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17 pages, 6429 KiB  
Article
Element Array Optimization for Skin-Attachable Ultrasound Probes to Improve the Robustness against Positional and Angular Errors
by Takumi Noda, Takashi Azuma, Ichiro Sakuma and Naoki Tomii
Appl. Sci. 2024, 14(20), 9320; https://doi.org/10.3390/app14209320 (registering DOI) - 12 Oct 2024
Abstract
Skin-attachable ultrasound probes face challenges in imaging the intended cross-section due to the difficulty in precisely adjusting the position and angle of attachment. While matrix element arrays are capable of imaging any cross-section within a three-dimensional field of view, their implementation presents a [...] Read more.
Skin-attachable ultrasound probes face challenges in imaging the intended cross-section due to the difficulty in precisely adjusting the position and angle of attachment. While matrix element arrays are capable of imaging any cross-section within a three-dimensional field of view, their implementation presents a challenge due to the significant number of required ultrasound elements. We propose a method for optimizing the coordinates and shapes of elements based on the focusing quality onto the imaging points under the positional and angular errors in the element array. A 128-element array was optimized through the proposed method and its imaging performance was evaluated with simulated phantoms. The optimized array demonstrated the ability to clearly visualize the simulated wires, cysts, and blood vessels even with the positional error of 3 mm and the angular error of 20°. These results indicate the feasibility of developing a skin-attachable ultrasound probe that can be easily used in daily life without requiring precise positional and angular accuracy. Full article
(This article belongs to the Special Issue Current Updates on Ultrasound for Biomedical Applications)
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Figure 1
<p>The arrangement of the focus point, nearby points, and peripheral points. The focus point for evaluating the main lobe level was randomly placed within the imaging region. The nearby points for evaluating the main lobe width were arranged at equal intervals on an ellipse centered on the focus point. The peripheral points for evaluating the side lobe level were randomly distributed within the region where the depth is close to the focus point.</p>
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<p>Simulated scatterer distributions used in the ultrasound imaging experiments. (<b>a</b>) Simulated wire scatterers. Nine wires, each 5 mm in length, are arranged with 10 mm intervals. Scattering points are placed on the wires at 1/10 wavelength intervals. In regions other than the wires, scattering points are randomly placed at a density of one per cubic volume with sides of one wavelength. (<b>b</b>) Simulated cyst scatterers. Four cysts, each with a diameter of 10 mm, are arranged with 15 mm intervals. There are no scattering points inside the cysts, while scattering points are randomly placed outside the cysts at a density of one per cubic volume with sides of one wavelength. (<b>c</b>) Simulated blood vessel scatterer. A blood vessel with an inner diameter of 6 mm and an outer diameter of 7 mm is positioned at a depth of 25 mm. There are no scattering points inside the blood vessel, while scattering points are randomly placed in the blood vessel wall and outside the blood vessel at densities of four and one per cubic volume with sides of one wavelength, respectively. (<b>d</b>–<b>f</b>) Ground truth maps of the US images for the wire, cyst, and blood vessel scatterers, respectively.</p>
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<p>Imaging performance comparison of the optimized element arrays with different cost function weights. (<b>a</b>) Representative examples of the optimized element arrays. The one on the right achieved the highest signal-to-noise ratio (SNR) in the imaging of wire scatterers. (<b>b</b>) Ultrasound images of the wire scatterers obtained with the optimized element arrays shown in (<b>a</b>) with an angle error of 20° around the <math display="inline"><semantics> <mrow> <mo> </mo> <mi>z</mi> </mrow> </semantics></math>-axis and a positional error of 3 mm in the <math display="inline"><semantics> <mrow> <mi>y</mi> </mrow> </semantics></math>-direction. The dynamic range is 25 dB. (<b>c</b>) Average SNRs of the nine wires, each imaged under nine different positional or angular error conditions: three angular errors (−20°, 0°, 20°) and three positional errors (−3 mm, 0 mm, 3 mm). The optimized array with the cost function weights of <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>β</mi> </mrow> <mrow> <mn>1</mn> </mrow> </msub> <mo>=</mo> <msup> <mrow> <mn>10</mn> </mrow> <mrow> <mo>−</mo> <mn>2</mn> </mrow> </msup> <mo>,</mo> <mo> </mo> <msub> <mrow> <mi>β</mi> </mrow> <mrow> <mn>2</mn> </mrow> </msub> <mo>=</mo> <msup> <mrow> <mn>10</mn> </mrow> <mrow> <mn>0</mn> </mrow> </msup> </mrow> </semantics></math> achieved the highest average SNR of the wires.</p>
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<p>Evaluation of the robustness of the element arrays against positional and angular errors in the imaging of wire scatterers. (<b>a</b>,<b>b</b>) The average SNR of the nine wires in US images obtained under various positional and angular errors, respectively.</p>
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<p>Examples of ultrasound images of wire scatterers obtained with the linear, matrix, and optimized arrays. The left column shows the element arrays, and the top row shows the positional relationship between the imaging plane and the element arrays. The dynamic range of the ultrasound images is 25 dB. The average SNR of the wires are displayed on each image.</p>
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<p>Evaluation of the robustness of the element arrays against positional and angular errors in the imaging of cyst scatterers. (<b>a</b>,<b>b</b>) The average CNR of the four cysts in US images obtained under various positional and angular errors, respectively.</p>
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<p>Examples of ultrasound images of cyst scatterers obtained with the linear, matrix, and optimized arrays. The left column shows the element arrays, and the top row shows the positional relationship between the imaging plane and the element arrays. The dynamic range of the ultrasound images is 25 dB. The average CNR of the cysts are displayed on each image.</p>
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<p>Examples of US images of blood vessel scatterers obtained with the linear, matrix, and optimized arrays. Before the image reconstruction, white noise was added to the US signals so that the SNR became 20 dB. The left column shows the element arrays, and the top row shows the positional relationship between the imaging plane and the element arrays. The dynamic range of the ultrasound images is 25 dB. The average measurement error from the ground truth blood vessel inner diameter of 6 mm is displayed on each image.</p>
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17 pages, 469 KiB  
Article
Emergency Detection in Smart Homes Using Inactivity Score for Handling Uncertain Sensor Data
by Sebastian Wilhelm and Florian Wahl
Sensors 2024, 24(20), 6583; https://doi.org/10.3390/s24206583 (registering DOI) - 12 Oct 2024
Abstract
In an aging society, the need for efficient emergency detection systems in smart homes is becoming increasingly important. For elderly people living alone, technical solutions for detecting emergencies are essential to receiving help quickly when needed. Numerous solutions already exist based on wearable [...] Read more.
In an aging society, the need for efficient emergency detection systems in smart homes is becoming increasingly important. For elderly people living alone, technical solutions for detecting emergencies are essential to receiving help quickly when needed. Numerous solutions already exist based on wearable or ambient sensors. However, existing methods for emergency detection typically assume that sensor data are error-free and contain no false positives, which cannot always be guaranteed in practice. Therefore, we present a novel method for detecting emergencies in private households that detects unusually long inactivity periods and can process erroneous or uncertain activity information. We introduce the Inactivity Score, which provides a probabilistic weighting of inactivity periods based on the reliability of sensor measurements. By analyzing historical Inactivity Scores, anomalies that potentially represent an emergency can be identified. The proposed method is compared with four related approaches on seven different datasets. Our method surpasses existing approaches when considering the number of false positives and the mean time to detect emergencies. It achieves an average detection time of approximately 05:23:28 h with only 0.09 false alarms per day under noise-free conditions. Moreover, unlike related approaches, the proposed method remains effective with noisy data. Full article
(This article belongs to the Special Issue Multi-sensor for Human Activity Recognition: 2nd Edition)
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<p>Example calculation of the Inactivity Score <math display="inline"><semantics> <mrow> <mi>I</mi> <mi>S</mi> <mo>(</mo> <mi>t</mi> <mo>)</mo> </mrow> </semantics></math> according to Wilhelm and Wahl for the sample dataset in <a href="#sensors-24-06583-t001" class="html-table">Table 1</a>, compared with the Duration of Inactivity <math display="inline"><semantics> <mrow> <mi>D</mi> <mi>I</mi> <mo>(</mo> <mi>t</mi> <mo>)</mo> </mrow> </semantics></math> according to Floeck and Litz [<a href="#B22-sensors-24-06583" class="html-bibr">22</a>].</p>
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<p>Number of false positives for each dataset–noise-level combination <math display="inline"><semantics> <msubsup> <mi>A</mi> <mrow> <msub> <mi>D</mi> <mi>i</mi> </msub> </mrow> <mi>n</mi> </msubsup> </semantics></math> and for the sum of all datasets per algorithm. The absolute number of false positives after an initialization period of 10 weeks is shown [<a href="#B22-sensors-24-06583" class="html-bibr">22</a>,<a href="#B42-sensors-24-06583" class="html-bibr">42</a>,<a href="#B43-sensors-24-06583" class="html-bibr">43</a>,<a href="#B45-sensors-24-06583" class="html-bibr">45</a>,<a href="#B46-sensors-24-06583" class="html-bibr">46</a>].</p>
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<p>Number of undetected emergencies due to the restriction that events are excluded if <math display="inline"><semantics> <mrow> <mo>Δ</mo> <mi>t</mi> </mrow> </semantics></math> exceeds 7 days [<a href="#B22-sensors-24-06583" class="html-bibr">22</a>,<a href="#B42-sensors-24-06583" class="html-bibr">42</a>,<a href="#B43-sensors-24-06583" class="html-bibr">43</a>,<a href="#B45-sensors-24-06583" class="html-bibr">45</a>,<a href="#B46-sensors-24-06583" class="html-bibr">46</a>].</p>
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<p>Boxplot showing <math display="inline"><semantics> <mrow> <mo>Δ</mo> <mi>t</mi> </mrow> </semantics></math> per noise level and algorithm for 1000 simulated emergency events across all evaluation datasets [<a href="#B22-sensors-24-06583" class="html-bibr">22</a>,<a href="#B42-sensors-24-06583" class="html-bibr">42</a>,<a href="#B43-sensors-24-06583" class="html-bibr">43</a>,<a href="#B45-sensors-24-06583" class="html-bibr">45</a>,<a href="#B46-sensors-24-06583" class="html-bibr">46</a>].</p>
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<p>Comparison of emergency detection algorithms by noise level: number of false positives vs. mean detection time on a logarithmic scale [<a href="#B22-sensors-24-06583" class="html-bibr">22</a>,<a href="#B42-sensors-24-06583" class="html-bibr">42</a>,<a href="#B43-sensors-24-06583" class="html-bibr">43</a>,<a href="#B45-sensors-24-06583" class="html-bibr">45</a>,<a href="#B46-sensors-24-06583" class="html-bibr">46</a>].</p>
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<p>Comparison of Inactivity Score (<math display="inline"><semantics> <mrow> <mi>I</mi> <mi>S</mi> </mrow> </semantics></math>) and Duration of Inactivity (<math display="inline"><semantics> <mrow> <mi>D</mi> <mi>I</mi> </mrow> </semantics></math>) in the presence of a faulty sensor.</p>
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39 pages, 6036 KiB  
Review
Recent Advancements in MXene-Based Biosensors for Health and Environmental Applications—A Review
by Ashraf Ali, Sanjit Manohar Majhi, Lamia A. Siddig, Abdul Hakeem Deshmukh, Hongli Wen, Naser N. Qamhieh, Yaser E. Greish and Saleh T. Mahmoud
Biosensors 2024, 14(10), 497; https://doi.org/10.3390/bios14100497 (registering DOI) - 12 Oct 2024
Abstract
Owing to their unique physicochemical properties, MXenes have emerged as promising materials for biosensing applications. This review paper comprehensively explores the recent advancements in MXene-based biosensors for health and environmental applications. This review begins with an introduction to MXenes and biosensors, outlining various [...] Read more.
Owing to their unique physicochemical properties, MXenes have emerged as promising materials for biosensing applications. This review paper comprehensively explores the recent advancements in MXene-based biosensors for health and environmental applications. This review begins with an introduction to MXenes and biosensors, outlining various types of biosensors including electrochemical, enzymatic, optical, and fluorescent-based systems. The synthesis methods and characteristics of MXenes are thoroughly discussed, highlighting the importance of these processes in tailoring MXenes for specific biosensing applications. Particular attention is given to the development of electrochemical MXene-based biosensors, which have shown remarkable sensitivity and selectivity in detecting various analytes. This review then delves into enzymatic MXene-based biosensors, exploring how the integration of MXenes with enzymes enhances sensor performance and expands the range of detectable biomarkers. Optical biosensors based on MXenes are examined, focusing on their mechanisms and applications in both healthcare and environmental monitoring. The potential of fluorescent-based MXene biosensors is also investigated, showcasing their utility in imaging and sensing applications. In addition, MXene-based potential wearable biosensors have been discussed along with the role of MXenes in volatile organic compound (VOC) detection for environmental applications. Finally, this paper concludes with a critical analysis of the current state of MXene-based biosensors and provides insights into future perspectives and challenges in this rapidly evolving field. Full article
(This article belongs to the Special Issue Nanotechnology-Enabled Biosensors)
25 pages, 7485 KiB  
Article
Design and Development of a Smart Fidget Toy Using Blockchain Technology to Improve Health Data Control
by Polina Bobrova, Paolo Perego and Raffaele Boiano
Sensors 2024, 24(20), 6582; https://doi.org/10.3390/s24206582 (registering DOI) - 12 Oct 2024
Abstract
This study explores the integration of blockchain technology in wearable health devices through the design and development of a Smart Fidget Toy. We aimed to investigate design challenges and opportunities of blockchain-based health devices, examine the impact of blockchain integration user experience, and [...] Read more.
This study explores the integration of blockchain technology in wearable health devices through the design and development of a Smart Fidget Toy. We aimed to investigate design challenges and opportunities of blockchain-based health devices, examine the impact of blockchain integration user experience, and assess its potential to improve data control and user trust. Using an iterative user-centered design approach, we developed a mid-fidelity prototype of a physical fidget device with a blockchain-based web application. Our key contributions include the design of a fidget toy using blockchain for secure health data management, an iterative development process balancing user needs with blockchain integration challenges, and insights into user perceptions of blockchain wearables for health. We conducted user studies, including a survey (n = 28), focus group (n = 6), interactive wireframe testing (n = 7), and prototype testing (n = 10). Our study revealed high user interest (70%) in blockchain-based data control and sharing features and improved perceived security of data (90% of users) with blockchain integration. However, we also identified challenges in user understanding of blockchain concepts, necessitating additional support. Our smart contract, deployed on the Polygon zkEVM testnet, efficiently manages data storage and retrieval while maintaining user privacy. This research advances the understanding of blockchain applications in health wearables, offering valuable insights for the future development of this field. Full article
(This article belongs to the Special Issue Wearable Sensors for Human Health Monitoring and Analysis)
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<p>Overview of Research Objectives, Challenges, Methodology, and Expected Outcomes.</p>
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<p>Sketch of Initial Concept of the Device.</p>
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<p>The Development Process of the Smart Fidget Toy.</p>
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<p>Participant Applying Transmittable Material on their Hands for an Experiment.</p>
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<p>Architecture of the Web app.</p>
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<p>Low-Fidelity Prototype during Focus Group: (<b>a</b>) participants discussing the low-fidelity prototype; (<b>b</b>) participants trying to use the low-fidelity prototype.</p>
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<p>Experiment during Focus Group with Transmittable Material on Hands of Participants: (<b>a</b>) participant trying the prototype with transmittable material on their hand; (<b>b</b>) low-fidelity prototype with marks left by participants’ trials after the completion of the study.</p>
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<p>User Clicks on Upload Page on the Web App.</p>
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<p>Mid-fidelity Prototype of Smart Fidget Toy.</p>
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<p>Mid-fidelity prototype of Smart Fidget Toy connected to a Web App.</p>
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<p>User Testing Session of Mid-fidelity Prototype.</p>
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16 pages, 1480 KiB  
Article
Protecting Infinite Data Streams from Wearable Devices with Local Differential Privacy Techniques
by Feng Zhao and Song Fan
Information 2024, 15(10), 630; https://doi.org/10.3390/info15100630 (registering DOI) - 12 Oct 2024
Abstract
The real-time data collected by wearable devices enables personalized health management and supports public health monitoring. However, sharing these data with third-party organizations introduces significant privacy risks. As a result, protecting and securely sharing wearable device data has become a critical concern. This [...] Read more.
The real-time data collected by wearable devices enables personalized health management and supports public health monitoring. However, sharing these data with third-party organizations introduces significant privacy risks. As a result, protecting and securely sharing wearable device data has become a critical concern. This paper proposes a local differential privacy-preserving algorithm designed for continuous data streams generated by wearable devices. Initially, the data stream is sampled at key points to avoid prematurely exhausting the privacy budget. Then, an adaptive allocation of the privacy budget at these points enhances privacy protection for sensitive data. Additionally, the optimized square wave (SW) mechanism introduces perturbations to the sampled points. Afterward, the Kalman filter algorithm is applied to maintain data flow patterns and reduce prediction errors. Experimental validation using two real datasets demonstrates that, under comparable conditions, this approach provides higher data availability than existing privacy protection methods for continuous data streams. Full article
(This article belongs to the Special Issue Digital Privacy and Security, 2nd Edition)
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Graphical abstract

Graphical abstract
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<p>Usage scenario of the algorithm.</p>
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<p>The framework design of WIDS-LDP.</p>
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<p>The impact of different window lengths on MRE (<b>left</b>: PAMAP, <b>right</b>: Taxi).</p>
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<p>The impact of different privacy budgets on MRE (<b>left</b>: PAMAP, <b>right</b>: Taxi).</p>
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<p>The impact of different data lengths on MRE (<b>left</b>: PAMAP, <b>right</b>: Taxi).</p>
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12 pages, 2427 KiB  
Article
Validity and Reliability of a New Wearable Chest Strap to Estimate Respiratory Frequency in Elite Soccer Athletes
by Adriano Di Paco, Diego A. Bonilla, Rocco Perrotta, Raffaele Canonico, Erika Cione and Roberto Cannataro
Sports 2024, 12(10), 277; https://doi.org/10.3390/sports12100277 (registering DOI) - 12 Oct 2024
Abstract
Assessing respiratory frequency (fR) is practical in monitoring training progress in competitive athletes, especially during exercise. This study aimed to validate a new wearable chest strap (wCS) to estimate fR against ergospirometry as a criterion device in soccer players. [...] Read more.
Assessing respiratory frequency (fR) is practical in monitoring training progress in competitive athletes, especially during exercise. This study aimed to validate a new wearable chest strap (wCS) to estimate fR against ergospirometry as a criterion device in soccer players. A total of 26 elite professional soccer players (mean [standard deviation]: 23.6 [4.8] years; 180.6 [5.7] cm; 77.2 [5.4] kg) from three Italian Serie A League teams participated in this cross-sectional study. The sample included attackers, midfielders, and defenders. fR was assessed during a maximal cardiopulmonary exercise test (CPET) on a treadmill using (i) a breath-by-breath gas exchange analyzer (Vyntus® CPX, Vyaire Medical) and (ii) a novel wCS with sensors designed to assess breath frequency following chest expansions. Pearson’s correlation coefficient (r), adjusted coefficient of determination (aR2), Bland–Altman plot analysis, and Lin’s concordance correlation coefficient (ρc) were used for comparative analysis (correlation and concordance) among the methods. The repeated measures correlation coefficient (rrm) was used to assess the strength of the linear association between the methods. The intraclass correlation coefficient (ICC) and the Finn coefficient (rF) were used for inter-rater reliability. All statistical analyses were performed within the R statistical computing environment, with 95% confidence intervals (95% CIs) reported and statistical significance set at p < 0.05. A total of 16529 comparisons were performed after collecting the CPET data. The robust time series analysis with Hodges–Lehmann estimation showed no significant differences between both methods (p > 0.05). Correlation among devices was statistically significant and very large (r [95% CI]: 0.970 [0.970, 0.971], p < 0.01; aR2 [95% CI]: 0.942 [0.942, 0.943], p < 0.01) with strong evidence supporting consistency of the new wCS (BF10 > 100). In addition, a high concordance was found (ρc [95% CI]: 0.970 [0.969, 0.971], bias correction factor: 0.999). VyntusTM CPX, as a standard criterion, showed moderate agreement with wCS after Bland–Altman analysis (bias [95% lower to the upper limit of agreement]; % agree: 0.170 [−4.582 to 4.923] breaths·min−1; 69.9%). A strong association between measurements (rrm [95% CI]: 0.960 [0.959, 0.961]), a high absolute agreement between methods (ICC [95% CI]: 0.970 [0.970, 0.971]), and high inter-rater reliability (rF: 0.947) were found. With an RMSE = 2.42 breaths·min−1, the new wCS seems to be an valid and reliable in-field method to evaluate fR compared to a breath-by-breath gas exchange analyzer. Notwithstanding, caution is advised if methods are used interchangeably while further external validation occurs. Full article
(This article belongs to the Special Issue Promoting and Monitoring Physical Fitness in All Contexts)
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<p>Novel wearable chest strap to measure respiratory frequency.</p>
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<p>Electronic board, both sides, with and without built-in cover.</p>
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<p>Measured and estimated respiratory frequency (<span class="html-italic">f</span><sub>R</sub>) values. The <span class="html-italic">f</span><sub>R</sub> is reported in breaths·min<sup>−1</sup>. The scatter plot shows individual measurements over time, with a smooth regression line highlighting the trend for both devices.</p>
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<p>(<b>A</b>) Pairwise scatter plot matrix, distribution, and Pearson correlation coefficient. The correlation plot includes histograms, density distributions, and a smooth regression line of the estimated and measured respiratory frequency (<span class="html-italic">f</span><sub>R</sub>) values. *** Statistical significance at <span class="html-italic">p</span> ≤ 0.001. (<b>B</b>) Repeated measures correlation concordance plot for each participant. Separate parallel lines are fitted to the data from each participant, and the corresponding line is shown in a different color. The blue dashed line is the fit of the simple correlation.</p>
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<p>Bland–Altman plot for differences between measured and estimated respiratory frequency (<span class="html-italic">f</span><sub>R</sub>) values. Individual differences between actual and estimated fat mass values are plotted against the mean of measured and estimated fat mass values.</p>
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25 pages, 3691 KiB  
Review
Metal–Organic Framework-Based Nanostructures for Electrochemical Sensing of Sweat Biomarkers
by Jing Meng, Moustafa Zahran and Xiaolin Li
Biosensors 2024, 14(10), 495; https://doi.org/10.3390/bios14100495 (registering DOI) - 12 Oct 2024
Abstract
Sweat is considered the most promising candidate to replace conventional blood samples for noninvasive sensing. There are many tools and optical and electrochemical methods that can be used for detecting sweat biomarkers. Electrochemical methods are known for their simplicity and cost-effectiveness. However, they [...] Read more.
Sweat is considered the most promising candidate to replace conventional blood samples for noninvasive sensing. There are many tools and optical and electrochemical methods that can be used for detecting sweat biomarkers. Electrochemical methods are known for their simplicity and cost-effectiveness. However, they need to be optimized in terms of selectivity and catalytic activity. Therefore, electrode modifiers such as nanostructures and metal–organic frameworks (MOFs) or combinations of them were examined for boosting the performance of the electrochemical sensors. The MOF structures can be prepared by hydrothermal/solvothermal, sonochemical, microwave synthesis, mechanochemical, and electrochemical methods. Additionally, MOF nanostructures can be prepared by controlling the synthesis conditions or mixing bulk MOFs with nanoparticles (NPs). In this review, we spotlight the previously examined MOF-based nanostructures as well as promising ones for the electrochemical determination of sweat biomarkers. The presence of NPs strongly improves the electrical conductivity of MOF structures, which are known for their poor conductivity. Specifically, Cu-MOF and Co-MOF nanostructures were used for detecting sweat biomarkers with the lowest detection limits. Different electrochemical methods, such as amperometric, voltammetric, and photoelectrochemical, were used for monitoring the signal of sweat biomarkers. Overall, these materials are brilliant electrode modifiers for the determination of sweat biomarkers. Full article
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<p>Schematic representation of (<b>A</b>) potentiometric, (<b>B</b>) impedimetric, (<b>C</b>) amperometric, (<b>D</b>) voltammetric, (<b>E</b>) organic electrochemical transistor, and (<b>F</b>) photoelectrochemical as electrochemical methods used for the detection of sweat biomarkers.</p>
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<p>Schematic representation of different pathways used for the synthesis of MOFs.</p>
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<p>Schematic representation of different conductive MOF structures.</p>
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<p>Schematic representation of sweat biomarkers detected by MOF-based NCs.</p>
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<p>Schematic illustration of electrocatalytic oxidation mechanism of ascorbic acid by Ni‒MOF‒based electrochemical sensor (reprinted from ref. [<a href="#B111-biosensors-14-00495" class="html-bibr">111</a>] with permission from El‒Sevier).</p>
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<p>Schematic illustration of the (<b>A</b>) synthesis of NiCo‒MOF, (<b>B</b>) preparation of NiCo‒MOF NC‒modified electrode, (<b>C</b>) electrochemical determination of cortisol detection, and (<b>D</b>) composition of cortisol sensor patch (reprinted from ref. [<a href="#B125-biosensors-14-00495" class="html-bibr">125</a>] with permission from El-Sevier).</p>
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<p>A schematic representation of a wearable levodopa sweat sensor, where 1, 2, and 3 refer to microcontroller, analog front-end, and Bluetooth transceiver (reprinted from Ref. [<a href="#B64-biosensors-14-00495" class="html-bibr">64</a>] with permission from El‒Sevier).</p>
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<p>A schematic illustration of a wearable electrochemical sensor for sweat ascorbic acid determination (reprinted from Ref. [<a href="#B62-biosensors-14-00495" class="html-bibr">62</a>] with permission from El‒Sevier).</p>
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17 pages, 4127 KiB  
Tutorial
Optimizing EEG Signal Integrity: A Comprehensive Guide to Ocular Artifact Correction
by Vincenzo Ronca, Rossella Capotorto, Gianluca Di Flumeri, Andrea Giorgi, Alessia Vozzi, Daniele Germano, Valerio Di Virgilio, Gianluca Borghini, Giulia Cartocci, Dario Rossi, Bianca M. S. Inguscio, Fabio Babiloni and Pietro Aricò
Bioengineering 2024, 11(10), 1018; https://doi.org/10.3390/bioengineering11101018 (registering DOI) - 12 Oct 2024
Abstract
Ocular artifacts, including blinks and saccades, pose significant challenges in the analysis of electroencephalographic (EEG) data, often obscuring crucial neural signals. This tutorial provides a comprehensive guide to the most effective methods for correcting these artifacts, with a focus on algorithms designed for [...] Read more.
Ocular artifacts, including blinks and saccades, pose significant challenges in the analysis of electroencephalographic (EEG) data, often obscuring crucial neural signals. This tutorial provides a comprehensive guide to the most effective methods for correcting these artifacts, with a focus on algorithms designed for both laboratory and real-world settings. We review traditional approaches, such as regression-based techniques and Independent Component Analysis (ICA), alongside more advanced methods like Artifact Subspace Reconstruction (ASR) and deep learning-based algorithms. Through detailed step-by-step instructions and comparative analysis, this tutorial equips researchers with the tools necessary to maintain the integrity of EEG data, ensuring accurate and reliable results in neurophysiological studies. The strategies discussed are particularly relevant for wearable EEG systems and real-time applications, reflecting the growing demand for robust and adaptable solutions in applied neuroscience. Full article
(This article belongs to the Section Biosignal Processing)
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<p>Raw EEG signal on frontal electrodes showing ocular artifacts, which can be easily identified due to their larger amplitudes compared to the EEG signal.</p>
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<p>Signal composition block diagram.</p>
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<p>Raw EEG signal affected by ocular artifacts. Such artifacts can be easily visually recognized as the prominent peaks visible along the signal trace.</p>
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<p>Example of artifactual component derived from the EEG signal affected by ocular artifacts through the regression-based algorithm.</p>
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<p>Overlapped representation of the raw (orange line) and clean (blue line) EEG signals. The figure shows how the algorithm successfully identified and corrected the ocular artifacts.</p>
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<p>Block diagram of the principal steps for approaching the identification and correction of ocular artifacts from an EEG signal through a regression-based method.</p>
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<p>Example of ICA’s performance in removing ocular artifacts. The presented plots show: (<b>i</b>) the raw EEG from frontal electrodes; (<b>ii</b>) the first five components from ICA, ordered by energy; and (<b>iii</b>) the clean EEG from the same electrodes after removing the artifactual components (specifically, the first and second components). Green rectangles highlight blink patterns in both the raw EEG and the ICA components, while red rectangles indicate saccade patterns. After cleaning the EEG signal, these rectangles no longer contain artifact patterns, demonstrating the effectiveness of the artifact removal process.</p>
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<p>Representation of the ASR method performance for correcting ocular blink artifacts from the EEG signal. The figure shows how the method was effective in identifying and correcting the ocular artifacts from the raw EEG signal (green line) and obtaining the clean (red line) EEG trace.</p>
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14 pages, 3103 KiB  
Article
Trimodal Watch-Type Wearable Health Monitoring Device
by Shanthala Lakshminarayana, Mrudula Ranganatha, Hyusim Park and Sungyong Jung
Appl. Sci. 2024, 14(20), 9267; https://doi.org/10.3390/app14209267 (registering DOI) - 11 Oct 2024
Abstract
In the domain of healthcare, wearable health monitoring devices have emerged as essential tools for the advancement of patient health tracking. These devices facilitate the provision of real-time medical data to clinicians, enabling early diagnosis, timely intervention, and enhanced management of individual health. [...] Read more.
In the domain of healthcare, wearable health monitoring devices have emerged as essential tools for the advancement of patient health tracking. These devices facilitate the provision of real-time medical data to clinicians, enabling early diagnosis, timely intervention, and enhanced management of individual health. This study introduces an innovative trimodal wearable health monitoring device in the form of a wristwatch. The device integrates a breath analyzer for the assessment of gaseous phase biomarkers, a sweat analyzer for the evaluation of aqueous-phase biomarkers, and an infrared sensor for the measurement of body temperature in the optical phase. Engineered on a compact 3 cm × 3 cm printed circuit board, the device has been optimized for wearability, power efficiency, and seamless integration with both wired and wireless charging and communication systems. Furthermore, custom software applications, designed for both Windows and Android platforms, have been developed to facilitate intuitive data visualization and storage on personal computers and smartphones. Empirical results from real-time chemical testing substantiate the device’s efficacy and potential as an advanced solution for wearable health monitoring. Full article
(This article belongs to the Section Electrical, Electronics and Communications Engineering)
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<p>System block diagram.</p>
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<p>System on PCB: (<b>a</b>) top of PCB; (<b>b</b>) bottom of PCB; (<b>c</b>) watch-type wristband.</p>
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<p>Block diagram of the cyclic voltammetry firmware.</p>
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<p>Firmware flowchart.</p>
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<p>Gas phase testing results (<b>a</b>) Windows GUI; (<b>b</b>) Android app.</p>
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<p>Cyclic voltammetry test results with resistor array.</p>
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<p>(<b>a</b>) Aqueous phase testing results; (<b>b</b>) calibration curve.</p>
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<p>Optical phase (body temperature) testing results (<b>a</b>) Windows GUI; (<b>b</b>) Android app.</p>
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<p>IR sensor ADC code versus body temperature calibration.</p>
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<p>Body temperature testing results.</p>
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18 pages, 4451 KiB  
Article
A Biometric Identification for Multi-Modal Biomedical Signals in Geriatric Care
by Yue Che, Lingyan Du, Guozhi Tang and Shihai Ling
Sensors 2024, 24(20), 6558; https://doi.org/10.3390/s24206558 - 11 Oct 2024
Abstract
With the acceleration of global population aging, the elderly have an increasing demand for home care and nursing institutions, and the significance of health prevention and management of the elderly has become increasingly prominent. In this context, we propose a biometric recognition method [...] Read more.
With the acceleration of global population aging, the elderly have an increasing demand for home care and nursing institutions, and the significance of health prevention and management of the elderly has become increasingly prominent. In this context, we propose a biometric recognition method for multi-modal biomedical signals. This article focuses on three key signals that can be picked up by wearable devices: ECG, PPG, and breath (RESP). The RESP signal is introduced into the existing two-mode signal identification for multi-mode identification. Firstly, the features of the signal in the time–frequency domain are extracted. To represent deep features in a low-dimensional feature space and expedite authentication tasks, PCA and LDA are employed for dimensionality reduction. MCCA is used for feature fusion, and SVM is used for identification. The accuracy and performance of the system were evaluated using both public data sets and self-collected data sets, with an accuracy of more than 99.5%. The experimental data fully show that this method significantly improves the accuracy of identity recognition. In the future, combined with the signal monitoring function of wearable devices, it can quickly identify individual elderly people with abnormal conditions, provide safer and more efficient medical services for the elderly, and relieve the pressure on medical resources. Full article
(This article belongs to the Section Biomedical Sensors)
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<p>Block diagram of multi-modal identification.</p>
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<p>Biomedical signal acquisition experiment diagram.</p>
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<p>Block diagram of signal preprocessing.</p>
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<p>Comparison of biomedical signals before and after filtering.</p>
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<p>Energy spectrum diagram of (<b>a</b>) ECG, (<b>b</b>) PPG, and (<b>c</b>) RESP signals.</p>
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<p>Localized waves of (<b>a</b>) ECG, (<b>b</b>) PPG, and (<b>c</b>) RESP signals. The waveform in the red box in (<b>a</b>) is a complete single-period beat.</p>
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<p>Complex vectors of (<b>a</b>) ECG, (<b>b</b>) PPG, and (<b>c</b>) RESP signals.</p>
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<p>Block diagram of feature dimension reduction fusion.</p>
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<p>Principal component contribution rate and cumulative contribution rate of ECG. (<b>a</b>) shows the contribution rates of the first ten feature principal components for PCA reduction of ECG, and (<b>b</b>) shows the cumulative contribution rates of the first ten feature principal components.</p>
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<p>Principal component contribution rate and cumulative contribution rate of PPG. (<b>a</b>) shows the contribution rates of the first ten feature principal components for PCA reduction of PPG, and (<b>b</b>) shows the cumulative contribution rates of the first ten feature principal components.</p>
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<p>Principal component contribution rate and cumulative contribution rate of RESP. (<b>a</b>) shows the contribution rates of the first ten feature principal components for PCA reduction of RESP, and (<b>b</b>) shows the cumulative contribution rates of the first ten feature principal components.</p>
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<p>LDA performs secondary dimensionality reduction results.</p>
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<p>Individual identification results.</p>
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16 pages, 5805 KiB  
Article
Numerical and Experimental Study of a Wearable Exo-Glove for Telerehabilitation Application Using Shape Memory Alloy Actuators
by Mohammad Sadeghi, Alireza Abbasimoshaei, Jose Pedro Kitajima Borges and Thorsten Alexander Kern
Actuators 2024, 13(10), 409; https://doi.org/10.3390/act13100409 - 11 Oct 2024
Abstract
Hand paralysis, caused by conditions such as spinal cord injuries, strokes, and arthritis, significantly hinders daily activities. Wearable exo-gloves and telerehabilitation offer effective hand training solutions to aid the recovery process. This study presents the development of lightweight wearable exo-gloves designed for finger [...] Read more.
Hand paralysis, caused by conditions such as spinal cord injuries, strokes, and arthritis, significantly hinders daily activities. Wearable exo-gloves and telerehabilitation offer effective hand training solutions to aid the recovery process. This study presents the development of lightweight wearable exo-gloves designed for finger telerehabilitation. The prototype uses NiTi shape memory alloy (SMA) actuators to control five fingers. Specialized end effectors target the metacarpophalangeal (MCP), proximal interphalangeal (PIP), and distal interphalangeal (DIP) joints, mimicking human finger tendon actions. A variable structure controller, managed through a web-based Human–Machine Interface (HMI), allows remote adjustments. Thermal behavior, dynamics, and overall performance were modeled in MATLAB Simulink, with experimental validation confirming the model’s efficacy. The phase transformation characteristics of NiTi shape memory wire were studied using the Souza–Auricchio model within COMSOL Multiphysics 6.2 software. Comparing the simulation to trial data showed an average error of 2.76°. The range of motion for the MCP, PIP, and DIP joints was 21°, 65°, and 60.3°, respectively. Additionally, a minimum torque of 0.2 Nm at each finger joint was observed, which is sufficient to overcome resistance and meet the torque requirements. Results demonstrate that integrating SMA actuators with telerehabilitation addresses the need for compact and efficient wearable devices, potentially improving patient outcomes through remote therapy. Full article
(This article belongs to the Special Issue Shape Memory Alloy (SMA) Actuators and Their Applications)
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<p>Illustration of the human finger movement mechanism and various joint structures.</p>
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<p>(<b>a</b>) Fabricated exoskeleton glove, (<b>b</b>) Control and power system, (<b>c</b>–<b>e</b>) Various end effectors designed for the treatment of the MCP, PIP, and DIP joints, respectively.</p>
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<p>Linkage mechanism: (<b>a</b>) Side view, (<b>b</b>) Four-bar model, (<b>c</b>) Hollow disks friction model.</p>
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<p>Schematic representation of the Simulink system model.</p>
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<p>Measurement apparatus for evaluating dynamic finger movements.</p>
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<p>(<b>a</b>) Schematic depiction of the Grip Sensor and test objects, (<b>b</b>) Calibration results.</p>
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<p>Comparison of simulation and experimental test for a profile input.</p>
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<p>Stress–temperature phase diagrams for NiTi shape memory alloy wire: (<b>a</b>) Under different constant DC voltage stimulation, (<b>b</b>) Under PWM stimulation signals. The color legend indicates the martensite volume fraction.</p>
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<p>Experimental results of finger movement measurements at different input speeds, with transparent margins indicating the measurement error bands.</p>
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<p>Experimental results of the joint displacements for all fingers: (<b>a</b>) Metacarpophalangeal (MCP) joint, (<b>b</b>) Proximal Interphalangeal (PIP) joint, and (<b>c</b>) Distal Interphalangeal/Interphalangeal (DIP/IP) joint.</p>
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<p>Experimental results of the torque measurement for all fingers: (<b>a</b>) Metacarpophalangeal (MCP) joint; (<b>b</b>) Proximal Interphalangeal (PIP) joint, and (<b>c</b>) Distal Interphalangeal/Interphalangeal (DIP/IP) joint.</p>
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28 pages, 7534 KiB  
Review
Recent Progress in Photodetectors: From Materials to Structures and Applications
by Tianjun Ma, Ning Xue, Abdul Muhammad, Gang Fang, Jinyao Yan, Rongkun Chen, Jianhai Sun and Xuguang Sun
Micromachines 2024, 15(10), 1249; https://doi.org/10.3390/mi15101249 - 11 Oct 2024
Abstract
Photodetectors are critical components in a wide range of applications, from imaging and sensing to communications and environmental monitoring. Recent advancements in material science have led to the development of emerging photodetecting materials, such as perovskites, polymers, novel two-dimensional materials, and quantum dots, [...] Read more.
Photodetectors are critical components in a wide range of applications, from imaging and sensing to communications and environmental monitoring. Recent advancements in material science have led to the development of emerging photodetecting materials, such as perovskites, polymers, novel two-dimensional materials, and quantum dots, which offer unique optoelectronic properties and high tunability. This review presents a comprehensive overview of the synthesis methodologies for these cutting-edge materials, highlighting their potential to enhance photodetection performance. Additionally, we explore the design and fabrication of photodetectors with novel structures and physics, emphasizing devices that achieve high figure-of-merit parameters, such as enhanced sensitivity, fast response times, and broad spectral detection. Finally, we discuss the demonstration of new applications enabled by these advanced photodetectors, including flexible and wearable devices, next-generation imaging systems, and environmental sensing technologies. Through this review, we aim to provide insights into the current trends and future directions in the field of photodetection, guiding further research and development in this rapidly evolving area. Full article
(This article belongs to the Special Issue Advances in Photodetecting Materials, Devices and Applications)
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<p>Design and application of photodetectors [<a href="#B36-micromachines-15-01249" class="html-bibr">36</a>,<a href="#B37-micromachines-15-01249" class="html-bibr">37</a>,<a href="#B38-micromachines-15-01249" class="html-bibr">38</a>].</p>
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<p>Microscope photographs of the device structure and the performance of 2D single-crystalline microplate photodetectors. (<b>a</b>) Schematic diagram of the device structure. (<b>b</b>) Photodetectors based on (BA)<sub>2</sub>(MA)<sub>n−1</sub>PbnI<sub>3n+1</sub> microplate stacking on Au electrodes (images i–v correspond to <span class="html-italic">n</span> = 1–5, respectively). Scale bar: 15 μm. (<b>c</b>) Schematic diagram of hetero-/homostructure-based photodetectors. (<b>d</b>) Band alignment diagram of the (BA)<sub>2</sub>(MA)<sub>3</sub>Pb<sub>4</sub>I<sub>13</sub>/(BA)<sub>2</sub>(MA)<sub>2</sub>Pb<sub>3</sub>I<sub>10</sub> heterostructure. (<b>e</b>) Self-powered property comparison of the ITO-n<sub>4</sub>/n<sub>3</sub>-Au, ITO-n<sub>4</sub>/n<sub>4</sub>-Au, ITO-n<sub>4</sub>-Au, and Au-n<sub>4</sub>-Au PDs. Semilogarithmic I-t curves under 600 nm illumination at 0 V [<a href="#B51-micromachines-15-01249" class="html-bibr">51</a>].</p>
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<p>Architecture of the flexible photodetector and the characterization of the active layer. (<b>a</b>) Schematic of the device. (<b>b</b>) Schematic representations of the solution growth including the following four steps: (i) cleaving the mica, (ii) dropping the solution between the micas, (iii) heating and quasi-static solution (QSS) growth, and (iv) bending the mica substrate. (<b>c</b>) Photograph of the device. Inset: micrograph of the device, with a scale bar of 100 μm. (<b>d</b>) False-color SEM image of the device, where light yellow outlines the Au electrodes, and the scale bar is 3 μm. Inset: tilted SEM image of the edge of the perovskite nanosheet on mica [<a href="#B11-micromachines-15-01249" class="html-bibr">11</a>].</p>
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<p>Characterization of light-trapping capability. (<b>a</b>–<b>d</b>) Schematic structure. (<b>e</b>–<b>h</b>) Cross-sectional SEM images, blue dashed lines marks the edge of PVK films. (<b>i</b>–<b>k</b>) Absorbance spectra, reflectance spectra, and light-harvesting efficiency. (<b>l</b>–<b>o</b>) Field plots of time-averaged electromagnetic energy density with respect to the <span class="html-italic">x</span>–<span class="html-italic">z</span> plane at the wavelength of 650 nm of F-PVK, T-G-PVK, B-G-PVK, and T-B-G-PVK films. T-B-G-PVK exhibits the highest light-harvesting capability [<a href="#B56-micromachines-15-01249" class="html-bibr">56</a>].</p>
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<p>(<b>a</b>) Schematic illustration of the fabrication process of the bilayer MoS<sub>2</sub>, silicon nanowire, silver nanoparticle, and hybrid photodetector. (<b>b</b>) Optical image of the hybrid MoS<sub>2</sub> device. Scale bar, 100 μm. (<b>c</b>) Normalized TRPL decay of bilayer MoS<sub>2</sub> on SiNW and sapphire substrates. The exponential fits of both trends are shown with a black solid line [<a href="#B75-micromachines-15-01249" class="html-bibr">75</a>]. (<b>d</b>) An illustration of the monolayer MoS<sub>2</sub>/BTP-4F device. (<b>e</b>) The energy-level marching for the monolayer MoS<sub>2</sub> and BTP-4F film at the VDS of 5 V. (<b>f</b>) The I–V curves corresponding to the pure MoS<sub>2</sub> and MoS<sub>2</sub>/BTP-4F devices, respectively [<a href="#B76-micromachines-15-01249" class="html-bibr">76</a>].</p>
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<p>Fabrication and characterization of bare β-Ga<sub>2</sub>O<sub>3</sub> and GQDs/β-Ga<sub>2</sub>O<sub>3</sub> PDs. (<b>a</b>) Schematic diagram of the hybrid GQDs/β-Ga<sub>2</sub>O<sub>3</sub> PD under light illumination. (<b>b</b>) Optical microscope image of the fabricated β-Ga<sub>2</sub>O<sub>3</sub> device after annealing with the SEM image of the effective area of the β-Ga<sub>2</sub>O<sub>3</sub> flake, as shown in the inset. (<b>c</b>) AFM images of the bare β-Ga<sub>2</sub>O<sub>3</sub> device (left) and (<b>d</b>) the GQDs/β-Ga<sub>2</sub>O<sub>3</sub> device (left) with a cross-sectional height profile (right) along the white dashed line depicted in the AFM images of (<b>c</b>,<b>d</b>). The enlarged images in (<b>c</b>,<b>d</b>) reveal that the size of these GQDs is ~10.1 nm [<a href="#B82-micromachines-15-01249" class="html-bibr">82</a>]. (<b>e</b>) A 3D schematic representation of the MoS<sub>2</sub>/SnS<sub>2</sub> QDs heterojunction. (<b>f</b>) Schematic illustration of the SnS<sub>2</sub>-QDs and monolayer MoS<sub>2</sub> band structure after the formation of a heterojunction with proposed (<b>e</b>–<b>h</b>) pair separation [<a href="#B83-micromachines-15-01249" class="html-bibr">83</a>]. (<b>g</b>) A 3D scheme of the a-IGZO/PbS QDs heterojunction device. (<b>h</b>) I–V curves under dark and NIR light (@1064 m, 11.3 μW) of the a-IGZO/PbS QDs heterojunction device and the PbS QDs-EDT film-only device [<a href="#B84-micromachines-15-01249" class="html-bibr">84</a>].</p>
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<p>(<b>a</b>) Schematic diagram of the CuI/Si photodiode. (<b>b</b>) Time-resolved photoresponse of the device at 0 V bias under illumination with different monochromatic light wavelengths. (<b>c</b>) Current–voltage characteristics of the CuI/Si photodetector in the dark and under illumination with 365 nm light at 1000 μWcm<sup>−2</sup>. (<b>d</b>) Transient responses of the CuI/Si photodetector under various light intensities of 365 nm light at 0 V bias. (<b>e</b>) Light–power-dependent photocurrent of the photodetector under 365 nm light irradiation at 0 V bias [<a href="#B98-micromachines-15-01249" class="html-bibr">98</a>]. (<b>f</b>) Schematic diagram of a single Ti<sub>3</sub>C<sub>2</sub>T<sub>x</sub>-RAN PD structure. (<b>g</b>) Photocurrent curves of devices with concentrations of 10, 7.5, and 5 mg mL<sup>−1</sup> at 915, 1064, 1122, and 1342 nm. (<b>h</b>) Plots of photocurrent changes with different optical power densities for devices with concentrations of 10, 7.5, and 5 mg mL<sup>−1</sup> at a wavelength of 1064 nm [<a href="#B99-micromachines-15-01249" class="html-bibr">99</a>].</p>
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<p>(<b>a</b>) Schematic illustration of the Ag NW@S-ZnO NR-based UV detector. (<b>b</b>) UV–Vis optical transmittance spectra of Ag NW@S-ZnO NR thin films with different drop-coating times. The insets are corresponding SEM images of the Ag NW@S-ZnO NRs network of PD1, PD2, and PD3. (<b>c</b>) Appearance of Ag NW@ZnO NR film on HIT-logo paper [<a href="#B100-micromachines-15-01249" class="html-bibr">100</a>]. (<b>d</b>) Schematic diagram of the Ti<sub>3</sub>C<sub>2</sub>T<sub>x</sub>/Al<sub>2</sub>O<sub>3</sub>/ZnO/Ti<sub>3</sub>C<sub>2</sub>T<sub>x</sub>/ITO/PET device, accompanied by digital images of it. (<b>e</b>) Transmittance profiles of the ZnO-based flexible photodetector with and without Ti<sub>3</sub>C<sub>2</sub>T<sub>x</sub>. (<b>f</b>) Cross-section TEM image of the Ti<sub>3</sub>C<sub>2</sub>T<sub>x</sub>/Al<sub>2</sub>O<sub>3</sub>/ZnO/Ti<sub>3</sub>C<sub>2</sub>T<sub>x</sub>/ITO/PET device, along with elemental mapping profiles of Ti, Al, Zn, In, and O [<a href="#B101-micromachines-15-01249" class="html-bibr">101</a>].</p>
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<p>(<b>a</b>) Schematic diagram of the CsI:Na scintillator with a PhC cavity (TiO<sub>2</sub> + porous SiO<sub>2</sub>). The TiO<sub>2</sub>/SiO<sub>2</sub> PhCs have been shown to be feasible in previous work. Here, we replace the SiO<sub>2</sub> film with a porous SiO<sub>2</sub> material so as to achieve a low refractive index (1.06) for the SiO<sub>2</sub> layer. The porous SiO<sub>2</sub> material can be realized by random SiO<sub>2</sub> nanorod arrangement. (<b>b</b>) Photodetector signal enhancement vs. period and filling factor of the photonic crystal. (<b>c</b>) Spectral density of photons (ph) and photoelectrons (phe) with optimized configuration of the PhC cavity (TiO<sub>2</sub> + porous SiO<sub>2</sub>). The emission spectrum is shifted to a longer wavelength to match the quantum efficiency spectrum of the photodetector [<a href="#B107-micromachines-15-01249" class="html-bibr">107</a>]. (<b>d</b>) The pulse photoresponse of the photodetector for red light with varying intensity at non-biased and self-biased conditions. (<b>e</b>) Different bias voltages at a 30 mW/cm<sup>2</sup> intensity [<a href="#B108-micromachines-15-01249" class="html-bibr">108</a>].</p>
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<p>(<b>a</b>) Chemical structures of PM6 and Y6. (<b>b</b>) Finger photoplethysmography setup. (<b>c</b>) Direct current read-out of the PPG device using 950 and 630 nm LEDs [<a href="#B36-micromachines-15-01249" class="html-bibr">36</a>]. (<b>d</b>) Photograph of a typical flexible photodetector based on 1D arrays bent at a bending radius of 10 mm, with the inset presenting the schematic illustration of the device. (<b>e</b>) Scheme of the flexible photodetectors monitoring the UV photodetection signals. (<b>f</b>) Typical I-V curves of the polymer array-based photodetectors under the dark condition and under different UV light illuminations, obtained from the attached flexible photodetector device on the back skin of the mouse. Inset: photograph of the flexible device attached closely to the back skin of a nude mouse [<a href="#B114-micromachines-15-01249" class="html-bibr">114</a>].</p>
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<p>(<b>a</b>) The schematic representation of the device under humid conditions shows the formation of physisorbed layers and dipoles on the basal planes of SnSe, and a schematic representation of a freshly prepared pristine Au/Ti/SnSe/Ti/Au device after air exposure and under white light illumination [<a href="#B120-micromachines-15-01249" class="html-bibr">120</a>]. (<b>b</b>) Structural schematic of a Sb<sub>2</sub>O<sub>3</sub>/PdTe<sub>2</sub>/Si heterojunction photodetector and a self-powered photoresponse mechanism of Sb<sub>2</sub>O<sub>3</sub>/PdTe<sub>2</sub>/Si heterojunction photodetectors [<a href="#B37-micromachines-15-01249" class="html-bibr">37</a>].</p>
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<p>(<b>a</b>) Schematic diagram of the Pd-Hf-contacted CNT photodetector under illumination and a false-colored SEM image showing the channel of an as-fabricated CNT photodetector with Lch = 200 nm and total Wch = 200 μm. Relative response as a function of the modulation frequency of the input signal for the CNT photodetector. The extracted 3 dB bandwidth is 40 GHz at V = −0.2 V [<a href="#B131-micromachines-15-01249" class="html-bibr">131</a>]. (<b>b</b>) A 3D cross-section representation of the heterogeneous InSe/SiN photodetector and electric-field profiles (|E|<sup>2</sup>) of TE modes of an unloaded SiN waveguide and 90 nm InSe on SiN at 976 nm (top panel). Normalized frequency response at 10 V. A total of 50 measurements (blue-scattered points) and average (red line) data are plotted. A 3 dB cut-off frequency of 85 MHz is measured [<a href="#B130-micromachines-15-01249" class="html-bibr">130</a>].</p>
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10 pages, 1018 KiB  
Article
A Non-Surgical Wearable Option for Bone Conduction Hearing Implants: A Comparative Study with Conventional Bone Conduction Hearing Aids Mounted on Eyeglasses
by Federica Di Berardino, Giovanni Ciavarro, Giulia Fumagalli, Claudia Albanese, Enrico Pasanisi, Diego Zanetti and Vincenzo Vincenti
Audiol. Res. 2024, 14(5), 893-902; https://doi.org/10.3390/audiolres14050075 - 11 Oct 2024
Abstract
Objectives. This study aimed to compare the audiological benefits of a non-implantable wearable option for a bone conduction (BC) implant mounted on an arch (SoundArc) to those of traditional BC hearing aids (HAs) mounted on eyeglasses (BCHAs) in patients with moderate to severe [...] Read more.
Objectives. This study aimed to compare the audiological benefits of a non-implantable wearable option for a bone conduction (BC) implant mounted on an arch (SoundArc) to those of traditional BC hearing aids (HAs) mounted on eyeglasses (BCHAs) in patients with moderate to severe conductive or mixed hearing loss. Methods: A preliminary cross-sectional observational prospective cohort study was conducted in the Tertiary Audiological Department, University Hospital. Fourteen adults with conductive or mixed hearing loss (PTA at 0.5-1-2-4 KHz = 67 ± 15 dB HL) who had been wearing conventional BCHAs mounted on eyeglasses for at least 3 years and had declined surgical implantation of a bone conduction hearing implant (BCHI) were included in the study. Unaided and aided pure-tone air conduction (AC) and bone conduction (BC) thresholds, as well as speech tests in quiet and noise, were recorded at baseline and in two different settings: with a BCHI mounted on SoundArc® and with their own BCHAs mounted on eyeglasses using two couplers. Participants completed questionnaires in both conditions, including the International Inventory for Hearing Aids (IOI-HA), the Hearing Handicap Inventory for Adults/Elderly (HHIA/E), the Speech, Spatial, and Qualities of Hearing Scale (SSQ), a 10-point visual analog scale (VAS), and the Fatigue Impact Scale (FIS). Results: A significant functional gain was observed in both settings (p = 0.0001). Better speech perception in quiet and noise was observed with SoundArc compared to conventional BCHAs on eyeglasses (improvements in word repetition scores in noise: +19.3 at SNR +10 dB, p = 0.002; +12.1 at SNR 0 dB, p = 0.006; and +11.4 at SNR −10 dB, p = 0.002). No significant differences were found in IOI-HA, FIS, and HHIA/E scores. However, significantly better SSQ scores were reported for SoundArc in all domains (p = 0.0038). Conclusions: Although patients were accustomed to using BCHAs mounted on eyeglasses, the bone conduction wearable option of the BCHI (SoundArc) proved to be a viable alternative for adult patients with conductive or mixed hearing loss who are unable or unwilling to undergo BCHI surgery. Full article
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<p>SoundArc, BCHA, and unaided differences in each patient. The cases (# ID) are reported on the horizontal axis, whereas the vertical axis describes the hearing thresholds (dB HL).</p>
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<p>The maximum intelligibility thresholds with BCHAs and SoundArc in quiet. The reported boxplot dots are the quartiles: the minimum value, the first quartile (Q1, 25° percentile), the median (Q2, 50° percentile), the third quartile (Q3, 75° percentile), and the maximum value.</p>
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<p>Word repetition scores with BCHAs and SoundArc. The reported boxplot dots are the quartiles: the minimum value, the first quartile (Q1, 25° percentile), the median (Q2, 50° percentile), the third quartile (Q3, 75° percentile), and the maximum value.</p>
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14 pages, 1664 KiB  
Article
Flexible Highly Thermally Conductive PCM Film Prepared by Centrifugal Electrospinning for Wearable Thermal Management
by Jiaxin Qiao, Chonglin He, Zijiao Guo, Fankai Lin, Mingyong Liu, Xianjie Liu, Yifei Liu, Zhaohui Huang, Ruiyu Mi and Xin Min
Materials 2024, 17(20), 4963; https://doi.org/10.3390/ma17204963 - 11 Oct 2024
Abstract
Personal thermal management materials integrated with phase-change materials have significant potential to satisfy human thermal comfort needs and save energy through the efficient storage and utilization of thermal energy. However, conventional organic phase-change materials in a solid state suffer from rigidity, low thermal [...] Read more.
Personal thermal management materials integrated with phase-change materials have significant potential to satisfy human thermal comfort needs and save energy through the efficient storage and utilization of thermal energy. However, conventional organic phase-change materials in a solid state suffer from rigidity, low thermal conductivity, and leakage, making their application challenging. In this work, polyethylene glycol (PEG) was chosen as the phase-change material to provide the energy storage density, polyethylene oxide (PEO) was chosen to provide the backbone structure of the three-dimensional polymer network and cross-linked with the PEG to provide flexibility, and carbon nanotubes (CNTs) were used to improve the mechanical and thermal conductivity of the material. The thermal conductivity of the composite fiber membranes was boosted by 77.1% when CNTs were added at 4 wt%. Water-resistant modification of the composite fiber membranes was successfully performed using glutaraldehyde-saturated steam. The resulting composite fiber membranes had a reasonable range of phase transition temperatures, and the CC4PCF-55 membranes had melting and freezing latent heats of 66.71 J/g and 64.74 J/g, respectively. The results of this study prove that the green CC4PCF-55 composite fiber membranes have excellent flexibility, with good thermal energy storage capacity and thermal conductivity and, therefore, high potential in the field of flexible wearable thermal management textiles. Full article
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<p>Centrifugal electrostatic spinning for the preparation of flexible and highly thermally conductive phase-change thermal storage membranes.</p>
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<p>Images of (<b>a</b>) PEO, (<b>b</b>) PCF-40, (<b>c</b>) PCF-45, (<b>d</b>) PCF-50, (<b>e</b>) PCF-55, (<b>f</b>) PCF-60, (<b>g</b>) C<sub>2</sub>PCF-55, (<b>h</b>) C<sub>4</sub>PCF-55, (<b>i</b>) C<sub>6</sub>PCF-55, (<b>j</b>) C<sub>8</sub>PCF-55, (<b>k</b>) C<sub>10</sub>PCF-55, and (<b>l</b>) CC<sub>4</sub>PCF-55 fibrous membranes and the corresponding single fiber.</p>
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<p>(<b>a</b>–<b>c</b>) Folding, curling, and stretching images, respectively, of C<sub>4</sub>PCF-55 and CC<sub>4</sub>PCF-55 fibrous membranes. (<b>d</b>–<b>f</b>) Optical images of a CC<sub>4</sub>PCF-55 membrane immersed in water for 0 min, 5 min, and 10 min, respectively. (<b>g</b>) FT-IR spectra of C<sub>4</sub>PCF-55 and CC<sub>4</sub>PCF-55 fibrous membranes. (<b>h</b>,<b>i</b>) Water contact angle images of C<sub>4</sub>PCF-55 and CC<sub>4</sub>PCF-55 fibrous membranes, respectively. (<b>j</b>) UV—visible spectrogram of C<sub>4</sub>PCF-55 and CC<sub>4</sub>PCF-55 fibrous membranes.</p>
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<p>(<b>a</b>) Thermal conductivity of the composite fibrous membranes. (<b>b</b>) XRD patterns of PEG1000, C<sub>4</sub>PCF-55, and CC<sub>4</sub>PCF-55. (<b>c</b>) Shape stability of PEG1000 and CC<sub>4</sub>PCF-55.</p>
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<p>Thermal properties of the prepared composite fiber membranes: DSC curves of PEG and the composite fiber membranes for (<b>a</b>) the endothermic process and (<b>b</b>) the exothermic process. (<b>c</b>) Melting/freezing enthalpies (ΔH<sub>m</sub>/ΔH<sub>f</sub>) and melting/freezing phase transition temperatures (T<sub>m</sub>/T<sub>f</sub>) of the composite fiber membranes. DSC curves of the CC<sub>4</sub>PCF-55 fiber membrane after 2, 20, and 50 cycles in the (<b>d</b>) endothermic process and (<b>e</b>) exothermic process.</p>
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<p>Representative thermal images of the PEO and CC<sub>4</sub>PCF55 membranes recorded by an IR camera in the (<b>a</b>) heating and (<b>b</b>) cooling processes. (<b>c</b>,<b>d</b>) Temperature evolution graphs of the PEO and CC<sub>4</sub>PCF55 fiber membranes.</p>
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18 pages, 2885 KiB  
Article
Recurrence Quantification Analysis Based Methodology in Automatic Aerobic Threshold Detection: Applicability and Accuracy across Age Groups, Exercise Protocols and Health Conditions
by Giovanna Zimatore, Cassandra Serantoni, Maria Chiara Gallotta, Marco Meucci, Laurent Mourot, Dafne Ferrari, Carlo Baldari, Marco De Spirito, Giuseppe Maulucci and Laura Guidetti
Appl. Sci. 2024, 14(20), 9216; https://doi.org/10.3390/app14209216 - 10 Oct 2024
Abstract
A new method based on the Recurrence Quantification Analysis (RQA) of the heart rate (HR) offers an objective, efficient alternative to traditional methods for Aerobic Threshold (AerT) identification that have practical limitations due to the complexity of equipment and interpretation. This study aims [...] Read more.
A new method based on the Recurrence Quantification Analysis (RQA) of the heart rate (HR) offers an objective, efficient alternative to traditional methods for Aerobic Threshold (AerT) identification that have practical limitations due to the complexity of equipment and interpretation. This study aims to validate the RQA-based method’s applicability across varied demographics, exercise protocols, and health status. Data from 123 cardiopulmonary exercise tests were analyzed, and participants were categorized into four groups: athletes, young athletes, obese individuals, and cardiac patients. Each participant’s AerT was assessed using both traditional ventilatory equivalent methods and the automatic RQA-based method. Ordinary Least Products (OLP) regression analysis revealed strong correlations (r > 0.77) between the RQA-based and traditional methods in both oxygen consumption (VO2) and HR at the AerT. Mean percentage differences in HR were below 2.5%, and the Technical Error for HR at AerT was under 8%. The study validates the RQA-based method, directly applied to HR time series, as a reliable tool for the automatic detection of the AerT, demonstrating its accuracy across diverse age groups and fitness levels. These findings suggest a versatile, cost-effective, non-invasive, and objective tool for personalized exercise prescription and health risk stratification, thereby fulfilling the study’s goal of broadening the method’s applicability. Full article
(This article belongs to the Special Issue AI-Based Biomedical Signal Processing)
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<p>An exemplificative graph depicting the original heart rate time series for a graded exercise over 500 points, along with the smoothed version using a 5-point moving average. The red line represents the smoothed heart rate.</p>
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<p>Standard CPET equipment: (<b>a</b>) mask, volume sensor, and gas analyzer tubing; (<b>b</b>) blood pressure monitor; (<b>c</b>) smartwatch for HR data collection; (<b>d</b>) ergometer (cycle or treadmill); (<b>e</b>) gas analyzer; and (<b>f</b>) display.</p>
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<p>HR (bpm) vs. VO<sub>2</sub> (mL/min) at AerT from 111 CPET tests. The participants are divided into athletes (group A, blue cross), obese (group O, red circle), cardiac patients (group C, light-blue diamond), and young athletes (group Y, yellow circle), respectively.</p>
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<p>Representative HR time series, panels (<b>a</b>,<b>d</b>), belong to groups C and Y, respectively. Panels (<b>b</b>,<b>e</b>) show DET(%), and the second derivative where the dashed red horizontal line corresponds to the cut-off; in panels (<b>c</b>,<b>f</b>), DET (%) (in black), and workload (in blue) are shown point by point, respectively. The red vertical line corresponds to AerT (the most convex minimum of DET (%), as explained in the Materials and Methods section).</p>
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<p>OLP regression line on (<b>a</b>) HR and (<b>b</b>) VO<sub>2</sub> at AerT (VT1), all values correspond to the minima DETmin. The participants are divided into athletes (group A, blue cross), obese (group O, red circle), cardiac patients (group C, light-blue diamond), and young athletes (group Y, yellow circle).</p>
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<p>Bland Altman plot for (<b>a</b>) HR (bpm) and (<b>b</b>) VO<sub>2</sub> (mL/min) at AerT. The participants are divided into athletes (group A, blue cross), obese (group O, red circle), cardiac patients (group C, light-blue diamond), and young athletes (group Y, yellow circle), respectively. The horizontal black line corresponds to bias (mean difference), and the dashed horizontal black line to the lower and upper limits of agreement (LOA); LOAs are calculated as the mean difference ±1.96 standard deviations (SD).</p>
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<p>Unthresholded recurrence plot of a HR time series recorded as a breath-by-breath, from a cardiopulmonary exercise test (CPET) device (Cosmed, Rome, Italy).</p>
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<p>Python code.</p>
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