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Search Results (1,082)

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Keywords = exoskeletons

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20 pages, 3715 KiB  
Article
L-GABS: Parametric Modeling of a Generic Active Lumbar Exoskeleton for Ergonomic Impact Assessment
by Manuel Pérez-Soto, Javier Marín and José J. Marín
Sensors 2025, 25(5), 1340; https://doi.org/10.3390/s25051340 - 22 Feb 2025
Viewed by 245
Abstract
Companies increasingly implement exoskeletons in their production lines to reduce musculoskeletal disorders. Studies have been conducted on the general ergonomic effects of exoskeletons in production environments; however, it remains challenging to predict the biomechanical effects these devices may have in specific jobs. This [...] Read more.
Companies increasingly implement exoskeletons in their production lines to reduce musculoskeletal disorders. Studies have been conducted on the general ergonomic effects of exoskeletons in production environments; however, it remains challenging to predict the biomechanical effects these devices may have in specific jobs. This article proposes the parametric modeling of an active lumbar exoskeleton using the Forces ergonomic method, which calculates the ergonomic risk using motion capture in the workplace, considering the internal joint forces. The exoskeleton was studied to model it in the Forces method using a four-phase approach based on experimental observations (Phase 1) and objective data collection via motion capture with inertial sensors and load cells for lifting load movements. From the experimentation the angles of each body segment, the effort perceived by the user, and the activation conditions were obtained (Phase 2). After modeling development (Phase 3), the experimental results regarding the force and risk were evaluated obtaining differences between model and experimental data of 0.971 ± 0.171 kg in chest force and 1.983 ± 0.678% in lumbar risk (Phase 4). This approach provides a tool to evaluate the biomechanical effects of this device in a work task, offering a parametric and direct approximation of the effects prior to implementation. Full article
(This article belongs to the Special Issue Wearable Robotics and Assistive Devices)
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<p>Apogee active exoskeleton diagram (images from Apogee User Manual).</p>
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<p>Apogee exoskeleton configuration examples and legend.</p>
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<p>Model diagram forces (right: R, left: L) from Delgado et al. [<a href="#B15-sensors-25-01340" class="html-bibr">15</a>] modified for Apogee Exoskeleton.</p>
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<p>Load cell assembly for force measurement. Experimentation with motion capture and synchronized force measurement. CAD drawing of load cell assembly (1: Load cell, 2: Ad hoc 3D printed part with a threaded insert, 3: Adjustable back support, 4: Casing with electric motors at the side).</p>
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<p>Experimental diagram.</p>
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<p>(<b>a</b>) Averaged chest force curves experimentally obtained concerning lumbar flexion. (<b>b</b>) Modeled passive torque curves on each side.</p>
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<p>(<b>a</b>) Averaged chest force curves obtained experimentally concerning lumbar angular velocity. (<b>b</b>) Modeled active torque curves on each side.</p>
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<p>Force measured on the chest compared to the force simulated by the model. (<b>a</b>) Passive assistance comparison. (<b>b</b>) Active assistance comparison. (<b>c</b>) Active Mod. assistance comparison.</p>
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<p>Force measured on the chest compared to the force simulated by the model. (<b>a</b>) Passive assistance comparison. (<b>b</b>) Active assistance comparison. (<b>c</b>) Active Mod. assistance comparison.</p>
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<p>Comparison of the hybrid assistance. Force measured on the chest compared to force simulated by the model.</p>
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20 pages, 9566 KiB  
Article
Investigation of Trajectory Tracking Control in Hip Joints of Lower-Limb Exoskeletons Using SSA-Fuzzy PID Optimization
by Wei Li, Xiaojie Wei, Dawen Sun, Siyu Zong and Zhengwei Yue
Sensors 2025, 25(5), 1335; https://doi.org/10.3390/s25051335 - 22 Feb 2025
Viewed by 245
Abstract
The application of lower-limb exoskeleton robots in rehabilitation is becoming more prevalent, where the precision of control and the speed of response are essential for effective movement tracking. This study tackles the challenge of optimizing both control accuracy and response speed in trajectory [...] Read more.
The application of lower-limb exoskeleton robots in rehabilitation is becoming more prevalent, where the precision of control and the speed of response are essential for effective movement tracking. This study tackles the challenge of optimizing both control accuracy and response speed in trajectory tracking for lower-limb exoskeleton hip robots. We introduce an optimization strategy that integrates the Sparrow Search Algorithm (SSA) with fuzzy Proportional-Integral-Derivative (PID) control. This approach addresses the inefficiencies and time-consuming process of manual parameter tuning, thereby improving trajectory tracking performance. First, recognizing the complexity of hip joint motion, which involves multiple degrees of freedom and intricate dynamics, we employed the Lagrangian method. This method is particularly effective for handling nonlinear systems and simplifying the modeling process, allowing for the development of a dynamic model for the hip joint. The SSA is subsequently utilized for the online self-tuning optimization of both the proportional and quantization factors within the fuzzy PID controller. Simulation experiments confirm the efficacy of this strategy in tracking hip joint trajectories during flat walking and standing hip flexion rehabilitation exercises. Experimental results from diverse test populations demonstrate that SSA-fuzzy PID control improves response times by 27.8% (for flat walking) and 30% (for standing hip flexion) when compared to traditional PID control, and by 6% and 2%, respectively, relative to fuzzy PID control. Regarding tracking accuracy, the SSA-fuzzy PID approach increases accuracy by 81.4% (for flat walking) and 80% (for standing hip flexion) when compared to PID control, and by 57.5% and 56.8% relative to fuzzy PID control. The proposed strategy significantly improves both control accuracy and response speed, offering substantial theoretical support for rehabilitation training in individuals with lower-limb impairments. Moreover, in comparison to existing methods, this approach uniquely tackles the challenges of parameter tuning and optimization, presenting a more efficient solution for trajectory tracking in exoskeleton systems. Full article
(This article belongs to the Section Biomedical Sensors)
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<p>Dynamic model of the hip joint.</p>
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<p>Structure of the PID control system.</p>
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<p>Principle of the fuzzy PID controller structure.</p>
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<p>Membership function of input and output variables.</p>
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<p>Fuzzy surfaces of Δk<sub>p</sub>, Δk<sub>i</sub>, and Δk<sub>d</sub>.</p>
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<p>Flowchart of SSA-fuzzy PID parameter optimization.</p>
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<p>Iteration plot of SSA algorithm adaptation degree.</p>
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<p>Parameter variations in the optimized SSA algorithm system. (<b>a</b>) Change in Ke and Kec parameters; (<b>b</b>) change in Ckp, Cki and Ckd parameters.</p>
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<p>Simulation models. (<b>a</b>) Proportional-Integral-Derivative (PID) controller; (<b>b</b>) fuzzy PID controller.</p>
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<p>Simulation model of the Sparrow Search Algorithm (SSA)-based fuzzy PID controller.</p>
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<p>Comparison of hip joint motion trajectory tracking curves during human-level walking using three control methods.</p>
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<p>Comparison of tracking errors in hip joint motion trajectory during human-level walking using three control methods.</p>
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<p>Comparison of trajectory tracking curves for standing hip flexion motion using three control methods.</p>
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<p>Comparison of tracking errors in standing hip flexion trajectory using three control methods.</p>
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<p>Experimental platform for the lower-limb exoskeleton hip robot. (<b>a</b>) Experimental platform; (<b>b</b>) lower-limb exoskeleton hip robot.</p>
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<p>Motion data acquisition process for Testers A, B, and C wearing the lower-limb exoskeleton device. (<b>a</b>) Acquisition of motion data for Testers A, B, and C while walking on level ground; (<b>b</b>) collection of standing hip flexion movement data for Testers A, B, and C.</p>
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<p>Comparison of hip joint trajectories and tracking errors during level walking for Testers A, B, and C under the three control methods. (<b>a</b>) Comparison of hip joint trajectory tracking curves during level walking for Tester A; (<b>b</b>) comparison of hip joint trajectory tracking errors during level walking for Tester A; (<b>c</b>) comparison of hip joint trajectory tracking curves during level walking for Tester B; (<b>d</b>) comparison of hip joint trajectory tracking errors during level walking for Tester B; (<b>e</b>) comparison of hip joint trajectory tracking curves during level walking for Tester C; (<b>f</b>) comparison of hip joint trajectory tracking errors during level walking for Tester C.</p>
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<p>Comparison of the trajectories and tracking errors of standing hip flexion movements for Testers A, B, and C under the three control methods. (<b>a</b>) Comparison of trajectory tracking curves for Tester A’s standing hip flexion movement; (<b>b</b>) comparison of tracking errors for Tester A’s standing hip flexion trajectory; (<b>c</b>) comparison of trajectory tracking curves for Tester B’s standing hip flexion movement; (<b>d</b>) comparison of tracking errors for Tester B’s standing hip flexion trajectory; (<b>e</b>) comparison of trajectory tracking curves for Tester C’s standing hip flexion movement; (<b>f</b>) comparison of tracking errors for Tester C’s standing hip flexion trajectory.</p>
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<p>Comparison of the trajectories and tracking errors of standing hip flexion movements for Testers A, B, and C under the three control methods. (<b>a</b>) Comparison of trajectory tracking curves for Tester A’s standing hip flexion movement; (<b>b</b>) comparison of tracking errors for Tester A’s standing hip flexion trajectory; (<b>c</b>) comparison of trajectory tracking curves for Tester B’s standing hip flexion movement; (<b>d</b>) comparison of tracking errors for Tester B’s standing hip flexion trajectory; (<b>e</b>) comparison of trajectory tracking curves for Tester C’s standing hip flexion movement; (<b>f</b>) comparison of tracking errors for Tester C’s standing hip flexion trajectory.</p>
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59 pages, 3714 KiB  
Review
Advances in Control Techniques for Rehabilitation Exoskeleton Robots: A Systematic Review
by Gazi Mashud, SK Hasan and Nafizul Alam
Actuators 2025, 14(3), 108; https://doi.org/10.3390/act14030108 - 21 Feb 2025
Viewed by 142
Abstract
This systematic review explores recent advancements in control methods for rehabilitation exoskeleton robots, which assist individuals with motor impairments through guided movement. As robotics technology progresses, precise, adaptable, and safe control techniques have become accessible for effective human–robot interaction in rehabilitation settings. Key [...] Read more.
This systematic review explores recent advancements in control methods for rehabilitation exoskeleton robots, which assist individuals with motor impairments through guided movement. As robotics technology progresses, precise, adaptable, and safe control techniques have become accessible for effective human–robot interaction in rehabilitation settings. Key control methods, including computed torque and adaptive control, excel in managing complex movements and adapting to diverse patient needs. Robust and sliding mode controls address stability under unpredictable conditions. Traditional approaches, like PD and PID control schemes, maintain stability, performance, and simplicity. In contrast, admittance control enhances user–robot interaction by balancing force and motion. Advanced methods, such as model predictive control (MPC) and Linear Quadratic Regulator (LQR), provide optimization-based solutions. Intelligent controls using neural networks, Deep Learning, and reinforcement learning offer adaptive, patient-specific solutions by learning over time. This review provides an in-depth analysis of these control strategies by examining advancements in recent scientific literature, highlighting their potential to improve rehabilitation exoskeletons, and offering future recommendations for greater efficiency, responsiveness, and patient-centered functionality. Full article
(This article belongs to the Section Actuators for Robotics)
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<p>Flow chart of the search and inclusion process.</p>
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<p>Robot dynamics including the friction model.</p>
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<p>Computed torque control architecture.</p>
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<p>Architecture of a sliding mode controller.</p>
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<p>Architecture of a sliding mode controller with chattering suppressor.</p>
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<p>Architecture of a Linear Quadratic Regulator.</p>
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<p>Simplified control architecture of a PD controller.</p>
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<p>Robot control architecture of a PID controller.</p>
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<p>Generalized control architecture of an AI-based controller.</p>
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20 pages, 4945 KiB  
Article
At-Home Stroke Neurorehabilitation: Early Findings with the NeuroExo BCI System
by Juan José González-España, Lianne Sánchez-Rodríguez, Maxine Annel Pacheco-Ramírez, Jeff Feng, Kathryn Nedley, Shuo-Hsiu Chang, Gerard E. Francisco and Jose L. Contreras-Vidal
Sensors 2025, 25(5), 1322; https://doi.org/10.3390/s25051322 - 21 Feb 2025
Viewed by 222
Abstract
Background: Democratized access to safe and effective robotic neurorehabilitation for stroke survivors requires innovative, affordable solutions that can be used not only in clinics but also at home. This requires the high usability of the devices involved to minimize costs associated with support [...] Read more.
Background: Democratized access to safe and effective robotic neurorehabilitation for stroke survivors requires innovative, affordable solutions that can be used not only in clinics but also at home. This requires the high usability of the devices involved to minimize costs associated with support from physical therapists or technicians. Methods: This paper describes the early findings of the NeuroExo brain–machine interface (BMI) with an upper-limb robotic exoskeleton for stroke neurorehabilitation. This early feasibility study consisted of a six-week protocol, with an initial training and BMI calibration phase at the clinic followed by 60 sessions of neuromotor therapy at the homes of the participants. Pre- and post-assessments were used to assess users’ compliance and system performance. Results: Participants achieved a compliance rate between 21% and 100%, with an average of 69%, while maintaining adequate signal quality and a positive perceived BMI performance during home usage with an average Likert scale score of four out of five. Moreover, adequate signal quality was maintained for four out of five participants throughout the protocol. These findings provide valuable insights into essential components for comprehensive rehabilitation therapy for stroke survivors. Furthermore, linear mixed-effects statistical models showed a significant reduction in trial duration (p-value < 0.02) and concomitant changes in brain patterns (p-value < 0.02). Conclusions: the analysis of these findings suggests that a low-cost, safe, simple-to-use BMI system for at-home stroke rehabilitation is feasible. Full article
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<p>Timeline and phases of the early-feasibility testing for the NeuroExo BMI-exoskeleton system.</p>
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<p>Graphics user interface (GUI) depicting the visual feedback provided to the user during the positioning of the NeuroExo device on the head. The impedance of EEG electrodes—scalp and EOG sensors—face are color-coded from low impedance (white) to high impedance (black) values. The correct positioning of the headset leads to lower impedance values.</p>
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<p>An example of a participant fitted with the NeuroExo device and upper-limb exoskeleton while performing a trial at home. The tablet allowed the participant to set up the system and receive visual feedback (reproduced with permission from [<a href="#B12-sensors-25-01322" class="html-bibr">12</a>]).</p>
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<p>Characterizations of the performance of the NeuroExo system in terms of users’ compliance, perceived BCI performance, and electrode signal quality. (<b>a</b>). For each of the five participants with chronic stroke, the age, sex, impaired side, and home state are provided. Each graph depicts the level of electrode impedance [0, <math display="inline"><semantics> <mrow> <mn>100</mn> <mspace width="3.33333pt"/> <mi mathvariant="normal">k</mi> <mo>Ω</mo> </mrow> </semantics></math>] (five symbols are used to code for electrode location along the frontocentral scalp in the 10–20 system). Users’ compliance is denoted as the number of blocks performed by the users per week in a counterclockwise direction (shading). The percentage of adequate impedance values (&lt;=<math display="inline"><semantics> <mrow> <mn>100</mn> <mspace width="3.33333pt"/> <mi mathvariant="normal">k</mi> <mo>Ω</mo> </mrow> </semantics></math>) per week is shown in parenthesis. Note that participant S3 conducted NeuroExo therapy over 18 weeks due to therapy interruptions caused by extensive travel. Perceived BCI performance is color-coded by week on each graph. (<b>b</b>). The signal quality distribution is shown; the majority of the percentages for adequate impedances are located in upper buckets. Key: * indicates that these participants did not receive any assistance from family or friends during therapy.</p>
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<p>Trial block duration decreased with training. Boxplots display the distribution of impedance data across weeks and participants, with a linear fit overlaid to highlight trends in trial block duration (min) over time. Red + symbol indicates the outliers in the data. The fit was performed using MATLAB’s polynomial curve fitting function. Key: * indicates that these participants did not receive assistance from family members or friends during the trial.</p>
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<p>MRCP amplitude in early versus late sessions. Early MRCPs in blue represent the MRCP across a block of trials at the beginning of this longitudinal study and green MRCPs represent the last block of trials at the end of the longitudinal study. The annotation of the impedance values is provided to assess signal quality. Key: * indicates that these participants were not assisted by family members/friends.</p>
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<p>AUC amplitude in FC1, FCz, and FC2 in early versus late sessions. Each graph shows the early versus late Area Under the Curve (AUC) computed from the first and last two blocks in this longitudinal study for every participant by channel location. Red + symbol indicate the outliers in the data.</p>
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<p>Newest NeuroExo headset version. Based on user feedback, some of the joints were reinforced, the micro-USB was replaced with USB-C, and the positioning of the EEG electrodes was more stable and easy to adjust.</p>
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<p>System assessment survey. Survey taken by participants after every session. It includes five prompts to assess usability, comfort, and perceived BCI performance of system.</p>
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11 pages, 4279 KiB  
Article
Soft, Stretchable, High-Sensitivity, Multi-Walled Carbon Nanotube-Based Strain Sensor for Joint Healthcare
by Zechen Guo, Xiaohe Hu, Yaqiong Chen, Yanwei Ma, Fuqun Zhao and Sheng Guo
Nanomaterials 2025, 15(5), 332; https://doi.org/10.3390/nano15050332 - 21 Feb 2025
Viewed by 129
Abstract
Exoskeletons play a crucial role in joint healthcare by providing targeted support and rehabilitation for individuals with musculoskeletal diseases. As an assistive device, the accurate monitoring of the user’s joint signals and exoskeleton status using wearable sensors is essential to ensure the efficiency [...] Read more.
Exoskeletons play a crucial role in joint healthcare by providing targeted support and rehabilitation for individuals with musculoskeletal diseases. As an assistive device, the accurate monitoring of the user’s joint signals and exoskeleton status using wearable sensors is essential to ensure the efficiency of conducting complex tasks in various scenarios. However, balancing sensitivity and stretchability in wearable devices for exoskeleton applications remains a significant challenge. Here, we introduce a wearable strain sensor for detecting finger and knee joint motions. The sensor utilizes a stretchable elastic conductive network, incorporating multi-walled carbon nanotubes (MWCNTs) into Ecoflex. The concentration of MWCNTs has been meticulously optimized to achieve both a high gauge factor (GF) and stability. With its high sensitivity, the sensor is enabled to be applied in the angle monitoring of finger joints. By integrating the sensor with human knee joints and an exoskeleton device, it can simultaneously detect the flexion and extension movements in real-time. This sensor holds significant potential for enhancing exoskeleton performance and improving joint healthcare technologies. Full article
(This article belongs to the Special Issue Advanced Nanotechnology in Intelligent Flexible Devices)
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<p>(<b>a</b>) Schematic illustration of the strain sensor and (<b>b</b>) the fabrication process.</p>
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<p>(<b>a</b>) Scanning electron microscopy (SEM) image of the multi-walled carbon nanotubes (MWCNTs) with a nanoscale diameter. (<b>b</b>) High-resolution field-emission scanning electron microscopy (HRTEM) image of MWCNTs. (<b>c</b>–<b>e</b>) SEM images of the surfaces of the sensing layer with MWCNTs weight fractions of 6.5 wt%, 7.0 wt%, and 7.5 wt%. (<b>f</b>) Cross-sectional view of the sensor with MWCNTs weight fraction of 7.0 wt%.</p>
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<p>(<b>a</b>) Raman spectra of the MWCNTs embedded in Ecoflex with a weight fraction of 7.0 wt% compared with that of the Ecoflex elastomeric matrix and pristine MWCNTs. (<b>b</b>) Comparison of the position and full width at half maximum (FHWM) of the D line and (<b>c</b>) G line for MWCNTs and MWCNTs/Ecoflex.</p>
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<p>(<b>a</b>) Relative resistance variation curves as tensile strain changes within the strain range of 0 to 105% of the sensors. (<b>b</b>) Real-time ∆<span class="html-italic">R</span>/<span class="html-italic">R</span><sub>0</sub> strain curves under various tensile strains. The inset shows the real-time response upon applied 15% tensile strain.</p>
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<p>Change mechanism of the MWCNTs-embedded elastomer under applied strain.</p>
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<p>Comparison of the performance of the sensor and those reported in the literature [<a href="#B10-nanomaterials-15-00332" class="html-bibr">10</a>,<a href="#B16-nanomaterials-15-00332" class="html-bibr">16</a>,<a href="#B17-nanomaterials-15-00332" class="html-bibr">17</a>,<a href="#B23-nanomaterials-15-00332" class="html-bibr">23</a>,<a href="#B24-nanomaterials-15-00332" class="html-bibr">24</a>,<a href="#B25-nanomaterials-15-00332" class="html-bibr">25</a>,<a href="#B31-nanomaterials-15-00332" class="html-bibr">31</a>].</p>
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<p>(<b>a</b>) Real-time frequency response of the strain sensor. (<b>b</b>) Relative ∆<span class="html-italic">R</span>/<span class="html-italic">R</span><sub>0</sub> variation curve at different tensile frequencies at a strain of 30%.</p>
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<p>(<b>a</b>) Dynamic stretch and release cycle response of the sensor under various strains (15–75%). (<b>b</b>) Real-time fatigue resistance of the sensor at 30% strain for 2000 loading–release cycles.</p>
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<p>Strain sensor used for joint movement detection. (<b>a</b>) Bending and extension movement detection of the sensor on interphalangeal joints (PIPs) of the index finger. (<b>b</b>) Grasping cylinders with different diameters (20 mm, 40 mm, 60 mm, 80 mm, and 100 mm). (<b>c</b>) Detection of the bending and extension of the knee joint.</p>
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<p>Exoskeleton movement monitoring with different bending angles. (<b>a</b>) Photograph of the sensor on an exoskeleton device. (<b>b</b>) Exoskeleton movement monitoring during flexion and extension at angles of 30°, 60°, and 90°.</p>
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16 pages, 1584 KiB  
Article
Utilization of Classification Learning Algorithms for Upper-Body Non-Cyclic Motion Prediction
by Bon H. Koo, Ho Chit Siu, Dava J. Newman, Ellen T. Roche and Lonnie G. Petersen
Sensors 2025, 25(5), 1297; https://doi.org/10.3390/s25051297 - 20 Feb 2025
Viewed by 262
Abstract
This study explores two methods of predicting non-cyclic upper-body motions using classification algorithms. Exoskeletons currently face challenges with low fluency, hypothesized to be in part caused by the lag in active control innate in many leader–follower paradigms seen in today’s systems, leading to [...] Read more.
This study explores two methods of predicting non-cyclic upper-body motions using classification algorithms. Exoskeletons currently face challenges with low fluency, hypothesized to be in part caused by the lag in active control innate in many leader–follower paradigms seen in today’s systems, leading to energetic inefficiencies and discomfort. To address this, we employ k-nearest neighbor (KNN) and deep learning models to predict motion characteristics, such as magnitude and category, from surface electromyography (sEMG) signals. Data were collected from six muscles located around the elbow. The sEMG signals were processed to identify significant activation changes. Two classification approaches were utilized: a KNN algorithm that categorizes motion based on the slopes of processed sEMG signals at change points and a deep neural network employing continuous categorization. Both methods demonstrated the capability to predict future voluntary non-cyclic motions up to and beyond commonly acknowledged electromechanical delay times, with the deep learning model able to predict, with certainty at or beyond 90%, motion characteristics even prior to myoelectric activation of the muscles involved. Our findings indicate that these classification algorithms can be used to predict upper-body non-cyclic motions to potentially increase machine interfacing fluency. Further exploration into regression-based prediction models could enhance the precision of these predictions, and further work could explore their effects on fluency when utilized in a tandem or wearable robotic application. Full article
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<p>A block diagram of the KNN raw data processing pipeline. The raw data consisted of 6 channels of 5 trials.</p>
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<p>A block diagram of the classification neural network’s structure. The exact design of each layer depends on input parameters, namely the number of features.</p>
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<p>A confusion matrix showing the performance of a Bayesian process-optimized KNN classification prediction algorithm. The class numbers on both axes represent unique motion groups, with 12 different groups in total, as elaborated in <a href="#sensors-25-01297-t002" class="html-table">Table 2</a>. Overall accuracy approaches 0.93, but certain motion groups are more frequently confused with others, as seen in the off-diagonals. Also shown are the true positive rate (TPR) and the false negative rate (FNR).</p>
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<p>Plot showing an example of the evolution of <math display="inline"><semantics> <mrow> <mi>P</mi> <mo>(</mo> <mi>c</mi> <mi>l</mi> <mi>a</mi> <mi>s</mi> <mi>s</mi> <mo>)</mo> </mrow> </semantics></math> over time during an EMG activation cycle. All 12 <math display="inline"><semantics> <mrow> <mi>P</mi> <mo>(</mo> <mi>c</mi> <mi>l</mi> <mi>a</mi> <mi>s</mi> <mi>s</mi> <mo>)</mo> </mrow> </semantics></math> values are plotted, with each line’s opacity corresponding to its mean <math display="inline"><semantics> <mrow> <mi>P</mi> <mo>(</mo> <mi>c</mi> <mi>l</mi> <mi>a</mi> <mi>s</mi> <mi>s</mi> <mo>)</mo> </mrow> </semantics></math>. Notice the incline in the correct <math display="inline"><semantics> <mrow> <mi>P</mi> <mo>(</mo> <mi>c</mi> <mi>l</mi> <mi>a</mi> <mi>s</mi> <mi>s</mi> <mo>)</mo> </mrow> </semantics></math> prior to the noticeable innervation of the primary agonist, which is the only EMG signal visible in the plot.</p>
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<p>Examples of the trajectories that <math display="inline"><semantics> <mrow> <mi>P</mi> <mo>(</mo> <mi>c</mi> <mi>l</mi> <mi>a</mi> <mi>s</mi> <mi>s</mi> <mo>)</mo> </mrow> </semantics></math> follows through trials of different magnitudes/motion groups. In subfigure (<b>a</b>), the prediction algorithm reaches certainty prior to the apparent myoelectric activation of the agonist muscle group, and that certainty remains dominant throughout the motion. This represents the majority of trials where the prediction algorithm performed nominally. However, in cases where no certainty was reached, the trajectories resembled those in subfigure (<b>b</b>), where there is no clear dominant prediction in terms of <math display="inline"><semantics> <mrow> <mi>P</mi> <mo>(</mo> <mi>c</mi> <mi>l</mi> <mi>a</mi> <mi>s</mi> <mi>s</mi> <mo>)</mo> </mrow> </semantics></math>, and, therefore, no reference point exists.</p>
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<p>A series of diagrams graphically representing the different motions prescribed to subjects. The exact magnitude (such as small or large) was up to the interpretation of the subject based on a visual guide without strict enforcement. Subfigure (<b>a</b>) is a visual representation of a subject performing the small or large elbow flexion motion from a lateral view, with torque application denoted with an arrow. Subfigure (<b>b</b>) is a visual representation of a subject performing the small or large elbow extension motion from a lateral view, with torque application denoted with an arrow. Subfigure (<b>c</b>) is a visual representation of a subject performing the small or large arm flexion motion from a lateral view, with torque application denoted with an arrow. Subfigure (<b>d</b>) is a visual representation of a subject performing the small or large arm extension motion from a lateral view, with torque application denoted with an arrow. Subfigure (<b>e</b>) is a visual representation of a subject performing the small or large arm abduction motion from a frontal view, with torque application denoted with an arrow. Subfigure (<b>f</b>) is a visual representation of a subject’s lower arm and wrist performing the small or large wrist extension motion from a lateral view.</p>
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<p>A series of diagrams graphically representing the different motions prescribed to subjects. The exact magnitude (such as small or large) was up to the interpretation of the subject based on a visual guide without strict enforcement. Subfigure (<b>a</b>) is a visual representation of a subject performing the small or large elbow flexion motion from a lateral view, with torque application denoted with an arrow. Subfigure (<b>b</b>) is a visual representation of a subject performing the small or large elbow extension motion from a lateral view, with torque application denoted with an arrow. Subfigure (<b>c</b>) is a visual representation of a subject performing the small or large arm flexion motion from a lateral view, with torque application denoted with an arrow. Subfigure (<b>d</b>) is a visual representation of a subject performing the small or large arm extension motion from a lateral view, with torque application denoted with an arrow. Subfigure (<b>e</b>) is a visual representation of a subject performing the small or large arm abduction motion from a frontal view, with torque application denoted with an arrow. Subfigure (<b>f</b>) is a visual representation of a subject’s lower arm and wrist performing the small or large wrist extension motion from a lateral view.</p>
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19 pages, 4921 KiB  
Article
Sports Biomechanics Analysis: Assisting Effectiveness Evaluations for Wearable Compliant Elbow Joint Powered Exoskeleton
by Huibin Qin, Kai Liu, Zefeng Zhang, Jie Zheng, Zhili Hou, Lina Li and Ruiqin Li
Machines 2025, 13(2), 168; https://doi.org/10.3390/machines13020168 - 19 Feb 2025
Viewed by 211
Abstract
Wearing an exoskeleton, the human body constantly experiences mechanical loading. However, quantifying internal loads within the musculoskeletal system remains challenging, especially during unconstrained dynamic activities such as manual material handling. Currently, exoskeleton systems are commonly integrated with sensor technologies to gather data and [...] Read more.
Wearing an exoskeleton, the human body constantly experiences mechanical loading. However, quantifying internal loads within the musculoskeletal system remains challenging, especially during unconstrained dynamic activities such as manual material handling. Currently, exoskeleton systems are commonly integrated with sensor technologies to gather data and assess performances. This is mainly performed to evaluate the physical exoskeletons, and cannot provide real-time feedback during the development phase. Firstly, a powered wearable elbow exoskeleton with variable stiffness is proposed. Through theoretical calculation, the power efficiency formula of exoskeleton is derived. Then, a human musculoskeletal model is built using the AnyBody Modeling System and coupled to the elbow exoskeleton. Under set experimental conditions, the simulation reveals that, when compared with the exoskeleton, the biceps and triceps muscle force parameters of the human model were reduced by 24% and 12%. The muscle activity was diminished by 28–31%, and muscle length shortened by about 6%, in comparison to the condition without the exoskeleton. Finally, through the muscle force experiment, it was verified that the power efficiency of the elbow exoskeleton in the real transport was about 18%. The project reduces costs in the development phase of the exoskeleton and can provide new insights into muscle function and sports biomechanics. Full article
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<p>Muscle stress of elbow flexion and extension [<a href="#B16-machines-13-00168" class="html-bibr">16</a>]. (<b>a</b>) Elbow flexion. (<b>b</b>) Elbow extension.</p>
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<p>Powered wearable compliant elbow joint exoskeleton structure design schematic diagram.</p>
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<p>Internal structure design of the variable stiffness compliant elbow joint.</p>
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<p>Simplified mechanical model of human body handling.</p>
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<p>Simplified mechanical model of human carrying action after wearing elbow joint.</p>
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<p>A schematic diagram of the Hill model.</p>
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<p>Simulation diagram of handling action.</p>
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<p>Human–machine integration model in the AnyBody Modeling System.</p>
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<p>Curve of selected muscle force change. (<b>a</b>) Biceps muscle strength change curve. (<b>b</b>) Triceps muscle strength change curve.</p>
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<p>Curve of maximum muscle activation. (<b>a</b>) Maximum biceps muscle activation. (<b>b</b>) Maximum triceps muscle activation.</p>
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<p>Curve of selected muscle length. (<b>a</b>) Bicep length curve. (<b>b</b>) Triceps length curve.</p>
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<p>Experimental platform and composition of handling aid.</p>
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<p>The mounting of the FSR sensor on the sensor band [<a href="#B15-machines-13-00168" class="html-bibr">15</a>].</p>
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<p>The process of subjects lifting heavy objects.</p>
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<p>The mean histogram of FSRs for the extension process. (<b>a</b>) Histogram of biceps FSR mean during extension. (<b>b</b>) Histogram of FSR mean of triceps during extension.</p>
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<p>Mean histogram of FSR for flexion process. (<b>a</b>) Histogram of biceps FSR mean during flexion. (<b>b</b>) Histogram of triceps FSR mean during flexion.</p>
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17 pages, 3574 KiB  
Article
Genome-Wide Identification and Expression Analyses of Glycoside Hydrolase Family 18 Genes During Nodule Symbiosis in Glycine max
by Rujie Li, Chuanjie Gou, Ke Zhang, Milan He, Lanxin Li, Fanjiang Kong, Zhihui Sun and Huan Liu
Int. J. Mol. Sci. 2025, 26(4), 1649; https://doi.org/10.3390/ijms26041649 - 14 Feb 2025
Viewed by 309
Abstract
Glycoside hydrolase family 18 (GH18) proteins can hydrolyze the β-1,4-glycosidic bonds of chitin, which is a common structure component of insect exoskeletons and fungal cell walls. In this study, 36 GH18 genes were identified and subjected to bioinformatic analysis based on the genomic [...] Read more.
Glycoside hydrolase family 18 (GH18) proteins can hydrolyze the β-1,4-glycosidic bonds of chitin, which is a common structure component of insect exoskeletons and fungal cell walls. In this study, 36 GH18 genes were identified and subjected to bioinformatic analysis based on the genomic data of Glycine max. They were distributed in 16 out of 20 tested soybean chromosomes. According to the amino acid sequences, they can be further divided into five subclades. Class III chitinases (22 members) and class V chitinases (6 members) are the major two subclades. The amino acid size of soybean GH18 proteins ranges from 173 amino acids (aa) to 820 aa and the molecular weight ranges from 19.46 kDa to 91.01 kDa. From an evolutionary perspective, soybean GH18 genes are closely related to Medicago (17 collinear loci with soybean) and Lotus (23 collinear loci with soybean). Promoter analysis revealed that GH18 genes could be induced by environmental stress, hormones, and embryo development. GmGH18-15, GmGH18-24, and GmGH18-33 were screened out due to their nodulation specific expression and further verified by RT-qPCR. These results provide an elaborate reference for the further characterization of specific GH18 genes, especially during nodule formation in soybean. Full article
(This article belongs to the Special Issue Genetics and Novel Techniques for Soybean Pivotal Characters)
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<p>Chromosome mapping of the <span class="html-italic">GH18</span> genes in <span class="html-italic">G. max</span>. Here, 20 soybean chromosomes were displayed in scale with a ruler beside. The position of each <span class="html-italic">GH18</span> gene was clearly marked on the chromosomes. The yellow to blue gradient represents different gene density, with yellow as high gene density region and blue as low gene density region.</p>
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<p>Phylogenetic analysis and protein structure identification of <span class="html-italic">GH18</span> genes in soybean. (<b>a</b>) A phylogenetic tree was constructed by the Maximum Likelihood method. Bootstrap tests with 1000 replicates were performed. (<b>b</b>) Here, 10 conserved motifs and 10 conserved domains were identified in soybean GH18 proteins, respectively.</p>
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<p>Phylogenetic analysis of GH18 proteins in soybean, Medicago, and Lotus. Based on the HMM search result of PF00704, 36, 47, and 18 putative GH18 proteins were identified in soybean, Medicago, and Lotus, respectively. They were further divided into 6 groups using the Maximum Likelihood method implemented on MEGA7.0. There were 50 genes in the class III chitinase clade, 23 genes in the class V chitinase clade, 3 genes in the stabilin-1 interacting chitinase-like protein clade (SI-CLP), 3 genes in the chitinase-like superfamily, 6 genes in the narbonin clade, and 16 genes in the Medicago-specific GH18 clade, respectively. Due to the reported biological function in legume–rhizobium symbiosis, MtGH18-20 (MtNFH1), MtGH18-21 (MtCHIT5b), and LjGH18-12 (LjChit5) are highlighted in red.</p>
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<p>Collinearity analysis of <span class="html-italic">GH18</span> genes in soybean. Here, 20 soybean chromosomes were arranged in circle. Gray lines represent the gene pairs in the whole genome. Red lines highlight the collinear relationship within the <span class="html-italic">GH18</span> gene family.</p>
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<p>Collinearity analysis of <span class="html-italic">GH18</span> genes between two species of soybean, Medicago, and Lotus. Collinearity analysis was performed between two given species: soybean–Medicago (<b>a</b>), soybean–Lotus (<b>b</b>), and Medicago–Lotus (<b>c</b>). Gray lines from the background show all collinear gene pairs between two genomes, while red lines highlight the collinear relationship within the GH18 family.</p>
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<p>Cis-acting element analysis of <span class="html-italic">GH18</span> gene promoter regions in <span class="html-italic">G. max</span>. 41 <span class="html-italic">GH18</span> gene promoter sequences (−2000 bp upstream of ATG) are obtained from <span class="html-italic">G. max</span> Wm82 genome (a2.v1). The gene symbols are listed on the left and the nucleotide positions are labeled at the bottom. In total, 13 cis-acting elements are identified, whose potential biological functions are related to drought responsiveness, anaerobic responsiveness, light responsiveness, gibberellin responsiveness, abscisic acid responsiveness, defense/stress responsiveness, low-temperature responsiveness, endosperm expression, zein metabolism regulation, meristem expression, Methyl jasmonate (MeJA) responsiveness, salicylic acid responsiveness, and auxin responsiveness.</p>
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<p>Expression profile of soybean <span class="html-italic">GH18</span> genes and rhizobial responsiveness validation by RT-qPCR. (<b>a</b>) The <span class="html-italic">GH18</span> gene expression pattern was extracted from the soybean RNA sequencing data [<a href="#B32-ijms-26-01649" class="html-bibr">32</a>] and displayed in the heatmap. According to their expression levels in pods, root hairs, leaves, roots, nodules, seeds, shoot apical meristems (SAM), stems, and flowers, 36 soybean <span class="html-italic">GH18</span> genes were grouped into 5 categories. Group 4 was highlighted, because members from this group are nodulation-specific (N.S.). (<b>b</b>–<b>d</b>) RT-qPCR validation of the expression behavior of group 4 members under symbiotic conditions. <span class="html-italic">G. max</span> Wm82 plants were inoculated with <span class="html-italic">Bradyrhizobium japonicum</span> USDA110; the transcript levels of <span class="html-italic">GmGH18-15</span>, <span class="html-italic">GmGH18-24</span>, and <span class="html-italic">GmGH18-33</span> in the roots (within 7 days post inoculation) and nodules (14 and 21 dpi) were measured (<span class="html-italic">n</span> = 3). The <span class="html-italic">Actin</span> gene served as a reference. Data indicate means ± SE of normalized expression values (mean value of control set to one). The asterisks indicate significantly increased expression compared to control roots without rhizobial inoculation (Student’s <span class="html-italic">t</span>-test; * <span class="html-italic">p</span> &lt; 0.05, ** <span class="html-italic">p</span> &lt; 0.01, *** <span class="html-italic">p</span> &lt; 0.001).</p>
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18 pages, 7357 KiB  
Article
Validation of Cable-Driven Experimental Setup to Assess Movements Made with Elbow Joint Assistance
by Sreejan Alapati, Deep Seth, Sanjeevi Nakka and Yannick Aoustin
Appl. Sci. 2025, 15(4), 1892; https://doi.org/10.3390/app15041892 - 12 Feb 2025
Viewed by 375
Abstract
This article investigates a cable-driven experimental setup to simulate elbow joint assistance in the sagittal plane provided by an exosuit. Cable-driven exosuits, particularly fabric-based designs, significantly enhance rehabilitation by enabling targeted joint exercises and promoting functional recovery. To achieve an optimal design, these [...] Read more.
This article investigates a cable-driven experimental setup to simulate elbow joint assistance in the sagittal plane provided by an exosuit. Cable-driven exosuits, particularly fabric-based designs, significantly enhance rehabilitation by enabling targeted joint exercises and promoting functional recovery. To achieve an optimal design, these devices require an analysis of the cable tension, reaction forces, and moments and their dependency on the anchor position. This study presents a cable-driven experimental setup with two rigid bars and variable anchor positions, designed to mimic the human forearm, upper arm, and elbow joint, to evaluate the performance of a potential cable-driven exosuit. Based on the experimental setup, a static model was developed to validate the measured cable tension and estimate the reaction force at the joint and the moments at the anchor positions. Furthermore, based on the observations, an optimization problem was defined to identify optimal anchor positions to improve the exosuit’s design. The optimal position on the forearm and upper arm is studied between 15% and 50% distance from the elbow joint. Our findings suggest that prioritizing user comfort requires both anchor points to be as far away from the elbow joint as possible, i.e., 50% distance, whereas, for optimal exosuit performance, the forearm anchor position can be adjusted based on the joint angle while keeping the upper arm anchor position at the farthest point. The findings in the current work can be used to decide the anchor point position for designing an elbow exosuit. Full article
(This article belongs to the Special Issue New Trends in Exoskeleton Robot)
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<p>(<b>I</b>,<b>II</b>) show the experimental setup mimicking the human upper limb in two different joint positions, i.e., <math display="inline"><semantics> <mrow> <mn>90</mn> <mo>°</mo> </mrow> </semantics></math> and <math display="inline"><semantics> <mrow> <mn>120</mn> <mo>°</mo> </mrow> </semantics></math>, as represented in (<b>V</b>,<b>VI</b>). (<b>III</b>,<b>IV</b>) highlights the components of the experimental setup which are the motor, cable, and load cell with a display.</p>
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<p>(<b>a</b>) Experimental setup to test cable under cyclic loading [<a href="#B30-applsci-15-01892" class="html-bibr">30</a>]. (<b>b</b>) Bar graph highlighting the number of cycles to failure for different cables under different weights.</p>
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<p>Schematic representation of the experimental setup. (<b>I</b>) highlights the geometrical parameters and (<b>II</b>) highlights the angles. Angles are positive in an anti-clockwise direction, with (<b>III</b>) highlighting the various forces on the experimental setup and moment at the elbow joint.</p>
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<p>(<b>a</b>–<b>f</b>) Surface plots of simulated tension, <math display="inline"><semantics> <msub> <mi>T</mi> <msub> <mi>s</mi> <mrow> <mi>s</mi> <mi>i</mi> <mi>m</mi> </mrow> </msub> </msub> </semantics></math>, with variations in anchor positions <math display="inline"><semantics> <msub> <mi>d</mi> <mn>1</mn> </msub> </semantics></math> and <math display="inline"><semantics> <msub> <mi>d</mi> <mn>2</mn> </msub> </semantics></math>, at joint positions <math display="inline"><semantics> <mrow> <mn>90</mn> <mo>°</mo> </mrow> </semantics></math> and <math display="inline"><semantics> <mrow> <mn>120</mn> <mo>°</mo> </mrow> </semantics></math>, and masses 0.5 kg, 1 kg, and 2 kg. Discrete dots along the surface plot represent the experimentally recorded tension, <math display="inline"><semantics> <msub> <mi>T</mi> <msub> <mi>s</mi> <mrow> <mi>e</mi> <mi>x</mi> <mi>p</mi> </mrow> </msub> </msub> </semantics></math> values.</p>
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<p>(<b>a</b>–<b>f</b>) Surface plots of the simulated reaction force at the elbow, with the variation in anchor position <math display="inline"><semantics> <msub> <mi>d</mi> <mn>1</mn> </msub> </semantics></math> and <math display="inline"><semantics> <msub> <mi>d</mi> <mn>2</mn> </msub> </semantics></math> at joint positions <math display="inline"><semantics> <mrow> <mn>90</mn> <mo>°</mo> </mrow> </semantics></math>, and <math display="inline"><semantics> <mrow> <mn>120</mn> <mo>°</mo> </mrow> </semantics></math> and masses 0.5 kg, 1 kg, and 2 kg. Discrete dots along the surface plot represent the reaction force calculated using the experimentally recorded tension.</p>
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<p>(<b>a</b>–<b>f</b>) Surface plots of the simulated moment at the anchor position <span class="html-italic">A</span>, by varying <math display="inline"><semantics> <msub> <mi>d</mi> <mn>1</mn> </msub> </semantics></math> and <math display="inline"><semantics> <msub> <mi>d</mi> <mn>2</mn> </msub> </semantics></math>, at joint positions <math display="inline"><semantics> <mrow> <mn>90</mn> <mo>°</mo> </mrow> </semantics></math> and <math display="inline"><semantics> <mrow> <mn>120</mn> <mo>°</mo> </mrow> </semantics></math> and masses 0.5 kg, 1 kg, and 2 kg. Discrete dots along the surface plot represent the moment at <span class="html-italic">A</span> calculated using the experimentally recorded tension.</p>
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<p>(<b>a</b>–<b>f</b>) Surface plots of the simulated moment at the anchor position <span class="html-italic">C</span>, by varying <math display="inline"><semantics> <msub> <mi>d</mi> <mn>1</mn> </msub> </semantics></math> and <math display="inline"><semantics> <msub> <mi>d</mi> <mn>2</mn> </msub> </semantics></math> at joint positions <math display="inline"><semantics> <mrow> <mn>90</mn> <mo>°</mo> </mrow> </semantics></math> and <math display="inline"><semantics> <mrow> <mn>120</mn> <mo>°</mo> </mrow> </semantics></math> and masses 0.5 kg, 1 kg, and 2 kg. Discrete dots along the surface plot represent the moment at <span class="html-italic">C</span> calculated using the experimentally recorded tension.</p>
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<p>(<b>a</b>) Variation in optimal anchor positions, <math display="inline"><semantics> <msub> <mi>d</mi> <mn>1</mn> </msub> </semantics></math> and <math display="inline"><semantics> <msub> <mi>d</mi> <mn>2</mn> </msub> </semantics></math>, along the elbow joint angle in order to minimize the moment generated at anchor positions. (<b>b</b>) <b>I</b>–<b>III</b> depict the scenario of cable attached at different values of <math display="inline"><semantics> <msub> <mi>d</mi> <mn>1</mn> </msub> </semantics></math> and <math display="inline"><semantics> <msub> <mi>d</mi> <mn>2</mn> </msub> </semantics></math> for joint positions <math display="inline"><semantics> <mrow> <mn>55</mn> <mo>°</mo> </mrow> </semantics></math>, <math display="inline"><semantics> <mrow> <mn>90</mn> <mo>°</mo> </mrow> </semantics></math>, and <math display="inline"><semantics> <mrow> <mn>120</mn> <mo>°</mo> </mrow> </semantics></math>. Green and red cables represent optimal and non-optimal positions.</p>
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<p>(<b>a</b>) Variation in optimal anchor positions, <math display="inline"><semantics> <msub> <mi>d</mi> <mn>1</mn> </msub> </semantics></math> and <math display="inline"><semantics> <msub> <mi>d</mi> <mn>2</mn> </msub> </semantics></math>, with respect to the elbow joint angle in order to minimize cable tension and the reaction force at the elbow joint. (<b>b</b>) <b>I</b>–<b>III</b> depict the scenario of cable attached at different values of <math display="inline"><semantics> <msub> <mi>d</mi> <mn>1</mn> </msub> </semantics></math> and <math display="inline"><semantics> <msub> <mi>d</mi> <mn>2</mn> </msub> </semantics></math> for joint positions <math display="inline"><semantics> <mrow> <mn>55</mn> <mo>°</mo> </mrow> </semantics></math>, <math display="inline"><semantics> <mrow> <mn>90</mn> <mo>°</mo> </mrow> </semantics></math>, and <math display="inline"><semantics> <mrow> <mn>120</mn> <mo>°</mo> </mrow> </semantics></math>. Green and red cables represent optimal and non-optimal positions.</p>
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26 pages, 9349 KiB  
Article
Long Short-Term Memory-Enabled Electromyography-Controlled Adaptive Wearable Robotic Exoskeleton for Upper Arm Rehabilitation
by S. M. U. S. Samarakoon, H. M. K. K. M. B. Herath, S. L. P. Yasakethu, Dileepa Fernando, Nuwan Madusanka, Myunggi Yi and Byeong-Il Lee
Biomimetics 2025, 10(2), 106; https://doi.org/10.3390/biomimetics10020106 - 12 Feb 2025
Viewed by 699
Abstract
Restoring strength, function, and mobility following an illness, accident, or surgery is the primary goal of upper arm rehabilitation. Exoskeletons offer adaptable support, enhancing patient engagement and accelerating recovery. This work proposes an adjustable, wearable robotic exoskeleton powered by electromyography (EMG) data for [...] Read more.
Restoring strength, function, and mobility following an illness, accident, or surgery is the primary goal of upper arm rehabilitation. Exoskeletons offer adaptable support, enhancing patient engagement and accelerating recovery. This work proposes an adjustable, wearable robotic exoskeleton powered by electromyography (EMG) data for upper arm rehabilitation. Three activation levels—low, medium, and high—were applied to the EMG data to forecast the Pulse Width Modulation (PWM) based on the range of motion (ROM) angle. Conventional machine learning (ML) models, including K-Nearest Neighbor Regression (K-NNR), Support Vector Regression (SVR), and Random Forest Regression (RFR), were compared with neural network approaches, including Gated Recurrent Units (GRUs) and Long Short-Term Memory (LSTM) to determine the best ML model for the ROM angle prediction. The LSTM model emerged as the best predictor with a high accuracy of 0.96. The system achieved 0.89 accuracy in exoskeleton control and 0.85 accuracy in signal categorization. Additionally, the proposed exoskeleton demonstrated a 0.97 performance in ROM correction compared to conventional methods (p = 0.097). These findings highlight the potential of EMG-based, LSTM-enabled exoskeleton systems to deliver accurate and adaptive upper arm rehabilitation, particularly for senior citizens, by providing personalized and effective support. Full article
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<p>The overall architecture of the proposed system.</p>
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<p>CAD design of the proposed robotic exoskeleton device.</p>
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<p>The exoskeleton prototype developed for the ROM exercise.</p>
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<p>Motion and safety limits of the exoskeleton.</p>
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<p>The architecture of the proposed AI model selection methodology.</p>
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<p>Closed-loop control mechanism of the exoskeleton device.</p>
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<p>Exoskeleton prototype. Image of an individual wearing the exoskeleton system (the device is in a non-operating state).</p>
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<p>Signal behavior before and after the preprocessing procedure.</p>
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<p>Flexion and extension regions of the EMG signals during the experiment.</p>
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<p>DL model performance evaluation. (<b>A</b>) Graph of the MAE of the GRU, (<b>B</b>) graph of the RMSE of the GRU, (<b>C</b>) graph of the MAE of the LSTM model, and (<b>D</b>) graph of the RMSE of the LSTM model.</p>
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<p>Actual angles vs. predicted angles for the LSTM model.</p>
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<p>(<b>A</b>) Low muscle activation during ROM exercises, (<b>B</b>) medium muscle activation during ROM exercises, and (<b>C</b>) high muscle activation during ROM exercises.</p>
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<p>Confusion matrix of the different activation levels during the experiment.</p>
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<p>PWM output of the exoskeleton at the (<b>A</b>) EMG<sub>L</sub>, (<b>B</b>) EMG<sub>M</sub>, and (<b>C</b>) EMG<sub>H</sub> stages during ROM exercises.</p>
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<p>(<b>A</b>) EMG signal for low activation, (<b>B</b>) PWM for low activation, (<b>C</b>) EMG signal for medium activation, (<b>D</b>) PWM for medium activation, (<b>E</b>) EMG signal for high activation, and (<b>F</b>) PWM for high activation.</p>
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<p>Time–frequency analysis of the low activation test case.</p>
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<p>Time–frequency analysis of the medium activation test case.</p>
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<p>Time–frequency analysis of the high activation test case.</p>
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<p>ROM angle comparison of individuals with high, medium, and low activation during exercises with the traditional method and exoskeleton method.</p>
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<p>Performance of the traditional method and exoskeleton method during the 12 weeks of exercises.</p>
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24 pages, 11320 KiB  
Article
Mechanism Design of a Novel Device to Facilitate Mobility, Sit-to-Stand Transfer Movement, and Walking Assistance
by Bo Li, Xinzhili Chen, Hailiang Liu, Dong Yuan, Jiafeng Zhang and Shiqing Lu
Machines 2025, 13(2), 134; https://doi.org/10.3390/machines13020134 - 10 Feb 2025
Viewed by 404
Abstract
To assist patients with lower limb dysfunction in mobility, standing, and walking, this paper proposes a novel device that integrates the functions of lower limb exoskeleton, wheelchair, and sit-to-stand (STS) transfer assistance. We designed a 10-degree-of-freedom lower limb exoskeleton based on gait analysis. [...] Read more.
To assist patients with lower limb dysfunction in mobility, standing, and walking, this paper proposes a novel device that integrates the functions of lower limb exoskeleton, wheelchair, and sit-to-stand (STS) transfer assistance. We designed a 10-degree-of-freedom lower limb exoskeleton based on gait analysis. To satisfy human–machine compatibility, the hip joint was conceptualized as a remote center-of-motion (RCM) mechanism, the knee joint was developed as a cam mechanism, and the ankle joint was designed as a revolute pair. We constructed a kinematic model of the exoskeleton by adopting the product-of-exponential (POE) formula. The STS transfer assistance mechanism was designed based on Stephenson III six-bar linkage through path synthesis methods. The length of this six-bar mechanism was determined based on using Newton–Jacobi iterative techniques. We connected the STS assistive mechanism to the wheelchair frame, and then, we connected the exoskeleton to the STS transfer assistive mechanism. The experimental results demonstrated that the STS assistance path aligned closely with human buttock trajectories, and the walking assistance paths corresponded with natural human gaits. This device produces a new choice for patients with lower limb dysfunction. Full article
(This article belongs to the Section Machine Design and Theory)
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<p>Gait analysis: (<b>a</b>) walking simulation in OpenSim; (<b>b</b>) rotation angle of hip, knee, and ankle joints. (<b>c</b>) Torque of hip, knee, and ankle joints.</p>
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<p>Configuration synthesis of hip joints: (<b>a</b>) three revolute pairs served as hip joints; (<b>b</b>) configuration of hip joints.</p>
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<p>Structure of hip joint.</p>
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<p>Design of knee joint: (<b>a</b>) human knee joint; (<b>b</b>) cam mechanism; (<b>c</b>) knee joint of exoskeleton.</p>
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<p>Ankle joint mechanism: (<b>a</b>) human ankle; (<b>b</b>) ankle joint of exoskeleton.</p>
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<p>Exoskeleton model: (<b>a</b>) configuration of the exoskeleton; (<b>b</b>) mechanism design of the exoskeleton.</p>
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<p>Kinematics coordinate system of the exoskeleton.</p>
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<p>Paden–Kahan definition of inverse kinematics: (<b>a</b>) first subproblem; (<b>b</b>) second subproblem; (<b>c</b>) third subproblem.</p>
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<p>Simulation process of human wearing the exoskeleton to walk.</p>
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<p>Comparation between simulation and theoretical path during walking locomotion: (<b>a</b>) path of knee joint; (<b>b</b>) path of foot joint.</p>
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<p>The workspace of the lower extremity exoskeleton on the sagittal plane during walking.</p>
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<p>The process of STS motion of heathy human: (<b>a</b>) initial stage; (<b>b</b>) balance stage; (<b>c</b>) rising stage; (<b>d</b>) stabilization stage.</p>
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<p>Coordinate variation in the hip joint on the sagittal plane during STS locomotion [<a href="#B29-machines-13-00134" class="html-bibr">29</a>].</p>
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<p>Simplified diagram of the linkage mechanism: (<b>a</b>) planar four-bar linkage; (<b>b</b>) Stephenson III six-bar mechanism.</p>
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<p>The configuration of the STS assistive mechanism.</p>
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<p>The STS assistive mechanism with the indication of the motion process.</p>
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<p>The STS assistive mechanism: (<b>a</b>) simplified diagram of the STS assistive mechanism; (<b>b</b>) prototype of the STS assistive mechanism.</p>
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<p>Structure of wheelchair: (<b>a</b>) prototype diagram of the wheelchair frame; (<b>b</b>) prototype diagram of wheelchair.</p>
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<p>Schematic diagram of the STS simulation: (<b>a</b>) sitting posture; (<b>b</b>) process of sit-to-stand transfer; (<b>c</b>) standing posture.</p>
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<p>Comparison between simulated and theoretical path of the hip joint during the STS process.</p>
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<p>Integration of the exoskeleton and STS assistive mechanism.</p>
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<p>System model: (<b>a</b>) sitting model; (<b>b</b>) standing model; (<b>c</b>) walking model.</p>
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<p>STS experiment preparation: (<b>a</b>) test scheme; (<b>b</b>) attached marker balls; (<b>c</b>) participant test.</p>
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<p>The comparison path of the buttock.</p>
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<p>Walking experiment preparation: (<b>a</b>) test scheme; (<b>b</b>) attached marker balls; (<b>c</b>) participant test.</p>
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<p>The path comparison of knee and ankle joints during walking experiments: (<b>a</b>) path coordinate of knee joint (slope is 0); (<b>b</b>) path coordinate of ankle joint (slope is 0). (<b>c</b>) Path coordinate of knee joint (slope is 15 deg); (<b>b</b>) path coordinate of ankle joint (slope is 15 deg).</p>
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15 pages, 2096 KiB  
Article
Conception of a System-on-Chip (SoC) Platform to Enable EMG-Guided Robotic Neurorehabilitation
by Rubén Nieto, Pedro R. Fernández, Santiago Murano, Victor M. Navarro, Antonio J. del-Ama and Susana Borromeo
Appl. Sci. 2025, 15(4), 1699; https://doi.org/10.3390/app15041699 - 7 Feb 2025
Viewed by 460
Abstract
Electromyography (EMG) signals are fundamental in neurorehabilitation as they provide a non-invasive means of capturing the electrical activity of muscles, enabling precise detection of motor intentions. This capability is essential for controlling assistive devices, such as therapeutic exoskeletons, that aim to restore mobility [...] Read more.
Electromyography (EMG) signals are fundamental in neurorehabilitation as they provide a non-invasive means of capturing the electrical activity of muscles, enabling precise detection of motor intentions. This capability is essential for controlling assistive devices, such as therapeutic exoskeletons, that aim to restore mobility and improve motor function in patients with neuromuscular impairments. The integration of EMG into neurorehabilitation systems allows for adaptive and patient-specific interventions, addressing the variability in motor recovery needs. However, achieving the high fidelity, low latency, and robustness required for real-time control of these devices remains a significant challenge. This paper introduces a novel multi-channel electromyography (EMG) acquisition system implemented on a System-on-Chip (SoC) architecture for robotic neurorehabilitation. The system employs the Zynq-7000 SoC, which integrates an Advanced RISC Machine (ARM) processor, for high-level control and an FPGA for real-time signal processing. The architecture enables precise synchronization of up to eight EMG channels, leveraging high-speed analog-to-digital conversion and advanced filtering techniques implemented directly at the measurement site. By performing filtering and initial signal processing locally, prior to transmission to other subsystems, the system minimizes noise both through optimized processing and by reducing the distance to the muscle, thereby significantly enhancing the signal-to-noise ratio (SNR). A dedicated communication interface ensures low-latency data transfer to external controllers, crucial for adaptive control loops in exoskeletal applications. Experimental results validate the system’s capability to deliver high signal fidelity and low processing delays, outperforming commercial alternatives in terms of flexibility and scalability. This implementation provides a robust foundation for real-time bio-signal processing, advancing the integration of EMG-based control in neurorehabilitation devices. Full article
(This article belongs to the Special Issue Human Biomechanics and EMG Signal Processing)
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<p>Proposed system architecture to integrate the ADS1298R AFE and its connection to a computer.</p>
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<p>Prototype developed based on AFE ADS1298 and TE0727 manufactured by Trenz Electronic GmbH, based in Bünde, Germany SoC connected. Its size is 3 cm × 6.5 cm × 2.6 cm.</p>
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<p>Signal acquisition for functional validation: Channels 1–8. Channel 2 corresponds to the Vastus Lateralis muscle, Channel 3 to the Rectus Femoris muscle, and the remaining channels have the same response because are dedicated to internal test signals.</p>
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<p>EMG signals obtained by the AFE in time (<b>top</b>) and frequency (<b>bottom</b>) at gain 12. Cap. 1 and 2 were taken at different times, but they represent the acquisition of the Rectus Femoris. The red box indicates the frequency range displayed in the zoomed inset.</p>
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22 pages, 14692 KiB  
Review
A Systematic Review of Locomotion Assistance Exoskeletons: Prototype Development and Technical Challenges
by Weiqi Lin, Hui Dong, Yongzhuo Gao, Wenda Wang, Yi Long, Long He, Xiwang Mao, Dongmei Wu and Wei Dong
Technologies 2025, 13(2), 69; https://doi.org/10.3390/technologies13020069 - 5 Feb 2025
Viewed by 842
Abstract
Exoskeletons can track the wearer’s movements in real time, thereby enhancing physical performance or restoring mobility for individuals with gait impairments. These wearable assistive devices have demonstrated significant potential in both rehabilitation and industrial applications. This review focuses on the major advancements in [...] Read more.
Exoskeletons can track the wearer’s movements in real time, thereby enhancing physical performance or restoring mobility for individuals with gait impairments. These wearable assistive devices have demonstrated significant potential in both rehabilitation and industrial applications. This review focuses on the major advancements in exoskeleton technology published since 2020, with particular emphasis on the development of structural designs for lower-limb exoskeletons employed in locomotion assistance. We employed a systematic literature review methodology, categorizing the included studies into three main types: rigid exoskeleton, soft exoskeleton, and tethered platform. The current development status of robotic exoskeletons is analyzed based on publication year, system weight, target assistive joints, and main effects. Furthermore, we examine the factors driving these advancements and their implications for the field. The key challenges and opportunities that may influence the future development of exoskeleton technologies are also highlighted in this review. Full article
(This article belongs to the Collection Review Papers Collection for Advanced Technologies)
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<p>PRISMA flow diagram of study selection and screening process.</p>
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<p>Rigid exoskeletons for locomotion assistance. (<b>a</b>) C. Meijneke et al.’s full-size exoskeleton for hip, knee, and ankle assistance [<a href="#B30-technologies-13-00069" class="html-bibr">30</a>]. (<b>b</b>) B. Hu et al.’s variable stiffness hip exoskeleton [<a href="#B31-technologies-13-00069" class="html-bibr">31</a>]. (<b>c</b>) L. Wang et al.’s full-size exoskeleton for load carrying [<a href="#B32-technologies-13-00069" class="html-bibr">32</a>]. (<b>d</b>) M. Ishmael et al.’s for hip assistance [<a href="#B33-technologies-13-00069" class="html-bibr">33</a>]. (<b>e</b>) S. Sarkisian et al.’s self-aligning joint for knee [<a href="#B34-technologies-13-00069" class="html-bibr">34</a>]. (<b>f</b>) C. Chen et al.’s full-size exoskeleton with SEA joint for locomotion assistance [<a href="#B35-technologies-13-00069" class="html-bibr">35</a>].</p>
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<p>Soft exoskeletons for locomotion assistance. (<b>a</b>) B. Conner et al.’s hybrid cable-driven exoskeleton for ankle assistance [<a href="#B55-technologies-13-00069" class="html-bibr">55</a>]. (<b>b</b>) L. Awad et al.’s cable-driven ankle exoskeleton [<a href="#B56-technologies-13-00069" class="html-bibr">56</a>]. (<b>c</b>) B. Zhong et al.’s hybrid cable-driven exoskeleton for stroke patients [<a href="#B57-technologies-13-00069" class="html-bibr">57</a>]. (<b>d</b>) Q. Chen et al.’s cable-driven exoskeleton for hip assistance [<a href="#B58-technologies-13-00069" class="html-bibr">58</a>]. (<b>e</b>) L. Zhu et al.’s cable-driven exoskeleton for hip and knee [<a href="#B59-technologies-13-00069" class="html-bibr">59</a>].</p>
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<p>Tethered platforms for physiological analysis and control algorithm testing. (<b>a</b>) D. Miller et al.’s tethered platform for ankle analysis [<a href="#B83-technologies-13-00069" class="html-bibr">83</a>]. (<b>b</b>) G. Bryan et al.’s tethered platform for hip, knee, and ankle analysis [<a href="#B84-technologies-13-00069" class="html-bibr">84</a>]. (<b>c</b>) W. Wang et al.’s tethered platform for ankle analysis [<a href="#B85-technologies-13-00069" class="html-bibr">85</a>]. (<b>d</b>) J. Kim et al.’s tethered platform/soft exoskeleton for hip analysis/assistance [<a href="#B86-technologies-13-00069" class="html-bibr">86</a>].</p>
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<p>The distribution of the studies included. (<b>a</b>) The distribution of studies over time. (<b>b</b>) The distribution of proportions among three configuration type.</p>
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<p>The comparison of system weight; n.s. indicates not significant. (<b>a</b>) The comparison among three configurations. (<b>b</b>) The comparison of system weight between rigid exoskeletons with and without self-adaptive joint. (<b>c</b>) The comparison of system weight between hybrid cable-driven and cable-driven configurations.</p>
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<p>The distribution of target assistive joints.</p>
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<p>Overview of physiological experimental results. The sample size refers to the number of participants reported in the study who were involved in physiological experiments. (<b>a</b>) The comparison of metabolic changes [<a href="#B33-technologies-13-00069" class="html-bibr">33</a>,<a href="#B37-technologies-13-00069" class="html-bibr">37</a>,<a href="#B38-technologies-13-00069" class="html-bibr">38</a>,<a href="#B42-technologies-13-00069" class="html-bibr">42</a>,<a href="#B44-technologies-13-00069" class="html-bibr">44</a>,<a href="#B46-technologies-13-00069" class="html-bibr">46</a>,<a href="#B58-technologies-13-00069" class="html-bibr">58</a>,<a href="#B59-technologies-13-00069" class="html-bibr">59</a>,<a href="#B60-technologies-13-00069" class="html-bibr">60</a>,<a href="#B61-technologies-13-00069" class="html-bibr">61</a>,<a href="#B62-technologies-13-00069" class="html-bibr">62</a>,<a href="#B64-technologies-13-00069" class="html-bibr">64</a>,<a href="#B66-technologies-13-00069" class="html-bibr">66</a>,<a href="#B67-technologies-13-00069" class="html-bibr">67</a>,<a href="#B71-technologies-13-00069" class="html-bibr">71</a>,<a href="#B72-technologies-13-00069" class="html-bibr">72</a>,<a href="#B73-technologies-13-00069" class="html-bibr">73</a>,<a href="#B83-technologies-13-00069" class="html-bibr">83</a>,<a href="#B84-technologies-13-00069" class="html-bibr">84</a>,<a href="#B85-technologies-13-00069" class="html-bibr">85</a>,<a href="#B86-technologies-13-00069" class="html-bibr">86</a>,<a href="#B87-technologies-13-00069" class="html-bibr">87</a>,<a href="#B88-technologies-13-00069" class="html-bibr">88</a>,<a href="#B93-technologies-13-00069" class="html-bibr">93</a>,<a href="#B94-technologies-13-00069" class="html-bibr">94</a>,<a href="#B95-technologies-13-00069" class="html-bibr">95</a>]. (<b>b</b>) The comparison of EMG muscle activity changes [<a href="#B31-technologies-13-00069" class="html-bibr">31</a>,<a href="#B36-technologies-13-00069" class="html-bibr">36</a>,<a href="#B40-technologies-13-00069" class="html-bibr">40</a>,<a href="#B41-technologies-13-00069" class="html-bibr">41</a>,<a href="#B43-technologies-13-00069" class="html-bibr">43</a>,<a href="#B45-technologies-13-00069" class="html-bibr">45</a>,<a href="#B57-technologies-13-00069" class="html-bibr">57</a>,<a href="#B62-technologies-13-00069" class="html-bibr">62</a>,<a href="#B68-technologies-13-00069" class="html-bibr">68</a>,<a href="#B70-technologies-13-00069" class="html-bibr">70</a>,<a href="#B72-technologies-13-00069" class="html-bibr">72</a>,<a href="#B85-technologies-13-00069" class="html-bibr">85</a>,<a href="#B88-technologies-13-00069" class="html-bibr">88</a>,<a href="#B89-technologies-13-00069" class="html-bibr">89</a>,<a href="#B92-technologies-13-00069" class="html-bibr">92</a>].</p>
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12 pages, 1639 KiB  
Article
Effectiveness of Powered Hand Exoskeleton on Upper Extremity Function in People with Chronic Stroke
by Shan-Ju Yeh, Yi-Chuan Wang, Wei-Chien Fang, Shyh-Chour Huang and Yu-Sheng Yang
Actuators 2025, 14(2), 67; https://doi.org/10.3390/act14020067 - 2 Feb 2025
Viewed by 548
Abstract
Impairment of upper limb function is common after a stroke and is closely linked to decreased functional independence in activities of daily living. Robot-assisted training has been used in clinical settings to improve hand function in stroke patients; however, many existing devices are [...] Read more.
Impairment of upper limb function is common after a stroke and is closely linked to decreased functional independence in activities of daily living. Robot-assisted training has been used in clinical settings to improve hand function in stroke patients; however, many existing devices are costly and require specialized training to operate. This study aimed to propose a novel powered hand exoskeleton (EO) and verify its effectiveness on upper extremity function in people with chronic stroke. Thirty participants were randomly assigned to either the experimental group or the control group. Each participant underwent 30 min interventions twice a week for 8 weeks. The experimental group received 15 min of conventional therapy followed by 15 min of training with the powered hand EO, while the control group received 30 min of conventional therapy. The primary outcome measures included the Fugl-Meyer Assessment for upper extremity function (FMA-UE), the Box and Block Test (BBT), and handgrip dynamometer. Assessments were conducted at baseline and then at 4-week intervals throughout the 8-week period. Results showed that, after the 8-week intervention, the average changes in FMA-UE scores for the experimental group were significantly greater than those for the control group (p < 0.01). A clear upward trend in both FMA-UE and BBT scores was observed in the EO group. Statistical analysis revealed significant improvements in the overall, proximal, and distal components of the FMA-UE scores (all p < 0.01) and in BBT scores (both p < 0.05) in the EO group compared to the control group at 4 and 8 weeks, respectively. However, no significant differences in grip strength were observed between the groups at either time point. Our findings suggest that the proposed powered hand EO is both feasible and safe for training the impaired hand in stroke survivors. Given the characteristics of the device, it has potential for use in hand rehabilitation aimed at regaining upper extremity function. Full article
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<p>Flowchart of the experimental design.</p>
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<p>(<b>a</b>) Design overview of the powered hand exoskeleton (<b>b</b>) releasing an object and (<b>c</b>) grasping an object with the exoskeleton.</p>
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<p>FMA-UE scores for experimental and control groups at baseline (T0), 4 weeks (T4) and 8 weeks (T8). Circles represent outliers; the median is shown by the thick black line.</p>
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<p>BBT and grip strength assessment for experimental and control groups at baseline (T0), 4 weeks (T4) and 8 weeks (T8). Circles represented the mean.</p>
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11 pages, 590 KiB  
Review
Advances and Current Status in the Use of Cuticular Hydrocarbons for Forensic Entomology Applications
by David Stewart-Yates, Garth L. Maker, Stefano D’Errico and Paola A. Magni
Insects 2025, 16(2), 144; https://doi.org/10.3390/insects16020144 - 1 Feb 2025
Viewed by 598
Abstract
Cuticular hydrocarbons (CHCs) are long-chain lipids found on the exoskeletons of insects, serving primarily as a protective barrier against water loss and environmental factors. In the last few decades, the qualitative and quantitative analysis of CHCs, particularly in blow flies, has emerged as [...] Read more.
Cuticular hydrocarbons (CHCs) are long-chain lipids found on the exoskeletons of insects, serving primarily as a protective barrier against water loss and environmental factors. In the last few decades, the qualitative and quantitative analysis of CHCs, particularly in blow flies, has emerged as a valuable tool in forensic entomology, offering promising potential for species identification and age estimation of forensically important insects. This review examines the current application of CHC analysis in forensic investigations and highlights the significant advancements in the field over the past few years. Studies have demonstrated that CHC profiles vary with insect development, and while intra-species variability exists due to factors such as age, sex, geographical location, and environmental conditions, these variations can be harnessed to refine post-mortem interval (PMI) estimations and improve the accuracy of forensic entomological evidence. Notably, CHC analysis can also aid in distinguishing between multiple generations of insects on a body, providing insights into post-mortem body movement and aiding in the interpretation of PMI in complex cases. Furthermore, recent studies have investigated the variability and degradation of CHCs over time, revealing how environmental factors—such as temperature, humidity, UV light exposure, and toxicological substances—affect CHC composition, providing valuable insights for forensic investigations. Despite the promise of CHC profiling, several challenges remain, and this review also aims to highlight future research directions to enhance the reliability of this technique in forensic casework. Full article
(This article belongs to the Section Role of Insects in Human Society)
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<p>Visual representation of the insect integument and cuticular hydrocarbons. The cuticle is present at every stage of insect development (shown on the right: blow fly larvae, fully formed puparia, and adult). It is composed of three distinct layers: the epicuticle, exocuticle, and endocuticle. These layers are arranged from the outermost to the innermost part of the body, with the endocuticle in direct contact with the insect epidermis. Hydrocarbons found in the insect cuticle, which are often extracted for experimental purposes, are primarily located in the epicuticle.</p>
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