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10 pages, 2243 KiB  
Article
Dynamically Tunable Multifunction Attenuator Based on Graphene-Integrated Dual-Mode Microstrip Resonators
by Zhi-Qiang Yang, Quan-Long Wen, Chi Fan, Bian Wu and Yang Qiu
Electronics 2025, 14(1), 137; https://doi.org/10.3390/electronics14010137 - 31 Dec 2024
Viewed by 407
Abstract
In this paper, a method for the design of tunable multifunctional attenuators is proposed by analyzing the characterization of dual-mode microstrip resonators loaded by a graphene-sandwiched structure (GSS). Firstly, the odd–even mode method is applied to analyze the resonance characteristics of two common [...] Read more.
In this paper, a method for the design of tunable multifunctional attenuators is proposed by analyzing the characterization of dual-mode microstrip resonators loaded by a graphene-sandwiched structure (GSS). Firstly, the odd–even mode method is applied to analyze the resonance characteristics of two common GSS-loaded dual-mode resonators, which clearly describe the influence of graphene on these resonators. Then, two kinds of multifunctional attenuator with dynamically tunable attenuation are proposed based on graphene-integrated dual-mode resonators, which enables controllable characteristics and multi-frequency transmission options for traditional attenuating devices. Finally, all the proposed multifunctional attenuators are fabricated and measured. The experimental results are in good agreement with the simulation results, which further verifies the conclusions and design method proposed in this paper. Full article
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Figure 1
<p>(<b>a</b>) Configuration; (<b>b</b>) the equivalent circuit; (<b>c</b>) a detailed sketch of the odd–even mode of the GSS-loaded open-ended resonator with a centrally loaded open stub.</p>
Full article ">Figure 1 Cont.
<p>(<b>a</b>) Configuration; (<b>b</b>) the equivalent circuit; (<b>c</b>) a detailed sketch of the odd–even mode of the GSS-loaded open-ended resonator with a centrally loaded open stub.</p>
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<p>The relationship between Rs and the transmission coefficient of the GSS-loaded open-ended resonator with a centrally loaded open stub: (<b>a</b>) position 1, d = 5; (<b>b</b>) position 1, d = 15; (<b>c</b>) position 2, d1 = 0.</p>
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<p>The relationship between Rs and bias voltage.</p>
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<p>(<b>a</b>) Tunable dual-band filtering attenuator I. (<b>b</b>) Tunable dual-band filtering attenuator II.</p>
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<p>The simulation results of tunable dual-band filtering attenuators I and II. (<b>a</b>) Control of the surface resistance of GSS1; (<b>b</b>) control of the surface resistance of GSS3; (<b>c</b>) control of the surface resistance of GSS2; (<b>d</b>) control of the surface resistance of GSS4; (<b>e</b>) control of the surface resistance of GSS1 and 2; (<b>f</b>) control of the surface resistance of GSS3 and 4.</p>
Full article ">Figure 6
<p>(<b>a</b>) Proposed filtering dual-band filtering attenuator I. (<b>b</b>) Proposed filtering dual-band filtering attenuator II. (<b>c</b>) Measured results of dual-band filtering attenuator I. (<b>d</b>) Measured results of dual-band filtering attenuator II.</p>
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16 pages, 5459 KiB  
Article
Impact of Cell Layout on Bandwidth of Multi-Frequency Piezoelectric Micromachined Ultrasonic Transducer Array
by Wanli Yang, Huimin Li, Yuewu Gong, Zhuochen Wang, Xingli Xu, Xiaofan Hu, Pengfei Niu and Wei Pang
Micromachines 2025, 16(1), 49; https://doi.org/10.3390/mi16010049 - 31 Dec 2024
Viewed by 550
Abstract
Piezoelectric micromachined ultrasonic transducers (PMUTs) show considerable promise for application in ultrasound imaging, but the limited bandwidth of the traditional PMUTs largely affects the imaging quality. This paper focuses on how to arrange cells with different frequencies to maximize the bandwidth and proposes [...] Read more.
Piezoelectric micromachined ultrasonic transducers (PMUTs) show considerable promise for application in ultrasound imaging, but the limited bandwidth of the traditional PMUTs largely affects the imaging quality. This paper focuses on how to arrange cells with different frequencies to maximize the bandwidth and proposes a multi-frequency PMUT (MF-PMUT) linear array. Seven cells with gradually changing frequencies are arranged in a monotonic trend to form a unit, and 32 units are distributed across four lines, forming one element. To investigate how the arrangement of cells affects the bandwidth, three different arrays were designed according to the extent of unit aggregation from the same frequency. Underwater experiments were conducted to assess the acoustic performance, especially the bandwidth. We found that the densest arrangement of the same cells produced the largest bandwidth, achieving a 92% transmission bandwidth and a 50% burst-echo bandwidth at 6 MHz. The mechanism was investigated from the coupling point of view by finite element analysis and laser Doppler vibrometry, focusing on the cell displacements. The results demonstrated strong ultrasound coupling in the devices, resulting in larger bandwidths. To exploit the advanced bandwidth but reduce the crosstalk, grooves for isolation were fabricated between elements. This work proposes an effective strategy for developing advanced PMUT arrays that would benefit ultrasound imaging applications. Full article
(This article belongs to the Section A:Physics)
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<p>Schematic diagram of the structure of a single cell and the geometric parameters of its simulation model.</p>
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<p>Arrangement (<b>a</b>–<b>c</b>) of cells with different resonant frequencies.</p>
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<p>(<b>a</b>) The FEA model for the PMUT array, displaying boundary conditions. The model is not depicted in proportion to show the configuration details. Simulation model mesh examples of the B-type combination: (<b>b</b>) free triangular mesh of the combination and (<b>c</b>) global mesh sweep.</p>
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<p>Displacement of the (<b>a</b>) A-type, (<b>b</b>) B-type, and (<b>c</b>) C-type combinations under a 1 Vpp excitation at a frequency of 4 MHz applied to the top electrode.</p>
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<p>Resonant frequencies of cells corresponding to various cavity sizes in the simulation of a single cell and the A-type, B-type, and C-type combinations.</p>
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<p>Displacement of each cell: (<b>a</b>) when the cell with a resonant frequency of about 4 MHz is in resonance; (<b>b</b>) when the cell with a resonant frequency of about 6 MHz in resonance; (<b>c</b>) when the cell with a resonant frequency of about 8 MHz in resonance.</p>
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<p>Optical images of (<b>a</b>) A-type, (<b>b</b>) B-type, and (<b>c</b>) C-type multi-frequency PMUT arrays. (<b>d</b>) A cross-section of a cell and (<b>e</b>) its enlarged view at the edge of the cavity.</p>
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<p>Impedance and phase characteristics of multi-frequency PMUT arrays under the (<b>a</b>) A-type, (<b>b</b>) B-type, and (<b>c</b>) C-type designs; (<b>d</b>) comparison schematic of actual measured resonant frequency and simulation results.</p>
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<p>Waveform of the signal received by the hydrophone from the PMUT array transmission.</p>
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<p>The amplitude–frequency variation curve of the received signal during the frequency sweep transmission of the (<b>a</b>) A-type, (<b>b</b>) B-type, and (<b>c</b>) C-type PMUT array.</p>
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<p>Time-domain response signals and their spectra of the 1-cycle burst echo of the (<b>a</b>) A-type, (<b>b</b>) B-type, and (<b>c</b>) C-type PMUT arrays under single-pulse sine wave excitation.</p>
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<p>Diagram of the use of an LDV to measure crosstalk.</p>
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<p>Comparison of normalized vibration displacement between excitation elements and their neighbor elements: comparison of arrays with different arrangements.</p>
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<p>Comparison of normalized vibration displacement between excitation elements and their neighbor elements: comparison of arrays with isolation grooves of different depths.</p>
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<p>Time-domain response signals and their FFT spectra of PMUT arrays with isolation grooves of different depths under single-pulse sinusoidal signal excitation: (<b>a</b>) grooves etched to a depth of 2 μm; (<b>b</b>) grooves etched to a depth of 5 μm; (<b>c</b>) grooves etched to a depth of 20 μm.</p>
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12 pages, 1118 KiB  
Article
Influence of Bladder Filling on Parameters of Body Composition by Bioimpedance Electrical Analysis: Observational Study
by Asunción Ferri-Morales, Sara Ando-Lafuente, Cristina Lirio-Romero, Emanuele Marzetti and Elisabeth Bravo-Esteban
Sensors 2024, 24(22), 7343; https://doi.org/10.3390/s24227343 - 18 Nov 2024
Viewed by 673
Abstract
Bioelectrical impedance analysis (BIA) is a widely used method for estimating body composition, and its accuracy may be influenced by various factors, including bladder filling. This study aims to investigate the impact of bladder filling on the accuracy of BIA measurements. An experimental [...] Read more.
Bioelectrical impedance analysis (BIA) is a widely used method for estimating body composition, and its accuracy may be influenced by various factors, including bladder filling. This study aims to investigate the impact of bladder filling on the accuracy of BIA measurements. An experimental crossover study was conducted with sedentary young adults. The influence of bladder filling on total body water (TBW), fat mass (FM), fat-free mass (FFM), and basal metabolic rate (BMR) was assessed. Participant in underwear followed an overnight fast. They were instructed to abstain from vigorous physical activity and alcohol for at least 24 h prior to the session. The results obtained from single-frequency and multi-frequency BIA devices were compared. The findings suggest that bladder filling does not affect measured impedance; however, changes in weight following bladder voiding influenced derived BIA results. Specifically, TBW, FM, and BMR values significantly reduced after voiding (p < 0.05). Furthermore, the study found poor agreement between single-frequency and multi-frequency BIA devices, indicating that they are not interchangeable. Bladder filling does affect BIA measurements, not clinically meaningful. Further research is needed to explore the implications of these findings for clinical practice and research protocols. Full article
(This article belongs to the Special Issue Advanced Sensors in Biomechanics and Rehabilitation)
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<p>Experimental protocol. BIA<sub>SF</sub>: Single-frequency bioelectrical impedance analysis; BIA<sub>MF</sub>: Multifrequency bioelectrical impedance analysis.</p>
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<p>Bland Altman plots of BIA<sub>SF</sub> versus BIA<sub>MF</sub> estimates of body composition with full and empty bladder.</p>
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12 pages, 5099 KiB  
Article
Application of Single-Frequency Arbitrarily Directed Split Beam Metasurface Reflector in Refractive Index Measurements
by Brian M. Wells, Joseph F. Tripp, Nicholas W. Krupa, Andrew J. Rittenberg and Richard J. Williams
Sensors 2024, 24(20), 6519; https://doi.org/10.3390/s24206519 - 10 Oct 2024
Viewed by 1037
Abstract
We present a sensor that utilizes a modified single-frequency split beam metasurface reflector to measure the refractive index of materials ranging from one to three. Samples are placed into a cavity between a PCB-etched dielectric and a reflecting ground plane. It is illuminated [...] Read more.
We present a sensor that utilizes a modified single-frequency split beam metasurface reflector to measure the refractive index of materials ranging from one to three. Samples are placed into a cavity between a PCB-etched dielectric and a reflecting ground plane. It is illuminated using a 10.525 GHz free-space transmit horn with reflecting angles measured by sweeping a receiving horn around the setup. Predetermined changes in measured angles determined through simulations will coincide with the material’s index. The sensor is designed using the Fourier transform method of array synthesis and verified with FEM simulations. The device is fabricated using PCB milling and 3D printing. The quality of the sensor is verified by characterizing 3D printed dielectric samples of various infill percentages and thicknesses. Without changing the metasurface design, the sensing performance is extended to accommodate larger sample thicknesses by including a modified 3D printed fish-eye lens mounted in front of the beam splitter; this helps to exaggerate changes in reflected angles for those samples. All the methods presented are in agreement and verified with single-frequency index measurements using Snell’s law. This device may offer a viable alternative to traditional index characterization methods, which often require large sample sizes for single-frequency measurements or expensive equipment for multi-frequency parameter extraction. Full article
(This article belongs to the Special Issue Optoelectronic Functional Devices for Sensing Applications)
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<p>(<b>a</b>) Schematic of the metasurface beam splitter reflecting sensor. (<math display="inline"><semantics> <mrow> <msub> <mrow> <mi>d</mi> </mrow> <mrow> <mi>x</mi> </mrow> </msub> </mrow> </semantics></math>, <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>d</mi> </mrow> <mrow> <mi>y</mi> </mrow> </msub> </mrow> </semantics></math>) are the sensor’s length and width proportional to <math display="inline"><semantics> <mrow> <mi>p</mi> </mrow> </semantics></math> and (<math display="inline"><semantics> <mrow> <msubsup> <mrow> <mi>θ</mi> </mrow> <mrow> <mi>R</mi> </mrow> <mrow> <mo>′</mo> </mrow> </msubsup> </mrow> </semantics></math>, <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>θ</mi> </mrow> <mrow> <mi>R</mi> </mrow> </msub> </mrow> </semantics></math>) represent the desired reflected angles. (<b>b</b>) Top view of the metasurface unit cell with <math display="inline"><semantics> <mrow> <mi>p</mi> <mo>=</mo> <mn>9.8</mn> <mo> </mo> <mi mathvariant="normal">m</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math>, and <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>l</mi> </mrow> <mrow> <mi>x</mi> </mrow> </msub> </mrow> </semantics></math> and <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>l</mi> </mrow> <mrow> <mi>y</mi> </mrow> </msub> </mrow> </semantics></math> are the patch dimensions varied from <math display="inline"><semantics> <mrow> <mn>50</mn> <mo> </mo> <mi mathvariant="sans-serif">μ</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math> to <math display="inline"><semantics> <mrow> <mn>9.3</mn> <mo> </mo> <mi mathvariant="normal">m</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math> for FEM simulations. (<b>c</b>) Illustrates the side view of the unit cell. <math display="inline"><semantics> <mrow> <mi>h</mi> <mo>=</mo> <mn>0.8</mn> <mo> </mo> <mi mathvariant="normal">m</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math> is the height of the substrate and <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>h</mi> </mrow> <mrow> <mi>s</mi> <mi>a</mi> <mi>m</mi> </mrow> </msub> <mo>=</mo> <mn>1</mn> <mo> </mo> <mi mathvariant="normal">m</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math> for the unit cell simulations. The sample height can be varied to accommodate various sample thicknesses. Simulated reflection (<b>d</b>) and phase (<b>e</b>) surface plots of the metasurface unit cell as a function of normalized lengths (<math display="inline"><semantics> <mrow> <msub> <mrow> <mi>l</mi> </mrow> <mrow> <mi>x</mi> </mrow> </msub> <mo>/</mo> <mi>p</mi> </mrow> </semantics></math>, <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>l</mi> </mrow> <mrow> <mi>y</mi> </mrow> </msub> <mo>/</mo> <mi>p</mi> </mrow> </semantics></math>) of the conductive patches.</p>
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<p>(<b>a</b>) Metasurface reflection magnitude and (<b>b</b>) reflection phase across the <span class="html-italic">x</span>-axis of the beam splitter. The solid line is calculated and the symbols are the nearest-neighbor fit. (<b>c</b>) Metasurface patch design from the nearest-neighbor fit. (<b>d</b>) A comparison of the electric far field for theory calculations, fabricated design calculations, and FEM simulations for the metasurface beam splitter sensor with a 1 mm air gap between the substrate and reflector. (<b>e</b>) Beam pointing error <math display="inline"><semantics> <mrow> <mi mathvariant="normal">B</mi> <mi mathvariant="normal">P</mi> <mi mathvariant="normal">E</mi> </mrow> </semantics></math> relative to the beam pointing error of a sample-free sensor <math display="inline"><semantics> <mrow> <mi mathvariant="normal">B</mi> <mi mathvariant="normal">P</mi> <msub> <mrow> <mi mathvariant="normal">E</mi> </mrow> <mrow> <mn>0</mn> </mrow> </msub> </mrow> </semantics></math> as a function of sensor size and sample index.</p>
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<p>(<b>a</b>) Surface plot of the electric-far-field response for varying the sample’s index of refraction and RX angle. The solid line indicates the maximum reflected angles. (<b>b</b>) A comparison of the electric far field for varying sample indices. Symbols indicate the location of the maximum reflected angles. (<b>c</b>) Close-up of the angle shifts observed for varying sample indices. (<b>d</b>) Change in angle from the initial reflected angles, not including a sample. The blue line is for the original −30° and the red line is for the original 30° reflected peaks.</p>
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<p>(<b>a</b>) Final metasurface beam splitter design etched on a FR4 single-sided copper-clad laminate circuit board. (<b>b</b>) Shows the schematic of the sensor holder and how all components fit together, including the aluminum reflector, sample, and metasurface beam splitter. These components slide and are held together using the 3D printed sample holder. The metasurface screen is enlarged to show detail. (<b>c</b>) The 3D printed 1 mm samples, from top to bottom, are 10%, 20%, 30%, and 100%. (<b>d</b>) Photograph of the experimental setup. This shows the location of the TX and RX horns with ray beams drawn to illustrate hypothetical locations of the reflected beams. The receiver is mechanically moved around the sensor using a motorized rotating optical platform at 0.1° increments ±20° from the measured maximum reflected peaks. It should be noted that the position of the TX horn does not affect the angle measurements due to their locations being outside the region of interference that would be produced by the TX horn when the RX is behind it.</p>
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<p>(<b>a</b>) Experimental setup for prism index measurements. (<b>b</b>) Top view of the experimental setup. The receiving horn (RX) is manually moved through 1° increments, identifying the location of the peak intensity first on the left-hand configuration and then repeated for the right-hand configuration. The average theta value is calculated and used for the final calculations. (<b>c</b>) Infill % compared with the index of refraction. The solid blue line is the polynomial fit, circles are the measured index, and squares are the FEM simulated index.</p>
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<p>(<b>a</b>) Normalized far-field electric field for the 1 mm samples of different infills at both −30° and 30° reflected angles. The symbols represent the location of the maximum angles. (<b>b</b>) Index of refraction as a function of <math display="inline"><semantics> <mrow> <mi mathvariant="sans-serif">Δ</mi> <mi>θ</mi> </mrow> </semantics></math>. The symbols are the FEM simulations and the solid line is the polynomial fit. (<b>c</b>) Measured delta theta (symbols) compared to FEM simulations (solid lines). The index of refractions of the measured delta theta is determined from the polynomial fit. (<b>d</b>) Comparison of the measured index of refraction from the metasurface beam splitter sensor (square symbols) compared with the measured index of refraction from the prism measurements (solid blue line) as a function of infill percentage.</p>
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<p>(<b>a</b>) Index of refraction as a function of <math display="inline"><semantics> <mrow> <mi mathvariant="sans-serif">Δ</mi> <mi>θ</mi> </mrow> </semantics></math>. The symbols represent FEM simulations and the solid line is the polynomial fit. (<b>b</b>) Measured delta theta (symbols) compared to FEM simulations (solid lines). (<b>c</b>) Comparison of the measured index of refraction from the metasurface beam splitter sensor (square symbols) compared with the measured index of refraction from the prism measurements (solid blue line) as a function of infill percentage.</p>
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<p>FEM simulations for <math display="inline"><semantics> <mrow> <mi mathvariant="sans-serif">Δ</mi> <mi>θ</mi> </mrow> </semantics></math> as a function of the index for varying sample thickness without the fish-eye lens (<b>a</b>,<b>b</b>) and including the fish-eye lens (<b>c</b>,<b>d</b>) for the −30° and 30° peaks, respectively. The 4 mm sample does not converge to two distinct reflected angles after an index of 1.7, but this is slightly improved to 1.8 in the presence of the lens.</p>
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<p>(<b>a</b>) Illustration of the modified sensor holder to accommodate the addition of the fish-eye lens. The lens position can be changed using the dovetail track, but it is positioned directly at the beam-splitting surface for the experiments. (<b>b</b>) Cross-section of the fish-eye lens design. (<b>c</b>) Ray tracing of the initial design to achieve maximum scattering. (<b>d</b>) FEM simulation of the normalized electric field for the fish-eye lens. (<b>e</b>) Measured normalized electric field for the fabricated fish-eye lens.</p>
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<p>(<b>a</b>,<b>d</b>) Index of refraction as a function of <math display="inline"><semantics> <mrow> <mi mathvariant="sans-serif">Δ</mi> <mi>θ</mi> </mrow> </semantics></math>. The symbols represent FEM simulations and the solid line is the polynomial fit. (<b>b</b>,<b>e</b>) Measured delta theta (symbols) compared to FEM simulations (solid lines). (<b>c</b>,<b>f</b>) Comparison of the measured index of refraction from the metasurface beam splitter sensor (square symbols) compared with the measured index of refraction from the prism measurements (solid blue line) as a function of infill percentage. The top row is the 3 mm samples and the bottom is the 4 mm samples.</p>
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13 pages, 4739 KiB  
Article
Multi-Frequency Asymmetric Absorption–Transmission Metastructures–Photonic Crystals and Their Application as a Refractive Index Sensor
by Lei Lei, Xiang Li and Haifeng Zhang
Sensors 2024, 24(19), 6281; https://doi.org/10.3390/s24196281 - 28 Sep 2024
Cited by 1 | Viewed by 806
Abstract
In this paper, a kind of metastructure–photonic crystal (MPC) with multi-frequency asymmetric absorption–transmission properties is proposed. It is composed of various dielectric layers arranged in a periodically tilting pattern. When electromagnetic waves (EMWs) enter from the opposite direction, MPC shows an obvious asymmetry. [...] Read more.
In this paper, a kind of metastructure–photonic crystal (MPC) with multi-frequency asymmetric absorption–transmission properties is proposed. It is composed of various dielectric layers arranged in a periodically tilting pattern. When electromagnetic waves (EMWs) enter from the opposite direction, MPC shows an obvious asymmetry. EMWs are absorbed at 13.71 GHz, 14.37 GHz, and 17.10 GHz in forward incidence, with maximum absorptions of 0.919, 0.917, and 0.956, respectively. In the case of backward incidence, transmission above 0.877 is achieved. Additionally, the MPC is utilized for refractive index (RI) sensing, allowing for wide RI range detection. The refractive index unit is denoted as RIU. The RI detection range is 1.4~3.0, with the corresponding absorption peak variation range being 17.054~17.194 GHz, and a sensitivity of 86 MHz/RIU. By adjusting the number of MPC cycles and tilt angle, the sensing performance and operating frequency band can be tailored to meet various operational requirements. This MPC-based RI sensor is simple to fabricate and has the potential to be used in the development of high-performance and compact sensing devices. Full article
(This article belongs to the Section Communications)
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<p>Schematic diagram of the MPC: (<b>a</b>) ordinary periodic structure; (<b>b</b>) introducing the analyte layer.</p>
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<p>Forward absorption and backward transmission curves in ordinary periodic MPC.</p>
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<p>(<b>a</b>) Forward absorption and backward transmission curves of the MPC introduced into the analyte layer. The black solid line represents the forward absorption curve, the red solid line indicates the backward transmission curve, and the black dashed arrow marks the resonance frequency. (<b>b</b>) Energy distribution of forward and backward incident electric fields at resonance frequency points.</p>
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<p>Forward absorption curves corresponding to different RI: (<b>a</b>) frequency range from 12 to 18 GHz, (<b>b</b>) frequency range from 17.00 to 17.25 GHz, and (<b>c</b>) relationship between wavelength and forward absorption curves.</p>
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<p>When <span class="html-italic">N</span> = 3, (<b>a</b>) shows the relationship between the resonance wavelength and RI, and (<b>b</b>) shows the linear fitting of the resonance frequency <span class="html-italic">f</span> and resonance wavelength <span class="html-italic">λ</span> to RI.</p>
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<p>When <span class="html-italic">N</span> = 4, (<b>a</b>) shows the change in the forward absorption curve with <span class="html-italic">n<sub>c</sub></span>, and (<b>b</b>) shows the linear fitting of the resonance frequency with RI. The blue dots represent the sampling points at various RI, while the black dashed lines indicate the fitting curves.</p>
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<p>When <span class="html-italic">N</span> = 5, (<b>a</b>) shows the change in the forward absorption curve with <span class="html-italic">n<sub>c</sub></span>, and (<b>b</b>) shows the linear fitting of the resonance frequency with RI. The orange dots represent the sampling points at various RI, while the black dashed lines indicate the fitting curves.</p>
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<p>Resonance frequency and period number <span class="html-italic">N</span> = 3, <span class="html-italic">N</span> = 4, and <span class="html-italic">N</span> = 5 are related in various cases.</p>
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<p>The linear fitting of the resonance frequency with RI at (<b>a</b>) <span class="html-italic">φ</span> = 30° and (<b>b</b>) <span class="html-italic">φ</span> = 50°. The green and blue stars represent the sampling points for the different RI, while the black dashed lines indicate the fitted curves.</p>
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<p>Resonance frequency and tilt angles <span class="html-italic">φ</span> = 30°, <span class="html-italic">φ</span> = 40°, and <span class="html-italic">φ</span> = 50° are related in various cases.</p>
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10 pages, 7547 KiB  
Article
Contrast-Enhanced Intraoperative Ultrasound Shows Excellent Performance in Improving Intraoperative Decision-Making
by Laura S. Kupke, Ivor Dropco, Markus Götz, Paul Kupke, Friedrich Jung, Christian Stroszczynski and Ernst-Michael Jung
Life 2024, 14(9), 1199; https://doi.org/10.3390/life14091199 - 22 Sep 2024
Viewed by 896
Abstract
Background: The aim of this study was to evaluate the performance and the impact of contrast-enhanced intraoperative ultrasound (CE-IOUS) on intraoperative decision-making, as there is still no standardized protocol for its use. Therefore, we retrospectively analyzed multiple CE-IOUS performed in hepato-pancreatic-biliary surgery with [...] Read more.
Background: The aim of this study was to evaluate the performance and the impact of contrast-enhanced intraoperative ultrasound (CE-IOUS) on intraoperative decision-making, as there is still no standardized protocol for its use. Therefore, we retrospectively analyzed multiple CE-IOUS performed in hepato-pancreatic-biliary surgery with respect to pre- and postoperative imaging and histopathological findings. Methods: Data of 50 patients who underwent hepato-pancreatic-biliary surgery between 03/2022 and 03/2024 were retrospectively collected. CE-IOUS was performed with a linear 6–9 MHz multifrequency probe connected to a high-resolution device. The ultrasound contrast agent used was a stabilized aqueous suspension of sulphur hexafluoride microbubbles. Results: In total, all 50 lesions indicated for surgery were correctly identified. In 30 cases, CE-IOUS was used to localize the primary lesion and to define the resection margins. In the remaining 20 cases, CE-IOUS identified an additional lesion. Fifteen of these findings were identified as malignant. In eight of these cases, the additional malignant lesion was subsequently resected. In the remaining seven cases, CE-IOUS again revealed an inoperable situation. In summary, CE-IOUS diagnostics resulted in a high correct classification rate of 95.7%, with positive and negative predictive values of 95.2% and 100.0%, respectively. Conclusions: CE-IOUS shows excellent performance in describing intraoperative findings in hepato-pancreatic-biliary surgery, leading to a substantial impact on intraoperative decision-making. Full article
(This article belongs to the Special Issue Microvascular Dynamics: Insights and Applications)
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<p>Flowchart demonstrating the categorization into subgroups after performance of contrast-enhanced intraoperative ultrasound (CE-IOUS).</p>
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<p>Hepatocellular carcinoma, marked by yellow circle, with typical contrast behavior in imaging: (<b>a</b>) computed tomography (CT) with hypervascularization in the arterial phase, (<b>b</b>) CT with washout in the portal-venous phase, (<b>c</b>) magnet resonance imaging with washout after contrast agent application, (<b>d</b>) contrast-enhanced intraoperative ultrasound (CE-IOUS) with surrounding neovascularization in early arterial contrast phase, (<b>e</b>) CE-IOUS with hypervascularization in the further course.</p>
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<p>Hepatocellular carcinoma, marked by yellow circle, with typical contrast behavior in imaging. (<b>a</b>) computed tomography (CT) with hypervascularization in the arterial phase, (<b>b</b>) CT with washout in the portal venous phase, (<b>c</b>) magnet resonance imaging with washout after contrast agent application, (<b>d</b>) contrast-enhanced intraoperative ultrasound with central washout in the portal venous phase.</p>
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<p>Unclear lesion, marked by yellow circle, in preoperative imaging: (<b>a</b>) computed tomography (CT) with homogenous liver parenchyma in arterial phase, (<b>b</b>) CT with hypodense lesion in portal-venous phase, (<b>c</b>) magnet resonance imaging with dull washout after contrast agent application, (<b>d</b>) contrast-enhanced intraoperative ultrasound with central washout in portal venous phase.</p>
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<p>Categorized visualization of the impact of contrast-enhanced intraoperative ultrasound on intraoperative decision-making.</p>
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<p>Predictive values of contrast-enhanced intraoperative ultrasound (CE-IOUS) in this study: (<b>a</b>) all lesions described by CE-IOUS; (<b>b</b>) additional lesions analyzed separately.</p>
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11 pages, 801 KiB  
Article
Characterization of Trap States in AlGaN/GaN MIS-High-Electron-Mobility Transistors under Semi-on-State Stress
by Ye Liang, Jiachen Duan, Ping Zhang, Kain Lu Low, Jie Zhang and Wen Liu
Nanomaterials 2024, 14(18), 1529; https://doi.org/10.3390/nano14181529 - 20 Sep 2024
Cited by 1 | Viewed by 1222
Abstract
Devices under semi-on-state stress often suffer from more severe current collapse than when they are in the off-state, which causes an increase in dynamic on-resistance. Therefore, characterization of the trap states is necessary. In this study, temperature-dependent transient recovery current analysis determined a [...] Read more.
Devices under semi-on-state stress often suffer from more severe current collapse than when they are in the off-state, which causes an increase in dynamic on-resistance. Therefore, characterization of the trap states is necessary. In this study, temperature-dependent transient recovery current analysis determined a trap energy level of 0.08 eV under semi-on-state stress, implying that interface traps are responsible for current collapse. Multi-frequency capacitance–voltage (C-V) testing was performed on the MIS diode, calculating that interface trap density is in the range of 1.37×1013 to 6.07×1012cm2eV1 from ECET=0.29 eV to 0.45 eV. Full article
(This article belongs to the Special Issue Epitaxial Growth of III-Nitride Hetero- and Nanostructures)
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<p>(<b>a</b>) The simplified schematic structure of AlGaN/GaN MIS-HEMTs with a 20 nm ALD-Al<sub>2</sub>O<sub>3</sub> as gate dielectric and passivation. (<b>b</b>) The fabrication process of the device.</p>
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<p>(<b>a</b>) Surface roughness after ICP etching. (<b>b</b>) Contact resistance was obtained using the TLM method.</p>
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<p>(<b>a</b>) Transfer characteristics (<math display="inline"><semantics> <msub> <mi mathvariant="normal">I</mi> <mi>D</mi> </msub> </semantics></math>-<math display="inline"><semantics> <msub> <mi mathvariant="normal">V</mi> <mrow> <mi>G</mi> <mi>S</mi> </mrow> </msub> </semantics></math>) and (<b>b</b>) output characteristics (<math display="inline"><semantics> <msub> <mi mathvariant="normal">I</mi> <mi>D</mi> </msub> </semantics></math>-<math display="inline"><semantics> <msub> <mi mathvariant="normal">V</mi> <mrow> <mi>D</mi> <mi>S</mi> </mrow> </msub> </semantics></math>) of the devices. (<b>c</b>) Off-state breakdown test results with a floating substrate.</p>
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<p>(<b>a</b>) Current collapse results are shown for off-state stress (green dotted line), semi-on-state stress (red dotted line), and no stress (black dotted line). (<b>b</b>) Changes in the R<math display="inline"><semantics> <msub> <mi mathvariant="normal">R</mi> <mrow> <mi>O</mi> <mi>N</mi> <mo>,</mo> <mi>D</mi> </mrow> </msub> </semantics></math>/<math display="inline"><semantics> <msub> <mi mathvariant="normal">R</mi> <mrow> <mi>O</mi> <mi>N</mi> <mo>,</mo> <mn>0</mn> </mrow> </msub> </semantics></math> ratio with increasing stress time.</p>
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<p>(<b>a</b>) Electrical field profile of AlGaN/GaN MIS-HEMT under semi-on-state stress. (<b>b</b>) Electrical field distribution along the 2DEG channel.</p>
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<p>(<b>a</b>) Schematic setup for transient measurement. (<b>b</b>) The semi-on-state stress at (<math display="inline"><semantics> <msub> <mi mathvariant="normal">V</mi> <mrow> <mi>G</mi> <mi>S</mi> <mo>,</mo> <mn>0</mn> </mrow> </msub> </semantics></math>, <math display="inline"><semantics> <msub> <mi mathvariant="normal">V</mi> <mrow> <mi>D</mi> <mi>S</mi> <mo>,</mo> <mn>0</mn> </mrow> </msub> </semantics></math>) = (−6 V, 40 V) is applied to the samples for 5 s. Then, after the stress period, the transient current is obtained by measuring the voltage drop across the resistive load during the on-state (<math display="inline"><semantics> <msub> <mi mathvariant="normal">V</mi> <mrow> <mi>G</mi> <mi>S</mi> <mo>,</mo> <mi>M</mi> </mrow> </msub> </semantics></math>, <math display="inline"><semantics> <msub> <mi mathvariant="normal">V</mi> <mrow> <mi>D</mi> <mi>S</mi> <mo>,</mo> <mi>M</mi> </mrow> </msub> </semantics></math>) = (1 V, 5 V) for 1 s.</p>
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<p>(<b>a</b>) The temperature-dependent transient recovery current results after semi-on-state stress. (<b>b</b>) Emission time constant spectra extracted from the temperature-dependent transient recovery current results. (<b>c</b>) Arrhenius plots calculate the activation energy of AlGaN/GaN MIS-HEMTs with Al<sub>2</sub>O<sub>3</sub> as dielectric under semi-on-state stress.</p>
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<p>(<b>a</b>) Multi-frequency C-V characteristics of AlGaN/GaN MIS diode. (<b>b</b>) <math display="inline"><semantics> <msub> <mi mathvariant="normal">D</mi> <mrow> <mi>i</mi> <mi>t</mi> </mrow> </msub> </semantics></math>-<math display="inline"><semantics> <msub> <mi mathvariant="normal">E</mi> <mi>T</mi> </msub> </semantics></math> mapping in the MIS diode. Measurement frequency <math display="inline"><semantics> <msub> <mi mathvariant="normal">f</mi> <mi>m</mi> </msub> </semantics></math> varies from 1 kHz to 1 MHz.</p>
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18 pages, 4912 KiB  
Article
Piezoelectrically and Capacitively Transduced Hybrid MEMS Resonator with Superior RF Performance and Enhanced Parasitic Mitigation by Low-Temperature Batch Fabrication
by Adnan Zaman, Ugur Guneroglu, Abdulrahman Alsolami and Jing Wang
Appl. Sci. 2024, 14(18), 8166; https://doi.org/10.3390/app14188166 - 11 Sep 2024
Viewed by 960
Abstract
This study investigates a hybrid microelectromechanical system (MEMS) acoustic resonator through a hybrid approach to combine capacitive and piezoelectric transduction mechanisms, thus harnessing the advantages of both transducer technologies within a single device. By seamlessly integrating both piezoelectric and capacitive transducers, the newly [...] Read more.
This study investigates a hybrid microelectromechanical system (MEMS) acoustic resonator through a hybrid approach to combine capacitive and piezoelectric transduction mechanisms, thus harnessing the advantages of both transducer technologies within a single device. By seamlessly integrating both piezoelectric and capacitive transducers, the newly designed hybrid resonators mitigate the limitations of capacitive and piezoelectric resonators. The unique hybrid configuration holds promise to significantly enhance overall device performance, particularly in terms of quality factor (Q-factor), insertion loss, and motional impedance. Moreover, the dual-transduction approach improves the signal-to-noise ratio and reduces feedthrough noise levels at higher frequencies. In this paper, the detailed design, complex fabrication processes, and thorough experimental validation are presented, demonstrating substantial performance enhancement potentials. A hybrid disk resonator with a single side-supporting anchor achieved an outstanding loaded Q-factor higher than 28,000 when operating under a capacitive drive and piezoelectric sense configuration. This is comparably higher than the measured Q-factor of 7600 for another disk resonator with two side-supporting anchors. The hybrid resonator exhibits a high Q-factor at its resonance frequency at 20 MHz, representing 2-fold improvement over the highest reported Q-factor for similar MEMS resonators in the literature. Also, the dual-transduction approach resulted in a more than 30 dB improvement in feedthrough suppression for devices with a 500 nm-thick ZnO layer, while hybrid resonators with a thicker piezoelectric layer of 1300 nm realized an even greater feedthrough suppression of more than 50 dB. The hybrid resonator integration strategy discussed offers an innovative solution for current and future advanced RF front-end applications, providing a versatile platform for future innovations in on-chip resonator technology. This work has the potential to lead to advancements in MEMS resonator technology, facilitating some significant improvements in multi-frequency and frequency agile RF applications through the original designs equipped with integrated capacitive and piezoelectric transduction mechanisms. The hybrid design also results in remarkable performance metrics, making it an ideal candidate for integrating next-generation wireless communication devices where size, cost, and energy efficiency are critical. Full article
(This article belongs to the Section Acoustics and Vibrations)
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<p>Schematic illustration of electrode and anchor design configurations for a hybrid MEMS resonator. This hybrid resonator integrates capacitive and piezoelectric transducers, which are designed to enhance performance metrics such as quality factor, insertion loss, and motional impedance, and so on.</p>
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<p>COMSOL<sup>®</sup> finite element eigenfrequency simulation depicting the first four lateral extensional contour modes of a disk-shaped resonator: (<b>a</b>) 1st lateral extensional mode, (<b>b</b>) 2nd lateral extensional mode, (<b>c</b>) 3rd lateral extensional mode, (<b>d</b>) 4th lateral extensional mode.</p>
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<p>(<b>a</b>) Top-view (3D) and (<b>b</b>) cross-sectional view (3D) diagrams of proposed hybrid resonator; (<b>c</b>–<b>f</b>) step-by-step illustration of the simplified fabrication process flow of a hybrid lateral extensional mode resonator with capacitive and piezoelectric transducers. The process begins with the preparation of a silicon-on-insulator (SOI) wafer and proceeds through steps such as photolithography, deep-reactive ion-etching (DRIE), atomic layer deposition (ALD) for gap spacing, and the deposition of a ZnO piezoelectric layer, which concludes with the final releasing step to suspend the resonator structure.</p>
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<p>(<b>a</b>) Top-view microscope image of the fabricated hybrid resonator after etching the ZnO piezoelectric transducer and silicon device layer to define the disk resonator body, (<b>b</b>) Zoomed-in view of the device showing piezoelectric and capacitive transducers. (<b>c</b>) Further zoomed-in view photo showing the resonator body with piezoelectric and capacitive electrodes, and the capacitive air gap between the resonator body and the capacitive electrode.</p>
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<p>Conceptual illustration of the primary feedthrough signal paths with different strengths for (<b>a</b>) a capacitively transduced resonator, and (<b>b</b>) a piezoelectrically transduced resonator.</p>
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<p>Cross-sectional schematic of a resonator device fabricated in an SOI wafer depicting the LCR circuit components, showing the key parasitics between electrodes and through the substrate, for (<b>a</b>) a capacitively transduced resonator, and (<b>b</b>) a piezoelectrically transduced resonator.</p>
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<p>Illustration of signal paths for a hybrid capacitive/piezoelectric resonator with reduced feedthrough as the device operates under different configurations, including (<b>a</b>) piezoelectric drive and capacitive sense, and (<b>b</b>) capacitive drive and piezoelectric sense.</p>
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<p>Illustration of RF probe measurement set-up for hybrid resonator devices with a set of two capacitive ports and another one or a pair of piezoelectric transducer ports, fully isolated by the resonator body and ground, showing two different activation schemes to generate electrostatic force in the capacitive gap. (<b>a</b>) One applies an AC voltage to the capacitive electrodes and a DC voltage to the resonator body with two anchors to generate electrostatic force; and (<b>b</b>) The other applies both AC and DC voltages to the capacitive electrodes to induce electrostatic force in the capacitive gap for a resonator design with wider capacitive electrodes and one side-supporting anchor.</p>
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<p>Measured feedthrough levels versus frequency for piezoelectric only, capacitive only, and hybrid resonators with different thin-film piezoelectric transducer thicknesses. The measured feedthrough level of a CS−5 calibration standard is included that exhibits a feedthrough level on par to that of a hybrid device.</p>
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<p>Measured broadband frequency response of a 125 µm−radius hybrid disk resonator with a 5 µm−thick Si device layer operating in its 1st later extensional mode, which is actuated by the fully integrated capacitive transducer through its surrounding electrodes and detected by a piezoelectric transducer via a pair of top electrodes on top of the ZnO piezoelectric layer.</p>
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<p>Measured broadband frequency response of a 150 µm−radius hybrid disk resonator, with a 5 µm−thick Si device layer operating in its 4th later extensional mode, which is actuated by the fully integrated capacitive transducer through its surrounding electrodes and detected by a piezoelectric transducer via a pair of top electrodes on top of the ZnO piezoelectric layer.</p>
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10 pages, 691 KiB  
Article
Comparing Device-Generated and Calculated Bioimpedance Variables in Community-Dwelling Older Adults
by Kworweinski Lafontant, Danielle A. Sterner, David H. Fukuda, Jeffrey R. Stout, Joon-Hyuk Park and Ladda Thiamwong
Sensors 2024, 24(17), 5626; https://doi.org/10.3390/s24175626 - 30 Aug 2024
Viewed by 713
Abstract
Despite BIA emerging as a clinical tool for assessing older adults, it remains unclear how to calculate whole-body impedance (Z), reactance (Xc), resistance (R), and phase angle (PhA) from segmental values using modern BIA devices that place electrodes on both sides of the [...] Read more.
Despite BIA emerging as a clinical tool for assessing older adults, it remains unclear how to calculate whole-body impedance (Z), reactance (Xc), resistance (R), and phase angle (PhA) from segmental values using modern BIA devices that place electrodes on both sides of the body. This investigation aimed to compare both the whole-body and segmental device-generated phase angle (PhADG) with the phase angle calculated using summed Z, Xc, and R from the left, right, and combined sides of the body (PhACalc) and to compare bioelectric variables between sides of the body. A sample of 103 community-dwelling older adults was assessed using a 50 kHz direct segmental multifrequency BIA device. Whole-body PhACalc values were assessed for agreement with PhADG using 2.5th and 97.5th quantile nonparametric limits of agreement and Spearman’s rho. Bioelectrical values between sides of the body were compared using Wilcoxon rank and Spearman’s rho. A smaller mean difference was observed between PhADG and right PhACalc (−0.004°, p = 0.26) than between PhACalc on the left (0.107°, p = 0.01) and on the combined sides (0.107°, p < 0.001). The sum of Z, R, and PhACalc was significantly different (p < 0.01) between the left (559.66 ± 99.55 Ω, 556.80 ± 99.52 Ω, 5.51 ± 1.5°, respectively) and the right sides (554.60 ± 94.52 Ω, 552.02 ± 94.23 Ω, 5.41 ± 0.8°, respectively). Bilateral BIA values do not appear to be interchangeable when determining whole-body measurements. Present data suggest that using right-sided segmental values would be the most appropriate choice for calculating whole-body bioelectrical variables. Full article
(This article belongs to the Special Issue Bioimpedance Sensors for Medical Monitoring and Diagnosis)
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<p>The flow of participants through recruitment, screening, and inclusion in this study.</p>
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<p>Locations of the InBody s10 touch-type electrodes in the seated position. Current-injecting electrodes were placed on the middle fingers and immediately inferior to the medial malleoli. Voltage-sensing electrodes were placed on the thumbs and immediately inferior to the lateral malleoli. Created with BioRender.com.</p>
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8 pages, 555 KiB  
Article
Comparison between Discrete Multi-Wavelength Near-Infrared Spectroscopy and Bioelectrical Impedance Analysis in the Assessment of Muscle Mass for Community-Dwelling Older People
by Jinyoung Shin and Eunki Park
J. Clin. Med. 2024, 13(8), 2350; https://doi.org/10.3390/jcm13082350 - 18 Apr 2024
Cited by 2 | Viewed by 1080
Abstract
(1) Background: This study evaluated the clinical implications of a new measurement technique for muscle mass using discrete multi-wavelength near-infrared spectroscopy (DMW-NIRS) compared with multifrequency bioelectrical impedance analysis (BIA) in older adults. (2) Methods: In a cross-sectional study involving 91 participants [...] Read more.
(1) Background: This study evaluated the clinical implications of a new measurement technique for muscle mass using discrete multi-wavelength near-infrared spectroscopy (DMW-NIRS) compared with multifrequency bioelectrical impedance analysis (BIA) in older adults. (2) Methods: In a cross-sectional study involving 91 participants aged 65 years, the agreement of total lean mass for each measurement was assessed using the intraclass correlation coefficient (ICC) and Pearson’s correlation analysis. The study was conducted at a university hospital from 10 July 2023 to 1 November 2023. (3) Results: A total of 45 men (mean age, 74.1) and 46 women (mean age, 73.6) were analyzed. In the comparisons of total lean mass between DMW-NIRS and BIA, ICC (2.1) was 0.943 and Cronbach’s α coefficient was 0.949 (p < 0.001). Across all segments of lean mass, we found excellent agreement with the ICCs (>0.90) and acceptable values of the correlation coefficients (>0.6) between DMW-NIRS and BIA. (4) Conclusions: This study confirmed agreement in the measurements of muscle mass between portable devices using DMW-NIRS and BIA among community-dwelling older adults. A simple screening of muscle mass in a home setting would help to detect early decreases in muscle mass. Full article
(This article belongs to the Section Epidemiology & Public Health)
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<p>Comparison of near-infrared spectroscopy (DMW-NIRS) and bioelectrical impedance analysis (BIA) according to sex.</p>
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<p>Comparison of near-infrared spectroscopy (DMW-NIRS) and bioelectrical impedance analysis (BIA) according to sex.</p>
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23 pages, 7409 KiB  
Article
Cardiac Multi-Frequency Vibration Signal Sensor Module and Feature Extraction Method Based on Vibration Modeling
by Zhixing Gao, Yuqi Wang, Kang Yu, Zhiwei Dai, Tingting Song, Jun Zhang, Chengjun Huang, Haiying Zhang and Hao Yang
Sensors 2024, 24(7), 2235; https://doi.org/10.3390/s24072235 - 30 Mar 2024
Viewed by 1774
Abstract
Cardiovascular diseases pose a long-term risk to human health. This study focuses on the rich-spectrum mechanical vibrations generated during cardiac activity. By combining Fourier series theory, we propose a multi-frequency vibration model for the heart, decomposing cardiac vibration into frequency bands and establishing [...] Read more.
Cardiovascular diseases pose a long-term risk to human health. This study focuses on the rich-spectrum mechanical vibrations generated during cardiac activity. By combining Fourier series theory, we propose a multi-frequency vibration model for the heart, decomposing cardiac vibration into frequency bands and establishing a systematic interpretation for detecting multi-frequency cardiac vibrations. Based on this, we develop a small multi-frequency vibration sensor module based on flexible polyvinylidene fluoride (PVDF) films, which is capable of synchronously collecting ultra-low-frequency seismocardiography (ULF-SCG), seismocardiography (SCG), and phonocardiography (PCG) signals with high sensitivity. Comparative experiments validate the sensor’s performance and we further develop an algorithm framework for feature extraction based on 1D-CNN models, achieving continuous recognition of multiple vibration features. Testing shows that the recognition coefficient of determination (R2), mean absolute error (MAE), and root mean square error (RMSE) of the 8 features are 0.95, 2.18 ms, and 4.89 ms, respectively, with an average prediction speed of 60.18 us/point, meeting the re-quirements for online monitoring while ensuring accuracy in extracting multiple feature points. Finally, integrating the vibration model, sensor, and feature extraction algorithm, we propose a dynamic monitoring system for multi-frequency cardiac vibration, which can be applied to portable monitoring devices for daily dynamic cardiac monitoring, providing a new approach for the early diagnosis and prevention of cardiovascular diseases. Full article
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<p>Cardiac multi-frequency vibration detection system. (<b>a</b>) Schematic diagram of the system acquisition scene. (<b>b</b>) System framework, including the sensor, a signal acquisition terminal, and feature extraction framework.</p>
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<p>(<b>a</b>) Three-dimensional shape drawing of the multi-frequency vibration sensor, the red arrow represents the direction of pressure transfer in the chest wall; (<b>b</b>) PVDF film; (<b>c</b>) Schematic of the laminated structure of the sensor module. From bottom to top are the fixed structure, the PVDF film, the metal electrode, the EVA foam adhesive, the shell, and the two holes in the shell.</p>
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<p>(<b>a</b>) Circuit structure diagram of the acquisition terminal, including the PVDF processing circuit, ECG analog front-end and control circuit; (<b>b</b>) Circuit diagram of the PVDF processing circuit, with the signals passing through the two-stage op-amps.</p>
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<p>Diagram of the structure of 1D-CNN, including the input layer, convolutional (conv) layer, fully connected (FC) layer, and output layer.</p>
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<p>(<b>a</b>) The built acquisition system, including the PVDF module, ECG electrodes, and acquisition terminal; (<b>b</b>) Raw ECG and raw PVDF signal from one subject with the PVDF attached to the sternum. (<b>c</b>) Synchronized signals, from top to bottom, of filtered ECGs, raw PVDF signals, filtered ULF-SCGs, filtered SCGs, and filtered PCGs, with the corresponding feature points labeled.</p>
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<p>Sensitivity testing of PVDF modules. (<b>a</b>) Calibration of the experimental setup, including control module, force sensing unit, and PVDF sensor. (<b>b</b>) An experimental procedure with different force levels set to record different voltage outputs. (<b>c</b>) Voltage output-force response curve of the PVDF module.</p>
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<p>(<b>a</b>) Comparison of PCG signals acquired by PVDF and MEMS including the PCG envelope extracted by the algorithm [<a href="#B25-sensors-24-02235" class="html-bibr">25</a>] and labeled S1 and S2. (<b>b</b>) Correlation of S1 and S2 positions measured by the PVDF module and MEMS (data from (<b>a</b>)). (<b>c</b>) Correlation of S1 position measured by PVDF module and MEMS (249 signal cycles). (<b>d</b>) Correlation of S2 position measured by PVDF module and MEMS (249 signal cycles).</p>
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<p>EMD decomposition plots. From top to bottom are the original PVDF waveform and the nine intrinsic modal functions (distributed from high to low frequencies).</p>
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<p>Layer 3, 4, and 7 IMFs are compared with the waveforms and feature points of the actual PCG, SCG, and ULF-SCG, respectively.</p>
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<p>Characteristic point calibration of SCGs with different morphologies, where (<b>a</b>–<b>l</b>) are two single cycles of data from subjects #1–6, respectively. Where the black, blue, and red curves are the ECG, SCG, and curvature features, respectively. The red dots are the SCG features.</p>
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<p>Feature point training results for seven model structures, including <math display="inline"><semantics> <mrow> <msup> <mrow> <mi>R</mi> </mrow> <mrow> <mn>2</mn> </mrow> </msup> </mrow> </semantics></math>, Epochs under the early stopping rule, and test duration of the model (377 test samples), corresponding to the red, blue and green lines, respectively.</p>
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<p>Optimal model structure of ten feature points. MC, IM, AO, IC, RE, AC, MO, RF, S1, and S2 use the sixth, sixth, second, third, third, fourth, first, second, seventh, and fifth model structures in <a href="#sensors-24-02235-t005" class="html-table">Table 5</a>, respectively.</p>
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<p><math display="inline"><semantics> <mrow> <msup> <mrow> <mi>R</mi> </mrow> <mrow> <mn>2</mn> </mrow> </msup> <mo> </mo> </mrow> </semantics></math>mean and standard deviation results for 10 experiments.</p>
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22 pages, 4602 KiB  
Article
The Feasibility of Semi-Continuous and Multi-Frequency Thoracic Bioimpedance Measurements by a Wearable Device during Fluid Changes in Hemodialysis Patients
by Melanie K. Schoutteten, Lucas Lindeboom, Hélène De Cannière, Zoë Pieters, Liesbeth Bruckers, Astrid D. H. Brys, Patrick van der Heijden, Bart De Moor, Jacques Peeters, Chris Van Hoof, Willemijn Groenendaal, Jeroen P. Kooman and Pieter M. Vandervoort
Sensors 2024, 24(6), 1890; https://doi.org/10.3390/s24061890 - 15 Mar 2024
Cited by 3 | Viewed by 1318
Abstract
Repeated single-point measurements of thoracic bioimpedance at a single (low) frequency are strongly related to fluid changes during hemodialysis. Extension to semi-continuous measurements may provide longitudinal details in the time pattern of the bioimpedance signal, and multi-frequency measurements may add in-depth information on [...] Read more.
Repeated single-point measurements of thoracic bioimpedance at a single (low) frequency are strongly related to fluid changes during hemodialysis. Extension to semi-continuous measurements may provide longitudinal details in the time pattern of the bioimpedance signal, and multi-frequency measurements may add in-depth information on the distribution between intra- and extracellular fluid. This study aimed to investigate the feasibility of semi-continuous multi-frequency thoracic bioimpedance measurements by a wearable device in hemodialysis patients. Therefore, thoracic bioimpedance was recorded semi-continuously (i.e., every ten minutes) at nine frequencies (8–160 kHz) in 68 patients during two consecutive hemodialysis sessions, complemented by a single-point measurement at home in-between both sessions. On average, the resistance signals increased during both hemodialysis sessions and decreased during the interdialytic interval. The increase during dialysis was larger at 8 kHz (∆ 32.6 Ω during session 1 and ∆ 10 Ω during session 2), compared to 160 kHz (∆ 29.5 Ω during session 1 and ∆ 5.1 Ω during session 2). Whereas the resistance at 8 kHz showed a linear time pattern, the evolution of the resistance at 160 kHz was significantly different (p < 0.0001). Measuring bioimpedance semi-continuously and with a multi-frequency current is a major step forward in the understanding of fluid dynamics in hemodialysis patients. This study paves the road towards remote fluid monitoring. Full article
(This article belongs to the Special Issue Bioimpedance Sensors for Medical Monitoring and Diagnosis)
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<p>Schematic presentation of the study design and the 3 methodological approaches. I current, P bias polar, V voltage.</p>
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<p>The wearable device (<b>A</b>), schematic presentation of the thoracic electrodes (<b>B</b>), and attachment of the electrodes and cables on the thoracic region of a study patient (<b>C</b>). I current, P bias polar, V voltage.</p>
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<p>Flow chart of the study process indicating technical malfunctioning of the device, outlier detection, and missing measurements.</p>
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<p>The evolution of thoracic resistance (Ω) w<span class="html-italic">i</span>th a focus on 8 and 160 kHz, and weight (kg) over time (hours) throughout the study (i.e., dialysis session 1 from 0–4 h, home measurement at 24 h, and dialysis session 2 from 48–52 h). Every time point represents the mean data from all subjects (n = 45); standard deviations are displayed as the grey shaded area.</p>
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<p>Number of dialysis sessions w<span class="html-italic">i</span>th increasing or decreasing thoracic resistance for each frequency, per interval.</p>
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<p>A subject-specific evolution of thoracic resistance (Ω) at 8 and 160 kHz, and weight (kg) over time, demonstrating <b>an increase</b> in resistance during both dialysis sessions, and a decrease during the interdialytic interval.</p>
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<p>A subject-specific evolution of thoracic resistance (Ω) at 8 and 160 kHz, and weight (kg) over time, demonstrating a <b>decrease</b> in resistance during dialysis session 1, an increase during the first interdialytic interval, a decrease during the second interdialytic interval, and an increase during dialysis session 2.</p>
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<p>The average slopes of thoracic resistance during hemodialysis based on single-point measurements. Resistance measurements are represented in Ω as mean ± standard deviation (arrowhead as a straight line for 8 kHz and a simple arrowhead for 160 kHz). The cut-off that divided a dialysis session was set at 30 (<b>A</b>), 50 (<b>B</b>), 90 (<b>C</b>), and 100 (<b>D</b>) minutes after the start of dialysis. The slopes were compared using a paired sample <span class="html-italic">t</span>-test. * and ** indicate <span class="html-italic">p</span> values &lt; 0.05 and &lt;0.01, respectively. Abbreviations: m, slope. m<sub>a</sub> and m<sub>b</sub> indicate the slope of the part <span class="html-italic">before</span> and <span class="html-italic">after</span> the cut-off point, respectively.</p>
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<p>Individual predicted evolution over time for a given patient.</p>
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24 pages, 7620 KiB  
Article
Analysis of Minimal Channel Electroencephalography for Wearable Brain–Computer Interface
by Arpa Suwannarat, Setha Pan-ngum and Pasin Israsena
Electronics 2024, 13(3), 565; https://doi.org/10.3390/electronics13030565 - 30 Jan 2024
Cited by 1 | Viewed by 2052
Abstract
Electroencephalography (EEG)-based brain—computer interface (BCI) is a non-invasive technology with potential in various healthcare applications, including stroke rehabilitation and neuro-feedback training. These applications typically require multi-channel EEG. However, setting up a multi-channel EEG headset is time-consuming, potentially resulting in patient reluctance to use [...] Read more.
Electroencephalography (EEG)-based brain—computer interface (BCI) is a non-invasive technology with potential in various healthcare applications, including stroke rehabilitation and neuro-feedback training. These applications typically require multi-channel EEG. However, setting up a multi-channel EEG headset is time-consuming, potentially resulting in patient reluctance to use the system despite its potential benefits. Therefore, we investigated the appropriate number of electrodes required for a successful BCI application in wearable devices using various numbers of EEG channels. EEG multi-frequency features were extracted using the “filter bank” feature extraction technique. A support vector machine (SVM) was used to classify a left/right-hand opening/closing motor imagery (MI) task. Nine electrodes around the center of the scalp (F3, Fz, F4, C3, Cz, C4, P3, Pz, and P4) provided high classification accuracy with a moderate setup time; hence, this system was selected as the minimal number of required channels. Spherical spline interpolation (SSI) was also applied to investigate the feasibility of generating EEG signals from limited channels on an EEG headset. We found classification accuracies of interpolated groups only, and combined interpolated and collected groups were significantly lower than the measured groups. The results indicate that SSI may not provide additional EEG data to improve classification accuracy of the collected minimal channels. The conclusion is that other techniques could be explored or a sufficient number of EEG channels must be collected without relying on generated data. Our proposed method, which uses a filter bank feature, session-dependent training, and the exploration of many groups of EEG channels, offers the possibility of developing a successful BCI application using minimal channels on an EEG device. Full article
(This article belongs to the Section Computer Science & Engineering)
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<p>The international 10/20 system [<a href="#B64-electronics-13-00565" class="html-bibr">64</a>].</p>
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<p>Groups of electrodes used for experiments. (<b>a</b>) Group of eleven; (<b>b</b>) Group of nine; (<b>c</b>) Group of 5B; (<b>d</b>) Group of 5A; (<b>e</b>) Group of three; (<b>f</b>) Group of two.</p>
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<p>Timeline of each experimental trial.</p>
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<p>Hand opening and closing task.</p>
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<p>Display on screen showing (<b>a</b>) right-hand opening; (<b>b</b>) right-hand closing; (<b>c</b>) left-hand opening; and (<b>d</b>) left-hand closing.</p>
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<p>Additional groups of electrodes for dataset 1: (<b>a</b>) Group of twenty-one; (<b>b</b>) Group of fifteen; (<b>c</b>) Group of thirteen; (<b>d</b>) Group of 11A; (<b>e</b>) Group of 9A; (<b>f</b>) Group of 5A_1.</p>
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<p>Additional groups of electrodes for dataset 1: (<b>a</b>) Group of twenty-one; (<b>b</b>) Group of fifteen; (<b>c</b>) Group of thirteen; (<b>d</b>) Group of 11A; (<b>e</b>) Group of 9A; (<b>f</b>) Group of 5A_1.</p>
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<p>Additional groups of electrodes for dataset 2: (<b>a</b>) Group of twenty-five; (<b>b</b>) Group of forty-one.</p>
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<p>Statistical comparison for each electrode group from our dataset. ‘x’ denotes average classification accuracy, colored seams denote the median and the black line ‘-‘ above the plots represents statistically differences between groups, with a <span class="html-italic">p</span>-value less than 0.01.</p>
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<p>Statistical comparison for each electrode group from dataset 1. ‘x’ denotes average classification accuracy, colored seams denote the median and the black line ‘-‘ above the plots represents statistically significant differences between groups, with a <span class="html-italic">p</span>-value less than 0.05.</p>
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<p>Statistical comparison for each electrode group from dataset 2. ‘x’ denotes average classification accuracy and colored seams denote the median.</p>
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<p>Comparison of measured and interpolated eleven-electrode group. ‘x’ denotes average classification accuracy, ‘-’ denotes median, and dots represent outliers.</p>
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<p>Comparison of measured and interpolated nine-electrode group. ‘x’ denotes average classification accuracy, ‘-’ denotes median, and dots represent outliers.</p>
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<p>Groups of combined electrodes.</p>
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<p>Comparison of classification accuracy with increasing number of electrodes. ‘x’ denotes average classification accuracy, ‘-’ denotes median, and dots represent outliers.</p>
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<p>Comparison of RMS values of each group of electrodes. ‘x’ denotes average classification accuracy, colored seams denote the median and the black line ‘-‘ above the plots represents significant differences between groups, with a <span class="html-italic">p</span>-value less than 0.05.</p>
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19 pages, 10690 KiB  
Article
Designing and Testing an IoT Low-Cost PPP-RTK Augmented GNSS Location Device
by Domenico Amalfitano, Matteo Cutugno, Umberto Robustelli and Giovanni Pugliano
Sensors 2024, 24(2), 646; https://doi.org/10.3390/s24020646 - 19 Jan 2024
Cited by 2 | Viewed by 2628
Abstract
Nowadays, the availability of affordable multi-constellation multi-frequency receivers has broadened access to accurate positioning. The abundance of satellite signals coupled with the implementation of ground- and satellite-based correction services has unlocked the potential for achieving real-time centimetre-level positioning with low-cost instrumentation. Most of [...] Read more.
Nowadays, the availability of affordable multi-constellation multi-frequency receivers has broadened access to accurate positioning. The abundance of satellite signals coupled with the implementation of ground- and satellite-based correction services has unlocked the potential for achieving real-time centimetre-level positioning with low-cost instrumentation. Most of the current and future applications cannot exploit well-consolidated satellite positioning techniques such as Network Real Time Kinematic (RTK) and Precise Point Positioning (PPP); the former is inapplicable for large user bases due to the necessity of a two-way communication link between the user and the NRTK service provider, while the latter necessitates long convergence times that are not in keeping with kinematic application. In this context, the hybrid PPP-RTK technique has emerged as a potential solution to meet the demand for real-time, low-cost, accurate, and precise positioning. This paper presents an Internet of Things (IoT) GNSS device developed with low-cost hardware; it leverages a commercial PPP-RTK correction service which delivers corrections via IP. The main target is to obtain both horizontal and vertical decimetre-level accuracies in urban kinematic tests, along with other requisites such as solution availability and the provision of connection ports for interfacing an IoT network. A vehicle-borne kinematic test has been conducted to evaluate the device performance. The results show that (i) the IoT device can deliver horizontal and vertical positioning solutions at decimetre-level accuracy with the targeted solution availability, and (ii) the provided IoT ports are feasible for gathering the position solutions over an internet connection. Full article
(This article belongs to the Special Issue GNSS Signals and Precise Point Positioning)
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<p>Combination of Hardware and Deployment views of the IoT location device.</p>
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<p>(<b>a</b>) Polycarbonate box with 5 inch screen for interfacing with the IoT system and (<b>b</b>) IoT Location Device Packaging (overall measurements: 19.5 cm × 15 cm × 9.5 cm).</p>
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<p>Component view of the Location service.</p>
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<p>Data view.</p>
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<p>Cartographic map of Fuorigrotta neighbourhood in Naples, Italy showing identification of the test track (red circles). The figure shows the start point (green marker), end point (blue marker), and location of the GNSS base station (magenta marker).</p>
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<p>Experimental setup, including the aluminium bar used for mounting the two geodetic-grade GNSS receivers (at the ends of the bar) and the low-cost GNSS antenna feeding the IoT GNSS receiver. The right part of the figure shows the GNSS base station mounted on a tripod.</p>
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<p>Images depicting the bar mounted on the test car. The left image displays a frontal view, while right image displays a side view. It is worth noting that a wood base of a certain thickness was employed to align the phase centres of the three antennas.</p>
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<p>IoT location device positioning solutions for the entire kinematic test. The markers colours have been chosen for better visualisation. Green markers refer to PPP-RTK fixed, yellow makers to PPP-RTK float, and red markers to code differential (DGNSS).</p>
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<p>Geometric Dilution of Precision (GDOP), number of satellites, and time series of East, North, and Up coordinate component errors; the green, yellow, and red background colours refer to PPP-RTK fixed, PPP-RTK float, and code differential (DGNSS) solutions, respectively.</p>
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<p>Cumulative density function estimates of positioning errors for the entire track. The green and yellow lines refer to PPP-RTK fixed and float solutions, respectively, while the red lines refer to code differential (DGNSS) solutions. The <b>top panel</b> and <b>bottom panel</b> refers to the horizontal and absolute values of the vertical error, respectively.</p>
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<p>Relative frequency histograms of the horizontal (<b>left panel</b>) and vertical (<b>right panel</b>) errors. The green bars correspond to PPP-RTK fixed solutions, while the yellow bars refer to PPP-RTK float solutions.</p>
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<p>Scatter plot of the horizontal coordinate component errors for the entire path. The red, yellow, and green markers refer to DGNSS, PPP-RTK float, and PPP-RTK fixed solutions, respectively.</p>
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<p>Screenshot of the developed web application.</p>
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<p>Panel (<b>a</b>) record session dashboard. Panel (<b>b</b>) load and view stored sessions dashboard.</p>
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15 pages, 6011 KiB  
Article
Digital Signal Compensation and Sounding Depth Analysis of Portable Frequency-Domain Electromagnetic Exploration System
by Huipeng Liu, Jianxin Liu, Fang Wang, Leiyun Qian and Rong Liu
Sensors 2024, 24(2), 566; https://doi.org/10.3390/s24020566 - 16 Jan 2024
Cited by 1 | Viewed by 967
Abstract
Low-resistivity objects produce eddy currents when excited with electromagnetic waves of a certain frequency and then generate an eddy electromagnetic field. A portable frequency-domain electromagnetic exploration system can be used to identify this eddy electromagnetic field, and then the low-resistivity objects can be [...] Read more.
Low-resistivity objects produce eddy currents when excited with electromagnetic waves of a certain frequency and then generate an eddy electromagnetic field. A portable frequency-domain electromagnetic exploration system can be used to identify this eddy electromagnetic field, and then the low-resistivity objects can be positioned. At present, portable frequency-domain electromagnetic method (FEM) exploration systems use analog signal compensation, and the sounding depth is generally calculated using empirical formulas. In order to improve the rationality of signal compensation, this paper puts forward a digital signal compensation technology, including a device design, an information extraction method, and a primary field calibration method, and makes an exploration prototype based on the digital signal compensation technology. Using 10 nV as the minimum potential detection capability, the sounding depth of the portable FEM was analyzed, and it was found that when investigating a target with the same depth, a lower frequency required a larger emission current. If this could not be met, the sounding depth became smaller, and a phenomenon appeared in which the lower the operating frequency, the smaller the sounding depth. Through the detection of known underground garages, the apparent conductivity and normalized secondary field anomalies with higher sensitivity were obtained, which indicates that the detection system based on the digital signal compensation technology is effective in practical exploration. Via long-distance detection experiments on cars, it was confirmed that the sounding depth of the portable multi-frequency FEM in practical work indeed decreases with a decrease in the operating frequency. Full article
(This article belongs to the Section Vehicular Sensing)
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<p>Principle of probing geologic bodies.</p>
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<p>The working principle of analog signal compensation for GEM-2 device.</p>
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<p>Design of simulated GEM-2 device.</p>
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<p>The working principle of the device.</p>
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<p>Portable FEM prototype based on digital signal compensation. (<b>a</b>) The composition of the prototype; (<b>b</b>) signal sending and receiving of the prototype.</p>
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<p>Secondary-field-induced electromotive force of 10 Ω·m geological body at different depths.</p>
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<p>Abnormalities caused by underground parking under simulated signal compensation conditions. (<b>a</b>) EMF of receiving coil; (<b>b</b>) EMF of reference coil; and (<b>c</b>) apparent conductivity.</p>
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<p>Apparent conductivity curve of underground garage survey.</p>
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<p>Normalized secondary field curve of underground garage survey. (<b>a</b>) The real component of normalized secondary field; (<b>b</b>) the virtual component of normalized secondary field.</p>
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<p>The position between car and survey line.</p>
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<p>Apparent resistivity and normalized secondary field curves of car survey (the center of the car at station 16). (<b>a</b>) Apparent resistivity; (<b>b</b>) the real component of normalized secondary field; and (<b>c</b>) the virtual component of normalized secondary field.</p>
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