yang Yang, Jie Sun, Yihang Ji, Jixin Zou, Hui Zhu and Songtao Hu
Buildings 2024, 14(10), 3122; https://doi.org/10.3390/buildings14103122 - 29 Sep 2024
Abstract
People working and studying indoors for a long time can easily experience mental fatigue and stress. Virtual natural elements introduced into indoor environments can stimulate the human visual and auditory senses, thus relieving psychological stress. In this study, stress induction was achieved through [...] Read more.
People working and studying indoors for a long time can easily experience mental fatigue and stress. Virtual natural elements introduced into indoor environments can stimulate the human visual and auditory senses, thus relieving psychological stress. In this study, stress induction was achieved through noise playback, and the recovery effects on psychological stress of three set indoor environments, visual, auditory, and audio-visual, were investigated through changes in subjects’ facial expressions, electromyographic (EMG) signals, and subjective questionnaires. The experiment found that after stress induction through noise, the participants’ stress levels changed significantly. At this time, the subject scored low on the questionnaire, with electromyography readings higher than usual, and micro-expression recognition indicated negative emotions. After the restoration effects under the three working conditions of visual, auditory, and audio-visual combination, the average EMG values during the recovery period decreased from the baseline period (10 min after the subject acclimated to the environment), respectively. The results indicate that all three restoration conditions have the effect of relieving psychological stress, with the stress recovery effects of auditory and audio-visual conditions being superior to visual conditions. This study is of great significance for creating comfortable indoor environments and minimizing psychological pressure on indoor office workers. Full article
(This article belongs to the Special Issue Recently Advances in the Thermal Performance of Buildings)
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<p>Floor plan of the laboratory.</p>
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<p>Audio spectrum.</p>
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<p>Restorative environment pictures.</p>
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<p>Experimental procedure.</p>
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<p>Mean values of uncomfortable probability during the stress induction and recovery stages.</p>
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<p>Percentage of uncomfortable people in the stress induction and recovery stages.</p>
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<p>Score of the subjective questionnaire for the stress induction of the three environments.</p>
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<p>Score of the subjective questionnaire for the recovery of the three environments.</p>
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<p>Mean values of normalized EMG in three types of environments. Note. * <span class="html-italic">p</span> &lt; 0.05, 95% confidence intervals.</p>
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<p>Scatter plot of MERCNN evaluation and questionnaire results.</p>
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<p>Percentage of uncomfortable people during the stress induction and recovery stages obtained by MERCNN and questionnaire.</p>
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<p>Comparison of mean values of normalized EMG between baseline and recovery stages. Note. * <span class="html-italic">p</span> &lt; 0.05, 95% confidence intervals.</p>
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16 pages, 3217 KiB  
Article
Electro-Stimulation System with Artificial-Intelligence-Based Auricular-Triggered Algorithm to Support Facial Movements in Peripheral Facial Palsy: A Simulation Pilot Study
by Katharina Steiner, Marius Arnz, Gerd Fabian Volk and Orlando Guntinas-Lichius
Diagnostics 2024, 14(19), 2158; https://doi.org/10.3390/diagnostics14192158 - 28 Sep 2024
Abstract
Background: Facial palsy causes severe functional disorders and impairs quality of life. Disturbing challenges for patients with acute facial palsy, but also with those with chronic facial palsy with synkinesis, are the loss of the ability to smile and insufficient eyelid closure. A [...] Read more.
Background: Facial palsy causes severe functional disorders and impairs quality of life. Disturbing challenges for patients with acute facial palsy, but also with those with chronic facial palsy with synkinesis, are the loss of the ability to smile and insufficient eyelid closure. A potential treatment for these conditions could be a closed-loop electro-stimulation system that stimulates the facial muscles on the paretic side as needed to elicit eye closure, eye blink and smile in a manner similar to the healthy side. Methods: This study focuses on the development and evaluation of such a system. An artificial intelligence (AI)-based auricular-triggered algorithm is used to classify the intended facial movements. This classification is based on surface electromyography (EMG) recordings of the extrinsic auricular muscles, specifically the anterior, superior, and posterior auricular muscle on the paretic side. The system then delivers targeted surface electrical stimulation to contract the appropriate facial muscles. Results: The evaluation of the system was conducted with 17 patients with facial synkinesis, who performed various facial movements according to a paradigm video. The system’s performance was evaluated through a simulation, using previously captured data as the inputs. The performance was evaluated by means of the median macro F1-score, which was calculated based on the stimulation signal (output of the system) and the actual movements the patients performed. Conclusions: This study showed that such a system, using an AI-based auricular-triggered algorithm, can support with a median macro F1-score of 0.602 for the facial movements on the synkinetic side in patients with unilateral chronic facial palsy with synkinesis. Full article
(This article belongs to the Section Machine Learning and Artificial Intelligence in Diagnostics)
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<p>Schematic of the experimental setup. The red and black dots visualize the electrodes (cathode and anode). The green dot represents the reference electrode. Anterior auricular muscle (AAM), superior auricular muscle (SAM), posterior auricular muscle (PAM), zygomaticus major muscle (ZM), and orbicularis oculi muscle (OOM).</p>
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<p>CRNN with different layers and parameters. The input data represent one EMG window for one patient during the movement ST (132 × 3 = number of samples in one window x number of EMG channels). Each layer has a dimensionality that is defined by the number of samples in one window x number of units. The final layer is a dense layer with an output size of six, corresponding to the six different classes. The predicted label is ST. The model was trained with a batch size of 15 and 60 epochs. The three colors in the EMG image on the left side illustrate the three different auricular muscle recordings.</p>
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<p>Visualization of the window-feature allocation based on the three labeled extrinsic auricular EMG signals. One EMG window with a length of 66 ms (yellow) (containing 132 samples per channel = 132 × 3 = 396) visualizes one input of the Neural Network. Each window receives one label (purple), depending on the most frequent label within it. All the different windows with all the datapoints are saved into the matrix X and all the according labels into the vector y. The three colors in the EMG image in the upper part of the figure illustrate the three different auricular muscle recordings.</p>
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<p>Schematic of the electro-stimulation system for patients with peripheral facial palsy. The red and black dots represent the EMG electrodes and the orange and gray dots the stimulation electrodes. The green dot visualizes the reference electrode.</p>
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<p>Overall performance of the electro-stimulation system based on the macro F1-score for the test data from the 17 patients. <span class="html-italic">n</span> = number of patients; med = median macro F1-score. Green: median value; red dots: individual values of each patient; black lines: 25% and 75% quartile.</p>
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<p>Per-class performance of the electro-stimulation system based on the per-class F1-score for the test data of the 17 patients. <span class="html-italic">n</span> = number of patients; med = median macro F1-score. Green: median value; red dots: individual values of each patient; black lines: 25% and 75% quartile.</p>
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<p>Overall performance of the electro-stimulation system based on the macro F1-score for the everyday activities of the 16 patients. <span class="html-italic">n</span> = number of patients; med = median macro F1-score. Green: median value; red dots: individual values of each patient; black lines: 25% and 75% quartile.</p>
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<p>Per-class performance of the electro-stimulation system based on the per-class F1-score for the everyday activities of the 17 patients. <span class="html-italic">n</span> = number of patients; med = median macro F1-score. Green: median value; red dots: individual values of each patient; black lines: 25% and 75% quartile.</p>
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12 pages, 1682 KiB  
Article
Post-Movement Beta Synchrony Inhibits Cortical Excitability
by Edward Rhodes, William Gaetz, Jonathan Marsden and Stephen D. Hall
Brain Sci. 2024, 14(10), 970; https://doi.org/10.3390/brainsci14100970 - 26 Sep 2024
Abstract
Background/Objectives: This study investigates the relationship between movement-related beta synchrony and primary motor cortex (M1) excitability, focusing on the time-dependent inhibition of movement. Voluntary movement induces beta frequency (13–30 Hz) event-related desynchronisation (B-ERD) in M1, followed by post-movement beta rebound (PMBR). Although PMBR [...] Read more.
Background/Objectives: This study investigates the relationship between movement-related beta synchrony and primary motor cortex (M1) excitability, focusing on the time-dependent inhibition of movement. Voluntary movement induces beta frequency (13–30 Hz) event-related desynchronisation (B-ERD) in M1, followed by post-movement beta rebound (PMBR). Although PMBR is linked to cortical inhibition, its temporal relationship with motor cortical excitability is unclear. This study aims to determine whether PMBR acts as a marker for post-movement inhibition by assessing motor-evoked potentials (MEPs) during distinct phases of the beta synchrony profile. Methods: Twenty-five right-handed participants (mean age: 24 years) were recruited. EMG data were recorded from the first dorsal interosseous muscle, and TMS was applied to the M1 motor hotspot to evoke MEPs. A reaction time task was used to elicit beta oscillations, with TMS delivered at participant-specific time points based on EEG-derived beta power envelopes. MEP amplitudes were compared across four phases: B-ERD, early PMBR, peak PMBR, and late PMBR. Results: Our findings demonstrate that MEP amplitude significantly increased during B-ERD compared to rest, indicating heightened cortical excitability. In contrast, MEPs recorded during peak PMBR were significantly reduced, suggesting cortical inhibition. While all three PMBR phases exhibited reduced cortical excitability, a trend toward amplitude-dependent inhibition was observed. Conclusions: This study confirms that PMBR is linked to reduced cortical excitability, validating its role as a marker of motor cortical inhibition. These results enhance the understanding of beta oscillations in motor control and suggest that further research on altered PMBR could be crucial for understanding neurological and psychiatric disorders. Full article
(This article belongs to the Section Neuromuscular and Movement Disorders)
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<p>Experimental Protocol. (<b>A</b>) Schematic summary of a trial, showing the screen presentation and time course of the cue onset and duration, rest period, and overall trial length. (<b>B</b>) EMG measurement and response–device arrangement, showing the location of the force sensor beneath the tip of the index finger (1), locations of the FDI EMG sensor (2) and ulnar process reference (3). (<b>C</b>) EEG and MEP block designs, showing the arrangement of data acquisition in Experiments 1 (top) and 2 (bottom). (<b>D</b>) The 5 electrode EEG array centred on the functionally–localized M1.</p>
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<p>Time-frequency spectrogram. Grand-averaged Morlet Wavelet time-frequency analysis output from all participants, showing the mean oscillatory power in M1 across the experimental trial, with zero time-locked to cue onset.</p>
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<p>Characterisation of the beta-change time-points for TMS stimulation showing a representative single trial for an individual participant. (<b>A</b>) Normalised beta power at individual peak frequency, (<b>B</b>) Normalised EMG amplitude, and (<b>C</b>) Mean force production. Dashed vertical lines indicate the time-point selected for stimulation, as summarised in <a href="#brainsci-14-00970-t001" class="html-table">Table 1</a>.</p>
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<p>EMG Amplitude at beta-change time-points showing the difference from baseline in the mean peak-to-peak amplitude of MEPs induced during the four beta-change time-points. Data are normalised to the rest period, with statistically significant differences denoted as follows: ** <span class="html-italic">p</span> &lt; 0.01; * <span class="html-italic">p</span> &lt; 0.05.</p>
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13 pages, 4862 KiB  
Article
Diosmin and Hesperidin Have a Protective Effect in Diabetic Neuropathy via the FGF21 and Galectin-3 Pathway
by Birzat Emre Gölboyu, Mümin Alper Erdoğan, Mehmet Ali Çoşar, Ezgi Balıkoğlu and Oytun Erbaş
Medicina 2024, 60(10), 1580; https://doi.org/10.3390/medicina60101580 - 26 Sep 2024
Abstract
Background and Objectives: This study aimed to investigate the protective effect of diosmin and hesperidin in diabetic neuropathy using a rat model, focusing on their impact on nerve regeneration through the fibroblast growth factor 21 (FGF21) and galectin-3 (gal3) pathway. Materials and [...] Read more.
Background and Objectives: This study aimed to investigate the protective effect of diosmin and hesperidin in diabetic neuropathy using a rat model, focusing on their impact on nerve regeneration through the fibroblast growth factor 21 (FGF21) and galectin-3 (gal3) pathway. Materials and Methods: Forty adult male Wistar rats were used in this study. Diabetes was induced using streptozotocin (STZ), and the rats were divided into control, diabetes and saline-treated, diabetes and diosmin + hesperidin (150 mg/kg) treated, and diabetes and diosmin + hesperidin (300 mg/kg) treated groups. Electromyography (EMG) and inclined plane testing were performed to assess nerve function and motor performance. Sciatic nerve sections were examined histopathologically. Plasma levels of FGF21, galectin-3, and malondialdehyde (MDA) were measured as markers of oxidative stress and inflammation. Results: Diabetic rats treated with saline displayed reduced nerve conduction parameters and impaired motor performance compared to controls. Treatment with diosmin and hesperidin significantly improved compound muscle action potential (CMAP) amplitude, distal latency, and motor performance in a dose-dependent manner. Histopathological examination revealed decreased perineural thickness in treated groups. Additionally, treatment with diosmin and hesperidin resulted in increased plasma FGF21 levels and reduced plasma levels of galectin-3 and MDA, indicating decreased oxidative stress and inflammation. Conclusions: Diosmin and hesperidin exhibited protective effects in diabetic neuropathy by promoting nerve regeneration, enhancing nerve conduction, and improving motor performance. These effects were associated with modulation of the FGF21 and galectin-3 pathway. These findings suggest that diosmin and hesperidin may hold potential as adjunctive therapies for diabetic neuropathy. Full article
(This article belongs to the Section Endocrinology)
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<p>Electromyography (EMG) recording system: a Wistar rat placed in a supine position on a nonconductive surface, with electrodes strategically positioned to stimulate and record the electrical activity of the sciatic nerve. Stimulating electrodes (yellow arrow), recording electrode (red arrow), grounding electrode (white arrow head), EMG recording device (blue arrow), temperature control (black arrow).</p>
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<p>Inclined plane test system.</p>
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<p>(<b>a</b>) Control group EMG, (<b>b</b>) diabetic and saline treatment EMG, (<b>c</b>) diabetic and diosmin + hesperidin 150 mg/kg EMG, (<b>d</b>) diosmin + hesperidin 300 mg/kg treatment EMG. M-wave: the initial sharp peak, representing the direct muscle response (black arrow). H-reflex (if present): a secondary, smaller peak representing the reflexive response (empty white arrow).</p>
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<p>The histological sections of the sciatic nerve in different experimental groups stained with H and E (×40 magnification). These images are longitudinal sections of the nerve: (<b>A</b>) control group: the image shows a healthy sciatic nerve with a normal perineurium (p) and well-organized axons (a). (<b>B</b>) Diabetic group treated with saline: this section shows increased perineural thickness (p) compared to the control group, indicating nerve damage due to diabetes. (<b>C</b>) Diabetic group treated with diosmin + hesperidin (150 mg/kg): this section shows a decrease in perineural thickness (p) compared to the saline-treated diabetic group, suggesting a protective effect of the treatment. (<b>D</b>) Diabetic group treated with diosmin + hesperidin (300 mg/kg): similar to (<b>C</b>), this section shows further decreased perineural thickness (p), indicating a dose-dependent protective effect of the treatment. In each image, p indicates the perineurium, which is the protective sheath surrounding the nerve, and a marks the axons, the long thread-like parts of a nerve cell along which impulses are conducted.</p>
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17 pages, 3794 KiB  
Article
Multi-Regional Pelvic Floor Muscle Function Diagnosis System Based on Inflatable Stretchable Electrode Array
by Hailu Chen, Siming Wu, Yinfeng Wang, Yinjuan Chang, Mingjie Li, Zhenwei Xie and Shengming Wang
Healthcare 2024, 12(19), 1910; https://doi.org/10.3390/healthcare12191910 - 24 Sep 2024
Abstract
Background: Effective prevention and treatment of pelvic floor dysfunction (PFD) necessitates the identification of lesions within the complex pelvic floor muscle (PFM) groups associated with various symptoms. Here, we developed a multi-region pelvic floor muscle functional diagnosis system (MPDS) based on an inflatable [...] Read more.
Background: Effective prevention and treatment of pelvic floor dysfunction (PFD) necessitates the identification of lesions within the complex pelvic floor muscle (PFM) groups associated with various symptoms. Here, we developed a multi-region pelvic floor muscle functional diagnosis system (MPDS) based on an inflatable stretchable electrode array, which aids in accurately locating areas related to PFD. Methods: Clinical diagnostic experiments were conducted on 56 patients with postpartum stress urinary incontinence (PSUI) and 73 postpartum asymptomatic controls. MPDS collects pelvic floor electromyography from all participants. By assessing EMG parameters such as activation time differences (ATD) and using Jensen–Shannon (JS) divergence to verify, with the aim of locating target muscle groups with functional abnormalities. Results: Clinical test results showed that by observing the AT sequence of the PSUI group and the control group, muscle groups with functional abnormalities in the Pubococcygeus muscle (PC) and Puborectalis muscle (PR) regions could be preliminarily diagnosed. In the assessment of regional muscle contribution values based on JS divergence, it was verified that the contribution values of rapid contraction in the PC and PR regions of the PSUI group were relatively lower compared to those of the control group, which correlated with urinary control dysfunction. Conclusions: These experiments demonstrate that the MPDS helps in accurately locating target muscle groups with functional abnormalities, showcasing its potential in precise assessment of complex muscle groups such as PFM, which may improve diagnostic precision and reliability. Full article
(This article belongs to the Special Issue Pelvic Floor Health and Care)
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<p>ASEA probe and the concept of regional division based on physiology. (<b>a</b>) Structural diagram of ASEA and (<b>b</b>) physical diagram; (<b>c</b>) side view schematic of the TUI imaging process, taking TI images at a distance of 2.5 mm; (<b>d</b>) spatial relationship of the slices represented in the entire panel reconstructed from the corresponding TUI images in, the green arrows and lines represent the horizontal axes separated by equal distances, and the yellow arrows represent the direction of the vertical axes (<b>c</b>); (<b>e</b>) 3D anatomical model of the PFM corresponding to the transverse section of the pubic muscle (cyan); (<b>f</b>) 2D regional mapping diagram based on the 3D anatomical model; (<b>g</b>) distribution map of PFM 24-regions based on physiology, the black arrows represent the pairing of different electrode units; (<b>h</b>) double-layer 3D contour-surface topographic map based on multi-electrode unit parameters. The lower layer displays functional parameters such as muscle contraction force, and the upper layer displays deep-level information on muscle contribution.</p>
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<p>The system architecture of the MPDS. (<b>a</b>) Regionalized precise assessment process of the MPDS (<b>b</b>) Physical structure diagram of the MPDS.</p>
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<p>Electromyographic characteristic analysis. (<b>a</b>) sEMG waveform evaluated by Galzer. 1. Pre-Resting state (1 min); 2. rapid contraction (×5); 3. tonic contraction (×5); 4. endurance contraction (1 min); 5. post-resting state (1 min). (<b>b</b>) Schematic diagram of ATD in the VS and IC regions.</p>
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<p>The implementation diagram of the PFM regional contribution assessment method based on JS divergence.</p>
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<p>ATD Diagnosis Analysis of two groups. (<b>a</b>) ATD for slow-twitch muscles in participants from the PSUI group and the control group. The green dashed line represents the instruction time for initiating the action. (<b>b</b>) ATD values for slow-twitch muscles in 24 sets of collection points across 6 muscle regions for participants from both groups. The blue area represents Group A, the control group, while the red area represents Group B, the PSUI group. (<b>c</b>) ATD for fast-twitch muscles in participants from the PSUI group and the control group. The green dashed line represents the instruction time for initiating the action. (<b>d</b>) ATD values for fast-twitch muscles in 24 sets of collection points across 6 muscle regions for participants from both groups. The blue area represents Group A, the control group, while the red area represents Group B, the PSUI group.</p>
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<p>Slow-twitch and fast-twitch muscles contribution value evaluation of two groups. (<b>a</b>) For the control group and (<b>b</b>) PSUI group, the upper mapping plane represents the contour map of the TCP of slow-twitch, and the lower 3D surface represents the contribution value W of slow-twitch. Significant differences in parameters within the region can be observed. The yellow circle corresponds to the puborectalis muscle and the pubococcygeus muscle. It can be seen that in these two regions, the TCP of the upper plane and the contribution value W of the lower 3D surface exhibit similar trends. (<b>c</b>) For the control group and (<b>d</b>) the PSUI group, the upper mapping plane represents the contour map of the RCP of fast-twitch, and the lower 3D surface represents the contribution value W of fast-twitch. Significant differences in parameters within the region can be observed. The red circle corresponds to the pubovaginalis muscle, the yellow circle corresponds to the puborectalis muscle and the pubococcygeus muscle, and the green circle corresponds to the iliococcygeus muscle. It can be seen that in these three regions, the RCP of the upper plane and the contribution value W of the lower 3D surface exhibit similar trends.</p>
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11 pages, 2116 KiB  
Article
Therapeutic Potential of Vitamin B Complex in Peripheral Nerve Injury Recovery: An Experimental Rat Model Study
by Ahmet Kahraman, Metin Temel, Numan Atilgan, Ahmet Saray and Recep Dokuyucu
Medicina 2024, 60(9), 1556; https://doi.org/10.3390/medicina60091556 - 23 Sep 2024
Abstract
Objectives: Vitamin B complexes are frequently used in clinical practice for peripheral nerve trauma. However, there is a lack of scientific data on their effectiveness. This study aims to investigate the impact of the vitamin B complex on nerve recovery in a [...] Read more.
Objectives: Vitamin B complexes are frequently used in clinical practice for peripheral nerve trauma. However, there is a lack of scientific data on their effectiveness. This study aims to investigate the impact of the vitamin B complex on nerve recovery in a rat model of peripheral nerve paralysis. Materials and Methods: Sixty male Wistar Albino rats were divided into six groups. Models of nerve injury, including blunt trauma, nerve incision, and autograft, were performed on all rats approximately 1 cm distal to the sciatic notch. B-complex vitamins were injected intraperitoneally at 0.2 mL/day to the treatment groups. The control groups were given 0.2 mL/day saline. After 1 month, the study was terminated, electromyography (EMG) was performed to measure the conduction velocity, and nerve tissue was taken from the repair line. The sciatic function indexes (SFIs) were calculated and analyzed. The histopathological samples were stained with hematoxylin and eosin and Toluidine blue and examined with a light microscope. Pathologically, myelination, fibrosis, edema, and mast cell densities in the nervous tissue were evaluated. Results: The vitamin B treatment groups demonstrated significant improvements in SFI compared to the control groups, indicating functional improvement in nerve damage (p < 0.05). In the nerve graft group, the vitamin B group showed a shorter latency, higher velocity, and larger peak-to-peak compared to the controls (p < 0.05). In the nerve transection group, the vitamin B group had better latency, velocity, and peak-to-peak values than the controls (p < 0.05). In the crush injury group, the vitamin B group exhibited an improved latency, velocity, and peak-to-peak compared to the controls (p < 0.05). Better myelination, less fibrosis, edema, and mast cells were also in the vitamin B group (p < 0.05). Conclusions: Vitamin B treatment significantly improves nerve healing and function in peripheral nerve injuries. It enhances nerve conduction, reduces fibrosis, and promotes myelination, indicating its therapeutic potential in nerve regeneration. Full article
(This article belongs to the Special Issue Current Therapies for Trauma and Surgical Critical Care)
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<p>Surgical procedures according to groups.</p>
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<p>Comparison of sciatic function index (SFI) between groups.</p>
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<p>(<b>A</b>) In transverse sections stained with Giemsa and Mason, the connective tissue sheaths of the nerve appeared in their normal structure. (<b>B</b>) Minimal edema was evaluated between the axons as vacuolization in the endoneurium layer. Sections stained with phosphotungstic acid-hematoxylin (PTAH) displayed irregularities and variations in the thicknesses of the myelin sheaths, along with non-myelinated axons wrapped in Schwann cell sheaths among the myelinated axons. (<b>C</b>) In other transverse sections stained with Giemsa and Mason, dense fibrosis and small axons were observed around the nerve’s peripheral region, whereas medium-sized axons were detected in the central region without fibrosis. (<b>D</b>) Sections stained with PTAH showed that thin to medium-thick myelin sheaths were predominant, with occasional irregularities and fluctuations. Minimal fibrosis was found in the endoneural tissue between the axons, and unmyelinated axons were also present. (<b>E</b>) Additional sections stained with Giemsa and Mason revealed varying sizes of axon sections accompanied by minimal edema. (<b>F</b>) In sections stained with PTAH, medium-sized myelinated axons with regular myelin sheaths were primarily observed. Some myelinated axons exhibited vacuoles between the axolemma and myelin sheaths, and there were also partially [<a href="#B12-medicina-60-01556" class="html-bibr">12</a>] myelin-free axon sections.</p>
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16 pages, 3373 KiB  
Article
Simplified Cost Functions Meet Advanced Muscle Models to Streamline Muscle Force Estimation
by Muhammad Hassaan Ahmed, Jacques-Ezechiel N’Guessan, Ranjan Das, Matthew Leineweber and Sachin Goyal
BioMed 2024, 4(3), 350-365; https://doi.org/10.3390/biomed4030028 - 19 Sep 2024
Abstract
Background/Objectives: This study explores an optimization-based strategy for muscle force estimation by employing simplified cost functions integrated with physiologically relevant muscle models. Methods: Considering elbow flexion as a case study, we employ an inverse-dynamics approach to estimate muscle forces for the biceps brachii, [...] Read more.
Background/Objectives: This study explores an optimization-based strategy for muscle force estimation by employing simplified cost functions integrated with physiologically relevant muscle models. Methods: Considering elbow flexion as a case study, we employ an inverse-dynamics approach to estimate muscle forces for the biceps brachii, brachialis, and brachioradialis, utilizing different combinations of cost functions and muscle constitutive models. Muscle force generation is modeled by accounting for active and passive contractile behavior to varying degrees using Hill-type models. In total, three separate cost functions (minimization of total muscle force, mechanical work, and muscle stress) are evaluated with each muscle force model to represent potential neuromuscular control strategies without relying on electromyography (EMG) data, thereby characterizing the interplay between muscle models and cost functions. Results: Among the evaluated models, the Hill-type muscle model that incorporates both active and passive properties, combined with the stress minimization cost function, provided the most accurate predictions of muscle activation and force production for all three arm flexor muscles. Our results, validated against existing biomechanical data, demonstrate that even simplified cost functions, when paired with detailed muscle models, can achieve high accuracy in predicting muscle forces. Conclusions: This approach offers a versatile, EMG-free alternative for estimating muscle recruitment and force production, providing a more accessible and adaptable tool for muscle force analysis. It has profound implications for enhancing rehabilitation protocols and athletic training, not only broadening the applicability of muscle force estimation in clinical and sports settings but also paving the way for future innovations in biomechanical research. Full article
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<p>Flexion of the elbow joint is actuated by the group of three muscles: Biceps brachii, brachialis, and brachoradialis.</p>
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<p>Elbow joint torque during curl (<math display="inline"><semantics> <mrow> <mn>15</mn> <mo>°</mo> <mo>≤</mo> <mi>θ</mi> <mo>≤</mo> <mn>120</mn> <mo>°</mo> </mrow> </semantics></math>).</p>
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<p>The forces exerted by the three muscle groups (bic, bra and brd) on the forearm as a function of angle of flexion as estimated by employing three different muscle models (<b>a</b>–<b>c</b>) along with the three cost functions <math display="inline"><semantics> <msub> <mi>J</mi> <mn>1</mn> </msub> </semantics></math>, <math display="inline"><semantics> <msub> <mi>J</mi> <mn>2</mn> </msub> </semantics></math> and <math display="inline"><semantics> <msub> <mi>J</mi> <mn>3</mn> </msub> </semantics></math> (arranged column-wise). For the two Hill-type models (<b>b</b>,<b>c</b>), the muscle activations are also shown. <math display="inline"><semantics> <msub> <mi>T</mi> <mi>L</mi> </msub> </semantics></math> refers to linear tendon length change approximation.</p>
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<p>Moment arm variation of muscles groups during the curling motion (<math display="inline"><semantics> <mrow> <mn>15</mn> <mo>°</mo> <mo>≤</mo> <mi>θ</mi> <mo>≤</mo> <mn>120</mn> <mo>°</mo> </mrow> </semantics></math>).</p>
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<p>Variations in normalized muscle lengths during the elbow curl.</p>
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<p>Force Length Relationship (both active and passive) for the arm muscles as a function of their stretch ratio. Both active (<math display="inline"><semantics> <mrow> <msub> <mi>f</mi> <mi>a</mi> </msub> <mrow> <mo>(</mo> <msub> <mi>l</mi> <mi>m</mi> </msub> <mo>)</mo> </mrow> </mrow> </semantics></math>) and passive (<math display="inline"><semantics> <mrow> <msub> <mi>f</mi> <mi>p</mi> </msub> <mrow> <mo>(</mo> <msub> <mi>l</mi> <mi>m</mi> </msub> <mo>)</mo> </mrow> </mrow> </semantics></math>) forces are normalized by the maximum isometric force at optimal length for each muscle. Normalized lengths for each muscle are expressed relative to its optimum length.</p>
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<p>Comparison of Estimated Normalized Moment arm of (<b>a</b>) Bicep, (<b>b</b>) Brachialis and (<b>c</b>) Brachoradialis for an Elbow flexion with the calculated moments by Wendy et al. [<a href="#B41-biomed-04-00028" class="html-bibr">41</a>] for a male and female subject and with their 3D-Computer model.</p>
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<p>Normalized moment plots of (<b>a</b>) Biceps, (<b>b</b>) Brachialis and (<b>c</b>) Brachoradialis muscles, obtained from the three optimization techniques, <math display="inline"><semantics> <msub> <mi>J</mi> <mn>1</mn> </msub> </semantics></math> (Force criterion), <math display="inline"><semantics> <msub> <mi>J</mi> <mn>2</mn> </msub> </semantics></math> (Work criterion) and <math display="inline"><semantics> <msub> <mi>J</mi> <mn>3</mn> </msub> </semantics></math> (Stress criterion), considering Hill-Type Active and Passive muscle model, compared with muscle moments obtained from a computational model using ADAMS Software by Ilbeigi et al. [<a href="#B42-biomed-04-00028" class="html-bibr">42</a>].</p>
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14 pages, 1458 KiB  
Article
Data-Driven Stroke Classification Utilizing Electromyographic Muscle Features and Machine Learning Techniques
by Jaehyuk Lee, Youngjun Kim and Eunchan Kim
Appl. Sci. 2024, 14(18), 8430; https://doi.org/10.3390/app14188430 - 19 Sep 2024
Abstract
Background: Predicting a stroke in advance or through early detection of subtle prodromal symptoms is crucial for determining the prognosis of the remaining life. Electromyography (EMG) has the advantage of easy and quick collection of biological data in clinical settings; however, its application [...] Read more.
Background: Predicting a stroke in advance or through early detection of subtle prodromal symptoms is crucial for determining the prognosis of the remaining life. Electromyography (EMG) has the advantage of easy and quick collection of biological data in clinical settings; however, its application in data processing and utilization is somewhat limited. Thus, this study aims to verify how simple signal processing and feature extraction utilize EMG in machine learning (ML)-based prediction models. Methods: EMG data were collected from the legs of 120 healthy individuals and 120 stroke patients during gait. Four statistical features were extracted from 16 EMG signals and trained on seven ML-based models. The accuracy of the validation and test datasets was also examined. Results: The model with the best performance was Random Forest. Among the 16 EMG signals, the average and maximum values of the muscle activities involved in knee extension (i.e., vastus medialis and rectus femoris) contributed significantly to the predictions. Conclusion: The results of this study confirmed that the simple processing and feature extraction of EMG signals effectively contributed to the accuracy of ML-based models. Routine use of EMG data collected in clinical environments is expected to provide benefits in terms of stroke prevention and rehabilitation. Full article
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<p>A sample of raw EMG data and filtered EMG data used for training 6 machine learning models.</p>
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<p>Schematic of EMG data processing and feature extraction procedures.</p>
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<p>Variables with high feature importance in the RF model.</p>
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11 pages, 2497 KiB  
Article
Patient-Reported Outcome Measures and Biomechanical Variables That May Be Related to Knee Functions Following Total Knee Arthroplasty
by Hannah Seymour, Fangjian Chen and Naiquan (Nigel) Zheng
Bioengineering 2024, 11(9), 938; https://doi.org/10.3390/bioengineering11090938 - 19 Sep 2024
Abstract
Total knee arthroplasty (TKA) is a commonly performed surgery aimed at alleviating pain and improving functionality. However, patients often face uncertainties in selecting the timing, location, and type of TKA implant that best meets their needs. This study aims to comprehensively compare various [...] Read more.
Total knee arthroplasty (TKA) is a commonly performed surgery aimed at alleviating pain and improving functionality. However, patients often face uncertainties in selecting the timing, location, and type of TKA implant that best meets their needs. This study aims to comprehensively compare various variables, explore trends, and identify factors potentially influencing TKA outcomes. A cohort of 40 TKA subjects received either unilateral posterior stabilized (Persona) TKA or bi-cruciate stabilized (Journey II) TKA. Additionally, 20 healthy controls matched for age, gender, and BMI were included. Participants underwent patient-reported outcome assessments, range of motion evaluations, balance assessments, proprioception tests, and biomechanical analyses. These analyses covered motion, loading, and electromyography during five daily activities and two clinical tests. Multifactor ANOVA was utilized to compare 283 variables and assess their impact on TKA outcomes. A knee biomechanics index was formulated to evaluate deviations from healthy norms. Significant differences were observed in EMG varus/valgus rotation during both ramp-up and ramp-down phases between the two implant groups. Although significant improvements were noted post-TKA for both implants, the results remained below those of the control group. Gender, age, and BMI exhibited noticeable effects on TKA outcomes across several biomechanical variables and demonstrated significant disparities compared to the controls. Full article
(This article belongs to the Section Biomedical Engineering and Biomaterials)
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<p>Sketch of location for motion capture markers (circles) and EMG sensors (x) on the front and back of a subject with the dotted lines indicating the fixed belt (<b>left</b>) and front and back view of a subject with markers and EMG sensors attached (<b>right</b>).</p>
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<p>Cross plots for BMI (kg/m<sup>2</sup>) and age (years) for the bilateral ratio of the superior/inferior (SI) knee force during level walking.</p>
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<p>Knee biomechanics index for both implant types for female (F) and male (M) patients, with the maximum index score being 10 during level walking (LW), walking ramp-up (RU) or ramp-down (RD), and stair ascending (SA) and stair descending (SD).</p>
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12 pages, 6639 KiB  
Article
The Effects of High-Intensity, Short-Duration and Low-Intensity, Long-Duration Hamstrings Static Stretching on Contralateral Limb Performance
by Emily J. Philpott, Mohammadmahdi Bahrami, Mahta Sardroodian and David G. Behm
Sports 2024, 12(9), 257; https://doi.org/10.3390/sports12090257 - 18 Sep 2024
Abstract
Introduction: Increases in contralateral range of motion (ROM) have been shown following acute high-intensity and high-duration static stretching (SS) with no significant change in contralateral force, power, and muscle activation. There are currently no studies comparing the effects of a high-intensity, short-duration (HISD) [...] Read more.
Introduction: Increases in contralateral range of motion (ROM) have been shown following acute high-intensity and high-duration static stretching (SS) with no significant change in contralateral force, power, and muscle activation. There are currently no studies comparing the effects of a high-intensity, short-duration (HISD) or low-intensity, long-duration (LILD) SS on contralateral performance. Purpose: The aim of this study was to examine how HISD and LILD SS of the dominant leg hamstrings influence contralateral limb performance. Methods: Sixteen trained participants (eight females, eight males) completed three SS interventions of the dominant leg hamstrings; (1) HISD (6 × 10 s at maximal point of discomfort), (2) LILD (6 × 30 s at initial point of discomfort), and (3) control. Dominant and non-dominant ROM, maximal voluntary isometric contraction (MVIC) forces, muscle activation (electromyography (EMG)), and unilateral CMJ and DJ heights were recorded pre-test and 1 min post-test. Results: There were no significant contralateral ROM or performance changes. Following the HISD condition, the post-test ROM for the stretched leg (110.6 ± 12.6°) exceeded the pre-test (106.0 ± 9.0°) by a small magnitude effect of 4.2% (p = 0.008, d = 0.42). With LILD, the stretched leg post-test (112.2 ± 16.5°) exceeded (2.6%, p = 0.06, d = 0.18) the pre-test ROM (109.3 ± 16.2°) by a non-significant, trivial magnitude. There were large magnitude impairments, evidenced by main effects for testing time for force, instantaneous strength, and associated EMG. A significant ROM interaction (p = 0.02) showed that with LILD, the stretched leg significantly (p = 0.05) exceeded the contralateral leg by 13.4% post-test. Conclusions: The results showing no significant increase in contralateral ROM with either HISD or LILD SS, suggesting the interventions may not have been effective in promoting crossover effects. Full article
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<p>Isometric knee flexion apparatus.</p>
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13 pages, 2068 KiB  
Article
Kinematic, Neuromuscular and Bicep Femoris In Vivo Mechanics during the Nordic Hamstring Exercise and Variations of the Nordic Hamstring Exercise
by Nicholas Ripley, Jack Fahey, Paul Comfort and John McMahon
Muscles 2024, 3(3), 310-322; https://doi.org/10.3390/muscles3030027 - 18 Sep 2024
Abstract
The Nordic hamstring exercise (NHE) is effective at decreasing hamstring strain injury risk. Limited information is available on the in vivo mechanics of the bicep femoris long head (BFLH) during the NHE. Therefore, the purpose of this study was to observe [...] Read more.
The Nordic hamstring exercise (NHE) is effective at decreasing hamstring strain injury risk. Limited information is available on the in vivo mechanics of the bicep femoris long head (BFLH) during the NHE. Therefore, the purpose of this study was to observe kinematic, neuromuscular and in-vivo mechanics of the BFLH during the NHE. Thirteen participants (24.7 ± 3.7 years, 79.56 ± 7.89 kg, 177.40 ± 12.54 cm) performed three repetitions of the NHE at three horizontal planes (0°, 20° and −20°). Dynamic ultrasound of the dominant limb BFLH, surface electromyography (sEMG) of the contralateral hamstrings and sagittal plane motion data were simultaneously collected. Repeated measures analysis of variance with Bonferroni post hoc corrections were used on the in vivo mechanics and the kinematic and sEMG changes in performance of the NHE. Likely differences in ultrasound waveforms for the BFLH were determined. Significant and meaningful differences in kinematics and in vivo mechanics between NHE variations were observed. Non-significant differences were observed in sEMG measures between variations. Changes to the NHE performance angle manipulates the lever arm, increasing or decreasing the amount of force required by the hamstrings at any given muscle length, potentially changing the adaptive response when training at different planes and providing logical progressions ore regressions of the NHE. All NHE variations result in a similar magnitude of fascicle lengthening, which may indicate similar positive adaptations from the utilization of any variation. Full article
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<p>Nordic hamstring exercise variations: flat (0°), decline (−20°) and incline (20°).</p>
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<p>Custom-designed cast, housing a 10 cm ultrasound probe.</p>
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<p>Individual, mean, interquartile range, minimum, maximum and outliers within box-and-whisker plots for the kinematic measures of knee angle. (<b>A</b>) Knee angle at break point, (<b>B</b>) change in knee angle, (<b>C</b>) knee angle at break point relative to the horizontal.</p>
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<p>Individual absolute fascicle length waveforms with upper- and lower-bound 95% confidence intervals (shaded) between performance angles (INC = incline; DEC = decline).</p>
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<p>Individual relative fascicle length waveforms with upper- and lower-bound 95% confidence intervals (shaded) between performance angles.</p>
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<p>Time–knee extension angle and time–knee extension angular velocity graphs, identifying the moment of break point &gt;20°/s threshold.</p>
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Article
Comprehensive Study of Mechanical, Electrical and Biological Properties of Conductive Polymer Composites for Medical Applications through Additive Manufacturing
by Emese Paari-Molnar, Kinga Kardos, Roland Told, Imre Simon, Nitin Sahai, Peter Szabo, Judit Bovari-Biri, Alexandra Steinerbrunner-Nagy, Judit E. Pongracz, Szilard Rendeki and Peter Maroti
Polymers 2024, 16(18), 2625; https://doi.org/10.3390/polym16182625 - 17 Sep 2024
Abstract
Conductive polymer composites are commonly present in flexible electrodes for neural interfaces, implantable sensors, and aerospace applications. Fused filament fabrication (FFF) is a widely used additive manufacturing technology, where conductive filaments frequently contain carbon-based fillers. In this study, the static and dynamic mechanical [...] Read more.
Conductive polymer composites are commonly present in flexible electrodes for neural interfaces, implantable sensors, and aerospace applications. Fused filament fabrication (FFF) is a widely used additive manufacturing technology, where conductive filaments frequently contain carbon-based fillers. In this study, the static and dynamic mechanical properties and the electrical properties (resistance, signal transmission, resistance measurements during cyclic tensile, bending and temperature tests) were investigated for polylactic acid (PLA)-based, acrylonitrile butadiene styrene (ABS)-based, thermoplastic polyurethane (TPU)-based, and polyamide (PA)-based conductive filaments with carbon-based additives. Scanning electron microscopy (SEM) was implemented to evaluate the results. Cytotoxicity measurements were performed. The conductive ABS specimens have a high gauge factor between 0.2% and 1.0% strain. All tested materials, except the PA-based conductive composite, are suitable for low-voltage applications such as 3D-printed EEG and EMG sensors. ABS-based and TPU-based conductive composites are promising raw materials suitable for temperature measuring and medical applications. Full article
(This article belongs to the Special Issue 3D Printing of Polymer Composites)
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<p>Method of the study.</p>
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<p>(<b>a</b>) Photograph (ESD-ABS). (<b>b</b>) Schematic representation of the specimens for the tensile–resistance test.</p>
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<p>Measuring equipment for temperature–resistance measurements. The specimen was insulated and fixed to the printing bed with Kapton tape. On the top, between the tape and the specimen, a thermistor was inserted, and the sample was connected to the voltage divider on both sides.</p>
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<p>Schematic representation of mixed flexural specimen.</p>
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<p>Schematic representation of the signal transfer measurements.</p>
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<p>Results of the tensile tests of ESD-ABS, ESD-PLA, ESD-TPU, and ESD-Onyx.</p>
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<p>Results of three-point bending tests of all tested materials.</p>
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<p>Experimental data from the Shore D hardness and Charpy Impact tests for all tested materials.</p>
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<p>(<b>a</b>) Resistance, standard travel for an ESD-ABS specimen with 100 µm layer height, the maximums were marked with black dots. (<b>b</b>) Maximum resistance, standard travel for the same specimen. The black dots indicate the maxima per cycle and the line indicates the fitted curve.</p>
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<p>Standard force and electrical resistance in elongation curve in case of the ESD-TPU specimen with 200 µm layer height. Dashed lines indicate the boundaries of the sections for the different gauge factors, and the percentage values show these elongation limits.</p>
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<p>Tensile force and electric resistance as a function of time in the case of ESD-TPU specimen with 200 µm layer height.</p>
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<p>Temperature–electrical resistance relationship for an ESD-ABS specimen with 200 µm layer height. (<b>a</b>) First day measurement and (<b>b</b>) repeated, second day measurement.</p>
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<p>Temperature–electrical resistance relationship for an ESD-TPU specimen with 200 µm layer height. (<b>a</b>) First measurement and (<b>b</b>) repeated, second measurement.</p>
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<p>Resistance during flexural test in the case of the ABS-ESD-ABS mixed specimen.</p>
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<p>Resistance during flexural test in the case of TPU-ESD-TPU mixed specimen.</p>
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<p>Bode plots with attenuation and standard deviation. ESD-PLA (<b>a</b>), ESD-ABS (<b>b</b>), ESD-TPU (<b>c</b>), and ESD-Onyx (<b>d</b>).</p>
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<p>SEM images of the fracture surface of (<b>a</b>) ESD-PLA, (<b>b</b>) ESD-ABS at 15,000× magnification (scale bar is 1 µm). The black dashed ellipses indicate the carbon black granules and black dashed rectangles show the carbon nanotubes.</p>
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<p>SEM image of the fracture surface of ESD-TPU at 100× magnification.</p>
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<p>Fracture surface of ESD-Onyx material at 250× magnification. The black dashed ellipses indicate micro carbon fibres, and arrows show holes on the surface.</p>
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<p>Light microscopic images of A549 cell lines following a 48 h incubation in the presence of various 3D printed materials (magnification: 20×, scale bar: 50 µm).</p>
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<p>Quantification of the living cell number after 48 h incubation of A549 cells in the presence of various 3D-printed inserts (statistical analysis was performed in GraphPad 9 software, using one-way ANOVA with Kolmogorov–Smirnov normality test, n = 9, error bars represent SD, significance levels were labelled according to the following: <span class="html-italic">p</span> &lt; 0.0001 (****) "ns" indicates that the bias was not significant.</p>
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19 pages, 10978 KiB  
Article
The Impact of Physiological and Psychological Fatigue on Work Efficiency: A Case Study of Parcel Sorting Work
by Miaomiao Li, Zuqin Ma, Rui Yan and Jielin Yin
Sensors 2024, 24(18), 5989; https://doi.org/10.3390/s24185989 - 15 Sep 2024
Abstract
The popularity of online shopping in China has increased significantly, creating new development opportunities for the express delivery industry. However, the rapid expansion of the express industry has also created challenges in the parcel sorting process. The demanding nature of parcel sorting work, [...] Read more.
The popularity of online shopping in China has increased significantly, creating new development opportunities for the express delivery industry. However, the rapid expansion of the express industry has also created challenges in the parcel sorting process. The demanding nature of parcel sorting work, which is characterized by intense and prolonged repetitive tasks, makes individuals particularly vulnerable to the effects of fatigue. Fatigue is a complex condition that encompasses both physiological and psychological exhaustion. It often results in reduced energy levels and diminished functionality, significantly impacting an individual’s performance at work and their overall well-being. This study aimed to investigate how physiological and psychological fatigue affects sorting efficiency and to identify appropriate rest periods that will allow employees to maintain their performance levels. The research involved fifteen participants who took part in a 60 min continuous sorting experiment and a similar experiment with scheduled breaks. During both trials, we collected data on participants’ electromyography (EMG) and electrodermal activity (EDA), as well as subjective fatigue ratings (RPE). Signal features such as the median frequency (MF) of EMG and the skin conductance level (SCL) were analyzed to assess physiological and psychological fatigue, respectively. The results show that physiological fatigue mainly affects sorting efficiency in the first 30 min, while psychological fatigue becomes more influential in the following half-hour period. In addition, subjective fatigue levels during the first 30 min are primarily determined by psychological factors, while beyond that point, both physiological and psychological fatigue contribute to subjective fatigue. Rest periods of 415–460 s, based on EDA recovery times, effectively support sorting efficiency and participants’ recovery. This study highlights the complex ways in which fatigue affects parcel sorting performance and provides valuable theoretical and practical insights for establishing labor quotas and optimizing work schedules in the parcel sorting industry. Full article
(This article belongs to the Section Intelligent Sensors)
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<p>The parcel sorting experiment employed three distinct types of boxes, which were labelled A, B, and C to represent the small, medium, and large sizes, respectively.</p>
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<p>The experimental setup, which shows the environment and tasks. The three blue sorting bins, labelled A, B, and C, are the designated areas for different types of parcels.</p>
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<p>Photo of electrode placement. The photo on the left illustrates the placement of electrodes for the collection of EMG data, while the photo on the right shows the positioning of the EDA data electrodes.</p>
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<p>Illustration of physiological signal stabilization, with EMG on the top and EDA on the bottom. EMG1 Raw Data: The original raw EMG data; EMG1 Processed: The filtered and normalized EMG data; EDA1 Raw Data: The original raw EDA data; SC: Skin conductance level; Tonic Data: The tonic component of the EDA.</p>
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<p>Sorting count over time.</p>
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<p>Correlation matrices for different experiments. Only significant correlations are displayed. The numbers in the matrices represent the Pearson correlation coefficients. The figure is organized vertically with Experiment A on top and Experiment B below. The data for each experiment are divided into three segments horizontally, from left to right: total duration, the first 30 min, and the last 30 min.</p>
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<p>The EMG illustrates the change in movement patterns of the participants during a work task. The corresponding video snapshots from the experiment provide visual evidence of the changes in movement patterns at the highlighted times. A Before change. B After change.</p>
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