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12 pages, 4047 KiB  
Article
Multilayer Core-Sheath Structured Nickel Wire/Copper Oxide/Cobalt Oxide Composite for Highly Sensitive Non-Enzymatic Glucose Sensor
by Yuxin Wu, Zhengwei Zhu, Xinjuan Liu and Yuhua Xue
Nanomaterials 2025, 15(6), 411; https://doi.org/10.3390/nano15060411 - 7 Mar 2025
Viewed by 152
Abstract
The development of micro glucose sensors plays a vital role in the management and monitoring of diabetes, facilitating real-time tracking of blood glucose levels. In this paper, we developed a three-layer core-sheath microwire (NW@CuO@Co3O4) with nickel wire as the [...] Read more.
The development of micro glucose sensors plays a vital role in the management and monitoring of diabetes, facilitating real-time tracking of blood glucose levels. In this paper, we developed a three-layer core-sheath microwire (NW@CuO@Co3O4) with nickel wire as the core and copper oxide and cobalt oxide nanowires as the sheath. The unique core-sheath structure of microwire enables it to have both good conductivity and excellent electrochemical catalytic activity when used as an electrode for glucose detecting. The non-enzymatic glucose sensor base on a NW@CuO@Co3O4 core-sheath wire exhibits a high sensitivity of 4053.1 μA mM−1 cm−2, a low detection limit 0.89 μM, and a short response time of less than 2 s. Full article
Show Figures

Figure 1

Figure 1
<p>(<b>a</b>) XRD spectrum of the NW@CuO@Co<sub>3</sub>O<sub>4</sub> electrode. XPS spectra of the NW@CuO@Co<sub>3</sub>O<sub>4</sub> electrode, (<b>b</b>) full spectrum, (<b>c</b>) Cu 2p spectrum, (<b>d</b>) Ni 2p spectrum, (<b>e</b>) Co 2p spectrum, and (<b>f</b>) O 1s spectrum.</p>
Full article ">Figure 2
<p>(<b>a</b>) SEM image of pure nickel wire. (<b>b</b>,<b>c</b>) SEM image of nickel wire after “alloy/de-alloy” treatment. (<b>d</b>–<b>f</b>) SEM image of NW@CuO@Co<sub>3</sub>O<sub>4</sub> electrode.</p>
Full article ">Figure 3
<p>(<b>a</b>) TEM image of CuO–Co<sub>3</sub>O<sub>4</sub> composite. (<b>b</b>) TEM image of Co<sub>3</sub>O<sub>4</sub> nanowires, (<b>c</b>,<b>d</b>) TEM images of CuO nanoparticles.</p>
Full article ">Figure 4
<p>(<b>a</b>) Cyclic voltammograms of pure nickel wire electrode and NW@CuO@Co<sub>3</sub>O<sub>4</sub> electrode at 50 mV s<sup>−1</sup> in 0.1 M NaOH solution with and without 1mM glucose added. (<b>b</b>) Cyclic voltammograms of NW@CuO@Co<sub>3</sub>O<sub>4</sub> electrode at 50 mV s<sup>−1</sup> in different 0.1M NaOH solutions with different concentrations of glucose added. (<b>c</b>) Cyclic voltammograms of NW@CuO@Co<sub>3</sub>O<sub>4</sub> electrode in 0.1 M NaOH at different scan rates (25~125 mv s<sup>−1</sup>). (<b>d</b>) Linear fitting diagram of cyclic voltammograms of oxidation peak current and reduction peak current at different scan rates and the half of the scan rate.</p>
Full article ">Figure 5
<p>Glucose detection performance of NW@CuO@Co<sub>3</sub>O<sub>4</sub> electrode (<b>a</b>) Current versus time curves of adding 0.5 mM glucose six times at 50 s intervals to 0.1 M NaOH solution at different voltages (0.5~0.65 V). (<b>b</b>) Selectivity curve after adding 1 mM glucose, ascorbic acid (AA), dopamine hydrochloride (UA), uric acid (DA), and glucose to 0.1 M NaOH solution in sequence. (<b>c</b>) Amperometric response curve of adding different concentrations of glucose in 0.1 M NaOH solution in sequence at 0.55 V. (<b>d</b>) Linear fitting diagram of current and glucose concentration in alkaline solution.</p>
Full article ">Figure 6
<p>(<b>a</b>) Stability of NW@CuO@Co<sub>3</sub>O<sub>4</sub> glucose sensors in 0.1 mM glucose solution. (<b>b</b>) EIS curves of NW and NW@CuO@Co<sub>3</sub>O<sub>4</sub>. (<b>c</b>) Current responses of five NW@CuO@Co<sub>3</sub>O<sub>4</sub> electrodes in 0.1 M NaOH with 2 mM glucose at 0.55 V.</p>
Full article ">
21 pages, 4019 KiB  
Review
Effect of Temperature on Magnetoimpedance Effect and Magnetic Properties of Fe- and Co-Rich Glass-Coated Microwires
by Paula Corte-Leon, Ivan Skorvanek, František Andrejka, Milos Jakubcin, Juan Maria Blanco, Valentina Zhukova and Arcady Zhukov
Materials 2025, 18(2), 287; https://doi.org/10.3390/ma18020287 - 10 Jan 2025
Viewed by 559
Abstract
We provide new experimental studies of the temperature dependence of the giant magnetoimpedance (GMI) effect and hysteresis loops of Fe-rich and Co-rich amorphous microwires with rather different room temperature magnetic properties and GMI effect features. We observed a remarkable modification of hysteresis loops [...] Read more.
We provide new experimental studies of the temperature dependence of the giant magnetoimpedance (GMI) effect and hysteresis loops of Fe-rich and Co-rich amorphous microwires with rather different room temperature magnetic properties and GMI effect features. We observed a remarkable modification of hysteresis loops and magnetic field dependence of the GMI ratio upon heating in both of the studied samples. We observed a noticeable improvement in the GMI ratio and a change in hysteresis loops from rectangular to inclined upon heating in Fe-rich microwire. However, the opposite trend was observed in Co-rich microwire, in which, upon heating, the shape of the hysteresis loop changed from linear to rectangular. Generally, the evolution of the shape of the hysteresis loops during heating correlates with the modification of the dependencies of the GMI ratio ΔZ/Z on the magnetic field. For Co-rich microwire, the double-peak magnetic field dependence changed to single-peak, while for Fe-rich microwire, the opposite tendency was observed. The origin of the observed temperature dependences of the hysteresis loop and the GMI effect is discussed, considering internal stresses’ relaxation during heating, the temperature dependencies of the magnetostriction coefficient, and internal stresses, as well as the Hopkinson effect. Full article
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Graphical abstract

Graphical abstract
Full article ">Figure 1
<p>Sketch of the Taylor–Ulitovsky preparation process.</p>
Full article ">Figure 2
<p>Hysteresis loops of as-prepared Fe<sub>75</sub>B<sub>9</sub>Si<sub>12</sub>C<sub>4</sub> (<b>a</b>) and Co<sub>69.2</sub>Fe<sub>3.6</sub>Ni<sub>1</sub>B<sub>12.5</sub>Si<sub>11</sub>Mo<sub>1.5</sub>C<sub>1.2</sub> (<b>b</b>) samples at room temperature.</p>
Full article ">Figure 3
<p>Hysteresis loops of Fe<sub>75</sub>B<sub>9</sub>Si<sub>12</sub>C<sub>4</sub> sample, measured at different <span class="html-italic">T</span> (<b>a</b>–<b>e,k</b>), and low field hysteresis loops of the same sample (<b>f</b>–<b>j</b>) and <span class="html-italic">H<sub>k</sub></span>(<span class="html-italic">T</span>) dependencies (<b>l</b>) evaluated from hysteresis loops. Figure (<b>l</b>) is adapted from [<a href="#B36-materials-18-00287" class="html-bibr">36</a>,<a href="#B43-materials-18-00287" class="html-bibr">43</a>]. Open Access Copyright © 2023 AIP and IARIA.</p>
Full article ">Figure 3 Cont.
<p>Hysteresis loops of Fe<sub>75</sub>B<sub>9</sub>Si<sub>12</sub>C<sub>4</sub> sample, measured at different <span class="html-italic">T</span> (<b>a</b>–<b>e,k</b>), and low field hysteresis loops of the same sample (<b>f</b>–<b>j</b>) and <span class="html-italic">H<sub>k</sub></span>(<span class="html-italic">T</span>) dependencies (<b>l</b>) evaluated from hysteresis loops. Figure (<b>l</b>) is adapted from [<a href="#B36-materials-18-00287" class="html-bibr">36</a>,<a href="#B43-materials-18-00287" class="html-bibr">43</a>]. Open Access Copyright © 2023 AIP and IARIA.</p>
Full article ">Figure 4
<p>Hysteresis loops of Fe<sub>75</sub>B<sub>9</sub>Si<sub>12</sub>C<sub>4</sub> sample measured at room <span class="html-italic">T</span> (<b>a</b>), at <span class="html-italic">T</span> = 100 °C (<b>b</b>), and at <span class="html-italic">T</span> = 150 °C (<b>c</b>).</p>
Full article ">Figure 5
<p>Hysteresis loops of Fe<sub>75</sub>B<sub>9</sub>Si<sub>12</sub>C<sub>4</sub> sample measured before (<b>a</b>) and after heating up to 300 °C (<b>b</b>). Adapted from [<a href="#B36-materials-18-00287" class="html-bibr">36</a>,<a href="#B43-materials-18-00287" class="html-bibr">43</a>]. Open Access Copyright © 2023 AIP and IARIA.</p>
Full article ">Figure 6
<p>Δ<span class="html-italic">Z</span>/<span class="html-italic">Z</span>(<span class="html-italic">H</span>) dependencies of Fe<sub>75</sub>B<sub>9</sub>Si<sub>12</sub>C<sub>4</sub> microwire measured at 10 (<b>a</b>), 50 MHz (<b>b</b>), and 1 and 100 MHz (<b>c</b>) at various temperatures.</p>
Full article ">Figure 7
<p>Δ<span class="html-italic">Z</span>/<span class="html-italic">Z<sub>max</sub></span> (<span class="html-italic">T</span>) dependencies evaluated for 10, 50, and 110 MHz in Fe<sub>75</sub>B<sub>9</sub>Si<sub>12</sub>C<sub>4</sub> sample.</p>
Full article ">Figure 8
<p>Δ<span class="html-italic">Z</span>/<span class="html-italic">Z</span>(<span class="html-italic">H</span>) dependencies measured at f= 50 MHz (<b>a</b>) and 110 MHz (<b>b</b>) at room temperature before and after heating at <span class="html-italic">T</span> = 300 °C in Fe<sub>75</sub>B<sub>9</sub>Si<sub>12</sub>C<sub>4</sub> sample.</p>
Full article ">Figure 9
<p>Effect of heating on hysteresis loops of Co<sub>69.2</sub>Fe<sub>3.6</sub>Ni<sub>1</sub>B<sub>12.5</sub>Si<sub>11</sub>Mo<sub>1.5</sub>C<sub>1.2</sub> microwires.</p>
Full article ">Figure 10
<p>Δ<span class="html-italic">Z</span>/<span class="html-italic">Z</span>(<span class="html-italic">H</span>) dependencies measured at <span class="html-italic">f</span> = 110 MHz at room temperature (<b>a</b>), 100 °C (<b>b</b>), 150 °C (<b>c</b>), 200 °C (<b>d</b>), and 300 °C (<b>e</b>) and modification of the Δ<span class="html-italic">Z</span>/<span class="html-italic">Z</span>(<span class="html-italic">H</span>) dependencies measured at 110 MHz upon heating of Co<sub>69.2</sub>Fe<sub>3.6</sub>Ni<sub>1</sub>B<sub>12.5</sub>Si<sub>11</sub>Mo<sub>1.5</sub>C<sub>1.2</sub> microwires (<b>f</b>).</p>
Full article ">Figure 11
<p>Δ<span class="html-italic">Z</span>/<span class="html-italic">Z</span>(<span class="html-italic">H</span>) dependencies of Co<sub>69.2</sub>Fe<sub>3.6</sub>Ni<sub>1</sub>B<sub>12.5</sub>Si<sub>11</sub>Mo<sub>1.5</sub>C<sub>1.2</sub> microwires measured at room temperature (<b>a</b>), at 150 °C (<b>b</b>), and at T= 200 °C (<b>c</b>).</p>
Full article ">Figure 12
<p>Δ<span class="html-italic">Z</span>/<span class="html-italic">Z</span>(<span class="html-italic">H</span>) dependencies of Co<sub>69.2</sub>Fe<sub>3.6</sub>Ni<sub>1</sub>B<sub>12.5</sub>Si<sub>11</sub>Mo<sub>1.5</sub>C<sub>1.2</sub> sample measured at f = 110 MHz at <span class="html-italic">T</span> = 200 °C (<b>a</b>), <span class="html-italic">T</span> = 250 °C (<b>b</b>), and T= 300 °C (<b>c</b>).</p>
Full article ">Figure 13
<p>Δ<span class="html-italic">Z</span>/<span class="html-italic">Z<sub>max</sub></span>(<span class="html-italic">T</span>) (<b>a</b>) and <span class="html-italic">H<sub>m</sub></span>(<span class="html-italic">T</span>) (<b>b</b>) dependencies evaluated from Δ<span class="html-italic">Z</span>/<span class="html-italic">Z</span>(<span class="html-italic">H</span>) dependencies at 50 and 110 MHz in Co<sub>69.2</sub>Fe<sub>3.6</sub>Ni<sub>1</sub>B<sub>12.5</sub>Si<sub>11</sub>Mo<sub>1.5</sub>C<sub>1.2</sub> sample.</p>
Full article ">Figure 14
<p>Δ<span class="html-italic">Z</span>/<span class="html-italic">Z</span>(<span class="html-italic">H</span>) dependencies measured at <span class="html-italic">f</span> = 10 MHz (<b>a</b>), 50 MHz (<b>b</b>), 100 MHz (<b>c</b>), and 110 MHz (<b>d</b>) in Co<sub>69.2</sub>Fe<sub>3.6</sub>Ni<sub>1</sub>B<sub>12.5</sub>Si<sub>11</sub>Mo<sub>1.5</sub>C<sub>1.2</sub> sample before and after heating to 300 °C.</p>
Full article ">Figure 15
<p>Hysteresis loops measured at room temperature of Co<sub>69.2</sub>Fe<sub>3.6</sub>Ni<sub>1</sub>B<sub>12.5</sub>Si<sub>11</sub>Mo<sub>1.5</sub>C<sub>1.2</sub> sample before (<b>a</b>) and after heating to 200 °C (<b>b</b>) and 300 °C (<b>c</b>).</p>
Full article ">Figure 16
<p><span class="html-italic">H<sub>k</sub></span>(<span class="html-italic">T</span>) dependence evaluated from hysteresis loops of Co<sub>69.2</sub>Fe<sub>3.6</sub>Ni<sub>1</sub>B<sub>12.5</sub>Si<sub>11</sub>Mo<sub>1.5</sub>C<sub>1.2</sub> sample. <span class="html-italic">H<sub>m</sub></span>(<span class="html-italic">T</span>) dependence is provided in the inset.</p>
Full article ">
15 pages, 2312 KiB  
Article
Microfluidic Integration of Magnetically Functionalized Microwires for Flow Cytometry Protein Quantification
by Liviu Clime, Catalin Pavel, Lidija Malic, Christina Nassif, Matthias Geissler, Nicoleta Lupu, Tibor-Adrian Óvári, Lucas Poncelet, Gaétan Veilleux, Elham Moslemi, Javier Alejandro Hernández-Castro, Daniel Sinnett, Diping Che and Teodor Veres
Materials 2025, 18(2), 215; https://doi.org/10.3390/ma18020215 - 7 Jan 2025
Viewed by 823
Abstract
A novel approach to protein quantification utilizing a microfluidic platform activated by a magnetic assembly of functionalized magnetic beads around soft magnetic capture centers is presented. Functionalized magnetic beads, known for their high surface area and facile manipulation under external magnetic fields, are [...] Read more.
A novel approach to protein quantification utilizing a microfluidic platform activated by a magnetic assembly of functionalized magnetic beads around soft magnetic capture centers is presented. Functionalized magnetic beads, known for their high surface area and facile manipulation under external magnetic fields, are injected inside microfluidic channels and immobilized magnetically on the surface of glass-coated soft magnetic microwires placed along the symmetry axis of these channels. A fluorescent (Cy5) immunomagnetic sandwich ELISA is then performed by sequentially flowing the sample and all necessary reagents in the microfluidic channels. Direct protein quantification is performed by magnetically releasing the beads from the microwire and evaluating their fluorescence intensity with the help of a miniature (microfluidic-based) flow cytometer. Measurements of ICAM-1 protein concentration in human blood plasma samples confirm the feasibility of the approach through extensive performance benchmarking. The automation and multiplexing capabilities of the proposed platform further demonstrate its potential for protein quantification in point-of-care settings using microfluidics and miniature flow cytometry instruments. Full article
(This article belongs to the Section Advanced Nanomaterials and Nanotechnology)
Show Figures

Graphical abstract

Graphical abstract
Full article ">Figure 1
<p>(<b>a</b>) Schematic drawing of a cross-sectional view of a microfluidic channel of width <math display="inline"><semantics> <mrow> <mi>w</mi> </mrow> </semantics></math> and height <math display="inline"><semantics> <mrow> <mi>h</mi> </mrow> </semantics></math> with the magnetic wire at the center filled with a colloidal suspension of functionalized magnetic beads floating freely in the solution. (<b>b</b>) Functionalization of the wire through magnetization in the transversal direction using an external magnetic field <math display="inline"><semantics> <mrow> <mover accent="true"> <mrow> <mi>H</mi> </mrow> <mo>→</mo> </mover> </mrow> </semantics></math>. (<b>c</b>) Schematic illustration of the sandwich ELISA implemented on the magnetic beads. (<b>d</b>) Longitudinal cross-sectional drawing of a section of the microfluidic channel highlighting the positioning of the wire and the direction of the flow.</p>
Full article ">Figure 2
<p>(<b>a</b>) Schematic drawings of the microfluidic device indicating the essential features of the design: the inlets and the outlets (1), the wire installation and tensioning holes (2) and (4), the wire fixing glue cavity (3), and the self-aligning channels (5). For figure footprint optimization purposes, the drawing excludes the central part of the device. (<b>b</b>) Cross-sectional view of the magnetic microwire used in this study featuring the magnetic core of dimeter <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>d</mi> </mrow> <mrow> <mi>m</mi> </mrow> </msub> <mo>=</mo> <mn>25</mn> <mo> </mo> <mi mathvariant="sans-serif">μ</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math> covered by a glass shell of <math display="inline"><semantics> <mrow> <mn>15</mn> <mo> </mo> <mi mathvariant="sans-serif">μ</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math> thickness for a total diameter of the wire <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>d</mi> </mrow> <mrow> <mi>w</mi> </mrow> </msub> <mo>=</mo> <mn>55</mn> <mo> </mo> <mi mathvariant="sans-serif">μ</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math>. (<b>c</b>) Longitudinal vertical sectional view along one channel of the microfluidic device featuring the outlet (1) and the additional features (2–7) for installing, aligning and fixing the wire in place. (<b>d</b>) Magnetization curves for the wire on the parallel (<math display="inline"><semantics> <mrow> <mo>∥</mo> </mrow> </semantics></math>) and perpendicular (<math display="inline"><semantics> <mrow> <mo>⊥</mo> </mrow> </semantics></math>) directions for the wire and for the magnetic beads (MB).</p>
Full article ">Figure 3
<p>(<b>a</b>) Drawing of the magnetic field applicator with the microfluidic device installed in the midplane <math display="inline"><semantics> <mrow> <mi>x</mi> <mi>O</mi> <mi>y</mi> </mrow> </semantics></math> between the two permanent magnets <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>M</mi> </mrow> <mrow> <mn>1</mn> </mrow> </msub> </mrow> </semantics></math> and <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>M</mi> </mrow> <mrow> <mn>2</mn> </mrow> </msub> </mrow> </semantics></math>; (<b>b</b>) numerical magnetostatic simulation of the magnetic field between the two magnet plates. Positions of the 3 wires situated at <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>x</mi> </mrow> <mrow> <mn>1</mn> </mrow> </msub> <mo>=</mo> <mn>10</mn> <mo> </mo> <mi mathvariant="normal">m</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math>, <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>x</mi> </mrow> <mrow> <mn>2</mn> </mrow> </msub> <mo>=</mo> <mn>5</mn> <mo> </mo> <mi mathvariant="normal">m</mi> <mi mathvariant="normal">m</mi> <mo>,</mo> <mi mathvariant="normal">a</mi> <mi mathvariant="normal">n</mi> <mi mathvariant="normal">d</mi> </mrow> </semantics></math> <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>x</mi> </mrow> <mrow> <mn>3</mn> </mrow> </msub> <mo>=</mo> <mn>0</mn> <mo>.</mo> <mo> </mo> </mrow> </semantics></math> <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>x</mi> </mrow> <mrow> <mi>e</mi> </mrow> </msub> </mrow> </semantics></math> corresponds to the edge of the microfluidic chip on the <math display="inline"><semantics> <mrow> <mi>O</mi> <mi>x</mi> </mrow> </semantics></math> direction. Maximum gradient value is <math display="inline"><semantics> <mrow> <mn>4.8</mn> <mo>×</mo> <msup> <mrow> <mn>10</mn> </mrow> <mrow> <mn>6</mn> </mrow> </msup> <mo> </mo> <mi mathvariant="normal">A</mi> <mo>/</mo> <msup> <mrow> <mi mathvariant="normal">m</mi> </mrow> <mrow> <mn>2</mn> </mrow> </msup> </mrow> </semantics></math> and corresponds to the edge wire situated at <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>x</mi> </mrow> <mrow> <mn>1</mn> </mrow> </msub> </mrow> </semantics></math>. Magnetic field at the center of the coordinate system <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>H</mi> </mrow> <mrow> <mn>0</mn> </mrow> </msub> <mo>=</mo> <mn>106</mn> <mo> </mo> <mi mathvariant="normal">k</mi> <mi mathvariant="normal">A</mi> <mo>/</mo> <mi mathvariant="normal">m</mi> </mrow> </semantics></math>.</p>
Full article ">Figure 4
<p>(<b>a</b>) Schematics of the microfluidic setup implementing the ICAM-1 immunoassay protocol; (<b>b</b>) schematic representation of the profile of the flow across the five channels of the microfluidic device.</p>
Full article ">Figure 5
<p>Photograph of the AZ-150 Personal and Portable Cytometer produced by Azure Biosystems Inc. (<b>a</b>) and screen captures of the FSC-SSC diagrams used for gating and fluorescence quantification of the beads (<b>b</b>–<b>d</b>).</p>
Full article ">Figure 6
<p>Quantification human blood plasma sample on channel #5 with negative control on channel #1 and three other recombinant solutions with known concentration values on channels #2, #3, and #4.</p>
Full article ">
16 pages, 4367 KiB  
Article
Laser Welding of Micro-Wire Stent Electrode as a Minimally Invasive Endovascular Neural Interface
by Bo Wen, Liang Shen and Xiaoyang Kang
Micromachines 2025, 16(1), 21; https://doi.org/10.3390/mi16010021 - 26 Dec 2024
Viewed by 756
Abstract
Minimally invasive endovascular stent electrodes are an emerging technology in neural engineering, designed to minimize the damage to neural tissue. However, conventional stent electrodes often rely on resistive welding and are relatively bulky, restricting their use primarily to large animals or thick blood [...] Read more.
Minimally invasive endovascular stent electrodes are an emerging technology in neural engineering, designed to minimize the damage to neural tissue. However, conventional stent electrodes often rely on resistive welding and are relatively bulky, restricting their use primarily to large animals or thick blood vessels. In this study, the feasibility is explored of fabricating a laser welding stent electrode as small as 300 μm. A high-precision laser welding technique was developed to join micro-wire electrodes without compromising structural integrity or performance. To ensure consistent results, a novel micro-wire welding with platinum pad method was introduced during the welding process. The fabricated electrodes were integrated with stent structures and subjected to detailed electrochemical performance testing to evaluate their potential as neural interface components. The laser-welded endovascular stent electrodes exhibited excellent electrochemical properties, including low impedance and stable charge transfer capabilities. At the same time, in this study, a simulation is conducted of the electrode distribution and arrangement on the stent structure, optimizing the utilization of the available surface area for enhanced functionality. These results demonstrate the potential of the fabricated electrodes for high-performance neural interfacing in endovascular applications. The approach provided a promising solution for advancing endovascular neural engineering technologies, particularly in applications requiring compact electrode designs. Full article
(This article belongs to the Section B:Biology and Biomedicine)
Show Figures

Figure 1

Figure 1
<p>The simulation of the relative position design for the micro-wire stent electrode employed three different models to evaluate electrode configurations. (<b>A</b>,<b>B</b>): the blue “×” and disks represent the positions of the working electrodes. In models A and B, the grounding electrode is configured as a large rectangular pad measuring 7 <math display="inline"><semantics> <mrow> <mi mathvariant="normal">m</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math> × 2 <math display="inline"><semantics> <mrow> <mi mathvariant="normal">m</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math> × 30 <math display="inline"><semantics> <mrow> <mi mathvariant="normal">m</mi> <mi mathvariant="normal">m</mi> <mo>;</mo> </mrow> </semantics></math> (<b>C</b>,<b>D</b>): the 3D surface streamline potential maps display the potential distribution after electrical stimulation in each of the three models; (<b>E</b>,<b>F</b>): the potential distribution maps correspond to the working electrode plane, which is defined as a circular area with a radius of 10 mm.</p>
Full article ">Figure 2
<p>(<b>A</b>–<b>C</b>) illustrate the three-dimensional heat-affected zone and melt pool dimensions during laser welding on a platinum disk, whereas (<b>D</b>–<b>F</b>) present two-dimensional cross-sectional views of the melt pool. It is observed that with an increasing number of laser cycles, the melt pool size on the platinum disk progressively expands.</p>
Full article ">Figure 3
<p>The main steps (<b>A</b>–<b>D</b>) of the fabrication of the laser welding endovascular stent electrode.</p>
Full article ">Figure 4
<p>The images of the fabricated laser welding endovascular stent electrode. (<b>A</b>) present the microscopic image of the bonding effect of the laser welding electrode with the stent. (<b>B</b>) present the normal image of the bonding effect.</p>
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<p>(<b>A</b>,<b>B</b>) Averaged EIS at different processing parameters (n = 6). It indicates the optimal choice for laser ablating the micro-wire. The impedance decreases correspondingly with the decrease in laser energy and the increase in processing times. At the same time, increasing the laser cutting marking speed was equivalent to increasing the laser energy.</p>
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<p>The laser ablation image of the micro-wire under the optimal parameter.</p>
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<p>The laser welding image of the micro-wire with the platinum disk under the optimal parameter.</p>
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<p>Averaged EIS of the laser welding endovascular stent electrodes at different current intensity (n = 6) (<b>A</b>) present the impedance of the electrode after the laser welding. (<b>B</b>) present the phase angle of the electrode after laser welding.</p>
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<p>(<b>A</b>) Averaged CV curve of the electrode. (<b>B</b>) Averaged voltage transient curve of electrodes (n = 6).</p>
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9 pages, 1415 KiB  
Article
The Interplay of Core Diameter and Diameter Ratio on the Magnetic Properties of Bistable Glass-Coated Microwires
by Valeria Kolesnikova, Irina Baraban, Alexander Omelyanchik, Larissa Panina and Valeria Rodionova
Micromachines 2024, 15(11), 1284; https://doi.org/10.3390/mi15111284 - 22 Oct 2024
Viewed by 855
Abstract
Glass-coated microwires exhibiting magnetic bistability have garnered significant attention as promising wireless sensing elements, primarily due to their rapid magnetization switching capabilities. These microwires consist of a metallic core with diameter d, encased in a glass coating, with a total diameter D [...] Read more.
Glass-coated microwires exhibiting magnetic bistability have garnered significant attention as promising wireless sensing elements, primarily due to their rapid magnetization switching capabilities. These microwires consist of a metallic core with diameter d, encased in a glass coating, with a total diameter D. In this study, we investigated how the dimensions of both components and their ratio (d/D) influence the magnetization reversal behavior of Fe-based microwires. While previous studies have focused on either d or d/D individually, our research uniquely considered the combined effect of both parameters to provide a comprehensive understanding of their impact on magnetic properties. The metallic core diameter d varied from 10 to 19 µm and the d/D ratio was in the range of 0.48–0.68. To assess the magnetic properties of these microwires, including the shape of the hysteresis loop, coercivity, remanent magnetization, and the critical length of bistability, we employed vibrating sample magnetometry in conjunction with FORC-analysis. Additionally, to determine the critical length of bistability, magnetic measurements were conducted on microwires with various lengths, ranging from 1.5 cm down to 0.05 cm. Our findings reveal that coercivity is primarily dependent on the d/D parameter. These observations are effectively explained through an analysis that considers the competition between magnetostatic and magnetoelastic anisotropy energies. This comprehensive study paves the way for the tailored design of glass-coated microwires for diverse wireless sensing applications. Full article
(This article belongs to the Section A:Physics)
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<p>Hysteresis loops for different lengths of amorphous glass-coated microwires with Fe<sub>77.5</sub>Si<sub>7.5</sub>B<sub>15</sub> composition of the metallic core with transverse parameters: (<b>a</b>) <span class="html-italic">d</span>/<span class="html-italic">D</span> = 19/29 (µm) = 0.66, (<b>b</b>) <span class="html-italic">d</span>/<span class="html-italic">D</span> = 13/19 (µm) = 0.68, (<b>c</b>) <span class="html-italic">d</span>/<span class="html-italic">D</span> = 13/26 (µm) = 0.50 (<span class="html-italic">H</span> is the external magnetic field, <span class="html-italic">M</span> is the magnetization as a function of <span class="html-italic">H</span>, and <span class="html-italic">M</span><sub>s</sub> is the saturation magnetization).</p>
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<p>(<b>a</b>) The hysteresis loop, (<b>b</b>) set of FORCs and SFDs, (<b>c</b>) FORC diagram and (<b>d</b>) illustration of the magnetization process and the domain structure of a single Fe<sub>77.5</sub>Si<sub>7.5</sub>B<sub>15</sub> (<span class="html-italic">d</span>/<span class="html-italic">D</span> = 13/26 µm) microwire at critical length (<span class="html-italic">H</span><sub>r</sub> is the reversal field, <span class="html-italic">H</span><sub>a</sub> is the applied field, and SFD is the switching field distribution).</p>
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<p>Hysteresis loops of amorphous glass-coated microwires of Fe<sub>77.5</sub>Si<sub>7.5</sub>B<sub>15</sub> composition with parameters <span class="html-italic">d</span>/<span class="html-italic">D</span> = 13/26 = 0.50 for different lengths (<span class="html-italic">L</span>) and a schematic representation of the corresponding micromagnetic structure.</p>
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<p>Hysteresis loops for microwires with different ratios of diameters. The length of the sample: (<b>a</b>) <span class="html-italic">L</span> = 1.5 cm, (<b>b</b>) <span class="html-italic">L</span> = 0.5 cm, (<b>c</b>) <span class="html-italic">L</span> = 0.2 cm, (<b>d</b>) <span class="html-italic">L</span> = 0.05 cm.</p>
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<p>Dependence of coercive force <span class="html-italic">H</span><sub>c</sub> (<b>a</b>) and <span class="html-italic">M</span><sub>r</sub>/<span class="html-italic">M</span><sub>s</sub> (<b>b</b>) on the wire length for different diameter ratios. The color legend is the same for (<b>a</b>,<b>b</b>).</p>
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15 pages, 3757 KiB  
Article
The Effect of Fe Content on the Shape Memory Effect of Ni-Mn-Ga-Fe Shape Memory Alloy Microwires after Ordering Heat Treatment
by Yanfen Liu, Zixuan Ma, Shuang Li, Puhan Yan, Qingnan Hou and Jianfei Sun
Metals 2024, 14(10), 1167; https://doi.org/10.3390/met14101167 - 12 Oct 2024
Viewed by 910
Abstract
The shape memory capabilities of Heusler alloy microwires with two different contents of Fe element instead of Ga element following step-by-step ordering heat treatment were explored based on the stoichiometric ratio of Ni2MnGa. The melt-drawing technique was used to create the [...] Read more.
The shape memory capabilities of Heusler alloy microwires with two different contents of Fe element instead of Ga element following step-by-step ordering heat treatment were explored based on the stoichiometric ratio of Ni2MnGa. The melt-drawing technique was used to create the polycrystalline microwires, and the two microwires had Fe atomic contents of 4.7 at.% and 5.5 at.%, respectively. The field emission scanning electron microscope was used to analyze the microwire’s surface condition as well as the microscopic tensile fracture morphology. Using an X-ray diffractometer, the microwires’ crystal structure was identified for phase analysis. Differential scanning calorimetry was used to examine the microwires’ behavior during martensitic transformation. Using a dynamic mechanical stretcher, the elongation and recovery rate of microwires’ one- and two-way shape memory behavior were examined. The findings demonstrated that the microwire phase structure, martensitic transformation behavior, and shape memory capabilities all displayed good properties after the heat treatment was ordered. Full article
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<p>(<b>a</b>) The diagram of melt drawing equipment schematic; (<b>b</b>) the diagram of step-by-step ladder ordered heat-treated schematic.</p>
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<p>SEM diagram of ordered heat-treated microwire: Microwire morphology at low magnification (<b>a</b>); Ni<sub>49.3</sub>Mn<sub>24.9</sub>Ga<sub>21.1</sub>Fe<sub>4.7</sub> microwire cross-section fracture diagram (<b>b</b>); Ni<sub>49.9</sub>Mn<sub>24.7</sub>Ga<sub>19.9</sub>Fe<sub>5.5</sub> microwire cross-section fracture diagram (<b>c</b>); free solidification circle surface microstructure (<b>d</b>); microwire flat surface grain (<b>e</b>); Ni<sub>49.3</sub>Mn<sub>24.9</sub>Ga<sub>21.1</sub>Fe<sub>4.7</sub> microwire modulation structure (<b>f</b>); Ni<sub>49.9</sub>Mn<sub>24.7</sub>Ga<sub>19.9</sub>Fe<sub>5.5</sub> microwire modulation structure (<b>g</b>).</p>
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<p>XRD diffraction patterns of microwires after ordering heat treatment: (<b>a</b>) Ni<sub>49.3</sub>Mn<sub>24.9</sub>Ga<sub>21.1</sub>Fe<sub>4.7</sub> microwire; (<b>b</b>) Ni<sub>49.9</sub>Mn<sub>24.7</sub>Ga<sub>19.9</sub>Fe<sub>5.5</sub> microwire.</p>
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<p>DSC diagram of two kinds of microwire ordering heat treatment: (<b>a</b>) Ni<sub>49.3</sub>Mn<sub>24.9</sub>Ga<sub>21.1</sub>Fe<sub>4.7</sub> microwire; (<b>b</b>) Ni<sub>49.9</sub>Mn<sub>24.7</sub>Ga<sub>19.9</sub>Fe<sub>5.5</sub> microwire.</p>
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<p>One-way curve stretching and shape recovery of ordered heat-treated microwires: (<b>a</b>) Ni<sub>49.3</sub>Mn<sub>24.9</sub>Ga<sub>21.1</sub>Fe<sub>4.7</sub> microwire; (<b>b</b>) Ni<sub>49.9</sub>Mn<sub>24.7</sub>Ga<sub>19.9</sub>Fe<sub>5.5</sub> microwire.</p>
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<p>Two-way stretching and shape recovery of ordered heat-treated microwires: Ni<sub>49.3</sub>Mn<sub>24.9</sub>Ga<sub>21.1</sub>Fe<sub>4.7</sub> microwire (<b>a</b>); Ni<sub>49.9</sub>Mn<sub>24.7</sub>Ga<sub>19.9</sub>Fe<sub>5.5</sub> microwire (<b>b</b>).</p>
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<p>Stress–temperature diagram of ordered heat-treated microwire: Ni<sub>49.3</sub>Mn<sub>24.9</sub>Ga<sub>21.1</sub>Fe<sub>4.7</sub> microwire (<b>a</b>): Ni<sub>49.9</sub>Mn<sub>24.7</sub>Ga<sub>19.9</sub>Fe<sub>5.5</sub> microwire (<b>b</b>).</p>
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15 pages, 3789 KiB  
Article
Dissimilar Resistance Welding of NiTi Microwires for High-Performance SMA Bundle Actuators
by Dominik Scholtes, Ralf-Kilian Zäh, Benedikt Faupel, Stefan Seelecke and Paul Motzki
Actuators 2024, 13(10), 400; https://doi.org/10.3390/act13100400 - 5 Oct 2024
Viewed by 953
Abstract
Shape memory alloys (SMAs) are becoming a more important factor in actuation technology. Due to their unique features, they have the potential to save weight and installation space as well as reduce energy consumption. The system integration of the generally small-diameter NiTi wires [...] Read more.
Shape memory alloys (SMAs) are becoming a more important factor in actuation technology. Due to their unique features, they have the potential to save weight and installation space as well as reduce energy consumption. The system integration of the generally small-diameter NiTi wires is an important cornerstone for the emerging technology. Crimping, a common method for the mechanical and electrical connection of SMA wires, has several drawbacks when it comes to miniaturization and high-force outputs. For high-force applications, for example, multiple SMA wires in parallel are needed to keep actuation frequencies high while scaling up the actuation force. To meet these challenges, the proposed study deals with the development of a resistance-welding process for manufacturing NiTi wire bundles. The wires are welded to a sheet metal substrate, resulting in promising functional properties and high joint strengths. The welding process benefits from low costs, easy-to-control parameters and good automation potential. A method for evaluating the resistance-welding process parameters is presented. With these parameters in place, a manufacturing process for bundled wire actuators is discussed and implemented. The welded joints are examined by peel tests, microscopy and fatigue experiments. The performance of the manufactured bundle actuators is demonstrated by comparison to a single wire with the same accumulated cross-sectional area. Full article
(This article belongs to the Section Actuator Materials)
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<p>Schematic of resistance gap welding (<b>left</b>) and resistance step welding (<b>right</b>) of NiTi wires to a sheet of metal. Displayed are the two copper-based electrodes, pressing down on the work pieces.</p>
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<p>Schematic of the distribution of the overall resistance in a resistance welding process. R2 R4 and R6 are contact resistances. R1 and R7 are the bulk resistances of the electrodes. R3 and R5 are the bulk resistances of the weld partners.</p>
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<p>Step by step pictures of the resistance welding process: (<b>1</b>) placement of sheet metal sample and NiTi wire under weld head; (<b>2</b>) weld head moved down, applying pressure on SMA wire with both electrodes; (<b>3</b>) welding current is run through workpieces via copper electrodes; (<b>4</b>) weld head is moved up and NiTi wire is joined to steel substrate.</p>
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<p>Picture of the test setup for pull-off and peel tests of the welded samples. The sample clamp is replaceable according to the type of experiment.</p>
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<p>(<b>Left</b>): thermography of a crimped 76 µm NiTi wire, where the influence of the heat sink on the temperature distribution in the activated SMA wire is visible. (<b>Right</b>): the heat-affected zone of a resistance-welded 100 µm NiTi wire to stainless steel is recognized by the tempering colors.</p>
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<p>Comparison of the joint break loads of a 100 µm NiTi wire welded to CuSn6, CuZn30 and stainless steel. The results for average value and the spread of the straight pull-off tests are displayed.</p>
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<p>Average values and spread for the joint break loads achieved by peel tests with 100 µm NiTi wire resistance step welded to 1.4571 steel sheet metal.</p>
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<p>Average values and spreads of joint break loads of peel tests with various parameters and 300 A of welding current.</p>
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<p>Microscopic analysis of resistance-welded NiTi to stainless steel. (<b>a</b>) shows microscopic pictures of samples cut radial to the wire with distances of 100 µm in between. In (<b>b</b>), an SEM picture of a different sample is displayed with the results of an EDS in (<b>c</b>).</p>
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<p>Fatigue test of three samples of 100 µm NiTi wire welded to steel sheet metal. Displayed is the maximum and minimum stroke of each cycle until failure.</p>
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<p>Pictures of a welded SMA wire bundle consisting of five 100 µm wires welded to stainless steel substrates. The upper picture shows a whole bundle with a 105 mm wire length. The bottom picture shows a detailed view of the weld spots.</p>
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<p>Comparison between bundle of four 100 µm wires and a single 200 µm diameter wire. Displayed are force, stroke and current over time of three consecutive actuation tests.</p>
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14 pages, 3209 KiB  
Article
Spiral Annealing of Magnetic Microwires
by Alexander Chizhik, Paula Corte-Leon, Valentina Zhukova, Juan Mari Blanco, Julian Gonzalez and Arcady Zhukov
Sensors 2024, 24(19), 6239; https://doi.org/10.3390/s24196239 - 26 Sep 2024
Viewed by 604
Abstract
A preprocessing technique named “spiral annealing” was applied for the first time to magnetic microwires. In this process, the sample was arranged in a flat spiral shape during annealing, and subsequent measurements were conducted on the unbent sample with the induced stress distribution [...] Read more.
A preprocessing technique named “spiral annealing” was applied for the first time to magnetic microwires. In this process, the sample was arranged in a flat spiral shape during annealing, and subsequent measurements were conducted on the unbent sample with the induced stress distribution along and transverse to the sample. The research utilized both magnetic and magneto-optical methods. The anisotropy field magnitude in both the volume and surface of the microwire was measured, and for the first time, a direct correlation between the anisotropy field and the curvature of a spirally annealed microwire was established. Additionally, a connection between the type of surface domain structure and the degree of spiral curvature was identified. The preservation of the distribution of spiral annealing-induced magnetic properties both along and across the microwire is a key effect influencing the technological application of the microwire. The range of induced curvature within which a specific helical magnetic structure can exist was also determined. This insight links the conditions of spiral annealing to the selection of microwires as active elements in magnetic sensors. Full article
(This article belongs to the Special Issue Feature Papers in Physical Sensors 2024)
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<p>Dependence of radius (<b>a</b>) and curvature (<b>b</b>) of the annealed sample on the distance X from the sample edge.</p>
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<p>The schematic picture of sample preprocessing.</p>
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<p>Fluxmetry hysteresis loops obtained at different points X along the length of the sample in long (<b>a</b>) and shorter (<b>b</b>) fields. Around a location of 5 cm (green line), saturation occurs at the maximum field value of about 1500 A/m (<b>a</b>). In this region of the spiral, the curvature is maximal. In short fields (<b>b</b>), one can see how the hysteresis loop becomes flatter in the middle part of the spiral (locations 9 cm, 13 cm).</p>
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<p>MOKE hysteresis loops obtained in different locations X along the sample length. The hysteresis loops obtained at locations of 2 cm and 15 cm have a rectangular shape, which indicates a surface Barkhausen jump. The loops obtained at locations of 3 cm, 4 cm and 7 cm have a smoother shape, which indicates the presence of a surface helical structure.</p>
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<p>Dependence of the anisotropy field values H<sub>k</sub> on X location. The black dots were extracted from magnetic measurements, while the gray dots were extracted from the MOKE experiments. During annealing the spiral formally started at point X = 3 cm and was reliably determined at point X = 4 cm. The peak of the anisotropy field value was observed at point X = 5 cm for volume and at point X = 4 cm for surface measurements.</p>
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<p>Distribution of bending stress in volume of sample (<b>a</b>) and in cross-section (<b>b</b>). Red and blue arrows show the direction of tensile and compressive stress, respectively. The stress value changes both in the sample volume and on the sample surface. In the case of spiral annealing, the absolute value of the induced stress decreases with increasing spiral radius (decreasing curvature).</p>
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<p>Dependence of the anisotropy field normalized to the curvature values H<sub>k</sub>/C on X location. The black dots were extracted from magnetic measurements, while the gray dots were extracted from the MOKE experiments. The red dashed line demonstrates that the magnitude of the surface anisotropy field is directly proportional to the geometric curvature of the sample.</p>
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<p>Experimental results obtained using the Sixtus–Tonks technique. (<b>a</b>) EMF peaks corresponding to different location of measurement X. The transformation of the peak shape is observed depending on location X. (<b>b</b>) Comparison of peaks obtained in locations X = 5 cm and X = 17 cm. (<b>c</b>) Schematic picture of the experiment. The black arrow shows the direction of DW motion. At locations of 2 cm and 17 cm (<b>a</b>), single sharp peaks are observed, corresponding to the movement of single compact domain boundaries. The width of the peaks depends on the degree of inclination of the isolated domain wall. An additional wide peak corresponds to the running of the helical wall shown in <a href="#sensors-24-06239-f009" class="html-fig">Figure 9</a>b.</p>
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<p>Surface domain structures observed in studied sample. (<b>a</b>) X = 2 cm, (<b>b</b>) X = 5 cm, (<b>c</b>) X = 17 cm. Black–white arrows show the direction of the magnetization in the domains. (<b>a</b>,<b>c</b>) show images of single surface domain walls with different inclinations from the transverse direction. (<b>b</b>) shows a combination of a single elliptical domain wall and a helical domain wall.</p>
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12 pages, 3242 KiB  
Article
Electrochemical Impedance Spectroscopy-Based Microfluidic Biosensor Using Cell-Imprinted Polymers for Bacteria Detection
by Shiva Akhtarian, Satinder Kaur Brar and Pouya Rezai
Biosensors 2024, 14(9), 445; https://doi.org/10.3390/bios14090445 - 18 Sep 2024
Cited by 1 | Viewed by 1406
Abstract
The rapid and sensitive detection of bacterial contaminants using low-cost and portable point-of-need (PoN) biosensors has gained significant interest in water quality monitoring. Cell-imprinted polymers (CIPs) are emerging as effective and inexpensive materials for bacterial detection as they provide specific binding sites designed [...] Read more.
The rapid and sensitive detection of bacterial contaminants using low-cost and portable point-of-need (PoN) biosensors has gained significant interest in water quality monitoring. Cell-imprinted polymers (CIPs) are emerging as effective and inexpensive materials for bacterial detection as they provide specific binding sites designed to capture whole bacterial cells, especially when integrated into PoN microfluidic devices. However, improving the sensitivity and detection limits of these sensors remains challenging. In this study, we integrated CIP-functionalized stainless steel microwires (CIP-MWs) into a microfluidic device for the impedimetric detection of E. coli bacteria. The sensor featured two parallel microchannels with three-electrode configurations that allowed simultaneous control and electrochemical impedance spectroscopy (EIS) measurements. A CIP-MW and a non-imprinted polymer (NIP)-MW suspended perpendicular to the microchannels served as the working electrodes in the test and control channels, respectively. Electrochemical spectra were fitted with equivalent electrical circuits, and the charge transfer resistances of both cells were measured before and after incubation with target bacteria. The charge transfer resistance of the CIP-MWs after 30 min of incubation with bacteria was increased. By normalizing the change in charge transfer resistance and analyzing the dose–response curve for bacterial concentrations ranging from 0 to 107 CFU/mL, we determined the limits of detection and quantification as 2 × 102 CFU/mL and 1.4 × 104 CFU/mL, respectively. The sensor demonstrated a dynamic range of 102 to 107 CFU/mL, where bacterial counts were statistically distinguishable. The proposed sensor offers a sensitive, cost-effective, durable, and rapid solution for on-site identification of waterborne pathogens. Full article
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<p>Impedimetric microfluidic bacteria sensor design and fabrication. (<b>A</b>) Upper and lower PDMS layers with integrated MWs. (<b>B</b>) Final microfluidic device post-plasma bonding of PDMS layers onto a glass slide. (<b>C</b>) Schematic of the sensor design illustrating flow directions and concurrent test and control measurement microchannels with CIP-MW and NIP-MW WEs, respectively. For REs and CEs, Ag-MWs and SS-MWs were used, respectively.</p>
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<p>Experimental setup used to test the impedimetric microfluidic bacteria sensor.</p>
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<p>Electrochemical impedance spectroscopy (EIS) measurements and equivalent electrical circuits of the microfluidic sensor with CIP-MWs as the working electrode (WE) in the presence of K<sub>3</sub>[Fe(CN)<sub>6</sub>]/K<sub>4</sub>[Fe(CN)<sub>6</sub>] as the redox probe. (<b>A</b>) Standard Randles circuit diagram fit. (<b>B</b>) Modified Randles circuit diagram fit. Insets show the goodness of fit values. The blue lines represent the experimental data, while the red lines correspond to the fitted curves from the circuit models.</p>
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<p>Electrochemical impedance spectroscopy (EIS) curves of microfluidic devices in 0.1 M KCl containing 5 mM K<sub>3</sub>[Fe(CN)<sub>6</sub>] with NIP-MWs and CIP-MWs serving as working electrodes. Minus and plus signs in the legend denote measurements obtained pre-and post-bacteria incubation, respectively. The inset shows an enlarged view of the NIP-MW (− and +) and CIP-MW data.</p>
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<p>Charge transfer resistance (R<sub>CT</sub>) values for microfluidic devices in 0.1 M KCl containing 5 mM K<sub>3</sub>[Fe(CN)<sub>6</sub>] with NIP-MWs and CIP-MWs serving as working electrodes. (<b>A</b>) R<sub>CT</sub> values obtained before normalization and (<b>B</b>) normalized R<sub>CT</sub> change values. The minus and plus signs in the x axis indicate pre-and post-bacteria incubation measurements, respectively. The error bars are standard deviations (SD). *: <span class="html-italic">p</span>-value &lt; 0.05; ***: <span class="html-italic">p</span>-value &lt; 0.001.</p>
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<p>EIS-based microfluidic bacteria sensor characterization. (<b>A</b>) Normalized post-incubation charge transfer resistance shift of the microfluidic sensor with CIP-MWs and parallel control experiments utilizing NIP-MWs, when exposed to different bacteria counts. (<b>B</b>) The dose–response ΔR/R<sub>CT,1</sub> curve established for the CIP-MW-based sensor. Error bars are standard deviations (SD). ns: non-significant; *: <span class="html-italic">p</span>-value &lt; 0.05; **: <span class="html-italic">p</span>-value &lt; 0.01; ***: <span class="html-italic">p</span>-value &lt; 0.001.</p>
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9 pages, 861 KiB  
Communication
Miniaturized Iridium Oxide Microwire pH Sensor for Biofluid Sensing
by Khengdauliu Chawang, Sen Bing, Ki Yong Kwon and J.-C. Chiao
Chemosensors 2024, 12(8), 168; https://doi.org/10.3390/chemosensors12080168 - 22 Aug 2024
Viewed by 1334
Abstract
pH regulation in human biofluids is a crucial step for disease diagnosis and health monitoring. Traditional pH sensors are limited by their bulky size in wearable systems, and fragile glass tips require frequent calibration, thus limiting their use in continuous monitoring. Flexible sensors, [...] Read more.
pH regulation in human biofluids is a crucial step for disease diagnosis and health monitoring. Traditional pH sensors are limited by their bulky size in wearable systems, and fragile glass tips require frequent calibration, thus limiting their use in continuous monitoring. Flexible sensors, particularly those utilizing microwires and thread-based substrates, present advantages for small sample analysis, including natural breathability and suitability for bandage or textile integration. This study examines iridium oxide and silver–silver chloride coated on thin gold wires, fabricated using sol–gel and dip-coating processes known for their simplicity. The flexible microwires demonstrated promising pH performance from a study of their pH characteristics, sensitivity, hysteresis, and potential drift. Electrodes tested in microwells allowed for small sample volumes and localized pH measurement in a controlled environment. Additional integration into fabrics for sweat sensing in wearables highlighted their potential for continuous, real-time health monitoring applications. Full article
(This article belongs to the Collection pH Sensors, Biosensors and Systems)
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<p>(<b>a</b>) Iridium oxide (IrO<sub>x</sub>) film coated on gold microwire. (<b>b</b>) A SEM image showing the 25 µm coated microwire.</p>
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<p>(<b>a</b>) A SEM image shows successful IrO<sub>x</sub> growth. (<b>b</b>) EDS peaks indicate the elemental composition.</p>
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<p>(<b>a</b>) Open-circuit potential (OCP) response of IrO<sub>x</sub> microwire vs. a commercial Ag/AgCl electrode. The dotted lines indicate hysteresis (dV) at the identical pH level. (<b>b</b>) The sensitivity plot with hysteresis (dV) and corresponding pH variation (dpH) at three pH levels.</p>
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<p>(<b>a</b>) The OCP and hysteresis (dV) of an IrO<sub>x</sub> microwire vs. a Ag/AgCl microwire. (<b>b</b>) The sensitivity plot with hysteresis (dV) and corresponding pH variation (dpH) at three pH levels.</p>
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<p>Sensitivities determined from cyclic voltammetry (CV) peak potentials and pH relationship for two different electrode-pair configurations: (<b>a</b>) an IrO<sub>x</sub> microwire vs. a commercial Ag/AgCl electrode. (<b>b</b>) IrO<sub>x</sub> vs. Ag/AgCl microwires.</p>
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<p>The test setup for the drift study among the two different electrode configurations includes the following: (<b>a</b>) an IrO<sub>x</sub> microwire vs. a commercial Ag/AgCl electrode in a beaker with 50 mL of solution; (<b>b</b>) IrO<sub>x</sub> vs. Ag/AgCl microwires in a microwell filled with 0.2 mL of solution. The potential drift (V′) analysis using the voltage reset technique for (<b>a</b>,<b>b</b>) electrode configurations is shown in (<b>c</b>,<b>d</b>), respectively. The yellow bar indicates the reset period of 2 min. The shaded areas of blue and red indicate the maximum drifting ranges.</p>
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<p>(<b>a</b>) OCP step response and (<b>b</b>) sensitivity of an IrO<sub>x</sub> vs. Ag/AgCl microwire pair tested in microwells filled with 0.2 mL artificial sweat adjusted to pH 4–9.</p>
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<p>(<b>a</b>) Three IrO<sub>x</sub> vs. Ag/AgCl microwire pairs weaved into the meshed fabric pad for wearable pH-sensing applications. The detailed drawing shows the application of the artificial sweat solution on the fabric area containing the microwires. (<b>b</b>) The sensitivity from the three pairs tested at pH 4, 6, and 9.</p>
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23 pages, 7345 KiB  
Review
Review of Underwater In Situ Voltammetry Analyzers for Trace Metals
by Jian Zhang, Shijun Wu, Ziying Wu, Feng Zhang, Bo Jin and Canjun Yang
Chemosensors 2024, 12(8), 158; https://doi.org/10.3390/chemosensors12080158 - 8 Aug 2024
Viewed by 1739
Abstract
This review is a comprehensive overview of recent advancements in underwater in situ heavy metal voltammetric analyzers (UIHVAs). It explores various types of in situ voltammetric analyzers, including the voltammetric in situ profiling system, submersible integrated multi-channel trace metal sensing probes, vibrating gold [...] Read more.
This review is a comprehensive overview of recent advancements in underwater in situ heavy metal voltammetric analyzers (UIHVAs). It explores various types of in situ voltammetric analyzers, including the voltammetric in situ profiling system, submersible integrated multi-channel trace metal sensing probes, vibrating gold microwire electrode voltammetric analyzers, and electrochemical analyzers designed for on-site flow measurements. It also covers electrochemical sensors based on flexible liquid crystal polymers, deep-sea mercury sensors, and other in situ electrochemical analyzers. This review systematically examines the research and development progress of microelectrode arrays, screen-printed, carbon, bismuth, antimony, and lab-on-a-chip electrodes. The final section looks at key trends in the research and development of voltammetric analyzers, highlighting the exploration of novel working electrodes, the integration of smart monitoring and data analysis technologies, and the promotion of interdisciplinary collaboration and innovation. From a global perspective, in situ heavy metal voltammetric analysis technology has demonstrated significant applicability in various fields, such as environmental monitoring, marine science, and biogeochemistry. This technology holds considerable potential for further development. However, extensive research and continuous improvement are required to improve detection performance. We are convinced that with continued technological advances and dedicated research efforts, these challenges can be overcome and will pave the way for the widespread application of UIHVAs. Full article
(This article belongs to the Special Issue Advances in Electrochemical Sensing and Analysis)
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<p>Instruments that have been developed include VIP/VGME/PG004. Advancements in electrode technology are of paramount importance for enhancing detection accuracy and efficiency. The main types of electrodes currently include microelectrode arrays, screen-printed, carbon, bismuth, antimony, and lab-on-a-chip electrodes.</p>
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<p>Picture of the (<b>A</b>) in-house flowthrough plexiglass cell with the mini-electrodes (1, 2, and 3) and the shielded Plexiglas holder (4) enabling incorporation of the flowthrough cell into the bottom of the VIP electronic housing; (<b>B</b>) mini-reference electrode (1), the working microelectrode (2), and the mini-counter electrode (3); and (<b>C</b>) the VIP system made up of the peristaltic pump (1), the chirurgical bag containing the nioxime and buffer solutions (2), the voltammetric probe with the in-house flowthrough plexiglass cell at the bottom (3), and the chirurgical bag to collect the waste (4) [<a href="#B51-chemosensors-12-00158" class="html-bibr">51</a>].</p>
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<p>Photographs of the instrumentation. (<b>A</b>) The electronics of the instrument. (<b>B</b>) Instrument and sensor on the buoy just before deployment. (<b>C</b>) The sensor’s protective housing. (<b>D</b>) The electrodes and the vibrator [<a href="#B56-chemosensors-12-00158" class="html-bibr">56</a>]. Copyright 2012 Elsevier.</p>
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<p>The PG004. (<b>A</b>) 1: GPS, 2: touchscreen, 3: panel with an optional keyboard, keys, and command buttons, 4: flow module, and 5: solar boards. The internal view of the PG004. (<b>B</b>) 1: 12 V batteries, 2: actuator of the flow system, 3: galvanostat board, 4: potentiostat board, 5: thermostatted control, 6: fan, 7: USB hub, 8: CPU, and 9: microcontrolled board to control the batteries. The Wi-Fi and Bluetooth board is inserted in the CPU. Flow module, with 1: EFC, 2: SVs, 3: solutions compartment, and 4: mPs [<a href="#B58-chemosensors-12-00158" class="html-bibr">58</a>]. Copyright 2015 Elsevier.</p>
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<p>(<b>A</b>) Thin film process flow steps for the manufacturing of the on-chip interconnected Ir-based microdisk arrays; (<b>B</b>) scheme of a chip incorporating an interconnected Ir microdisk array and an Ir microcounter electrode [<a href="#B50-chemosensors-12-00158" class="html-bibr">50</a>]. Copyright 2021 Elsevier.</p>
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<p>Common geometries in SPE: (<b>a</b>) micro-disc [<a href="#B75-chemosensors-12-00158" class="html-bibr">75</a>], (<b>b</b>) micro-band [<a href="#B80-chemosensors-12-00158" class="html-bibr">80</a>], (<b>c</b>) micro-array [<a href="#B81-chemosensors-12-00158" class="html-bibr">81</a>], (<b>d</b>) dual SPE in perpendicular [<a href="#B73-chemosensors-12-00158" class="html-bibr">73</a>] (<b>d-i</b>) and parallel (<b>d-ii</b>) and (<b>e</b>) double-sided SPE [<a href="#B74-chemosensors-12-00158" class="html-bibr">74</a>]. Copyright 2021 Elsevier.</p>
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<p>(<b>a</b>) SEM image of the self-assembled carbon sphere electrodes. (<b>b</b>) The scheme of the first layer (<b>left</b>) and ordered structures (<b>right</b>) of the hexagonal close-packed structures model. (<b>c</b>) The process of the electrochemical detection of trace Pb(II) in an aqueous solution using SWASV [<a href="#B89-chemosensors-12-00158" class="html-bibr">89</a>]. Copyright 2016 Elsevier.</p>
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<p>Simultaneous determination of lead (II) and cadmium (II) in water paint using a bismuth-modified gassy carbon electrode with anodic stripping voltammetry [<a href="#B101-chemosensors-12-00158" class="html-bibr">101</a>]. Copyright 2014 Elsevier. Copyright 2023 Elsevier.</p>
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<p>(<b>a</b>) Microfluidic channels of the graphene oxide–polydimethylsiloxane (GO-PDMS) chip. A—inlet section of the chip, B—middle section, C—outlet section. (<b>b</b>) GO-PDMS chip device. Despite the high content of GO, the composite maintains typical physical properties of PDMS like mechanical durability and elasticity [<a href="#B120-chemosensors-12-00158" class="html-bibr">120</a>]. Copyright 2017 Elsevier.</p>
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22 pages, 8833 KiB  
Article
Stability of Conducting Polymer-Coated Carbon Microfibers for Long-Term Electrical Stimulation of Injured Neural Tissue
by Hugo Vara, Gabriel Raúl Hernández-Labrado, Alexandra Alves-Sampaio and Jorge E. Collazos-Castro
Polymers 2024, 16(14), 2093; https://doi.org/10.3390/polym16142093 - 22 Jul 2024
Cited by 2 | Viewed by 1217
Abstract
Electroactive microfiber-based scaffolds aid neural tissue repair. Carbon microfibers (CMFs) coated with the conducting polymer poly(3,4-ethylenedioxythiophene) doped with poly[(4-styrenesulfonic acid)-co-(maleic acid)] (PEDOT:PSS-co-MA) provide efficient support and guidance to regrowing axons across spinal cord lesions in rodents and pigs. We [...] Read more.
Electroactive microfiber-based scaffolds aid neural tissue repair. Carbon microfibers (CMFs) coated with the conducting polymer poly(3,4-ethylenedioxythiophene) doped with poly[(4-styrenesulfonic acid)-co-(maleic acid)] (PEDOT:PSS-co-MA) provide efficient support and guidance to regrowing axons across spinal cord lesions in rodents and pigs. We investigated the electrical and structural performance of PEDOT:PSS-co-MA-coated carbon MFs (PCMFs) for long-term, biphasic electrical stimulation (ES). Chronopotentiometry and electrochemical impedance spectroscopy (EIS) allowed the characterization of charge transfer in PCMFs during ES in vitro, and morphological changes were assessed by scanning electron microscopy (SEM). PCMFs that were 4 mm long withstood two-million-biphasic pulses without reaching cytotoxic voltages, with a 6 mm length producing optimal results. Although EIS and SEM unveiled some polymer deterioration in the 6 mm PCMFs, no significant changes in voltage excursions appeared. For the preliminary testing of the electrical performance of PCMFs in vivo, we used 12 mm long, 20-microfiber assemblies interconnected by metallic microwires. PCMFs-assemblies were implanted in two spinal cord-injured pigs and submitted to ES for 10 days. A cobalt–alloy interconnected assembly showed safe voltages for about 1.5 million-pulses and was electrically functional at 1-month post-implantation, suggesting its suitability for sub-chronic ES, as likely required for spinal cord repair. However, improving polymer adhesion to the carbon substrate is still needed to use PCMFs for prolonged ES. Full article
(This article belongs to the Section Polymer Fibers)
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<p>Characterization of PCMFs. (<b>a</b>) Illustration of the typical polymerization potential for PEDOT:PSS-<span class="html-italic">co</span>-MA when applying constant current through 1 mm CMFs. (<b>b</b>) SEM image of the PCMF shaft after the polymerization. (<b>c</b>,<b>c’</b>) High-resolution SEM images of the microfiber shaft, showing the rough, nanoporous structure of the polymer. (<b>d</b>,<b>d’</b>) Same details of the polymer structure at the microfiber tip. (<b>e</b>) Representative traces of voltage transients produced by the application of −50/+50 μA biphasic rectangular pulses through the PCMFs of different lengths. Arrows indicate the E<sub>mc</sub> and E<sub>ma</sub> measured at zero current. (<b>f</b>) Average values of E<sub>mc</sub> and E<sub>ma</sub> from the tested PCMFs: 1 mm (n = 3), 2 mm (n = 3), 4 mm (n = 2), 6 mm (n = 4). Dashed line indicates water electrolysis potential value. (<b>g</b>) EIS Bode plots from the same PCMFs. When not visible, error bars are smaller than symbols. (<b>h</b>) Equivalent electrical circuit proposed for impedance data fitting. The model consists of three elements in a series: R<sub>s</sub>, electrolyte resistance; Z<sub>GD</sub>, generalized Warburg diffusion impedance; CPE, constant phase element modeling the pseudo-capacitance C<sub>d</sub>. (<b>i</b>) Nyquist plot from a representative PCMF of each length, superimposing experimental and simulated data. The arrows signal impedance values for a frequency of 15.8 Hz.</p>
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<p>Evolution of PCMFs voltage transients as a function of the number of ES pulses. (<b>a</b>–<b>d</b>) Representative recordings of voltage transients from microfibers of different lengths. Arrows point to E<sub>mc</sub> and E<sub>ma</sub> potentials measured at zero current. (<b>e</b>–<b>h</b>) Average E<sub>mc</sub> and E<sub>ma</sub> values measured from all the tested PCMFs. Dashed lines indicate water electrolysis potential values.</p>
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<p>Changes in PCMFs impedance as a function of the number of ES pulses. (<b>a</b>–<b>d</b>) Bode plots of data averaged from all PCMFs of each length. (<b>e</b>) Bode plot of impedance data for all PCMF lengths at the end of the ES protocol, i.e., 2 million pulses for 2, 4, and 6 mm microfibers, and 800k pulses for 1 mm microfibers. (<b>f</b>) Nyquist plot from a 6 mm long PCMF along the whole ES protocol. R(Ω) and X(Ω) are the real and imaginary parts of the impedance, respectively. Arrows indicate impedance values for a frequency of 15.8 Hz.</p>
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<p>SEM imaging of PCMFs after ES. (<b>a</b>–<b>c</b>) The 6 mm PCMFs after 2 million electric current pulses, showing polymer surface degradation and cracking transversal to the microfiber longitudinal axis. Cracks appear both in the microfiber shafts (<b>a</b>,<b>b</b>) and tips. Examples of 6 mm PCMFs tips with different degrees of deterioration are shown in (<b>c<sub>1</sub></b>,<b>c<sub>2</sub></b>). The polymer of the tip shown in (<b>c<sub>2</sub></b>) delaminated, but the carbon surface was intact. (<b>d</b>–<b>f</b>) SEM images of 1 mm PCMFs after 800k pulses, displaying extensive polymer cracking and wrinkling in the shafts (<b>d</b>,<b>e</b>) and damage in the tips (<b>f<sub>1</sub></b>,<b>f<sub>2</sub></b>), including the etching of the carbon microfiber itself (<b>f<sub>2</sub></b>). (<b>g</b>) Evaluation of PCMFs width after 2 million electrical pulses compared to non-pulsed electrodes. * <span class="html-italic">p</span> (ANOVA) &lt; 0.05.</p>
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<p>Effects of PEDOT:PSS-<span class="html-italic">co</span>-MA electrodeposition on a 35N LT-interconnected carbon microfiber assembly. (<b>a</b>,<b>d</b>) Voltage pulses (0.3 V biphasic rectangular waves, 0.1/s phase) applied for testing the assembly before (<b>a</b>) and after (<b>d</b>) forming the PEDOT coating. (<b>b</b>,<b>e</b>) Electric current responses of the carbon microfiber assembly when applying the voltage pulses before (<b>b</b>) and after (<b>e</b>) PEDOT electropolymerization. (<b>c</b>,<b>f</b>) Appearance of the assembly before (<b>b</b>) and after (<b>f</b>) the electrodeposition of the polymer.</p>
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<p>Effects of PEDOT:PSS-<span class="html-italic">co</span>-MA electrodeposition on a 35N LT-interconnected carbon microfiber assembly. (<b>a</b>,<b>d</b>) Voltage pulses (0.3 V biphasic rectangular waves, 0.1/s phase) applied for testing the assembly before (<b>a</b>) and after (<b>d</b>) forming the PEDOT coating. (<b>b</b>,<b>e</b>) Electric current responses of the carbon microfiber assembly when applying the voltage pulses before (<b>b</b>) and after (<b>e</b>) PEDOT electropolymerization. (<b>c</b>,<b>f</b>) Appearance of the assembly before (<b>b</b>) and after (<b>f</b>) the electrodeposition of the polymer.</p>
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<p>Porcine spinal cord injury model and implantation of a PCMF assembly. (<b>a</b>) Exeresis of the right side of the spinal cord segment C6 creating a 1 cm long cavity in the tissue. (<b>b</b>) Simultaneous handling of the fibrin gel (star) containing the interconnected assembly, together with the connector receiving the metallic microcable from the assembly. (<b>c</b>) Fibrin gel/PCMFs-assembly implanted into the lesion. (<b>d</b>) Meningeal suture and placement of epidural stainless-steel disks (white arrows) used as reference- and counter-electrodes at 1 cm from the lesion borders. Black arrows in (<b>c</b>,<b>d</b>) signal the metallic microcable exiting from the gel and the dura mater.</p>
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<p>Electrical performance of PCMF assemblies implanted in the injured porcine spinal cord. (<b>a</b>,<b>c</b>,<b>e</b>) Data from the assembly interconnected by a 35N LT-microwire. (<b>b</b>,<b>d</b>,<b>f</b>) Data from the assembly interconnected by a stainless steel microwire. (<b>a</b>,<b>b</b>) Waveforms of the electric current applied by the potentiostat/galvanostat through the assemblies and the resulting voltage immediately after the implantation in the porcine spinal cord. (<b>c</b>,<b>d</b>) Voltage transients produced by the assemblies at the indicated number of pulses. Note that the vertical scales are different for (<b>c</b>,<b>d</b>). Arrows point to the maximum cathodic and anodic microfiber polarization (E<sub>mc</sub> and E<sub>ma</sub>, respectively) measured after the cathodic or anodic phases when the intensity of the electric current i = 0. (<b>e</b>,<b>f</b>) Evolution of E<sub>mc</sub> and E<sub>ma</sub> for the assemblies in relation with the accumulated number of pulses. Data are expressed as mean ± standard error from 3 consecutive pulses of a chronopotentiometric test. Dashed lines indicate water electrolysis potential values.</p>
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<p>Electrical performance of PCMF assemblies implanted in the injured porcine spinal cord. (<b>a</b>,<b>c</b>,<b>e</b>) Data from the assembly interconnected by a 35N LT-microwire. (<b>b</b>,<b>d</b>,<b>f</b>) Data from the assembly interconnected by a stainless steel microwire. (<b>a</b>,<b>b</b>) Waveforms of the electric current applied by the potentiostat/galvanostat through the assemblies and the resulting voltage immediately after the implantation in the porcine spinal cord. (<b>c</b>,<b>d</b>) Voltage transients produced by the assemblies at the indicated number of pulses. Note that the vertical scales are different for (<b>c</b>,<b>d</b>). Arrows point to the maximum cathodic and anodic microfiber polarization (E<sub>mc</sub> and E<sub>ma</sub>, respectively) measured after the cathodic or anodic phases when the intensity of the electric current i = 0. (<b>e</b>,<b>f</b>) Evolution of E<sub>mc</sub> and E<sub>ma</sub> for the assemblies in relation with the accumulated number of pulses. Data are expressed as mean ± standard error from 3 consecutive pulses of a chronopotentiometric test. Dashed lines indicate water electrolysis potential values.</p>
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26 pages, 2111 KiB  
Article
Using Biosensors to Detect and Map Language Areas in the Brain for Individuals with Traumatic Brain Injury
by Ahmed Alduais, Hessah Saad Alarifi and Hind Alfadda
Diagnostics 2024, 14(14), 1535; https://doi.org/10.3390/diagnostics14141535 - 16 Jul 2024
Cited by 2 | Viewed by 1513
Abstract
The application of biosensors in neurolinguistics has significantly advanced the detection and mapping of language areas in the brain, particularly for individuals with brain trauma. This study explores the role of biosensors in this domain and proposes a conceptual model to guide their [...] Read more.
The application of biosensors in neurolinguistics has significantly advanced the detection and mapping of language areas in the brain, particularly for individuals with brain trauma. This study explores the role of biosensors in this domain and proposes a conceptual model to guide their use in research and clinical practice. The researchers explored the integration of biosensors in language and brain function studies, identified trends in research, and developed a conceptual model based on cluster and thematic analyses. Using a mixed-methods approach, we conducted cluster and thematic analyses on data curated from Web of Science, Scopus, and SciSpace, encompassing 392 articles. This dual analysis facilitated the identification of research trends and thematic insights within the field. The cluster analysis highlighted Functional Magnetic Resonance Imaging (fMRI) dominance and the importance of neuroplasticity in language recovery. Biosensors such as the Magnes 2500 watt-hour (WH) neuromagnetometer and microwire-based sensors are reliable for real-time monitoring, despite methodological challenges. The proposed model synthesizes these findings, emphasizing biosensors’ potential in preoperative assessments and therapeutic customization. Biosensors are vital for non-invasive, precise mapping of language areas, with fMRI and repetitive Transcranial Magnetic Stimulation (rTMS) playing pivotal roles. The conceptual model serves as a strategic framework for employing biosensors and improving neurolinguistic interventions. This research may enhance surgical planning, optimize recovery therapies, and encourage technological advancements in biosensor precision and application protocols. Full article
(This article belongs to the Section Medical Imaging and Theranostics)
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<p>PRISMA Flow Diagram.</p>
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<p>Density Visualization of Co-occurrence from Web of Science.</p>
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<p>Density Visualization of Co-occurrence from Scopus and SciSpace.</p>
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<p>A Landscape Visualization of the Largest 10 Clusters.</p>
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<p>Top 15 Keywords with the Strongest Citation Bursts.</p>
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<p>A Model Guiding the Use of Biosensors in Language Area Detection in the Brain.</p>
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20 pages, 9844 KiB  
Article
Micro-WEDM of Ti-29Nb-13Ta-4.6Zr Alloy for Antibacterial Properties: Experimental Investigation and Optimization
by Shahid Ali, Salikh Omarov, Altynay Utebayeva, Tri Thanh Pham, Didier Talamona and Asma Perveen
Metals 2024, 14(6), 714; https://doi.org/10.3390/met14060714 - 16 Jun 2024
Viewed by 1499
Abstract
Recent developments of orthopedic implant applications have discovered a variety of new metallic biomaterials known as β-type titanium alloys. The μ-WEDM (micro-wire electro discharge machining) surface treatment technique, capable of improving the surface properties of orthopedic implants, was studied in a machining Ti-29Nb-13Ta-4.6Zr [...] Read more.
Recent developments of orthopedic implant applications have discovered a variety of new metallic biomaterials known as β-type titanium alloys. The μ-WEDM (micro-wire electro discharge machining) surface treatment technique, capable of improving the surface properties of orthopedic implants, was studied in a machining Ti-29Nb-13Ta-4.6Zr alloy. This study aimed to evaluate material removal rate (MRR), kerf width, average surface roughness, microhardness and antibacterial response at different machining parameters which are capacitance (1 nF, 10 nF and 100 nF) and gap voltage (80 V, 95 V and 110 V). The Taguchi method was used to optimize the mentioned output parameters, while ANOVA (analysis of variance) described the significance and contribution of capacitance and gap voltage. Grey relation analysis (GRA) was conducted to perform multiple output optimization. For antibacterial response, cultivations of B. subtilis, E. coli, P. aeruginosa and S. aureus bacteria on treated surfaces for 72 h were performed. As the results, optimal values of MRR, kerf width, crater area, average surface roughness and microhardness were equal to 0.0637 mm3/min, 93.0 μm, 21.8 μm2, 0.348 μm and 442 HV, respectively. Meanwhile, μ-WEDM treatment improved antibacterial properties while the highest antibacterial response was achieved at the lowest average surface roughness resulting in least biofilm formation on treated surfaces. Full article
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<p>The schematic diagram of μ-WEDM process.</p>
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<p>The schematic illustration of kerf width.</p>
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<p>Schematic diagram showing how antibacterial tests were performed, visualized and quantified.</p>
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<p>Main effects plot of means for (<b>a</b>) MRR, (<b>b</b>) KW, (<b>c</b>) CS, (<b>d</b>) SR and (<b>e</b>) microhardness.</p>
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<p>3D plots of regression models for (<b>a</b>) MRR, (<b>b</b>) KW, (<b>c</b>) CS, (<b>d</b>) SR and (<b>e</b>) microhardness.</p>
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<p>3D plots of regression models for (<b>a</b>) MRR, (<b>b</b>) KW, (<b>c</b>) CS, (<b>d</b>) SR and (<b>e</b>) microhardness.</p>
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<p>SEM image analysis for the influence of capacitance on the surface morphology at voltage = 95 V and (<b>a</b>) capacitance = 1 nF; (<b>b</b>) capacitance = 10 nF; (<b>c</b>) capacitance = 100 nF.</p>
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<p>AFM analysis for the influence of capacitance on the surface morphology at voltage = 95 V and (<b>a</b>) capacitance = 1 nF; (<b>b</b>) capacitance = 10 nF; (<b>c</b>) capacitance = 100 nF.</p>
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<p>3D plots of regression models for GRG.</p>
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<p>Representative images of crystal violet-stained, bright field (BF) and MATLAB biofilms detection of bacterial biofilms for all bacterial strains on μ-WEDM-treated TNTZ surfaces with different discharge energy levels and untreated surfaces. Quantifications of the percentage of biofilm coverage on machined surfaces was estimated within the yellow box.</p>
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<p>Comparison of the percentage of biofilm coverage for all four bacterial strains on three different energy-level-treated surfaces as well as untreated surfaces.</p>
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17 pages, 5085 KiB  
Article
Removal Forces of a Helical Microwire Structure Electrode
by Amelia Howe, Zhanda Chen, Kyle Golobish, Victoria R. Miduri, Derrick Liu, David Valencia, Morgan McGaughey, Emily Szabo, Manfred Franke and Stephan Nieuwoudt
Bioengineering 2024, 11(6), 611; https://doi.org/10.3390/bioengineering11060611 - 13 Jun 2024
Viewed by 1373
Abstract
(1) Background: Medical devices, especially neuromodulation devices, are often explanted for a variety of reasons. The removal process imparts significant forces on these devices, which may result in device fracture and tissue trauma. We hypothesized that a device’s form factor interfacing with tissue [...] Read more.
(1) Background: Medical devices, especially neuromodulation devices, are often explanted for a variety of reasons. The removal process imparts significant forces on these devices, which may result in device fracture and tissue trauma. We hypothesized that a device’s form factor interfacing with tissue is a major driver of the force required to remove a device, and we isolated helical and linear electrode structures as a means to study atraumatic removal. (2) Methods: Ductile linear and helical microwire structure electrodes were fabricated from either Gold (Au) or Platinum–Iridium (Pt-Ir, 90-10). Removal forces were captured from synthetic gel models and following chronic implantation in rodent and porcine models. Devices were fully implanted in the animal models, requiring a small incision (<10 mm) and removal via tissue forceps. (3) Results: Helical devices were shown to result in significantly lower maximal removal forces in both synthetic gel and rodent studies compared to their linear counterparts. Chronically (1 yr.), the maximal removal force of helical devices remained under 7.30 N, for which the Platinum–Iridium device’s tensile failure force was 32.90 ± 2.09 N, resulting in a safety factor of 4.50. (4) Conclusions: An open-core helical structure that can freely elongate was shown to result in reduced removal forces both acutely and chronically. Full article
(This article belongs to the Special Issue Medical Devices and Implants, 2nd Edition)
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<p>The removal of a (<b>a</b>) linear and (<b>b</b>) helical Gold microwire device from a synthetic gel model with sequential images from left to right. The scale bar is 5 mm.</p>
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<p>Benchtop tensile force testing equipment. Vertical test stand used for tensile testing with force transducer prior to loading (<b>a</b>) and at moment of tensile failure (<b>b</b>) with arrow pointing to failure site. Custom capstan grips (<b>c</b>,<b>d</b>) that were used in all testing increased test accuracy. For synthetic gel removal tests, (<b>e</b>) devices were suspended in gel prior to reheating in vacuum oven. (<b>f</b>) Same custom capstan grips were also used in tensile removal testing of gel-embedded devices.</p>
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<p>Removal forces of helical versus linear devices for (<b>a</b>) Gold devices from synthetic gel in pilot study and (<b>b</b>) Platinum–Iridium-based devices at varying lengths, * <span class="html-italic">p</span> &lt; 0.01. (<b>c</b>) Average cumulative distribution plots of pull force data taken for helical vs. linear samples at 8 cm embedded length. (<b>d</b>) Gold helical and linear devices following chronic implantation in rodent model of 107 days.</p>
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<p>Removal forces of helical devices from rodent model and chronic time points. (<b>a</b>) Gold helical microwire devices implanted and removed at various time points across 15 months, with horizontal line representing ultimate failure force of devices (dotted line for standard deviation) and (<b>b</b>) same plot for chronically implanted Platinum–Iridium helical devices, with higher ultimate failure force represented by horizontal line. (<b>c</b>) Representative force time plots of helical devices during removal. (<b>d</b>) Sequence of fluoroscopy images of removal of helical device showing sequential release of device from tissue (arrows 1 and 2 pointing to location where transitions from helical to linear occurs, seen as change in device opacity from black to gray).</p>
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<p>(<b>a</b>) The force time plot of different removal force profiles detected during the explant of helical devices from a porcine model, highlighting the abrupt transition from tissue ripping force to true removal forces imparted on the device during pull-out. (<b>b</b>) The maximal removal forces measured across 56 days for helical Platinum–Iridium devices removed from the porcine model, with a horizontal line indicating the ultimate failure force of the device (dotted lines for standard deviation from the mean). (<b>c</b>,<b>d</b>) Images of tissue forceps engaging with a helical device prior to removal and fluoroscopy. (<b>e</b>) Sequential fluoroscopy images of the removal of an implanted helical device from the hindlimb in the porcine model (day 42) next to another implanted device.</p>
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<p>Histological sections with Toluene blue staining of implanted devices and visual assessment of removed devices. (<b>a</b>) Histology of electrode on nerve and tissue ingrowth between microwires at transition point from coating to no coating at 5 months in rodents. (<b>b</b>) Histology of subcutaneous component of device in pig following 1 month of implantation. Scale bars are 100 microns. Microscopy image of coating to no-coating transition point of (<b>c</b>) control non-implanted Platinum–Iridium device, (<b>d</b>) Platinum–Iridium device implanted for 12 months, and (<b>e</b>) Gold device implanted for 15 months with arrows pointing out tissue extracted with device during removal. Scale bars are 500 microns.</p>
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<p>(<b>a</b>) A model of the removal of a linear device, which results in crack propagation along Z for a device of length L, the radius of the device, and a gel matrix radius of r. (<b>b</b>) A depiction of the hypothesized peel force, Fpeel, occurring during the removal of a helical device coil by coil as one helical segment separates from another and the gel at the inclined plane interface as the crack propagates along direction Z.</p>
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<p>(<b>a</b>) A high-resolution image of the inward collapse of the helical device, leaving behind an imprint of the device in the gel. (<b>b</b>) A “bunched” non-linear placement of a helical device and the stepwise removal process.</p>
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