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Keywords = non-contact respiration detection

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22 pages, 7658 KiB  
Article
Emotion Recognition in a Closed-Cabin Environment: An Exploratory Study Using Millimeter-Wave Radar and Respiration Signals
by Hanyu Wang, Dengkai Chen, Sen Gu, Yao Zhou, Jianghao Xiao, Yiwei Sun, Jianhua Sun, Yuexin Huang, Xian Zhang and Hao Fan
Appl. Sci. 2024, 14(22), 10561; https://doi.org/10.3390/app142210561 - 15 Nov 2024
Viewed by 589
Abstract
In the field of psychology and cognition within closed cabins, noncontact vital sign detection holds significant potential as it can enhance the user’s experience by utilizing objective measurements to assess emotions, making the process more sustainable and easier to deploy. To evaluate the [...] Read more.
In the field of psychology and cognition within closed cabins, noncontact vital sign detection holds significant potential as it can enhance the user’s experience by utilizing objective measurements to assess emotions, making the process more sustainable and easier to deploy. To evaluate the capability of noncontact methods for emotion recognition in closed spaces, such as submarines, this study proposes an emotion recognition method that employs a millimeter-wave radar to capture respiration signals and uses a machine-learning framework for emotion classification. Respiration signals were collected while the participants watched videos designed to elicit different emotions. An automatic sparse encoder was used to extract features from respiration signals, and two support vector machines were employed for emotion classification. The proposed method was experimentally validated using the FaceReader software, which is based on audiovisual signals, and achieved an emotion classification accuracy of 68.21%, indicating the feasibility and effectiveness of using respiration signals to recognize and assess the emotional states of individuals in closed cabins. Full article
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<p>Overall research framework.</p>
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<p>Millimeter-wave radar sensor.</p>
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<p>Valence–arousal (VA) two-dimensional model of emotion.</p>
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<p>Flowchart of respiration data acquisition experiment.</p>
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<p>Experiment Scenario.</p>
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<p>Score distribution of video clips.</p>
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<p>Respiration signal processing.</p>
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<p>Respiration signal segments after processing.</p>
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<p>Structure of SAE-SVM classification system.</p>
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<p>Structure of an auto-encoder.</p>
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<p>Original (blue) and reconstructed (red) respiration signal segment.</p>
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<p>Training loss curve of two support vector machines: (<b>a</b>) training loss curve of valence SVM; (<b>b</b>) training loss curve of arousal SVM.</p>
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<p>Confusion matrix of classification results for (<b>a</b>) valence and (<b>b</b>) arousal.</p>
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<p>Change in accuracy of classification results of (<b>a</b>) valence and (<b>b</b>) arousal.</p>
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<p>Comparison between different methods of measurement on the dimensions of intrusiveness, system complexity, and deployment cost.</p>
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15 pages, 6981 KiB  
Article
Noncontact Monitoring of Respiration and Heartbeat Based on Two-Wave Model Using a Millimeter-Wave MIMO FM-CW Radar
by Mie Mie Ko and Toshifumi Moriyama
Electronics 2024, 13(21), 4308; https://doi.org/10.3390/electronics13214308 - 1 Nov 2024
Viewed by 809
Abstract
This paper deals with the non-contact measurement of heartbeat and respiration using a millimeter-wave multiple-input–multiple-output (MIMO) frequency-modulated continuous-wave (FM-CW) radar. Monitoring heartbeat and respiration is useful for detecting cardiac diseases and understanding stress levels. Contact sensors are not suitable for these sorts of [...] Read more.
This paper deals with the non-contact measurement of heartbeat and respiration using a millimeter-wave multiple-input–multiple-output (MIMO) frequency-modulated continuous-wave (FM-CW) radar. Monitoring heartbeat and respiration is useful for detecting cardiac diseases and understanding stress levels. Contact sensors are not suitable for these sorts of long-term measurements due to the discomfort and skin irritation they cause. Therefore, the use of non-contact sensors, such as radars, is desirable. In this study, we obtained heartbeat and respiration information from phase data measured using a millimeter-wave MIMO FM-CW radar. We propose a two-wave model based on a Fourier series expansion and extract respiration and heartbeat information as a minimization problem. This model makes it possible to produce respiration and heartbeat waveforms. The produced heartbeat waveform can be used for estimating the interbeat interval (IBI). Experiments were conducted to confirm the usefulness of the proposed method. Moreover, the estimated results were compared with the contact sensor’s results. The results for both types of sensors were in good agreement. Full article
(This article belongs to the Special Issue Feature Papers in Microwave and Wireless Communications Section)
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<p>The relationship between frequency and time in the FM-CW radar.</p>
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<p>Antenna array and element arrangement.</p>
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<p>Window function (<math display="inline"> <semantics> <mrow> <msub> <mi>t</mi> <mn>0</mn> </msub> <mo>=</mo> <mn>0</mn> </mrow> </semantics> </math>, <math display="inline"> <semantics> <mrow> <msub> <mi>T</mi> <mi>w</mi> </msub> </mrow> </semantics> </math> = 5 s, and <math display="inline"> <semantics> <mrow> <mi mathvariant="normal">Δ</mi> <mi>T</mi> </mrow> </semantics> </math> = 1 s).</p>
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<p>Flow chart of two-step estimation.</p>
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<p>Measurement setup.</p>
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<p>MIMO radar measurement.</p>
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<p>Measured phase data of target 1 (<b>a</b>) in the time domain and (<b>b</b>) in the frequency domain.</p>
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<p>A comparison between the original waveform and the waveform calculated using the parameters estimated at 10 s. (<b>a</b>) The first step; (<b>b</b>) the second step.</p>
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<p>The estimated results for target 1. (<b>a</b>) Respiration rate, (<b>b</b>) heartbeat rate.</p>
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<p>The reconstructed waveforms of target 1. (<b>a</b>) Respiration waveform; (<b>b</b>) heartbeat waveform.</p>
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<p>The heartbeat IBI values of target 1, obtained via radar and BVP sensor.</p>
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<p>Measured phase data of target 2 (<b>a</b>) in the time domain and (<b>b</b>) in the frequency domain.</p>
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<p>The estimated results of target 2. (<b>a</b>) Respiration rate; (<b>b</b>) heartbeat rate.</p>
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<p>The reconstructed waveforms of target 2. (<b>a</b>) Respiration waveform; (<b>b</b>) heartbeat waveform.</p>
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<p>The heartbeat IBI values of target 2, obtained via radar and BVP sensor.</p>
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<p>Measured phase data of target 1 (solid line) and their body movement (dotted line), estimated by <math display="inline"> <semantics> <mrow> <msub> <mi>a</mi> <mrow> <mn>0</mn> <mo>,</mo> <mi>r</mi> </mrow> </msub> </mrow> </semantics> </math>.</p>
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18 pages, 6050 KiB  
Article
Investigation of a Camera-Based Contactless Pulse Oximeter with Time-Division Multiplex Illumination Applied on Piglets for Neonatological Applications
by René Thull, Sybelle Goedicke-Fritz, Daniel Schmiech, Aly Marnach, Simon Müller, Christina Körbel, Matthias W. Laschke, Erol Tutdibi, Nasenien Nourkami-Tutdibi, Elisabeth Kaiser, Regine Weber, Michael Zemlin and Andreas R. Diewald
Biosensors 2024, 14(9), 437; https://doi.org/10.3390/bios14090437 - 9 Sep 2024
Viewed by 1115
Abstract
(1) Objective: This study aims to lay a foundation for noncontact intensive care monitoring of premature babies. (2) Methods: Arterial oxygen saturation and heart rate were measured using a monochrome camera and time-division multiplex controlled lighting at three different wavelengths (660 nm, 810 [...] Read more.
(1) Objective: This study aims to lay a foundation for noncontact intensive care monitoring of premature babies. (2) Methods: Arterial oxygen saturation and heart rate were measured using a monochrome camera and time-division multiplex controlled lighting at three different wavelengths (660 nm, 810 nm and 940 nm) on a piglet model. (3) Results: Using this camera system and our newly designed algorithm for further analysis, the detection of a heartbeat and the calculation of oxygen saturation were evaluated. In motionless individuals, heartbeat and respiration were separated clearly during light breathing and with only minor intervention. In this case, the mean difference between noncontact and contact saturation measurements was 0.7% (RMSE = 3.8%, MAE = 2.93%). (4) Conclusions: The new sensor was proven effective under ideal animal experimental conditions. The results allow a systematic improvement for the further development of contactless vital sign monitoring systems. The results presented here are a major step towards the development of an incubator with noncontact sensor systems for use in the neonatal intensive care unit. Full article
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Graphical abstract

Graphical abstract
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<p>Molar absorption spectrum of hemoglobin and oxyhemoglobin based on Prahl [<a href="#B18-biosensors-14-00437" class="html-bibr">18</a>].</p>
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<p>Schematic representation of the light path from the transmitter through the skin and back to the receiver including remission and scattering as well as the path length <span class="html-italic">l</span> and the time-dependent path length <math display="inline"><semantics> <mrow> <mi>l</mi> <mo>(</mo> <mi>t</mi> <mo>)</mo> </mrow> </semantics></math> in the artery. <math display="inline"><semantics> <msubsup> <mi>I</mi> <mi>λ</mi> <mi>i</mi> </msubsup> </semantics></math> means the intensity or power of the incident light and <math display="inline"><semantics> <msubsup> <mi>I</mi> <mi>λ</mi> <mi>t</mi> </msubsup> </semantics></math> means the intensity of the light escaping from the measuring medium. <math display="inline"><semantics> <msubsup> <mi>I</mi> <mi>λ</mi> <mi>r</mi> </msubsup> </semantics></math> means the power of reflected light.</p>
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<p>Time diagram of the LEDs for standard settings. The numbers indicate the clock cycles. During the first clock cycle, there is an empty measurement without any illumination; during the second cycle, the 660 nm LEDs are switched on; during the third cycle, the 810 nm LEDs; during the fourth cycle, the 660 nm LEDs again; during the fifth cycle, the 940 nm LEDs; and during the sixth cycle, the 660 nm LEDs again. Then the sequence repeats from the beginning.</p>
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<p>Undersampling diagram for expected background light frequencies over different sampling frequencies. Example: A 50 Hz modulated light (light blue color) results in 10 Hz (maximum) when sampled with 20 Hz, in 0 Hz when sampled with 25 Hz and in 16.6 Hz when sampled with 33.3 Hz. The selected sampling frequencies are chosen for 660 nm at 110 Hz (black line) and 810/940 nm at 36.67 Hz = 110/3 Hz in a manner that the undersampling frequencies of the modulated background light are out of the frequencies of interest.</p>
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<p>Block diagram of the algorithm used for the detection of a heartbeat and calculation of the oxygen saturation.</p>
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<p>(<b>A</b>) Number of LEDs per supply line and wavelength. (<b>B</b>) Arrangement of LEDs for lighting board. Numbers indicate the supply lines.</p>
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<p>Attenuation normalized to the intensity <math display="inline"><semantics> <msubsup> <mi>I</mi> <mi>λ</mi> <mi>i</mi> </msubsup> </semantics></math> for the wavelength of 940 nm on the target. The pixel pitch and pixel size is 5.3 μm.</p>
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<p>A screenshot (2) Figure seem to be cut on the top in a way that may affect scientific reading. Please check and provide whole image. of the measurement GUI including a picture of the piglet in the incubator with active illumination. The quadratic area is the area of interest (AOI) of 128 × 128 pixels for signal processing. The colors of the quadratic sub-areas have no additional meaning.</p>
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<p>Measurement setup: A piglet was placed in a NICU incubator. Pulse, oxygen saturation and respiration rate were measured by a camera-based contactless pulse oximeter which was placed on the incubator. For validation, an independent monitor, which is commonly used in neonatal intensive care units, was linked via a pulse oximeter sensor to the piglet leg together with a three-channel electrocardiograph. The red color in the incubator is caused by the active illumination of the SpO<sub>2</sub> sensor system and not from an infrared heating lamp, which would disturb the measurement. The camera and the illumination are mounted at the bottom side of the metallic box above the incubator and point into the incubator. The camera and the illumination are shown in the lower-left corner of the picture.</p>
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<p>Example measurement 1. Camera data showing a recording from the oxygen saturation sensor: Example of a cumulated spectrum with respiration superimposed onto the heartbeat (multiplex scheme see <a href="#biosensors-14-00437-f003" class="html-fig">Figure 3</a>).</p>
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<p>Example measurement 2. Camera data of a recording from the oxygen saturation sensor: Example of a cumulative spectrum with successful heartbeat detection (multiplex scheme see <a href="#biosensors-14-00437-f002" class="html-fig">Figure 2</a>). Heartbeat and respiration rate are clearly identifiable, as well as artifacts and respiratory interruptions.</p>
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<p>Bland– Altman diagram demonstrating the successful measurement of oxygen saturation of one piglet within a period of 20 min. This serves to compare the two measurement methods used.</p>
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<p>Time signals of oxygen saturation compare camera and monitor. Calculated according to <a href="#biosensors-14-00437-f011" class="html-fig">Figure 11</a>.</p>
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22 pages, 5916 KiB  
Article
Penetrating Barriers: Noncontact Measurement of Vital Bio Signs Using Radio Frequency Technology
by Kobi Aflalo and Zeev Zalevsky
Sensors 2024, 24(17), 5784; https://doi.org/10.3390/s24175784 - 5 Sep 2024
Viewed by 1534
Abstract
The noninvasive measurement and sensing of vital bio signs, such as respiration and cardiopulmonary parameters, has become an essential part of the evaluation of a patient’s physiological condition. The demand for new technologies that facilitate remote and noninvasive techniques for such measurements continues [...] Read more.
The noninvasive measurement and sensing of vital bio signs, such as respiration and cardiopulmonary parameters, has become an essential part of the evaluation of a patient’s physiological condition. The demand for new technologies that facilitate remote and noninvasive techniques for such measurements continues to grow. While previous research has made strides in the continuous monitoring of vital bio signs using lasers, this paper introduces a novel technique for remote noncontact measurements based on radio frequencies. Unlike laser-based methods, this innovative approach offers the advantage of penetrating through walls and tissues, enabling the measurement of respiration and heart rate. Our method, diverging from traditional radar systems, introduces a unique sensing concept that enables the detection of micro-movements in all directions, including those parallel to the antenna surface. The main goal of this work is to present a novel, simple, and cost-effective measurement tool capable of indicating changes in a subject’s condition. By leveraging the unique properties of radio frequencies, this technique allows for the noninvasive monitoring of vital bio signs without the need for physical contact or invasive procedures. Moreover, the ability to penetrate barriers such as walls and tissues opens new possibilities for remote monitoring in various settings, including home healthcare, hospital environments, and even search and rescue operations. In order to validate the effectiveness of this technique, a series of experiments were conducted using a prototype device. The results demonstrated the feasibility of accurately measuring respiration patterns and heart rate remotely, showcasing the potential for real-time monitoring of a patient’s physiological parameters. Furthermore, the simplicity and low-cost nature of the proposed measurement tool make it accessible to a wide range of users, including healthcare professionals, caregivers, and individuals seeking to monitor their own health. Full article
(This article belongs to the Section Radar Sensors)
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<p>The variation in the complex dielectric constant: real (<b>a</b>), imaginary (<b>b</b>), and conductivity (<b>c</b>) with microwave frequency, with emphasis on the 2.4 GHz frequency indicated by a black vertical line, for 23 different tissues located in the abdominal and upper chest regions.</p>
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<p>This method, as evidenced by the spectrogram (<b>a</b>) and its cross-section (<b>b</b>) at the point of interest, is not optimal for discerning details about low frequencies due to the lower resolution at these frequencies. Since the spectrogram is based on a Fourier transformation of a finite signal within a window function, it has several frequency components that are clearly visible in the horizontal blue lines (<b>a</b>).</p>
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<p>The scalogram (<b>a</b>), which illustrates the time-dependent frequency components of the ECG signal’s pulses, features a red cross as a noteworthy point that is examined in the cross-section (<b>b</b>), showing all axes information at the cross position.</p>
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<p>Depiction of the RF trajectory and the subject’s position, with both antennas aimed at the same point. The test subject is equipped with a piezoelectric sensor on the torso, providing an extra reference for chest movements.</p>
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<p>The separation of targets in close proximity is greatly influenced by the beam width and the targets’ distance from the antenna. Scenario (<b>a</b>) demonstrates a situation where the target of greater magnitude obscures the slower, less intense target. On the other hand, scenario (<b>b</b>) depicts a case where the targets are distinct and separated. In this scenario, since the beam is narrow and aimed toward the slower target, it can be detected.</p>
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<p>Illustration of the linearly polarized antenna that was used, with its corresponding horizontal (H) and vertical (E) planes (<b>a</b>) and the corresponding beam pattern in each plane (<b>b</b>). (<b>a</b>) Illustration of the rectangular aperture linearly polarized antenna and its corresponding linear planes. (<b>b</b>) Beam pattern of the deployed antenna across both horizontal (H) and vertical (E) planes.</p>
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<p>The respiration experiment demonstrates the positioning of antennas towards the subject’s chest (<b>a</b>). The same experiment was conducted in both an anechoic chamber (<b>b</b>) and an uncontrolled environment (<b>a</b>) to demonstrate the ability to detect signals in a noisy environment. The anechoic chamber isolates our measurements from unknown exterior electromagnetic signals due to the radiation-absorbent material coated on its walls. For the validation of remote measurements of the respiration rate, a piezoelectric crystal was placed on the subject’s chest, as shown in (<b>c</b>), serving as an additional analog measurement for our system. The complete connections of our system are depicted in (<b>d</b>).</p>
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<p>The process of respiration over a period of time (<b>a</b>), as recorded by two antennas receiving signals during normal breathing patterns. The scalogram of regular respiration (<b>b</b>), captured from one of the antennas, reveals a clear signal variation in the low-frequency region. This fluctuation is attributed to the varying respiration rates over time.</p>
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<p>Respiratory signal captured using radio frequency with the reference signal derived from a piezoelectric sensor attached to the subject’s torso (<b>a</b>), accompanied by a histogram that illustrates the variances between the two signals (<b>b</b>). The green circles indicate a point of the piezoelectric sensor’s high dependency on torso placement, where increased pressure results in a higher magnitude. (<b>a</b>) Radio frequency signal alongside the reference signal. (<b>b</b>) Histogram of the discrepancies between the signal and the reference.</p>
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<p>Measured heart rate detection using wavelet denoising (<b>a</b>) involves the display of the original signal after it has undergone coarse filtering. The scalogram of measured data (<b>b</b>) displays a constant heart rate of 60 bpm over time. These data are presented after the high-frequency background noise has been filtered out during the preprocessing stage.</p>
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<p>RF signals are transmitted and then reflected off the surface of the speaker’s membrane (<b>a</b>). These reflected signals are then detected by two differently positioned receiving antennas for the purpose of spatial representation. The antenna frequency response (<b>b</b>) of the speaker membrane exhibits an acceptable SNR of above zero for frequencies up to 850 Hz. Beyond this point, the SNR starts to decrease below zero, eventually reaching the noise level where the signal becomes indistinguishable. The variations in the reflected signal stem from its inherent response when it generates a specific frequency. A perfect speaker, on the other hand, would emit such a signal without these variations.</p>
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<p>Variation in SNR with source power level for various distances between the antenna source and test subject.</p>
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<p>Depiction of pendulum motion over time, where the movement is perpendicular (<b>a</b>) and parallel (<b>b</b>) to the plane of the antenna. The terms <math display="inline"><semantics> <msub> <mi>t</mi> <mn>0</mn> </msub> </semantics></math> to <math display="inline"><semantics> <msub> <mi>t</mi> <mn>2</mn> </msub> </semantics></math> describe the temporal position of the pendulum over time where <math display="inline"><semantics> <msub> <mi>t</mi> <mn>0</mn> </msub> </semantics></math> is the initial time and <math display="inline"><semantics> <msub> <mi>t</mi> <mn>2</mn> </msub> </semantics></math> corresponds to a later time.</p>
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<p>The experimental setup is depicted in two different environments. (<b>a</b>) Controlled environment within an anechoic chamber designed to eliminate any interference. (<b>b</b>) Uncontrolled environment, specifically a typical office space with surrounding modern electronics.</p>
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<p>The scalogram showcases the captured signals from a pendulum moving in two separate directions: perpendicular (<b>a</b>) and parallel (<b>b</b>) to the antenna’s plane. This representation allows us to observe a damping effect in the pendulum’s motion over time, as the frequency components exhibit a decrease, indicating a slowdown in the pendulum’s movement. (<b>a</b>) The scalogram illustrates the motion of a pendulum, which moves perpendicular to the plane of the antenna. (<b>b</b>) The scalogram depicts the pendulum’s motion, which occurs alongside the antenna’s plane.</p>
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<p>Illustration of the experimental setup: (<b>a</b>) participants in parallel and vertical orientations relative to the antenna. The breathing patterns of the participants, displayed as amplitude versus time (<b>b</b>), highlighting the differences in chest movements among the subjects.</p>
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11 pages, 6309 KiB  
Communication
Dual-Mode Embedded Impulse-Radio Ultra-Wideband Radar System for Biomedical Applications
by Wei-Ping Hung and Chia-Hung Chang
Sensors 2024, 24(17), 5555; https://doi.org/10.3390/s24175555 - 28 Aug 2024
Viewed by 808
Abstract
This paper presents a real-time and non-contact dual-mode embedded impulse-radio (IR) ultra-wideband (UWB) radar system designed for microwave imaging and vital sign applications. The system is fully customized and composed of three main components, an RF front-end transmission block, an analog signal processing [...] Read more.
This paper presents a real-time and non-contact dual-mode embedded impulse-radio (IR) ultra-wideband (UWB) radar system designed for microwave imaging and vital sign applications. The system is fully customized and composed of three main components, an RF front-end transmission block, an analog signal processing (ASP) block, and a digital processing block, which are integrated in an embedded system. The ASP block enables dual-path receiving for image construction and vital sign detection, while the digital part deals with the inverse scattering and direct current (DC) offset issues. The self-calibration technique is also incorporated into the algorithm to adjust the DC level of each antenna for DC offset compensation. The experimental results demonstrate that the IR-UWB radar, based on the proposed algorithm, successfully detected the 2D image profile of the object as confirmed by numerical derivation. In addition, the radar can wirelessly monitor vital sign behavior such as respiration and heartbeat information. Full article
(This article belongs to the Special Issue Radar Receiver Design and Application)
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<p>System architecture of the IR-UWB radar for hybrid biomedical applications.</p>
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<p>Structure of antenna unit.</p>
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<p>Dual-channel ASP for microwave imaging and vital sign data.</p>
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<p>Dual-channel ASP for microwave imaging and physiological data.</p>
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<p>(<b>a</b>) Antenna array module with eight 2 × 2 square patch antenna units and (<b>b</b>) backside view of the implemented radar sensor.</p>
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<p>Measured return loss of the antenna unit.</p>
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<p>Measured (<b>a</b>) E-plane and (<b>b</b>) H-plane of the antenna unit.</p>
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<p>Recorded real-time signal with a periodical full scan antenna.</p>
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<p>Profile plot of the L-shaped object.</p>
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<p>Radar experimental setup for vital sign detection.</p>
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<p>Measured vital sign results from the IR-UWB sensor.</p>
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<p>Error rate percentage of vital sign detection with different subjects and distances.</p>
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17 pages, 14057 KiB  
Article
Identification of Respiratory Pauses during Swallowing by Unconstrained Measuring Using Millimeter Wave Radar
by Toma Kadono and Hiroshi Noguchi
Sensors 2024, 24(12), 3748; https://doi.org/10.3390/s24123748 - 9 Jun 2024
Viewed by 936
Abstract
Breathing temporarily pauses during swallowing, and the occurrence of inspiration before and after these pauses may increase the likelihood of aspiration, a serious health problem in older adults. Therefore, the automatic detection of these pauses without constraints is important. We propose methods for [...] Read more.
Breathing temporarily pauses during swallowing, and the occurrence of inspiration before and after these pauses may increase the likelihood of aspiration, a serious health problem in older adults. Therefore, the automatic detection of these pauses without constraints is important. We propose methods for measuring respiratory movements during swallowing using millimeter wave radar to detect these pauses. The experiment involved 20 healthy adult participants. The results showed a correlation of 0.71 with the measurement data obtained from a band-type sensor used as a reference, demonstrating the potential to measure chest movements associated with respiration using a non-contact method. Additionally, temporary respiratory pauses caused by swallowing were confirmed by the measured data. Furthermore, using machine learning, the presence of respiring alone was detected with an accuracy of 88.5%, which is higher than that reported in previous studies. Respiring and temporary respiratory pauses caused by swallowing were also detected, with a macro-averaged F1 score of 66.4%. Although there is room for improvement in temporary pause detection, this study demonstrates the potential for measuring respiratory movements during swallowing using millimeter wave radar and a machine learning method. Full article
(This article belongs to the Special Issue Biomedical Sensors for Diagnosis and Rehabilitation2nd Edition)
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<p>Overall procedure of the proposed method for identifying temporary respiratory pauses during swallowing.</p>
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<p>Proposed method to estimate the chest movement distance.</p>
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<p>Results of FFT.</p>
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<p>Results of histogram.</p>
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<p>Band-type sensor.</p>
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<p>Experimental conditions.</p>
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<p>Flowchart of the experiment.</p>
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<p>Result of the band-type sensor and the radar.</p>
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<p>Correlation of respiratory waveforms between the band-type sensor and the radar.</p>
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<p>Respiratory pattern during swallowing.</p>
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<p>Relationship between window size and identification performance.</p>
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<p>Example data of swallowing.</p>
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<p>Example of respiring data.</p>
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21 pages, 1406 KiB  
Article
Contactless Heart and Respiration Rates Estimation and Classification of Driver Physiological States Using CW Radar and Temporal Neural Networks
by Amal El Abbaoui, David Sodoyer and Fouzia Elbahhar
Sensors 2023, 23(23), 9457; https://doi.org/10.3390/s23239457 - 28 Nov 2023
Cited by 3 | Viewed by 1675
Abstract
The measurement and analysis of vital signs are a subject of significant research interest, particularly for monitoring the driver’s physiological state, which is of crucial importance for road safety. Various approaches have been proposed using contact techniques to measure vital signs. However, all [...] Read more.
The measurement and analysis of vital signs are a subject of significant research interest, particularly for monitoring the driver’s physiological state, which is of crucial importance for road safety. Various approaches have been proposed using contact techniques to measure vital signs. However, all of these methods are invasive and cumbersome for the driver. This paper proposes using a non-contact sensor based on continuous wave (CW) radar at 24 GHz to measure vital signs. We associate these measurements with distinct temporal neural networks to analyze the signals to detect and extract heart and respiration rates as well as classify the physiological state of the driver. This approach offers robust performance in estimating the exact values of heart and respiration rates and in classifying the driver’s physiological state. It is non-invasive and requires no physical contact with the driver, making it particularly practical and safe. The results presented in this paper, derived from the use of a 1D Convolutional Neural Network (1D-CNN), a Temporal Convolutional Network (TCN), a Recurrent Neural Network particularly the Bidirectional Long Short-Term Memory (Bi-LSTM), and a Convolutional Recurrent Neural Network (CRNN). Among these, the CRNN emerged as the most effective Deep Learning approach for vital signal analysis. Full article
(This article belongs to the Section Biomedical Sensors)
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<p>The general architecture of the proposed models.</p>
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<p>A dilated causal convolution with dilation factors d = 1, 2, 4, 8, 16, and 32 and a filter size k = 3.</p>
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<p>Fundamental mechanism of CW radar.</p>
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<p>Loss function of regression models.</p>
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<p>Loss function of classification models.</p>
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<p>Confusion Matrix for Each Model Using the Simulated Dataset, Dependent on Individual variances.</p>
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<p>Comparative accuracy curves: predicting heart and respiration rates based on physiological state.</p>
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<p>Confusion Matrix for Each Model Using the Simulated Dataset, Independent of Individual Variances.</p>
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<p>Loss function of classification models.</p>
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<p>Loss function of regression models.</p>
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<p>Confusion matrix for each model Using the Real Dataset, Independent of Individual Variances.</p>
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18 pages, 11175 KiB  
Article
Wearable Fabric Loop Sensor Based on Magnetic-Field-Induced Conductivity for Simultaneous Detection of Cardiac Activity and Respiration Signals
by Hyun-Seung Cho, Jin-Hee Yang, Sang-Yeob Lee, Jeong-Whan Lee and Joo-Hyeon Lee
Sensors 2022, 22(24), 9884; https://doi.org/10.3390/s22249884 - 15 Dec 2022
Cited by 5 | Viewed by 2168
Abstract
In this study, a noncontact fabric loop sensor based on magnetic-field-induced conductivity, which can simultaneously detect cardiac activity and respiration signals, was developed and the effects of the sensor’s shape and measurement position on the sensing performance were analyzed. Fifteen male subjects in [...] Read more.
In this study, a noncontact fabric loop sensor based on magnetic-field-induced conductivity, which can simultaneously detect cardiac activity and respiration signals, was developed and the effects of the sensor’s shape and measurement position on the sensing performance were analyzed. Fifteen male subjects in their twenties wore sleeveless shirts equipped with various types of fabric loop sensors (spiky, extrusion, and spiral), and the cardiac activity and respiratory signals were measured twice at positions P2, P4, and P6. The measurements were verified by comparing them against the reference electrocardiogram (ECG) and respiratory signals measured using BIOPAC® (MP150, ECG100B, RSP100C). The waveforms of the raw signal measured by the fabric loop sensor were filtered with a bandpass filter (1–20 Hz) and qualitatively compared with the ECG signal obtained from the Ag/AgCI electrode. Notwithstanding a slight difference in performance, the three fabric sensors could simultaneously detect cardiac activity and respiration signals at all measurement positions. In addition, it was verified through statistical analysis that the highest-quality signal was obtained at the measurement position of P4 or P6 using the spiral loop sensor. Full article
(This article belongs to the Special Issue Wearable Sensors and Technology for Human Health Monitoring)
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<p>Current and magnetic field induced by the external magnetic field.</p>
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<p>Colpitts oscillator circuit.</p>
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<p>Time delay between ECG and fabric loop sensor signals.</p>
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<p>Hardware system structure.</p>
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<p>Cardiac activity and respiration signal acquisition experiment: (<b>a</b>) experimental image, (<b>b</b>) measurement position.</p>
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<p>Differences in the acquired signals according to the shape of the fabric loop sensor for each measurement position: (<b>a</b>) P2, (<b>b</b>) P4, and (<b>c</b>) P6 (spiral &gt; spiky &gt; extrusion).</p>
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<p>Differences in the acquired signals according to the shape of the fabric loop sensor for each measurement position: (<b>a</b>) P2, (<b>b</b>) P4, and (<b>c</b>) P6 (spiral &gt; spiky &gt; extrusion).</p>
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<p>Cardiac activity signals according to the shape and measurement position of the fabric loop sensor: spiral loop sensor at (<b>a</b>) P2, (<b>b</b>) P4, and (<b>c</b>) P6; (<b>d</b>) spiral, (<b>e</b>) extrusion, and (<b>f</b>) spiky loop sensors at P4.</p>
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<p>Cardiac activity signals measured using clinical ECG signals and spiral loop sensor at P4 (R-peak–PLL-peak analysis).</p>
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<p>Respiration signals according to the shape and measurement position of the fabric loop sensor: spiral loop sensor at (<b>a</b>) P2, (<b>b</b>) P4, and (<b>c</b>) P6; (<b>d</b>) spiral, (<b>e</b>) extrusion, and (<b>f</b>) spiky loop sensors at P4.</p>
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<p>Respiration signals according to the shape and measurement position of the fabric loop sensor: spiral loop sensor at (<b>a</b>) P2, (<b>b</b>) P4, and (<b>c</b>) P6; (<b>d</b>) spiral, (<b>e</b>) extrusion, and (<b>f</b>) spiky loop sensors at P4.</p>
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<p>Cardiac activity and respiratory signals detected in subject A: spiky loop sensor at (<b>a</b>) P2, (<b>b</b>) P4, and (<b>c</b>) P6; extrusion loop sensor at (<b>d</b>) P2, (<b>e</b>) P4, and (<b>f</b>) P6; and spiral loop sensor at (<b>g</b>) P2, (<b>h</b>) P4, and (<b>i</b>) P6.</p>
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<p>Cardiac activity and respiratory signals detected in subject A: spiky loop sensor at (<b>a</b>) P2, (<b>b</b>) P4, and (<b>c</b>) P6; extrusion loop sensor at (<b>d</b>) P2, (<b>e</b>) P4, and (<b>f</b>) P6; and spiral loop sensor at (<b>g</b>) P2, (<b>h</b>) P4, and (<b>i</b>) P6.</p>
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26 pages, 5322 KiB  
Article
A Real-Time Remote Respiration Measurement Method with Improved Robustness Based on a CNN Model
by Hyeonsang Hwang, Kunyoung Lee and Eui Chul Lee
Appl. Sci. 2022, 12(22), 11603; https://doi.org/10.3390/app122211603 - 15 Nov 2022
Cited by 5 | Viewed by 2806
Abstract
Human respiration reflects meaningful information, such as one’s health and psychological state. Rates of respiration are an important indicator in medicine because they are directly related to life, death, and the onset of a serious disease. In this study, we propose a noncontact [...] Read more.
Human respiration reflects meaningful information, such as one’s health and psychological state. Rates of respiration are an important indicator in medicine because they are directly related to life, death, and the onset of a serious disease. In this study, we propose a noncontact method to measure respiration. Our proposed approach uses a standard RGB camera and does not require any special equipment. Measurement is performed automatically by detecting body landmarks to identify regions of interest (RoIs). We adopt a learning model trained to measure motion and respiration by analyzing movement from RoI images for high robustness to background noise. We collected a remote respiration measurement dataset to train the proposed method and compared its measurement performance with that of representative existing methods. Experimentally, the proposed method showed a performance similar to that of existing methods in a stable environment with restricted motion. However, its performance was significantly improved compared to existing methods owing to its robustness to motion noise. In an environment with partial occlusion and small body movement, the error of the existing methods was 4–8 bpm, whereas the error of our proposed method was around 0.1 bpm. In addition, by measuring the time required to perform each step of the respiration measurement process, we confirmed that the proposed method can be implemented in real time at over 30 FPS using only a standard CPU. Since the proposed approach shows state-of-the-art accuracy with the error of 0.1 bpm in the wild, it can be expanded to various applications, such as medicine, home healthcare, emotional marketing, forensic investigation, and fitness in future research. Full article
(This article belongs to the Special Issue New Trends in Image Processing III)
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<p>Principle of motion-based respiration measurement.</p>
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<p>Examples of various pixel value changes that can occur as a result of the same breathing movement: (<b>a</b>) changes in pixel value that are similar to a reference breathing signal, (<b>b</b>) changes in pixel value that are opposite to the reference breathing signal, and (<b>c</b>) pixel value if the changes in the reference respiratory signal are not similar.</p>
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<p>Overall process of the proposed method.</p>
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<p>Example of chest RoI detection results based on body landmark point: (<b>a</b>) if only a portion of the chest area is in the image; (<b>b</b>) if all the chest area is in the image.</p>
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<p>Proposed CNN architecture for respiration measurement.</p>
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<p>Constructing a training dataset construction from video and respiration signals with a contact sensor.</p>
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<p>Examples of trended raw signals and detrending results: (<b>a</b>) raw signals, (<b>b</b>) detrending results.</p>
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<p>Data acquisition equipment for remote respiration measurement: (<b>a</b>) Logitech C920 pro, (<b>b</b>) Go Direct Respiration Belt.</p>
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<p>Example of respiration dataset with motion and background noise.</p>
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<p>Comparison of respiration estimation accuracy and computational time according to window size change.</p>
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<p>Bland–Altman plot of three breathing estimation methods for scene #1 and #2: (<b>a</b>) ours, (<b>b</b>) optical flow-based, and (<b>c</b>) intensity-based.</p>
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<p>Comparison analysis of reference and inference respiration signal.</p>
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<p>Bland-Altman plot of three respiration estimation methods for scene #3, #4: (<b>a</b>) ours, (<b>b</b>) optical flow-based, and (<b>c</b>) intensity-based.</p>
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<p>Examples of references and estimated signals on motion noise environment: (<b>a</b>) reference, (<b>b</b>) ours, (<b>c</b>) optical flow-based, and (<b>d</b>) intensity-based.</p>
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24 pages, 21859 KiB  
Article
High-Precision Vital Signs Monitoring Method Using a FMCW Millimeter-Wave Sensor
by Mingxu Xiang, Wu Ren, Weiming Li, Zhenghui Xue and Xinyue Jiang
Sensors 2022, 22(19), 7543; https://doi.org/10.3390/s22197543 - 5 Oct 2022
Cited by 21 | Viewed by 6004
Abstract
The method of using millimeter-wave radar sensors to detect human vital signs, namely respiration and heart rate, has received widespread attention in non-contact monitoring. These sensors are compact, lightweight, and able to sense and detect various scenarios. However, it still faces serious problems [...] Read more.
The method of using millimeter-wave radar sensors to detect human vital signs, namely respiration and heart rate, has received widespread attention in non-contact monitoring. These sensors are compact, lightweight, and able to sense and detect various scenarios. However, it still faces serious problems of noisy interference in hardware, which leads to a low signal-to-noise ratio (SNR). We used a frequency-modulated continuous wave (FMCW) radar sensor operating at 77 GHz in an office environment to extract the respiration and heart rate of a person accustomed to sitting in a chair. Indeed, the proposed signal processing includes novel impulse denoising operations and the spectral estimation decision method, which are unique in terms of noise reduction and accuracy improvement. In addition, the proposed method provides high-quality, repeatable respiration and heart rates with relative errors of 1.33% and 1.96% on average compared with the reference values measured by a reliable smart bracelet. Full article
(This article belongs to the Section Remote Sensors)
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<p>The proposed signal processing algorithm chain.</p>
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<p>Range-FFT: (<b>a</b>) before static signal-clutter removal; (<b>b</b>) after static signal-clutter removal.</p>
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<p>The complex data at the selected range bin: (<b>a</b>) before DC offset compensation; (<b>b</b>) after DC offset compensation.</p>
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<p>Extracted phase by the extended DACM: (<b>a</b>) in the time domain; (<b>b</b>) in the frequency domain.</p>
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<p>Phase difference: (<b>a</b>) in the time domain; (<b>b</b>) in the frequency domain.</p>
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<p>The algorithm chain of Iterative VMD Wavelet-Interval-Thresholding.</p>
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<p>The impulse noise removal: (<b>a</b>) in the time domain; (<b>b</b>) in the frequency domain; (<b>c</b>) waveform comparison before and after denoising.</p>
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<p>(<b>a</b>) TI AWR1642 sensor system; (<b>b</b>) Measurement scenario.</p>
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<p>The parameter settings of the sensor.</p>
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<p>Subject #1: (<b>a</b>) extracted phase; (<b>b</b>) phase difference; (<b>c</b>) the impulse noise removal; (<b>d</b>) breathing waveform; (<b>e</b>) heart waveform.</p>
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<p>Subject #1: (<b>a</b>) extracted phase; (<b>b</b>) phase difference; (<b>c</b>) the impulse noise removal; (<b>d</b>) breathing waveform; (<b>e</b>) heart waveform.</p>
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<p>Subject #2: (<b>a</b>) extracted phase; (<b>b</b>) phase difference; (<b>c</b>) the impulse noise removal; (<b>d</b>) breathing waveform; (<b>e</b>) heart waveform.</p>
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<p>Subject #2: (<b>a</b>) extracted phase; (<b>b</b>) phase difference; (<b>c</b>) the impulse noise removal; (<b>d</b>) breathing waveform; (<b>e</b>) heart waveform.</p>
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<p>Subject #3: (<b>a</b>) extracted phase; (<b>b</b>) phase difference; (<b>c</b>) the impulse noise removal; (<b>d</b>) breathing waveform; (<b>e</b>) heart waveform.</p>
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<p>Subject #3: (<b>a</b>) extracted phase; (<b>b</b>) phase difference; (<b>c</b>) the impulse noise removal; (<b>d</b>) breathing waveform; (<b>e</b>) heart waveform.</p>
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<p>Experimental results of the heartbeat (<b>a</b>) with and (<b>b</b>) without Iterative VMD Wavelet-Interval-Thresholding algorithm. (The bars represent the reference values and the error bars represent the absolute errors of the measurement values obtained by the two algorithms compared to the reference values).</p>
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<p>Bland–Altman plots of the values obtained by the proposed method against the reference values obtained by the smart bracelet: (<b>a</b>) respiratory rate of Group #1; (<b>b</b>) respiratory rate of Group #2; (<b>c</b>) heart rate of Group #1; (<b>d</b>) heart rate of Group #2.</p>
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<p>Bland–Altman plots of the values obtained by the proposed method against the reference values obtained by the smart bracelet: (<b>a</b>) respiratory rate of Group #1; (<b>b</b>) respiratory rate of Group #2; (<b>c</b>) heart rate of Group #1; (<b>d</b>) heart rate of Group #2.</p>
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<p>(<b>a</b>) The complex data at the selected range bin in a coughing situation; (<b>b</b>) The complex data at the selected range bin in the case of arm swinging; (<b>c</b>) The heartbeat waveform of coughing scene; (<b>d</b>) The heartbeat waveform of arm-swing scene.</p>
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21 pages, 5735 KiB  
Article
Non-Contact Detection of Vital Signs Based on Improved Adaptive EEMD Algorithm (July 2022)
by Didi Xu, Weihua Yu, Changjiang Deng and Zhongxia Simon He
Sensors 2022, 22(17), 6423; https://doi.org/10.3390/s22176423 - 25 Aug 2022
Cited by 14 | Viewed by 3017
Abstract
Non-contact vital sign detection technology has brought a more comfortable experience to the detection process of human respiratory and heartbeat signals. Ensemble empirical mode decomposition (EEMD) is a noise-assisted adaptive data analysis method which can be used to decompose the echo data of [...] Read more.
Non-contact vital sign detection technology has brought a more comfortable experience to the detection process of human respiratory and heartbeat signals. Ensemble empirical mode decomposition (EEMD) is a noise-assisted adaptive data analysis method which can be used to decompose the echo data of frequency modulated continuous wave (FMCW) radar and extract the heartbeat and respiratory signals. The key of EEMD is to add Gaussian white noise into the signal to overcome the mode aliasing problem caused by original empirical mode decomposition (EMD). Based on the characteristics of clutter and noise distribution in public places, this paper proposed a static clutter filtering method for eliminating ambient clutter and an improved EEMD method based on stable alpha noise distribution. The symmetrical alpha stable distribution is used to replace Gaussian distribution, and the improved EEMD is used for the separation of respiratory and heartbeat signals. The experimental results show that the static clutter filtering technology can effectively filter the surrounding static clutter and highlight the periodic moving targets. Within the detection range of 0.5 m~2.5 m, the improved EEMD method can better distinguish the heartbeat, respiration, and their harmonics, and accurately estimate the heart rate. Full article
(This article belongs to the Special Issue mm Wave Integrated Circuits Based Sensing Systems and Applications)
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<p>FMCW radar block diagram.</p>
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<p>Spectrum of chirped signal frequency with time.</p>
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<p>Flow chart of human heartbeat and respiration signal detection.</p>
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<p>Spectrum of simulated phase signal. Respiration rate <math display="inline"><semantics> <mrow> <msub> <mi>f</mi> <mrow> <mi>r</mi> <mi>e</mi> </mrow> </msub> </mrow> </semantics></math> = 0.32 Hz, heartbeat rate <math display="inline"><semantics> <mrow> <msub> <mi>f</mi> <mrow> <mi>h</mi> <mi>r</mi> </mrow> </msub> </mrow> </semantics></math> = 1.54 Hz. The 2nd, 3rd, 4th and 6th breath harmonics have been added. The original signal has respiratory harmonics in the range of 0.8~2.0 Hz.</p>
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<p>(<b>a</b>) EMD decomposition results of simulated signals, the red line is the component close to the respiratory rate, and the blue line is the component close to the respiratory rate. (<b>b</b>) Spectrums of simulated signals, respiratory and heartbeat spectrums. Respiration rate <math display="inline"><semantics> <mrow> <msub> <mi>F</mi> <mrow> <mi>r</mi> <mi>e</mi> </mrow> </msub> </mrow> </semantics></math> = 0.32 Hz, heartbeat rate <math display="inline"><semantics> <mrow> <msub> <mi>F</mi> <mrow> <mi>h</mi> <mi>r</mi> </mrow> </msub> </mrow> </semantics></math> = 1.54 Hz. The 2nd, 3rd, 4th, and 6th breath harmonics have been added. IMF2 and IMF1 are considered to be the closest respiratory and heartbeat components, respectively. In (<b>b</b>), false peaks exist in both the original signal and the heartbeat spectrum within 0.8−2.0 Hz, making it difficult to estimate the heartbeat frequency.</p>
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<p>(<b>a</b>) EEMD results of simulated signals, the red line is the component close to the respiratory rate, and the blue line is the component close to the respiratory rate. (<b>b</b>) Simulated signal spectrum, respiratory spectrum and heartbeat spectrum. (<b>c</b>) Spectral details of simulated signals, respiratory and heartbeat domains. The respiratory rate and heartbeat rate are set as shown in <a href="#sensors-22-06423-f004" class="html-fig">Figure 4</a>, that is, <math display="inline"><semantics> <mrow> <msub> <mi>F</mi> <mrow> <mi>r</mi> <mi>e</mi> </mrow> </msub> </mrow> </semantics></math> = 0.32 Hz and <math display="inline"><semantics> <mrow> <msub> <mi>F</mi> <mrow> <mi>h</mi> <mi>r</mi> </mrow> </msub> </mrow> </semantics></math> = 1.54 Hz. The second, third, fourth and sixth breath harmonics were added, and the SNR was set to 0.2. IMF5 and IMF3 are considered to be the closest respiratory and heartbeat components, respectively. The heart rate can be estimated from the IMF3 spectrum of (<b>c</b>).</p>
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<p>(<b>a</b>) Decomposition results of simulated signals using the improved EEMD, the red line is the component close to the respiratory rate, and the blue line is the component close to the respiratory rate. (<b>b</b>) Spectrum comparison of heartbeat IMF obtained from simulated signals using EMD, EEMD and the improved EEMD. The respiratory rate and heartbeat rate are set as shown in <a href="#sensors-22-06423-f005" class="html-fig">Figure 5</a>, that is, <math display="inline"><semantics> <mrow> <msub> <mi>F</mi> <mrow> <mi>r</mi> <mi>e</mi> </mrow> </msub> </mrow> </semantics></math> = 0.32 Hz and <math display="inline"><semantics> <mrow> <msub> <mi>F</mi> <mrow> <mi>h</mi> <mi>r</mi> </mrow> </msub> </mrow> </semantics></math> = 1.54 Hz. The second, third, fourth and sixth breath harmonics were added, and the SNR was set to 0.2.</p>
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<p>(<b>a</b>) Experimental setup, which included volunteers, FMCW radar (IWR1843) component, and a laptop. (<b>b</b>) Radar chirp parameter setting.</p>
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<p>Before (<b>a</b>) and after (<b>b</b>) static clutter filtering technology for echo signal, the raised lines in the figure represent targets detected by radar, it can be seen that, before processing, the radar detects moving targets and stationary objects, and it is difficult for us to distinguish the location of the subject target. After processing, we can see that only the subject target exists in the whole picture.</p>
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<p>Target range, radar target distance is 0.65 m, radar range resolution is <span class="html-italic">C</span>/2B, range resolution is 4 cm.</p>
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<p>(<b>a</b>) EMD decomposition results of actual signals, the red line is the component close to the respiratory rate. (<b>b</b>) Spectrograms of actual signals, respiratory spectrograms, and (<b>c</b>) heartbeat spectrograms. IMF3 and IMF2 are considered to be the closest respiratory and heartbeat components, respectively. In (<b>c</b>), there are false peaks in the range of 0.8−2.0 Hz in both the original signal and the heartbeat spectrum, making it difficult to estimate the heartbeat frequency.</p>
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<p>(<b>a</b>) Decomposition results of actual signals using the method proposed in this paper, the red line is the component close to the respiratory rate, and the blue line is the component close to the respiratory rate. (<b>b</b>) spectrograms of actual signals, respiratory spectrograms and (<b>c</b>) heartbeat spectrograms. IMF5 and IMF3 are considered to be the closest respiratory and heartbeat components, respectively. The heart rate of 1.2 Hz can be estimated from the IMF3 spectrum of (<b>c</b>) in the range of 0.8−2.0 Hz.</p>
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<p>Spectrum comparison of heartbeat IMF obtained from actual signals using EMD, EEMD, and the algorithm proposed in this paper. (<b>a</b>–<b>d</b>) are the calculated results of selecting four parts from an actual signal.</p>
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<p>The stream processing results of the original signal, 5000 frames (250 s) of stream data, a window every 10 s, the time interval is 1 s.</p>
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21 pages, 6085 KiB  
Article
A Non-Contact Detection Method for Multi-Person Vital Signs Based on IR-UWB Radar
by Xiaochao Dang, Jinlong Zhang and Zhanjun Hao
Sensors 2022, 22(16), 6116; https://doi.org/10.3390/s22166116 - 16 Aug 2022
Cited by 13 | Viewed by 3543
Abstract
With the vigorous development of ubiquitous sensing technology, an increasing number of scholars pay attention to non-contact vital signs (e.g., Respiration Rate (RR) and Heart Rate (HR)) detection for physical health. Since Impulse Radio Ultra-Wide Band (IR-UWB) technology has good characteristics, such as [...] Read more.
With the vigorous development of ubiquitous sensing technology, an increasing number of scholars pay attention to non-contact vital signs (e.g., Respiration Rate (RR) and Heart Rate (HR)) detection for physical health. Since Impulse Radio Ultra-Wide Band (IR-UWB) technology has good characteristics, such as non-invasive, high penetration, accurate ranging, low power, and low cost, it makes the technology more suitable for non-contact vital signs detection. Therefore, a non-contact multi-human vital signs detection method based on IR-UWB radar is proposed in this paper. By using this technique, the realm of multi-target detection is opened up to even more targets for subjects than the more conventional single target. We used an optimized algorithm CIR-SS based on the channel impulse response (CIR) smoothing spline method to solve the problem that existing algorithms cannot effectively separate and extract respiratory and heartbeat signals. Also in our study, the effectiveness of the algorithm was analyzed using the Bland–Altman consistency analysis statistical method with the algorithm’s respiratory and heart rate estimation errors of 5.14% and 4.87%, respectively, indicating a high accuracy and precision. The experimental results showed that our proposed method provides a highly accurate, easy-to-implement, and highly robust solution in the field of non-contact multi-person vital signs detection. Full article
(This article belongs to the Topic Internet of Things: Latest Advances)
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<p>The system flow chart of this study.</p>
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<p>IR-UWB radar equipment and its structure diagram. (<b>a</b>) Radar equipment diagram. (<b>b</b>) Radar equipment structure diagram.</p>
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<p>Experimental scene diagram. (<b>a</b>) Complex indoor environment. (<b>b</b>) Open indoor environment. (<b>c</b>) Open indoor environment.</p>
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<p>The estimated vital signs of subject A in three different environments and at different distances. (<b>a</b>) Complex indoor environment. (<b>b</b>) Open indoor environment. (<b>c</b>) Open outdoor environment.</p>
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<p>Vital signs signals obtained by IR-UWB radar in Outdoor open environment. (<b>a</b>) Time domain at different distances. (<b>b</b>) Frequency domain at different distances.</p>
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<p>Indoor environment. (<b>a</b>) Respiratory rate estimation. (<b>b</b>) Heartbeat frequency estimation. (<b>c</b>) Range estimation.</p>
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<p>Open environment. (<b>a</b>) Respiratory rate estimation. (<b>b</b>) Heartbeat frequency estimation. (<b>c</b>) Range estimation.</p>
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<p>Distribution of accuracy and error accumulation when penetrating different media. (<b>a</b>) Accuracy rate. (<b>b</b>) Cumulative distribution of errors.</p>
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<p>Time domain and frequency domain diagram of penetration through different media. (<b>a</b>) Time domain of penetrating different media. (<b>b</b>) Frequency domain penetration of different media.</p>
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<p>IR-UWB radar experiment scene diagram under different number of tested targets. (<b>a</b>) One subject. (<b>b</b>) Two subjects. (<b>c</b>) Three subjects.</p>
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<p>Bland–Altman consistency analysis of respiration measured by IR-UWB radar and respiration belt under different number of targets. (<b>a</b>) One subject. (<b>b</b>) Two subjects. (<b>c</b>) Three subjects.</p>
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<p>Bland–Altman consistency analysis of heartbeat measured by IR-UWB radar and ECG under different number of targets. (<b>a</b>) One subject. (<b>b</b>) Two subjects. (<b>c</b>) Three subjects.</p>
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<p>Time domain and frequency domain of breathing estimation using different algorithms. (<b>a</b>) Time domain diagram of breathing estimation. (<b>b</b>) Frequency domain diagram of breathing estimation.</p>
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<p>Time domain and frequency domain of heartbeat estimation using different algorithms. (<b>a</b>) Time domain diagram of heartbeat estimation. (<b>b</b>) Frequency domain diagram of heartbeat estimation.</p>
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19 pages, 4422 KiB  
Article
Cheyne-Stokes Respiration Perception via Machine Learning Algorithms
by Chang Yuan, Muhammad Bilal Khan, Xiaodong Yang, Fiaz Hussain Shah and Qammer Hussain Abbasi
Electronics 2022, 11(6), 958; https://doi.org/10.3390/electronics11060958 - 20 Mar 2022
Cited by 6 | Viewed by 4376
Abstract
With the development of science and technology, transparent, non-invasive general computing is gradually applied to disease diagnosis and medical detection. Universal software radio peripherals (USRP) enable non-contact awareness based on radio frequency signals. Cheyne-Stokes respiration has been reported as a common symptom in [...] Read more.
With the development of science and technology, transparent, non-invasive general computing is gradually applied to disease diagnosis and medical detection. Universal software radio peripherals (USRP) enable non-contact awareness based on radio frequency signals. Cheyne-Stokes respiration has been reported as a common symptom in patients with heart failure. Compared with the disadvantages of traditional detection equipment, a microwave sensing method based on channel state information (CSI) is proposed to qualitatively detect the normal breathing and Cheyne-Stokes breathing of patients with heart failure in a non-contact manner. Firstly, USRP is used to collect subjects’ respiratory signals in real time. Then the CSI waveform is filtered, smoothed and normalized, and the relevant features are defined and extracted from the signal. Finally, the machine learning classification algorithm is used to establish a recognition model to detect the Cheyne-Stokes respiration of patients with heart failure. The results show that the system accuracy of support vector machine (SVM) is 97%, which can assist medical workers to identify Cheyne-Stokes respiration symptoms of patients with heart failure. Full article
(This article belongs to the Section Bioelectronics)
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<p>Schematic diagram of human respiration.</p>
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<p>Breathing subcarrier sequence during sitting (<b>a</b>) one of the subcarriers; (<b>b</b>) superposition of 64 subcarriers.</p>
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<p>The system block diagram.</p>
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<p>Outlier processing.</p>
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<p>Subcarrier smoothing processing.</p>
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<p>Collection schematic.</p>
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<p>Normal respiration waveform.</p>
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<p>Cheyne-Stokes breathing waveform.</p>
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<p>Precision comparison for the classification algorithm.</p>
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<p>Confusion matrix of SVM model.</p>
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<p>The influence of the number of PCA selections on the prediction accuracy of SVM model.</p>
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<p>Comparison between CSI data and HKH-11C data.</p>
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<p>Comparison between CSI data and HKH-11C data.</p>
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17 pages, 2766 KiB  
Article
Accurate Heart Rate and Respiration Rate Detection Based on a Higher-Order Harmonics Peak Selection Method Using Radar Non-Contact Sensors
by Hongqiang Xu, Malikeh P. Ebrahim, Kareeb Hasan, Fatemeh Heydari, Paul Howley and Mehmet Rasit Yuce
Sensors 2022, 22(1), 83; https://doi.org/10.3390/s22010083 - 23 Dec 2021
Cited by 45 | Viewed by 9210
Abstract
Vital signs such as heart rate and respiration rate are among the most important physiological signals for health monitoring and medical applications. Impulse radio (IR) ultra-wideband (UWB) radar becomes one of the essential sensors in non-contact vital signs detection. The heart pulse wave [...] Read more.
Vital signs such as heart rate and respiration rate are among the most important physiological signals for health monitoring and medical applications. Impulse radio (IR) ultra-wideband (UWB) radar becomes one of the essential sensors in non-contact vital signs detection. The heart pulse wave is easily corrupted by noise and respiration activity since the heartbeat signal has less power compared with the breathing signal and its harmonics. In this paper, a signal processing technique for a UWB radar system was developed to detect the heart rate and respiration rate. There are four main stages of signal processing: (1) clutter removal to reduce the static random noise from the environment; (2) independent component analysis (ICA) to do dimension reduction and remove noise; (3) using low-pass and high-pass filters to eliminate the out of band noise; (4) modified covariance method for spectrum estimation. Furthermore, higher harmonics of heart rate were used to estimate heart rate and minimize respiration interference. The experiments in this article contain different scenarios including bed angle, body position, as well as interference from the visitor near the bed and away from the bed. The results were compared with the ECG sensor and respiration belt. The average mean absolute error (MAE) of heart rate results is 1.32 for the proposed algorithm. Full article
(This article belongs to the Special Issue Microwave Sensors: From Sensing Principle to Application)
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<p>An overview of heart rate radar monitoring system.</p>
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<p>The block diagram of the signal processing algorithm.</p>
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<p>The setup of devices: the radar is mounted 1 m above the bed. Two laptops are used for radar sensor data and reference signals recording.</p>
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<p>Fast–time–slow–time matrix.</p>
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<p>ECG, respiration signals, and ICs.</p>
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<p>Result of FFT on extracted breathing signal.</p>
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<p>Results of modified covariance method before ICA vital signs extraction and after vital signs extraction.</p>
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<p>Results of modified covariance method for all ICs. The reference heart rate is 79 bpm. The red dash lines are the integer multiple of reference heart rate.</p>
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<p>Heart rate estimation with different methods with a window length of 35 s. The red star is the reference heart rate, the pink cross is FFT after the high-pass filter, the black triangle is the modified covariance method after the high-pass filter, and the blue circle is the proposed method.</p>
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21 pages, 3706 KiB  
Article
Through-Wall Multi-Subject Localization and Vital Signs Monitoring Using UWB MIMO Imaging Radar
by Zhi Li, Tian Jin, Yongpeng Dai and Yongkun Song
Remote Sens. 2021, 13(15), 2905; https://doi.org/10.3390/rs13152905 - 23 Jul 2021
Cited by 43 | Viewed by 6116
Abstract
Radar-based non-contact vital signs monitoring has great value in through-wall detection applications. This paper presents the theoretical and experimental study of through-wall respiration and heartbeat pattern extraction from multiple subjects. To detect the vital signs of multiple subjects, we employ a low-frequency ultra-wideband [...] Read more.
Radar-based non-contact vital signs monitoring has great value in through-wall detection applications. This paper presents the theoretical and experimental study of through-wall respiration and heartbeat pattern extraction from multiple subjects. To detect the vital signs of multiple subjects, we employ a low-frequency ultra-wideband (UWB) multiple-input multiple-output (MIMO) imaging radar and derive the relationship between radar images and vibrations caused by human cardiopulmonary movements. The derivation indicates that MIMO radar imaging with the stepped-frequency continuous-wave (SFCW) improves the signal-to-noise ratio (SNR) critically by the factor of radar channel number times frequency number compared with continuous-wave (CW) Doppler radars. We also apply the three-dimensional (3-D) higher-order cumulant (HOC) to locate multiple subjects and extract the phase sequence of the radar images as the vital signs signal. To monitor the cardiopulmonary activities, we further exploit the VMD algorithm with a proposed grouping criterion to adaptively separate the respiration and heartbeat patterns. A series of experiments have validated the localization and detection of multiple subjects behind a wall. The VMD algorithm is suitable for separating the weaker heartbeat pattern from the stronger respiration pattern by the grouping criterion. Moreover, the continuous monitoring of heart rate (HR) by the MIMO radar in real scenarios shows a strong consistency with the reference electrocardiogram (ECG). Full article
(This article belongs to the Special Issue Radar Signal Processing and System Design for Urban Health)
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<p>Schematic diagram of vital signs detection by MIMO radar imaging.</p>
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<p>Propagation path for through-wall detection.</p>
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<p>Flowchart of the proposed method.</p>
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<p>Schematic diagram of through-wall multi-subject vital signs measurement.</p>
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<p>(<b>a</b>) Experiment scenario of through-wall vital signs detection. (<b>b</b>) Photograph of the contact vital signs sensor.</p>
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<p>Block diagram of the MIMO radar system.</p>
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<p>Line-of-sight detection results of multiple subjects. (<b>a</b>) Projection of the initial 3-D image. (<b>b</b>) Projection and CFAR detection of the fourth-order cumulant.</p>
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<p>Through-wall detection results of radar imaging for multiple subjects. (<b>a</b>) Projection of the initial 3-D image. (<b>b</b>) Projection and CFAR detection of the fourth-order cumulant.</p>
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<p>Vital signs signal (Subject 1) extracted by radar imaging. (<b>a</b>) vital signs signal in time domain. (<b>b</b>) Spectrum of the vital signs signal. The fundamental and harmonic frequencies of respiration and heartbeat are indicated.</p>
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<p>Vital signs signal (Subject 1) decomposited by VMD. (<b>a</b>) The IMFs. (<b>b</b>) Spectrums of the IMFs.</p>
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<p>Vital signs signal (Subject 1) decomposited by VMD. (<b>a</b>) The IMFs. (<b>b</b>) Spectrums of the IMFs.</p>
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<p>Separation results of respiration and heartbeat patterns for one of the subjects (Subject 1). The red lines are the reference signals (in mV). The other ones are displacement signals (in mm) separated by different algorithms. (<b>a</b>) Separated respiration patterns compared with the reference respiration signal. (<b>b</b>) Separated heartbeat patterns compared with the reference ECG signal.</p>
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<p>(<b>a</b>) Vital signs signal and separation results of Subject 2 with apnea. (<b>b</b>) Zoom of the respiration and heartbeat patterns extracted with radar and its associated reference signals.</p>
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<p>Through-wall vital signs detection results of multiple subjects. (<b>a</b>) The extracted vital signs signals of the three subjects. (<b>b</b>) The separated respiration patterns. (<b>c</b>) The separated heartbeat patterns.</p>
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<p>RR and HR monitoring results of Subject 2 in line-of-sight and through-wall cases. (<b>a</b>) Line-of-sight RR monitoring with apnea from the 12th s. (<b>b</b>) Through-wall RR monitoring. (<b>c</b>) Line-of-sight HR monitoring. (<b>d</b>) Through-wall HR monitoring.</p>
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