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Keywords = biomimetic sensing

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26 pages, 6323 KiB  
Article
Design and Characterization of Biomimetic Hybrid Construct Based on Hyaluronic Acid and Alginate Bioink for Regeneration of Articular Cartilage
by Cristina Galocha-León, Cristina Antich, Beatriz Clares-Naveros, Ana Voltes-Martínez, Juan Antonio Marchal and Patricia Gálvez-Martín
Pharmaceutics 2024, 16(11), 1422; https://doi.org/10.3390/pharmaceutics16111422 - 7 Nov 2024
Viewed by 462
Abstract
Background/Objectives: Three-dimensional bioprinting technology has enabled great advances in the treatment of articular cartilage (AC) defects by the biofabrication of biomimetic constructs that restore and/or regenerate damaged tissue. In this sense, the selection of suitable cells and biomaterials to bioprint constructs that mimic [...] Read more.
Background/Objectives: Three-dimensional bioprinting technology has enabled great advances in the treatment of articular cartilage (AC) defects by the biofabrication of biomimetic constructs that restore and/or regenerate damaged tissue. In this sense, the selection of suitable cells and biomaterials to bioprint constructs that mimic the architecture, composition, and functionality of the natural extracellular matrix (ECM) of the native tissue is crucial. In the present study, a novel cartilage-like biomimetic hybrid construct (CBC) was developed by 3D bioprinting to facilitate and promote AC regeneration. Methods: The CBC was biofabricated by the co-bioprinting of a bioink based on hyaluronic acid (HA) and alginate (AL) loaded with human mesenchymal stromal cells (hMSCs), with polylactic acid supporting the biomaterial, in order to mimic the microenvironment and structural properties of native AC, respectively. The CBC was biologically in vitro characterized. In addition, its physiochemical characteristics were evaluated in order to determine if the presence of hMSCs modified its properties. Results: Results from biological analysis demonstrated that CBC supported the high viability and proliferation of hMSCs, facilitating chondrogenesis after 5 weeks in vitro. The evaluation of physicochemical properties in the CBCs confirmed that the CBC developed could be suitable for use in cartilage tissue engineering. Conclusions: The results demonstrated that the use of bioprinted CBCs based on hMSC-AL/HA-bioink for AC repair could enhance the regeneration and/or formation of hyaline cartilaginous tissue. Full article
(This article belongs to the Section Pharmaceutical Technology, Manufacturing and Devices)
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Figure 1
<p>Three-dimensional bioprinting of CBCs based on hMSC-AL/HA-bioink. (<b>A</b>) REGEMAT Bioprinter system and bioinks. (<b>B</b>) Design of CBCs using REGEMAT software designer. (<b>C</b>) Scheme of dispensing and crosslinking of bioink in the PLA framework: hMSC-AL/HA-bioink (pink), calcium solution (blue), and crosslinked hMSC-AL/HA-bioink (purple). (<b>D</b>) Steps of biofabrication procedure of CBCs based on hMSC-AL/HA-bioink by 3D bioprinting.</p>
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<p>Phenotypic characterization of hMSCs. FACS characterization of hMSCs showed a positive expression of the surface markers CD90, CD73, and CD105 and negative or low expression of CD45, CD19, and HLA.</p>
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<p>Cell differentiation staining assay. The differentiation potential of hMSCs obtained from IFP towards osteogenic, adipogenic, and chondrogenic lineage was confirmed by Alizarin red S, Oil Red O, and Toluidine Blue staining, respectively. Scale bar: 200 μm. Images were taken at 10× magnification.</p>
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<p>Cell viability and proliferation of hMSCs in control constructs based on hMSC-AL-bioink and CBCs based on hMSC-AL/HA-bioink. (<b>A</b>) Representative image of hMSCs in control constructs and CBCs after 1, 3, 5, 7, 14, and 21 days in culture, showing live (green) and dead (red) cells. (<b>B</b>) Percentage of hMSC viability in control constructs and CBCs with respect to time in culture. (<b>C</b>) Cell proliferation inside the CBCs based on hMSC-AL/HA-bioink (black) and control constructs based on hMSC-loaded AL-bioink (white). Error bars represent standard deviations (n = 3). (*) <span class="html-italic">p</span> &lt; 0.05; (***) <span class="html-italic">p</span> &lt; 0.005; (#) <span class="html-italic">p</span> &lt; 0.05. Scale bar: 100 μm.</p>
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<p>Chondrogenesis of hMSCs in CBCs based on hMSC-AL/HA-bioink and in control constructs based on hMSC-AL-bioink after 5 weeks in culture. (<b>A</b>) Gene expression levels of hyaline-specific chondrogenic marker genes (<span class="html-italic">COL2A1</span>, <span class="html-italic">ACAN</span>, and <span class="html-italic">SOX9</span>) and other genes such as <span class="html-italic">COL10A1</span> and <span class="html-italic">RUNX2</span> from cells in CBCs based on hMSC-AL/HA-bioink compared to cells of control constructs. (<b>B</b>) Quantitative analysis of GAGs. (<b>C</b>) Quantitative analysis type II collagen in the total extract per construct. Values represent mean ± SD (n = 3).</p>
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<p>Swelling ratio of CBCs based on hMSC-AL/HA-bioink and cell-free CBCs based on AL/HA-bioink. (<b>A</b>) Swelling ratio at pH 7.4 and 37 °C after 24 h. (<b>B</b>) Swelling ratio at pH 7.4 and 37 °C after 120 days. Values represent mean ± SD (n = 3).</p>
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<p>Degradation percentage of CBCs based on hMSC-AL/HA-bioink and cell-free CBCs based on AL/HA-bioink at pH 7.4 and 37 °C. Values represent mean ± SD (n = 3).</p>
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<p>Zeta potential (ζ, mV) of CBCs based on hMSC-AL/HA-bioink and cell-free CBCs based on AL/HA-bioink. (<b>A</b>) ζ as a function of ionic strength at pH = 6 at 25 °C. (<b>B</b>) ζ as a function of pH in the presence of 10<sup>−3</sup> M KNO<sub>3</sub> concentration at 25 °C. Values represent mean ± SD (n = 9).</p>
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<p>SEM microscopy analysis of hMSCs in constructs. (<b>A</b>,<b>G</b>,<b>M</b>) Cell-free CBCs based on AL/HA-bioink in cell culture conditions after 1 day. (<b>B</b>,<b>H</b>,<b>N</b>) CBCs based on hMSC-AL/HA-bioink in cell culture conditions after 1 day. (<b>C</b>,<b>I</b>,<b>O</b>) Cell-free CBCs based on AL/HA-bioink in cell culture conditions after 7 days. (<b>D</b>,<b>J</b>,<b>P</b>) CBCs based on hMSC-AL/HA-bioink in cell culture conditions after 7 days. (<b>E</b>,<b>K</b>,<b>Q</b>) Cell-free CBCs based on AL/HA-bioink in cell culture conditions after 21 days. (<b>F</b>,<b>L</b>,<b>R</b>) CBCs based on hMSC-AL/HA-bioink in cell culture conditions after 21 days. Images were taken at 150× (<b>A</b>–<b>F</b>; scale bar: 500 μm), 1500× (<b>G</b>–<b>L</b>; scale bar: 50 μm), and 5000× (<b>M</b>–<b>R</b>; scale bar: 20 μm).</p>
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27 pages, 9044 KiB  
Review
Comprehensive Review of Hydrogel Synthesis, Characterization, and Emerging Applications
by Arumugasamy Sathiya Priya, Rajaraman Premanand, Indhumathi Ragupathi, Vijayabhaskara Rao Bhaviripudi, Radhamanohar Aepuru, Karthik Kannan and Krishnamoorthy Shanmugaraj
J. Compos. Sci. 2024, 8(11), 457; https://doi.org/10.3390/jcs8110457 - 4 Nov 2024
Viewed by 940
Abstract
Hydrogels play a crucial role due to their high-water content and 3D structure, which make them ideal for various applications in biomedicine, sensing, and beyond. They can be prepared from a variety of biomaterials, polymers, and their combinations, allowing for versatility in properties [...] Read more.
Hydrogels play a crucial role due to their high-water content and 3D structure, which make them ideal for various applications in biomedicine, sensing, and beyond. They can be prepared from a variety of biomaterials, polymers, and their combinations, allowing for versatility in properties and applications. Hydrogels include natural types derived from collagen, gelatin, alginate, and hyaluronic acid, as well as synthetic types based on polyethylene glycol (PEG), polyvinyl alcohol (PVA), and polyacrylamide (PAAm). Each type possesses distinct properties, such as mechanical strength, biodegradability, and biocompatibility, which can be tailored for applications such as wound healing, contact lenses, 3D bioprinting, and tissue engineering. The high-water content of hydrogels mimics natural tissue environments, promoting cell growth and allowing nutrient and waste exchange, which supports the development of functional tissues. They serve as scaffolds in tissue engineering applications, including wound healing, cartilage and bone regeneration, vascular tissue engineering, and organ-on-a-chip systems. Additionally, hydrogels can encapsulate and deliver therapeutic agents, such as growth factors or drugs, to specific target sites in the body. Hydrogels can be prepared through three primary methods: physical crosslinking, which relies on non-covalent interactions such as physical entanglements or hydrogen bonding; chemical crosslinking, which forms covalent bonds between polymer chains to create a stable structure; and irradiation-based crosslinking, where UV irradiation induces rapid hydrogel formation. The choice of crosslinking method depends on the desired properties and applications of the hydrogel. By providing a biomimetic environment, hydrogels facilitate cell growth and differentiation, support tissue formation, and aid in the regeneration of damaged or diseased tissues while delivering therapeutic agents. This review focuses on the critical advancements in processing routes for hydrogel development, summarizing the characterization and application of hydrogels. It also details key applications, including wound healing and cartilage and bone regeneration, as well as the challenges and future perspectives in the field. Full article
(This article belongs to the Section Biocomposites)
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<p>Hydrogel preparation methods.</p>
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<p>Flow chart of affected parameters of hydrogel preparation methods.</p>
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<p>(<b>a</b>) The swelling ratio of PDIV1-PDIV4 hydrogel in deionized water, (<b>b</b>) Values of equilibrium swelling ratio for PDIV1-PDIV4 hydrogel in various thermal conditions, (<b>c</b>) swelling-shrinking reversible curves of PDIV1-PDIV4 hydrogels at 37 °C and 25 °C, (<b>d</b>) Values of equilibrium swelling ratio for PDIV1-PDIV4 hydrogel in various pH solutions, (<b>e</b>) swelling-shrinking reversible curves of PDIV1-PDIV4 hydrogels at pH = 1.2 and pH = 7.4 [<a href="#B38-jcs-08-00457" class="html-bibr">38</a>].</p>
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<p>(<b>a</b>) SEM images of natural and enzyme-induced hydrogels [<a href="#B40-jcs-08-00457" class="html-bibr">40</a>]. (<b>b</b>,<b>c</b>) SEM images of SAF- and LAF-WPI hydrogel composites at various concentrations of NaCl with (<b>b</b>) ×40,000 and (<b>c</b>) ×10,000 magnifications. The NaCl concentration (mM) has been specified on the top of the images. Scale bars correspond to 100 nm and 1 μm for parts (<b>b</b>) and (<b>c</b>), respectively [<a href="#B41-jcs-08-00457" class="html-bibr">41</a>].</p>
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<p>SEM images of external and cross-sectional aspect of the different hydrogel beads. (<b>a</b>,<b>d</b>) SA; (<b>b</b>,<b>e</b>) B1; (<b>c</b>,<b>f</b>) B2 [<a href="#B42-jcs-08-00457" class="html-bibr">42</a>].</p>
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<p>Tensile (<b>a</b>) and compression (<b>b</b>) stress-strain curves of S—Alg and D—Alg. (<b>c</b>) Oscillatory amplitude sweep of S—Alg and D—Alg. (<b>d</b>) Oscillatory frequency sweep of S—Alg and D—Alg [<a href="#B44-jcs-08-00457" class="html-bibr">44</a>].</p>
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<p>(<b>a</b>) PVA/CMC hydrogel hanging weight, twisting, knotting, stretching performance. (<b>b</b>) PVA/CMC hydrogel film stretching, poking performance. (<b>c</b>) PVA/CMC hydrogel block poking performance [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>]. (<b>d</b>) Tensile stress–strain curves of PVA-CMC (H2O/DMSO) hydrogels, pure PVA (H2O/DMSO) hydrogels and pure PVA (H<sub>2</sub>O) hydrogels. (<b>e</b>) Freeze moulding of CMC and PVA chains. (<b>f</b>) Continuous loading–unloading curves of PVA-CMC hydrogels with different strains [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>]. (<b>g</b>) Cyclic loading–unloading, (<b>h</b>) residual strain and (<b>i</b>) dissipated energy tests of PVA-CMC hydrogel and pure PVA hydrogels [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>]. SEM images of Ag-CMC conductive hydrogel at magnifications of (<b>j1</b>) 500×, (<b>j2</b>) 2.5 k × and (<b>j3</b>) 40.56 k× [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>]. (<b>k</b>) XRD of PVA/CMC hydrogel and Ag-CMC conductive hydrogel. (<b>l1</b>) Cross sections of Ag-CMC conductive hydrogels and corresponding (<b>l2</b>) [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>]. (<b>m</b>) Shore hardness of pure PVA and PVA-CMC hydrogel before and after silver reduction. (<b>n</b>) Tensile stress-strain curve of conductive hydrogel with varying concentrations of AgNO<sub>3</sub> and VC concentration of 0.08 M. (<b>o</b>) Tensile stress–strain curve of conductive hydrogel with varying VC concentrations and AgNO<sub>3</sub> concentration of 1.0 M [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>].</p>
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<p>(<b>a</b>) PVA/CMC hydrogel hanging weight, twisting, knotting, stretching performance. (<b>b</b>) PVA/CMC hydrogel film stretching, poking performance. (<b>c</b>) PVA/CMC hydrogel block poking performance [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>]. (<b>d</b>) Tensile stress–strain curves of PVA-CMC (H2O/DMSO) hydrogels, pure PVA (H2O/DMSO) hydrogels and pure PVA (H<sub>2</sub>O) hydrogels. (<b>e</b>) Freeze moulding of CMC and PVA chains. (<b>f</b>) Continuous loading–unloading curves of PVA-CMC hydrogels with different strains [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>]. (<b>g</b>) Cyclic loading–unloading, (<b>h</b>) residual strain and (<b>i</b>) dissipated energy tests of PVA-CMC hydrogel and pure PVA hydrogels [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>]. SEM images of Ag-CMC conductive hydrogel at magnifications of (<b>j1</b>) 500×, (<b>j2</b>) 2.5 k × and (<b>j3</b>) 40.56 k× [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>]. (<b>k</b>) XRD of PVA/CMC hydrogel and Ag-CMC conductive hydrogel. (<b>l1</b>) Cross sections of Ag-CMC conductive hydrogels and corresponding (<b>l2</b>) [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>]. (<b>m</b>) Shore hardness of pure PVA and PVA-CMC hydrogel before and after silver reduction. (<b>n</b>) Tensile stress-strain curve of conductive hydrogel with varying concentrations of AgNO<sub>3</sub> and VC concentration of 0.08 M. (<b>o</b>) Tensile stress–strain curve of conductive hydrogel with varying VC concentrations and AgNO<sub>3</sub> concentration of 1.0 M [<a href="#B45-jcs-08-00457" class="html-bibr">45</a>].</p>
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<p>(<b>a</b>,<b>b</b>) SEM images of composite hydrogel, (<b>c</b>,<b>d</b>) TEM images of composite hydrogel [<a href="#B48-jcs-08-00457" class="html-bibr">48</a>].</p>
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<p>(<b>i</b>) FTIR spectra of (a) chitosan, (b) starch, (c) chitosan—starch hydrogel, (d) cefixime drug, and (e) cefixime loaded hydrogel. (<b>ii</b>) FTIR spectra of chitosan/alginate hydrogels [<a href="#B50-jcs-08-00457" class="html-bibr">50</a>].</p>
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<p>Inhibition zone diameter in the antibacterial study at 37 °C for the developed hydrogels [<a href="#B53-jcs-08-00457" class="html-bibr">53</a>].</p>
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<p>(<b>a</b>) Demonstration of the antibacterial effect of PVA/PA/GL hydrogel on <span class="html-italic">Escherichia coli</span> and <span class="html-italic">Bacillus subtilis</span>; (<b>b</b>) comparison of growth curves of hydrogels in <span class="html-italic">Escherichia coli</span>; (<b>c</b>) comparison of growth curves of hydrogels in <span class="html-italic">Bacillus subtilis</span>; (<b>d</b>) demonstration of the diameter of the circle of inhibition of PVA/GL hydrogel and PVA/PA/GL hydrogel; (<b>e</b>) stability of PVA/PA/GL hydrogels for 7 day bacterial inhibition in <span class="html-italic">Escherichia coli</span>; (<b>f</b>) stability of PVA/PA/GL hydrogels for 7 day bacterial inhibition in <span class="html-italic">Bacillus cereus</span> [<a href="#B54-jcs-08-00457" class="html-bibr">54</a>].</p>
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<p>Schematic illustration of EGCG@GEL/GAS/CS-OGEP hydrogel prepared and applied to diabetic wound healing [<a href="#B64-jcs-08-00457" class="html-bibr">64</a>].</p>
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<p>Electrofabrication of chitosan-based hydrogel contact lenses [<a href="#B73-jcs-08-00457" class="html-bibr">73</a>].</p>
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<p>Schematic illustration of approaches to make injectable hydrogels for cartilage and bone tissue engineering applications [<a href="#B81-jcs-08-00457" class="html-bibr">81</a>].</p>
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<p>(<b>i</b>) Stages of the 3 D bioprinting process, (<b>ii</b>) the printability of 3 D printing hydrogel scaffold. (a) The digital model of the 3D scaffold, (b) the outline of the first layer of hydrogel scaffold shape after filled the blank area (c) (the filling rate is 100%), (d) three views of the printed hydrogel scaffold from three different angles (the structure has 30 layers and the height is 15 mm; the fidelity of the top surface is about 80%) [<a href="#B92-jcs-08-00457" class="html-bibr">92</a>].</p>
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<p>(<b>i</b>) Electrochemical performance of PANi—NF hydrogel symmetric supercapacitors in a 1 M H<sub>2</sub>SO<sub>4</sub> electrolyte; (A) Schematic diagram for PANi-NF hydrogel in a two-electrode system, (B) CV curves at different scan rates, (C) charge/discharge curves at different current densities, and (D) gravimetric and areal capacitances calculated under different current densities. (<b>ii</b>) (a) GCD of the antifreezing supercapacitor for different current densities at −20 °C, (b) CV curves of antifreezing supercapacitors for various scan rates at −20 °C, (c) GCD of single device and three devices combined in series at −20 °C, and the inset shows practical application picture of antifreezing supercapacitor; (d) CV curves at −20 °C and under different deformations; (e) cyclic stability of the antifreezing supercapacitor at −20 °C; (f) photograph of a watch lighted by the device in series and as part of watch band at −27 °C, and −25 °C [<a href="#B101-jcs-08-00457" class="html-bibr">101</a>].</p>
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19 pages, 9872 KiB  
Article
A Portable Electronic Nose Coupled with Deep Learning for Enhanced Detection and Differentiation of Local Thai Craft Spirits
by Supakorn Harnsoongnoen, Nantawat Babpan, Saksun Srisai, Pongsathorn Kongkeaw and Natthaphon Srisongkram
Chemosensors 2024, 12(10), 221; https://doi.org/10.3390/chemosensors12100221 - 19 Oct 2024
Viewed by 850
Abstract
In this study, our primary focus is the biomimetic design and rigorous evaluation of an economically viable and portable ‘e-nose’ system, tailored for the precise detection of a broad range of volatile organic compounds (VOCs) in local Thai craft spirits. This e-nose system [...] Read more.
In this study, our primary focus is the biomimetic design and rigorous evaluation of an economically viable and portable ‘e-nose’ system, tailored for the precise detection of a broad range of volatile organic compounds (VOCs) in local Thai craft spirits. This e-nose system is innovatively equipped with cost-efficient metal oxide gas sensors and a temperature/humidity sensor, ensuring comprehensive and accurate sensing. A custom-designed real-time data acquisition system is integrated, featuring gas flow control, humidity filters, dual sensing/reference chambers, an analog-to-digital converter, and seamless data integration with a laptop. Deep learning, utilizing a multilayer perceptron (MLP), is employed to achieve highly effective classification of local Thai craft spirits, demonstrated by a perfect classification accuracy of 100% in experimental studies. This work underscores the significant potential of biomimetic principles in advancing cost-effective, portable, and analytically precise e-nose systems, offering valuable insights into future applications of advanced gas sensor technology in food, biomedical, and environmental monitoring and safety. Full article
(This article belongs to the Special Issue Gas Sensors and Electronic Noses for the Real Condition Sensing)
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<p>E-nose system.</p>
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<p>E-nose configuration: (<b>a</b>) gas flow direction and (<b>b</b>) sensor interface.</p>
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<p>A low-cost portable electronic nose: (<b>a</b>) top and front view and (<b>b</b>) inside view.</p>
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<p>Measurement setup.</p>
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<p>Data extraction: (<b>a</b>) sensor response and (<b>b</b>) data extraction.</p>
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<p>Multilayer perceptron architecture.</p>
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<p>Temperature and humidity sensing: (<b>a</b>) temperature and (<b>b</b>) humidity.</p>
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<p>Relationship of humidity to various quantities: (<b>a</b>) time, (<b>b</b>) MQ-135, (<b>c</b>) MQ-136, (<b>d</b>) MQ-137, (<b>e</b>) MQ-138, (<b>f</b>) MQ-139, (<b>g</b>) MQ-9, (<b>h</b>) MQ-6, and (<b>i</b>) MQ-3.</p>
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<p>Relationship of humidity to various quantities: (<b>a</b>) time, (<b>b</b>) MQ-135, (<b>c</b>) MQ-136, (<b>d</b>) MQ-137, (<b>e</b>) MQ-138, (<b>f</b>) MQ-139, (<b>g</b>) MQ-9, (<b>h</b>) MQ-6, and (<b>i</b>) MQ-3.</p>
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<p>Gas sensor response: (<b>a</b>) Koon, (<b>b</b>) Onson, (<b>c</b>) Pandanus, and (<b>d</b>) alcohol.</p>
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<p>Maximum and minimum of sensor response: (<b>a</b>) Koon, (<b>b</b>) Onson, (<b>c</b>) Pandanus, and (<b>d</b>) alcohol.</p>
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<p>Pair plot of sensor responses based on local Thai craft spirits.</p>
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<p>Heatmap of correlation coefficients between gas sensors based on local Thai craft spirits.</p>
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<p>The decision regions in 2D derived from the 8 input features of the sensor array: (<b>a</b>) MLP with PCA and (<b>b</b>) K-means with PCA.</p>
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<p>Scatter plots and classifications: (<b>a</b>) and (<b>b</b>) MQ-136 vs. MQ-3, (<b>c</b>) and (<b>d</b>) MQ-136 vs. MQ-6, (<b>e</b>) and (<b>f</b>) MQ-136 vs. MQ-9, (<b>g</b>) and (<b>h</b>) MQ-136 vs. MQ-135, (<b>i</b>) and (<b>j</b>) MQ-136 vs. MQ-137, (<b>k</b>) and (<b>l</b>) MQ-136 vs. MQ-138, and (<b>m</b>) and (<b>n</b>) MQ-136 vs. MQ-139.</p>
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<p>Scatter plots and classifications: (<b>a</b>) and (<b>b</b>) MQ-136 vs. MQ-3, (<b>c</b>) and (<b>d</b>) MQ-136 vs. MQ-6, (<b>e</b>) and (<b>f</b>) MQ-136 vs. MQ-9, (<b>g</b>) and (<b>h</b>) MQ-136 vs. MQ-135, (<b>i</b>) and (<b>j</b>) MQ-136 vs. MQ-137, (<b>k</b>) and (<b>l</b>) MQ-136 vs. MQ-138, and (<b>m</b>) and (<b>n</b>) MQ-136 vs. MQ-139.</p>
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<p>Classifications: (<b>a</b>) MQ-136 vs. MQ-3, (<b>b</b>) MQ-136 vs. MQ-6, (<b>c</b>) MQ-136 vs. MQ-9, (<b>d</b>) MQ-136 vs. MQ-135, (<b>e</b>) MQ-136 vs. MQ-137, (<b>f</b>) MQ-136 vs. MQ-138, and (<b>g</b>) MQ-136 vs. MQ-139.</p>
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13 pages, 5008 KiB  
Article
Biomimetic Layered Hydrogel Coating for Enhanced Lubrication and Load-Bearing Capacity
by Xuxu Hu, Yu Zhao, Shuai Cheng, Jinming Zhen, Zhengfeng Jia and Ran Zhang
Coatings 2024, 14(9), 1229; https://doi.org/10.3390/coatings14091229 - 23 Sep 2024
Viewed by 722
Abstract
Biomimetic hydrogel lubrication coatings with high wettability and low friction show great promise in tissue engineering, wound dressing, drug delivery, and intelligent sensing. Inspired by the hierarchical structure of natural cartilage, a layered hydrogel coating was constructed to functionalize rigid polyetheretherketone (PEEK). The [...] Read more.
Biomimetic hydrogel lubrication coatings with high wettability and low friction show great promise in tissue engineering, wound dressing, drug delivery, and intelligent sensing. Inspired by the hierarchical structure of natural cartilage, a layered hydrogel coating was constructed to functionalize rigid polyetheretherketone (PEEK). The layered hydrogel coating features a structural design comprising a top soft layer and a middle robust layer. The porous structure of the top soft hydrogel layer stores water molecules, providing surface lubrication, while the dense structure of the middle robust hydrogel layer offers load-bearing capacity. These synergistic effects of the gradient hydrogel layer endow the PEEK substrate with an ultra-low coefficient of friction (COF~0.010 at 5 N load), good load-bearing capacity (COF~0.031 at 10 N load), and excellent wear resistance (COF < 0.05 at 5 N load after 20,000 sliding cycles). This study introduces a novel design paradigm for robust hydrogel coatings with exceptional lubricity, displaying the potential application in cartilage replacement materials. Full article
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Figure 1
<p>Schematic illustration of the fabrication of PEEK coated with layered hydrogel (LHP).</p>
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<p>The optical microscopic images of (<b>a</b>) PEEK, (<b>b</b>) HP, (<b>c</b>) LHP-1, (<b>d</b>) LHP-2, and (<b>e</b>) LHP-5 samples, and the cross-sectional image of (<b>f</b>) LHP-2 sample.</p>
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<p>(<b>a</b>,<b>c</b>,<b>e</b>) SEM images of the surface morphologies of LHP-1, LHP-2, and LHP-5 samples; (<b>b</b>,<b>d</b>,<b>f</b>) SEM images of the cross-section morphologies of LHP-1, LHP-2, and LHP-5 samples.</p>
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<p>(<b>a</b>) XPS spectra of PEEK, HP, and LHP-2 samples; (<b>b</b>) fine XPS spectra of Fe 2p for PEEK, HP, and LHP-2 samples.</p>
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<p>(<b>a</b>) Contact angles at different time intervals for PEEK, LHP-2, and LHP-5 samples; (<b>b</b>) the mean contact angles at initial contact (~0 s) for PEEK, HP, LHP-1, LHP-2, and LHP-5 samples. Values in (<b>b</b>) are expressed as mean ± SD (<span class="html-italic">n</span> = 3).</p>
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<p>(<b>a</b>) Schematic illustration of the peeling test process; (<b>b</b>) photograph of the peeling test for LHP-2 sample; (<b>c</b>) force/width versus displacement curve of the peeling test for LHP-2 sample (the inset is the sample after peeling test).</p>
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<p>(<b>a</b>) The friction test curves of different samples in deionized water (load: 5 N; frequency: 1 Hz); (<b>b</b>) the average friction coefficients of different samples. Values in (<b>b</b>) are expressed as mean ± SD (<span class="html-italic">n</span> = 3).</p>
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<p>Optical microscopic images of PEEK, HP, LHP-1, LHP-2, and LHP-5 samples after 1800 friction cycles (middle: wear zone).</p>
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<p>(<b>a</b>) The average friction coefficients of LHP-2 sample under different loads (frequency: 1 Hz; water); (<b>b</b>) the average friction coefficients of LHP-2 sample under different frequencies (load: 5 N; water); (<b>c</b>) the average friction coefficients of LHP-2 sample in biological fluids (load: 5 N; frequency: 1 Hz). Values are expressed as mean ± SD (<span class="html-italic">n</span> = 3).</p>
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<p>(<b>a</b>) Long-term wear resistance properties of LHP-2 sample at a sliding frequency of 1 Hz under an applied load of 5 N (the inset images are the setup for friction test and schematic depiction of friction test, the yellow line represents the COF value of 0.05); (<b>b</b>) the optical and SEM morphologies of LHP-2 sample after long-term friction cycles (the inset is the photograph of LHP-2 sample).</p>
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21 pages, 14432 KiB  
Article
Facile Formation of Multifunctional Biomimetic Hydrogel Fibers for Sensing Applications
by Mengwei Jia, Mingle Guan, Ryan Yao, Yuan Qing, Xiaoya Hou and Jie Zhang
Gels 2024, 10(9), 590; https://doi.org/10.3390/gels10090590 - 13 Sep 2024
Viewed by 833
Abstract
To face the challenges in preparing hydrogel fibers with complex structures and functions, this study utilized a microfluidic coaxial co-extrusion technique to successfully form functional hydrogel fibers through rapid ionic crosslinking. Functional hydrogel fibers with complex structures, including linear fibers, core–shell structure fibers, [...] Read more.
To face the challenges in preparing hydrogel fibers with complex structures and functions, this study utilized a microfluidic coaxial co-extrusion technique to successfully form functional hydrogel fibers through rapid ionic crosslinking. Functional hydrogel fibers with complex structures, including linear fibers, core–shell structure fibers, embedded helical channels, hollow tubes, and necklaces, were generated by adjusting the composition of internal and external phases. The characteristic parameters of the hydrogel fibers (inner and outer diameter, helix generation position, pitch, etc.) were achieved by adjusting the flow rate of the internal and external phases. As biocompatible materials, hydrogel fibers were endowed with electrical conductivity, temperature sensitivity, mechanical enhancement, and freeze resistance, allowing for their use as temperature sensors for human respiratory monitoring and other biomimetic application developments. The hydrogel fibers had a conductivity of up to 22.71 S/m, a response time to respiration of 37 ms, a recovery time of 1.956 s, and could improve the strength of respiration; the tensile strength at break up to 8.081 MPa, elongation at break up to 159%, and temperature coefficient of resistance (TCR) up to −13.080% °C−1 were better than the existing related research. Full article
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<p>(<b>a</b>) Schematic of the preparation of linear hydrogel fibers with temperature-sensitive conductive function. (<b>b</b>) Schematic diagram of hydrogel fibers prepared by ionic crosslinking and covalent crosslinking. (<b>c</b>) Reaction equation of ionic crosslinking and covalent crosslinking.</p>
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<p>(<b>a</b>,<b>b</b>) Preparation of core–shell structured hydrogel fibers, in which the core was red stained for easy observation. (<b>c</b>) Preparation of anti-freeze hydrogel fibers. (<b>d</b>) The molding mechanism of anti-freeze hydrogel fibers, freezing promoted the formation of microcrystalline regions of PVA and the formation of a large number of hydrogen bonds between the hydroxyl groups of PVA and propanetriol, so that the hydrogel fibers had good mechanical and anti-freeze properties.</p>
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<p>Fabrication of hydrogel fibers with embedded helical channel based on heterogenerated rope coil effect [<a href="#B52-gels-10-00590" class="html-bibr">52</a>]: (<b>a</b>) Schematic diagram of rope coil effect. (<b>b</b>) Continuous preparation of calcium alginate hydrogel fibers containing helical channels using a homemade coaxial co-extruder (<span class="html-italic">Q<sub>in</sub></span> is the internal phase solution flow rate, <span class="html-italic">Q<sub>out</sub></span> is the external phase solution flow rate, <span class="html-italic">D<sub>hsp</sub></span> is the helix-starting position, <span class="html-italic">D<sub>out</sub></span> is the diameter of the calcium alginate hydrogel fiber, <span class="html-italic">D<sub>in</sub></span> is the diameter of the embedded helical channel, <span class="html-italic">p</span> is the pitch of the helical channel, and the internal phase calcium chloride aqueous solution is dyed red). (<b>c</b>) Schematic diagram of heterogenerated rope coil effect. (<b>d</b>) Optical magnification of the embedded helical channel hydrogel fibers after CaCl<sub>2</sub> coagulation collection bath. (<b>e</b>–<b>h</b>) Physical and optical magnification of hydrogel fibers with different channels embedded.</p>
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<p>Preparation of hollow tubular hydrogel fibers (<b>a</b>), characteristic dimensions (<b>b</b>,<b>c</b>), and demonstration of circulation (<b>d</b>).</p>
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<p>(<b>a</b>) Preparation of necklace-shaped hydrogel fibers, with black staining of the oil phase for observation. (<b>b</b>) (<b>i</b>,<b>ii</b>) Physical photographs of necklace-shaped hydrogel fibers. (<b>c</b>) (<b>i</b>–<b>iii</b>) (<b>i</b>,<b>ii</b>) Modulation of the spacing of embedded oil-phase microspheres by adjusting the flow rate of the internal-phase solution; (<b>iii</b>) Change in the shape of hydrogel fibers after drying.</p>
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<p>Testing characterization of hydrogel microfiber: (<b>a</b>) Temperature response of PNIPAM/Ca-Alg hydrogel microfiber demonstrated. (<b>b</b>) Conductivity demonstration of PEDOT:PSS/PNIPAM/Ca-Alg hydrogel microfiber. (<b>c</b>) Variation of sample resistance with time and length. (<b>d</b>) Hydrogel microfiber lost water and became thin. (<b>e</b>) Physical demonstration and microscopic morphology of hydrogel microfiber.</p>
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<p>(<b>a</b>) Effect of internal phase flow rate on antifreeze hydrogel fiber diameter. (<b>b</b>) Effect of external phase flow rate on the diameter of antifreeze hydrogel fibers.</p>
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<p>(<b>a</b>) Effect of NaCl content on the diameter of antifreeze hydrogel fibers. (<b>b</b>) Effect of NaCl content on the conductivity of antifreeze hydrogel fibers. (<b>c</b>) Effect of stretching process of antifreeze hydrogel fiber on the brightness of light-emitting diode. (<b>d</b>) Effect of NaCl content on the breaking tensile strength of antifreeze hydrogel fibers. (<b>e</b>) SEM observation of pristine PVA/GL antifreeze hydrogel fibers. (<b>f</b>) SEM observation of stretched PVA/GL antifreeze hydrogel fibers. (<b>g</b>) Effect of NaCl content on elongation at break of antifreeze hydrogel fibers. (<b>h</b>) SEM observation of pristine PVA/GL/NaCl antifreeze hydrogel fibers. (<b>i</b>) SEM observation of stretched PVA/GL/NaCl antifreeze hydrogel fibers.</p>
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<p>Diameter, electrical conductivity, and mechanical properties of fibers with different formulations. Microscopic morphology of PVA/GL fiber (<b>a</b>), PVA/GL/NaCl fiber (<b>b</b>), PVA/GL/Na-Alg fiber (<b>c</b>), PVA/GL/PNIPAM fiber (<b>d</b>), PVA/GL/NaCl/Na-Alg fiber (<b>e</b>), PVA/GL/NaCl/PNIPAM fiber (<b>f</b>), PVA/GL/NaCl/PNIPAM/Na-Alg fiber (<b>g</b>).</p>
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<p>Effect of inner- and outer-phase flow rates on characteristic parameters: (<b>a</b>) The effect of increasing <span class="html-italic">Q<sub>in</sub></span> on <span class="html-italic">L<sub>hsp</sub></span> with fixed <span class="html-italic">Q<sub>out</sub></span>. (<b>b</b>) The effect of increasing <span class="html-italic">Q<sub>out</sub></span> on <span class="html-italic">L<sub>hsp</sub></span> with fixed <span class="html-italic">Q<sub>in</sub></span>. (<b>c</b>) The effect of fixed <span class="html-italic">Q<sub>out</sub></span> and increasing <span class="html-italic">Q<sub>in</sub></span> on <span class="html-italic">D<sub>in</sub></span> and <span class="html-italic">D<sub>out</sub></span>. (<b>d</b>) The effect of fixed <span class="html-italic">Q<sub>in</sub></span> and increasing <span class="html-italic">Q<sub>out</sub></span> on <span class="html-italic">D<sub>in</sub></span> and <span class="html-italic">D<sub>out</sub></span>. (<b>e</b>) The effects of fixed <span class="html-italic">Q<sub>out</sub></span> and increasing <span class="html-italic">Q<sub>in</sub></span> on <span class="html-italic">p</span>, where <span class="html-italic">Q<sub>in</sub></span> for (<b>i</b>–<b>vi</b>) was 25, 35, 50, 65, 80, 100 μL/min in that order. (<b>f</b>) The effects of fixed <span class="html-italic">Q<sub>in</sub></span> and increasing <span class="html-italic">Q<sub>out</sub></span> on <span class="html-italic">p</span>, where <span class="html-italic">Q<sub>out</sub></span> for (<b>i</b>–<b>vi</b>) was 480, 500, 640, 800, 960, and 1040 μL/min in that order.</p>
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<p>Conductivity, tensile, and circulation tests of hydrogel fibers with embedded helical channels: (<b>a</b>) The variation of resistance with length for hydrogel fibers in wet and dry states, where the inset figure (<b>i</b>) showed the physical appearance of hydrogel fibers with PEDOT:PSS added. (<b>b</b>) Local enlargements of hydrogel fibers before (<b>i</b>) and after stretching (<b>ii</b>). (<b>c</b>) Local enlargements of hydrogel fibers with PVA added before (<b>i</b>) and after (<b>ii</b>) stretching. (<b>d</b>) Long-distance injection flow performance of embedded helical channel hydrogel fibers (<b>i</b>), where (<b>ii</b>,<b>iii</b>) were local enlargements. (<b>e</b>) Slow release phenomenon of embedded helical channel hydrogel fibers.</p>
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<p>Thermosensitive and electrically conductive hydrogel fibers for human respiratory monitoring. Relative change rates of resistance of hydrogel fibers during (<b>a</b>) normal and (<b>b</b>) fluctuating breathing. (<b>c</b>) Response time and (<b>d</b>) recovery time for monitoring the change in hydrogel fiber resistance during normal breathing.</p>
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<p>Anti-freeze hydrogel fibers for temperature sensing. Cycling tests for warming from 22 °C to (<b>a</b>,<b>b</b>) 30 °C and (<b>c</b>,<b>d</b>) 55 °C, and the respective response and recovery times. (<b>e</b>,<b>f</b>) TCR of hydrogel fibers and comparison with related research. (<b>g</b>–<b>i</b>) Fitted curves of TCR for different temperature intervals.</p>
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<p>Schematic diagram showing the preparation of multifunctional biomimetic hydrogel fibers.</p>
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23 pages, 6430 KiB  
Review
Bio-Inspired Strategies Are Adaptable to Sensors Manufactured on the Moon
by Alex Ellery
Biomimetics 2024, 9(8), 496; https://doi.org/10.3390/biomimetics9080496 - 15 Aug 2024
Viewed by 1267
Abstract
Bio-inspired strategies for robotic sensing are essential for in situ manufactured sensors on the Moon. Sensors are one crucial component of robots that should be manufactured from lunar resources to industrialize the Moon at low cost. We are concerned with two classes of [...] Read more.
Bio-inspired strategies for robotic sensing are essential for in situ manufactured sensors on the Moon. Sensors are one crucial component of robots that should be manufactured from lunar resources to industrialize the Moon at low cost. We are concerned with two classes of sensor: (a) position sensors and derivatives thereof are the most elementary of measurements; and (b) light sensing arrays provide for distance measurement within the visible waveband. Terrestrial approaches to sensor design cannot be accommodated within the severe limitations imposed by the material resources and expected manufacturing competences on the Moon. Displacement and strain sensors may be constructed as potentiometers with aluminium extracted from anorthite. Anorthite is also a source of silica from which quartz may be manufactured. Thus, piezoelectric sensors may be constructed. Silicone plastic (siloxane) is an elastomer that may be derived from lunar volatiles. This offers the prospect for tactile sensing arrays. All components of photomultiplier tubes may be constructed from lunar resources. However, the spatial resolution of photomultiplier tubes is limited so only modest array sizes can be constructed. This requires us to exploit biomimetic strategies: (i) optical flow provides the visual navigation competences of insects implemented through modest circuitry, and (ii) foveated vision trades the visual resolution deficiencies with higher resolution of pan-tilt motors enabled by micro-stepping. Thus, basic sensors may be manufactured from lunar resources. They are elementary components of robotic machines that are crucial for constructing a sustainable lunar infrastructure. Constraints imposed by the Moon may be compensated for using biomimetic strategies which are adaptable to non-Earth environments. Full article
(This article belongs to the Special Issue A Systems Approach to BioInspired Design)
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<p>Artistic impression of a lunar industrial architecture for building lunar infrastructure.</p>
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<p>Error excursion of camera from its desired pointing trajectory (<b>a</b>) using feedback control alone and (<b>b</b>) using feedback supplemented by feedforward control (from [<a href="#B97-biomimetics-09-00496" class="html-bibr">97</a>]).</p>
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<p>Error excursion of camera from its desired pointing trajectory (<b>a</b>) using feedback control alone and (<b>b</b>) using feedback supplemented by feedforward control (from [<a href="#B97-biomimetics-09-00496" class="html-bibr">97</a>]).</p>
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<p>FDM-printed rotor and stator using Proto-Pasta<sup>TM</sup>: the rotor has a diameter of 50 mm by length of 15 mm embedded with the stator of width of 95 mm by height of 105 mm by length of 25 mm.</p>
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<p>Industrial ecology for industrialisation of the Moon [<a href="#B22-biomimetics-09-00496" class="html-bibr">22</a>] (emboldened oxides are feedstock for molten salt electrolytic reduction to metal [<a href="#B14-biomimetics-09-00496" class="html-bibr">14</a>]).</p>
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20 pages, 3370 KiB  
Review
Biomimetic Neuromorphic Sensory System via Electrolyte Gated Transistors
by Sheng Li, Lin Gao, Changjian Liu, Haihong Guo and Junsheng Yu
Sensors 2024, 24(15), 4915; https://doi.org/10.3390/s24154915 - 29 Jul 2024
Viewed by 1408
Abstract
Biomimetic neuromorphic sensing systems, inspired by the structure and function of biological neural networks, represent a major advancement in the field of sensing technology and artificial intelligence. This review paper focuses on the development and application of electrolyte gated transistors (EGTs) as the [...] Read more.
Biomimetic neuromorphic sensing systems, inspired by the structure and function of biological neural networks, represent a major advancement in the field of sensing technology and artificial intelligence. This review paper focuses on the development and application of electrolyte gated transistors (EGTs) as the core components (synapses and neuros) of these neuromorphic systems. EGTs offer unique advantages, including low operating voltage, high transconductance, and biocompatibility, making them ideal for integrating with sensors, interfacing with biological tissues, and mimicking neural processes. Major advances in the use of EGTs for neuromorphic sensory applications such as tactile sensors, visual neuromorphic systems, chemical neuromorphic systems, and multimode neuromorphic systems are carefully discussed. Furthermore, the challenges and future directions of the field are explored, highlighting the potential of EGT-based biomimetic systems to revolutionize neuromorphic prosthetics, robotics, and human–machine interfaces. Through a comprehensive analysis of the latest research, this review is intended to provide a detailed understanding of the current status and future prospects of biomimetic neuromorphic sensory systems via EGT sensing and integrated technologies. Full article
(This article belongs to the Section Biosensors)
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<p>Schematic diagram of the integral architecture of the biomimetic neuromorphic sensory system and the biological nervous sensory system, depicting, on the left, the pathway from sensing to the neurological signal acquisition element to the implementation of the artificial brain, and on the right, the signaling process in a living organism [<a href="#B76-sensors-24-04915" class="html-bibr">76</a>,<a href="#B77-sensors-24-04915" class="html-bibr">77</a>].</p>
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<p>Working mechanisms of the operation of (<b>a</b>) EDL transistors and (<b>b</b>) ECTs at different gate voltages [<a href="#B75-sensors-24-04915" class="html-bibr">75</a>]. (<b>c</b>) Schematic diagram of a neurotransmitter-mediated chemical synapse between biological neurons. (<b>d</b>,<b>e</b>) Schematic illustration of typical synaptic transistor characteristics [<a href="#B46-sensors-24-04915" class="html-bibr">46</a>,<a href="#B92-sensors-24-04915" class="html-bibr">92</a>]. (Pink lines represents the pre-synaptic stimulis, and blue plot indecates the EPSC) (<b>f</b>) Three major stages of memory and forgetting in the human brain, as described by the Atkinson–Shiffrin memory model [<a href="#B93-sensors-24-04915" class="html-bibr">93</a>]. (<b>g</b>) Transformation from STP to LTP by stimulation with different frequencies and pulses [<a href="#B94-sensors-24-04915" class="html-bibr">94</a>]. (<b>h</b>) Artificial synaptic learning and forgetting processes [<a href="#B95-sensors-24-04915" class="html-bibr">95</a>]. (Red dots indicate increasing synaptic weights during potentiation corresponding to the left panel, and blue dots shows decreasing synaptic weights during depression).</p>
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<p>(<b>a</b>) Structure of biological neurons and (<b>b</b>) bioelectric signals generated by neurons. (<b>c</b>–<b>e</b>) Various model-based artificial neural components and their corresponding neural pulse signals [<a href="#B73-sensors-24-04915" class="html-bibr">73</a>,<a href="#B130-sensors-24-04915" class="html-bibr">130</a>,<a href="#B131-sensors-24-04915" class="html-bibr">131</a>,<a href="#B132-sensors-24-04915" class="html-bibr">132</a>,<a href="#B133-sensors-24-04915" class="html-bibr">133</a>].</p>
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<p>Tactile perception system based on EGTs. (<b>a</b>) Biological and neuromorphic mechanisms for tactile sensing systems, with (<b>b</b>) TENG for mechanosensory and power supply functions. (<b>c</b>,<b>d</b>) Optical image of the integrated tactile system showing two TENG inputs and their synaptic signals [<a href="#B134-sensors-24-04915" class="html-bibr">134</a>]. (<b>e</b>) Schematic diagram of the overall process for implementing an artificial sensory (tactile and temperature) motion loop, combining a ring oscillator and an edge detection module. (<b>f</b>,<b>g</b>) Structural diagram of the artificial sensorimotor system and pulse train output under five variable stages, according to the pressure sensor [<a href="#B135-sensors-24-04915" class="html-bibr">135</a>].</p>
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<p>(<b>a</b>) Biological optical synapses and artificial photoelectric synapses. (<b>b</b>) Photoresponsive principles and photoactive materials for EGTs [<a href="#B136-sensors-24-04915" class="html-bibr">136</a>]. (<b>c</b>) Photomodulated neuromorphic systems, comprising photodetector units, neuromorphic transistors, amplification circuits, and actuators. The red arrow indicates the inputs to the synaptic transistor, and the blue arrows represent the synapse-like output. (<b>d</b>) Neuromorphic signaling of visible light response based on various encoding modalities [<a href="#B145-sensors-24-04915" class="html-bibr">145</a>].</p>
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<p>(<b>a</b>) A schematic of a modular neuromorphic biosensor showcasing various functions. (<b>b</b>) Conductance values of electrochemical random-access memories within a small neuromorphic array, along with three electrochemical random-access memory devices serving as synaptic weights [<a href="#B146-sensors-24-04915" class="html-bibr">146</a>]. (<b>c</b>) The c-OECN circuit of Na-OECT for Na<sup>+</sup> ion sensing and its integration with the mouse vagus nerve using an OECT-based amplifier. The image also displays the amplifier output and corresponding heart rate changes at various concentrations of NaCl [<a href="#B132-sensors-24-04915" class="html-bibr">132</a>]. (<b>d</b>) A schematic representation of a biohybrid neuron, composed of an organic artificial spiking neuron and a doped biofilm. The image further illustrates the variation of I<sub>out</sub> of biohybrid neurons over time and corresponding time-frequency analysis [<a href="#B72-sensors-24-04915" class="html-bibr">72</a>]. (<b>e</b>) A schematic representation of an artificial neuron in conjunction with a biological neuron, where the dopamine concentration at the cell–device interface is contingent on the firing rate of the presynaptic neuron. Moreover, the change in the postsynaptic current is dependent on the pulse rate of the presynaptic and postsynaptic salient regions, giving rise to the associated spike-learning mechanism [<a href="#B147-sensors-24-04915" class="html-bibr">147</a>].</p>
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<p>(<b>a</b>) Signal processing in biosensory systems, in which presynaptic impulses from a preneuron are transmitted through the axon to the synapse to elicit a postsynaptic response in response to an external stimulus. (<b>b</b>) The direction of the sound is determined by calculating the difference between the currents of the two post-neurons (ΔI<sub>PSC</sub>) as a function of time. (<b>c</b>) Detection of 0.1 M and 1 M acetic acid and generation of taste mappings in a 3 × 3 array artificial tongue arrangement scheme [<a href="#B148-sensors-24-04915" class="html-bibr">148</a>]. (<b>d</b>) BASE patches for visual and tactile fusion. Subfigures (<b>i</b>) to (<b>iv</b>) show the photodetector, pressure sensor, hydrogel (stained with 0.04% methylene blue), and synaptic transistor, respectively. The scale bar is 5 mm. (<b>e</b>) Visual–haptic fusion motion control. Subfigure (<b>I</b>): “Yes” and “No” positions inferred from visual (top, pink) or haptic (bottom, blue) feedback. The position is labeled as “yes” if the robot’s hand can hold the ball based on one type of sensory feedback, and “no” otherwise. Subfigure (<b>II</b>): Enlarged image of the modified BASE patch and the BASE patch on the robot. The scale line is 5 mm [<a href="#B149-sensors-24-04915" class="html-bibr">149</a>]. (<b>f</b>) Schematic of NISNT after repeated stretching and recovery. (<b>g</b>) Photographs of NISNT attached to the knuckle in three gestures, and schematic diagrams of the joint in three different degrees of finger bending (case #1, straight; case #2, 30°; and case #3, 45°), The scale bar is 1 cm. (<b>h</b>) The confusion matrix for three different gesture categorization tests with different exposure times and numbers of iterations [<a href="#B150-sensors-24-04915" class="html-bibr">150</a>].</p>
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11 pages, 4012 KiB  
Article
Flexible Organic Electrochemical Transistors for Energy-Efficient Neuromorphic Computing
by Li Zhu, Junchen Lin, Yixin Zhu, Jie Wu, Xiang Wan, Huabin Sun, Zhihao Yu, Yong Xu and Cheeleong Tan
Nanomaterials 2024, 14(14), 1195; https://doi.org/10.3390/nano14141195 - 12 Jul 2024
Viewed by 1058
Abstract
Brain-inspired flexible neuromorphic devices are of great significance for next-generation high-efficiency wearable sensing and computing systems. In this paper, we propose a flexible organic electrochemical transistor using poly[(bithiophene)-alternate-(2,5-di(2-octyldodecyl)- 3,6-di(thienyl)-pyrrolyl pyrrolidone)] (DPPT-TT) as the organic semiconductor and poly(methyl methacrylate) (PMMA)/LiClO4 solid-state electrolyte as [...] Read more.
Brain-inspired flexible neuromorphic devices are of great significance for next-generation high-efficiency wearable sensing and computing systems. In this paper, we propose a flexible organic electrochemical transistor using poly[(bithiophene)-alternate-(2,5-di(2-octyldodecyl)- 3,6-di(thienyl)-pyrrolyl pyrrolidone)] (DPPT-TT) as the organic semiconductor and poly(methyl methacrylate) (PMMA)/LiClO4 solid-state electrolyte as the gate dielectric layer. Under gate voltage modulation, an electric double layer (EDL) forms between the dielectric layer and the channel, allowing the device to operate at low voltages. Furthermore, by leveraging the double layer effect and electrochemical doping within the device, we successfully mimic various synaptic behaviors, including excitatory post-synaptic currents (EPSC), paired-pulse facilitation (PPF), high-pass filtering characteristics, transitions from short-term plasticity (STP) to long-term plasticity (LTP), and demonstrate its image recognition and storage capabilities in a 3 × 3 array. Importantly, the device’s electrical performance remains stable even after bending, achieving ultra-low-power consumption of 2.08 fJ per synaptic event at −0.001 V. This research may contribute to the development of ultra-low-power neuromorphic computing, biomimetic robotics, and artificial intelligence. Full article
(This article belongs to the Special Issue Neuromorphic Devices: Materials, Structures and Bionic Applications)
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<p>(<b>a</b>) Schematic diagram of the device structure. (<b>b</b>) Cross-sectional SEM image of the organic electrochemical transistor. (<b>c</b>) 3D AFM morphology image of the DPPT-TT film surface. (<b>d</b>) Raman spectrum of DPPT-TT, with an inset showing the molecular structure of DPPT-TT (A = 1367 cm<sup>−1</sup>, B = 1405 cm<sup>−1</sup>, C = 1432 cm<sup>−1</sup>, D = 1512 cm<sup>−1</sup>).</p>
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<p>(<b>a</b>) Working mechanism of the OECT. (<b>b</b>) C–F characteristic curve of the PMMA/LiClO<sub>4</sub> film, with an inset showing the I-V characteristic curve of the PMMA/LiClO<sub>4</sub> film. (<b>c</b>) Transfer characteristic curve of the OECT device. (<b>d</b>) Output characteristic curve as V<sub>GS</sub> varies from 0 V to −2 V.</p>
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<p>(<b>a</b>) Schematic of the artificial synapse. (<b>b</b>) Current response of the organic OECT to pulse voltage stimulation. (<b>c</b>) EPSC characteristics dependent on peak voltage at V<sub>DS</sub> = −0.5 V with single-pulse triggering (V<sub>GS</sub> = −2 V, 110 ms). (<b>d</b>) Function graph of PPF index (A<sub>2</sub>/A<sub>1</sub> × 100%) as a function of time interval Δt between two electrical pulses, with an inset showing the PPF behavior triggered by two consecutive electrical pulses (−2 V, 290 ms).</p>
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<p>(<b>a</b>) EPSC triggered by eight consecutive pulse sequences at different frequencies (−2 V, 290 ms). (<b>b</b>) Relationship between EPSC gain triggered by consecutive electrical pulse stimulation and pulse frequency, with an inset showing the simulated high-pass filtering behavior of the device.</p>
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<p>OECT device’s EPSC responses triggered by (<b>a</b>) different pulse widths, (<b>b</b>) different numbers, and (<b>c</b>) different gate voltages. Inset shows the EPSC holding value after 30 s of decay. Statistics of weight change after the stimulation ends for (<b>d</b>) different pulse widths, (<b>e</b>) different numbers, and (<b>f</b>) different gate voltages after 15 s and 30 s of decay.</p>
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<p>Image memory in the OECT 3 × 3 imaging array. The change in current values after stimulation with different numbers of pulses (−2 V, pulse width and pulse interval both 160 ms) under V<sub>DS</sub> = −1 V.</p>
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<p>(<b>a</b>) Optical image of the OECT device in a bent state. (<b>b</b>) Transfer characteristics curves of the flexible device in bent (bending radius = 5 mm) and unbent states. (<b>c</b>) EPSC response triggered at different V<sub>DS</sub> and corresponding power consumption. (<b>d</b>) The power consumption of our work is compared with that of some recently published papers [<a href="#B7-nanomaterials-14-01195" class="html-bibr">7</a>,<a href="#B43-nanomaterials-14-01195" class="html-bibr">43</a>,<a href="#B44-nanomaterials-14-01195" class="html-bibr">44</a>,<a href="#B45-nanomaterials-14-01195" class="html-bibr">45</a>,<a href="#B46-nanomaterials-14-01195" class="html-bibr">46</a>,<a href="#B47-nanomaterials-14-01195" class="html-bibr">47</a>,<a href="#B48-nanomaterials-14-01195" class="html-bibr">48</a>,<a href="#B49-nanomaterials-14-01195" class="html-bibr">49</a>,<a href="#B50-nanomaterials-14-01195" class="html-bibr">50</a>,<a href="#B51-nanomaterials-14-01195" class="html-bibr">51</a>,<a href="#B52-nanomaterials-14-01195" class="html-bibr">52</a>].</p>
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25 pages, 13480 KiB  
Review
Conductive Polymer-Based Hydrogels for Wearable Electrochemical Biosensors
by Dinakaran Thirumalai, Madhappan Santhamoorthy, Seong-Cheol Kim and Hyo-Ryoung Lim
Gels 2024, 10(7), 459; https://doi.org/10.3390/gels10070459 - 12 Jul 2024
Cited by 3 | Viewed by 1705
Abstract
Hydrogels are gaining popularity for use in wearable electronics owing to their inherent biomimetic characteristics, flexible physicochemical properties, and excellent biocompatibility. Among various hydrogels, conductive polymer-based hydrogels (CP HGs) have emerged as excellent candidates for future wearable sensor designs. These hydrogels can attain [...] Read more.
Hydrogels are gaining popularity for use in wearable electronics owing to their inherent biomimetic characteristics, flexible physicochemical properties, and excellent biocompatibility. Among various hydrogels, conductive polymer-based hydrogels (CP HGs) have emerged as excellent candidates for future wearable sensor designs. These hydrogels can attain desired properties through various tuning strategies extending from molecular design to microstructural configuration. However, significant challenges remain, such as the limited strain-sensing range, significant hysteresis of sensing signals, dehydration-induced functional failure, and surface/interfacial malfunction during manufacturing/processing. This review summarizes the recent developments in polymer-hydrogel-based wearable electrochemical biosensors over the past five years. Initially serving as carriers for biomolecules, polymer-hydrogel-based sensors have advanced to encompass a wider range of applications, including the development of non-enzymatic sensors facilitated by the integration of nanomaterials such as metals, metal oxides, and carbon-based materials. Beyond the numerous existing reports that primarily focus on biomolecule detection, we extend the scope to include the fabrication of nanocomposite conductive polymer hydrogels and explore their varied conductivity mechanisms in electrochemical sensing applications. This comprehensive evaluation is instrumental in determining the readiness of these polymer hydrogels for point-of-care translation and state-of-the-art applications in wearable electrochemical sensing technology. Full article
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<p>Chemical structures of conducting polymers: (<b>a</b>) poly(p-phenylene), (<b>b</b>) polyacetylene, (<b>c</b>) polypyrrole (PPy), (<b>d</b>) polythiophene (pTh), (<b>e</b>) polyaniline (PANI), and (<b>f</b>) polyethylene dioxythiophene (PEDOT).</p>
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<p>Conductive hydrogel fabrication and conductive mechanisms. (<b>a</b>) Direct gelation of conductive materials as cross-linking monomers, (<b>b</b>) suspending conductive materials within the hydrogel network, (<b>c</b>) in situ polymerization within a prepolymer hydrogel matrix, and (<b>d</b>) introduction of conductive ionic compounds.</p>
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<p>Fabrication of Ca-PAA-SA-CNT hydrogel-based strain sensor. (<b>a</b>) Human body movement sensing; (<b>b</b>) Ca-PAA-SA-CNT preparation by printing process; (<b>c</b>) prepared Ca-PAA-SA-CNTs HGs; (<b>d</b>) different 3D-printed patterns. Reprinted with permission from Ref. [<a href="#B37-gels-10-00459" class="html-bibr">37</a>].</p>
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<p>(<b>a</b>) Preparation method of rGO/PPy nanocomposite aerogel. The symbol (*) depicts the continuous attachment of the participating monomeric units. (<b>b</b>) Photo image of rGO/PPy composite aerogel standing on a feather. (<b>c</b>) SEM image of rGO/PPy composite aerogel. Reprinted with permission from Ref. [<a href="#B40-gels-10-00459" class="html-bibr">40</a>] (Copyright 2022, Elsevier). (<b>d</b>,<b>e</b>) Mechanical properties of 3D rGO aerogel. (<b>f</b>) Preparation of PANI/rGO composite aerogel by electropolymerization. Reprinted with permission from Ref. [<a href="#B41-gels-10-00459" class="html-bibr">41</a>] (Copyright 2017, Springer).</p>
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<p>(<b>a</b>) Porous CP HGs with GO and PVA show excellent mechanical properties: bend, curl, and stretch. (<b>b</b>,<b>c</b>) PAA-OSA-AG HG mechanical properties. Reprinted with permission of Refs. [<a href="#B65-gels-10-00459" class="html-bibr">65</a>,<a href="#B70-gels-10-00459" class="html-bibr">70</a>].</p>
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<p>Self-healing of cut HGs after rejoining, and the stretching behavior of the healed HGs. Reprinted with permission of Ref. [<a href="#B79-gels-10-00459" class="html-bibr">79</a>].</p>
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<p>(<b>a</b>) The hydrogel patch is versatile, allowing for sweat sampling at various locations during periods of rest. (<b>b</b>) It can be placed on the finger, palm, or back of the hand for efficient sweat collection. (<b>c</b>) It utilizes preferential glucose pathways to sample sweat naturally through the hydrogel patches. (<b>d</b>) The sweat glucose sensor features a multi-layered enzymatic PB-PEDOT NC electrode and operates with a GOx mechanism alongside a PB probe. (<b>e</b>) This device is capable of monitoring sweat glucose levels without the need for high-intensity activity or external stimuli, at various sites including the finger (F), palm (P), and back of the hand (B). Reprinted with permission from Ref. [<a href="#B110-gels-10-00459" class="html-bibr">110</a>] (Copyright 2022, Elsevier).</p>
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<p>(<b>a</b>) Preparation of the LOx@CS PC sensor. (<b>b</b>–<b>e</b>) Photographs of the sensors prepared for measuring lactate in sweat. Reprinted with permission from Ref. [<a href="#B120-gels-10-00459" class="html-bibr">120</a>] (Copyright 2024, American Chemical Society).</p>
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<p>(<b>a</b>) Depiction of a wearable sweat patch designed for cortisol level monitoring. This device integrates a microfluidic system with an electrochemical sensor that captures, processes, and instantaneously detects cortisol levels. It employs a conformation-switching aptamer featuring a pseudoknot structure. The measured cortisol concentrations and sweat pH levels can be wirelessly transmitted for visualization and analysis to an adjacent smart device, and measurement of on-body signal regeneration (a–d). (<b>b</b>) Application of the sweat patch on the lower neck of participants during trials. (<b>c</b>) Photographs of the microfluidic reservoir filling with sweat during physical activity, with blue dye added to each inlet for visual confirmation. (<b>d</b>) Test protocol, including control and stress induction phases. (<b>e</b>–<b>g</b>) Continuous monitoring of sweat from three distinct individuals. (<b>h</b>) Long-term continuous monitoring, (h-a) Initial period of exercise, (h-b) Rapid increase after sweat fills the reservoir, (h-c) Subsequent restoration to a normal level in 7–8 minutes, (h-d) Stress was induced by a cold pressure test, corresponding measurement of on-body signal regeneration (a–d). Reprinted with permission from Ref. [<a href="#B126-gels-10-00459" class="html-bibr">126</a>] (Copyright 2023, Elsevier).</p>
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26 pages, 1145 KiB  
Review
Biomimetic Hydrogel Strategies for Cancer Therapy
by Awatef M. Alshehri and Otto C. Wilson
Gels 2024, 10(7), 437; https://doi.org/10.3390/gels10070437 - 30 Jun 2024
Cited by 1 | Viewed by 1470
Abstract
Recent developments in biomimetic hydrogel research have expanded the scope of biomedical technologies that can be used to model, diagnose, and treat a wide range of medical conditions. Cancer presents one of the most intractable challenges in this arena due to the surreptitious [...] Read more.
Recent developments in biomimetic hydrogel research have expanded the scope of biomedical technologies that can be used to model, diagnose, and treat a wide range of medical conditions. Cancer presents one of the most intractable challenges in this arena due to the surreptitious mechanisms that it employs to evade detection and treatment. In order to address these challenges, biomimetic design principles can be adapted to beat cancer at its own game. Biomimetic design strategies are inspired by natural biological systems and offer promising opportunities for developing life-changing methods to model, detect, diagnose, treat, and cure various types of static and metastatic cancers. In particular, focusing on the cellular and subcellular phenomena that serve as fundamental drivers for the peculiar behavioral traits of cancer can provide rich insights into eradicating cancer in all of its manifestations. This review highlights promising developments in biomimetic nanocomposite hydrogels that contribute to cancer therapies via enhanced drug delivery strategies and modeling cancer mechanobiology phenomena in relation to metastasis and synergistic sensing systems. Creative efforts to amplify biomimetic design research to advance the development of more effective cancer therapies will be discussed in alignment with international collaborative goals to cure cancer. Full article
(This article belongs to the Special Issue Cancer Cell Biology in Biological Hydrogel)
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<p>Schematic to represent the tumor microenvironment (TME) and biomimetic strategies of tumor microenvironment models: composition of the TME and cellular and non-cellular components (<b>right</b>); biomimetic strategies of tumor microenvironment model, in vivo and in vitro, associated with the biomimetic features in the TME (<b>left</b>).</p>
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<p>Cell membrane biomimetic nanoparticles consist of cell membrane coatings encapsulating different nanoparticles (NPs) for cancer therapy.</p>
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<p>Comparison between primary tumor and MACMM model: (<b>a</b>) schematic representation of a primary tumor microenvironment structure, (<b>b</b>) the magnetically actuated cancer metastasis model (MACMM) provides the ability for microstructural alterations involving compression, tension, and shear on the collagen network to mimic the in vivo micromechanical environment surrounding a tumor.</p>
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23 pages, 3937 KiB  
Review
Progress on Electrochemical Biomimetic Nanosensors for the Detection and Monitoring of Mycotoxins and Pesticides
by Kavitha Lakavath, Chandan Kafley, Anjana Sajeevan, Soumyajit Jana, Jean Louis Marty and Yugender Goud Kotagiri
Toxins 2024, 16(6), 244; https://doi.org/10.3390/toxins16060244 - 26 May 2024
Viewed by 1063
Abstract
Monitoring agricultural toxins such as mycotoxins is crucial for a healthy society. High concentrations of these toxins lead to the cause of several chronic diseases; therefore, developing analytical systems for detecting/monitoring agricultural toxins is essential. These toxins are found in crops such as [...] Read more.
Monitoring agricultural toxins such as mycotoxins is crucial for a healthy society. High concentrations of these toxins lead to the cause of several chronic diseases; therefore, developing analytical systems for detecting/monitoring agricultural toxins is essential. These toxins are found in crops such as vegetables, fruits, food, and beverage products. Currently, screening of these toxins is mostly performed with sophisticated instrumentation such as chromatography and spectroscopy techniques. However, these techniques are very expensive and require extensive maintenance, and their availability is limited to metro cities only. Alternatively, electrochemical biomimetic sensing methodologies have progressed hugely during the last decade due to their unique advantages like point-of-care sensing, miniaturized instrumentations, and mobile/personalized monitoring systems. Specifically, affinity-based sensing strategies including immunosensors, aptasensors, and molecular imprinted polymers offer tremendous sensitivity, selectivity, and stability to the sensing system. The current review discusses the principal mechanisms and the recent developments in affinity-based sensing methodologies for the detection and continuous monitoring of mycotoxins and pesticides. The core discussion has mainly focused on the fabrication protocols, advantages, and disadvantages of affinity-based sensing systems and different exploited electrochemical transduction techniques. Full article
(This article belongs to the Section Mycotoxins)
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<p>Schematic representation of an overview of the biomimetic nanosensors towards the detection of mycotoxins and pesticides.</p>
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<p>Scopus search results of mycotoxins and pesticide detection through electrochemical MIP/aptamer-based sensors for the period of 2018 to 2024.</p>
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<p>Schematic representation for the synthesis of MIPs. (i) Self-assembly of the template, functional monomer, and cross-linker. (ii) Polymerization of the template with a monomer and crosslinker. (iii) Removal of the template from the molecular imprint and creation of cavities. Reproduced with permission [<a href="#B50-toxins-16-00244" class="html-bibr">50</a>].</p>
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<p>MIP-based electrochemical sensor for mycotoxins detection. (<b>A</b>) MIP-based techniques for the evaluation of the mycotoxins AFB1 and FuB1 [<a href="#B50-toxins-16-00244" class="html-bibr">50</a>]. (<b>B</b>) A nano MIP-based plasmonic sensor for AFM1 detection in raw milk samples [<a href="#B55-toxins-16-00244" class="html-bibr">55</a>]. (<b>C</b>) A novel MIP-capped AgNPs@ZnMOF sensor for patulin detection [<a href="#B58-toxins-16-00244" class="html-bibr">58</a>].</p>
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<p>Electrochemically labeled aptasensors for the detection of mycotoxins. (<b>A</b>) Functionalized GO-based electrochemically labeled aptasensor for AFB1 detection employing an MB-labeled aptamer as the signaling fragment [<a href="#B20-toxins-16-00244" class="html-bibr">20</a>]. (<b>B</b>) AuNP-modified gold electrode and luminescence-labelled aptamer approach for OTA measurement in wheat samples [<a href="#B84-toxins-16-00244" class="html-bibr">84</a>].</p>
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<p>Electrochemical label-free aptasensors for the detection of mycotoxins. (<b>A</b>) Principle of label-free detection of AFM1 with magneto-electrochemical Fe<sub>3</sub>O<sub>4</sub>/PANi-based aptasensor [<a href="#B85-toxins-16-00244" class="html-bibr">85</a>]. (<b>B</b>) Au/MWCNT-rGONR based label-free electrochemical aptasensors for the detection of acetamiprid [<a href="#B103-toxins-16-00244" class="html-bibr">103</a>]. (<b>C</b>) Label-free electrochemical aptasensor, SPCE/4-CP/Apt/AFB1 for the detection of AFB1 [<a href="#B94-toxins-16-00244" class="html-bibr">94</a>].</p>
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<p>MIP-based electrochemical sensor for pesticide detection. (<b>A</b>) The Au-SPE-based MIP sensor is designed to detect MAL in olive oil and fruits [<a href="#B74-toxins-16-00244" class="html-bibr">74</a>]. (<b>B</b>) MOF-based MIP sensor for the detection of MP [<a href="#B113-toxins-16-00244" class="html-bibr">113</a>]. (<b>C</b>) A GCE MIP-based nanosensor for ATR detection [<a href="#B73-toxins-16-00244" class="html-bibr">73</a>]. (<b>D</b>) Detection of CBZ using Mo<sub>2</sub>C/C spheres (N, S-Mo<sub>2</sub>C) integrated with MIP [<a href="#B75-toxins-16-00244" class="html-bibr">75</a>].</p>
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13 pages, 4288 KiB  
Article
Ti3C2 Nanosheets Functionalized with Ferritin–Biomimetic Platinum Nanoparticles for Electrochemical Biosensors of Nitrite
by Rongqiu Mu, Danzhu Zhu and Gang Wei
Biosensors 2024, 14(5), 258; https://doi.org/10.3390/bios14050258 - 19 May 2024
Cited by 1 | Viewed by 1391
Abstract
Nitrites widely exist in human life and the natural environment, but excessive contents of nitrites will result in adverse effects on the environment and human health; hence, sensitive and stable nitrite detection systems are needed. In this study, we report the synthesis of [...] Read more.
Nitrites widely exist in human life and the natural environment, but excessive contents of nitrites will result in adverse effects on the environment and human health; hence, sensitive and stable nitrite detection systems are needed. In this study, we report the synthesis of Ti3C2 nanosheets functionalized with apoferritin (ApoF)–biomimetic platinum (Pt) nanoparticle (Pt@ApoF/Ti3C2) composite materials, which were formed by using ApoF as a template and protein-inspired biomineralization. The formed nanohybrid exhibits excellent electrochemical sensing performance towards nitrite (NaNO2). Specifically, the Pt@ApoF catalyzes the conversion of nitrites into nitrates, converting the chemical signal into an electrical signal. The prepared Pt@ApoF/Ti3C2-based electrochemical NaNO2 biosensors demonstrate a wide detection range of 0.001–9 mM with a low detection limit of 0.425 μM. Additionally, the biosensors possess high selectivity and sensitivity while maintaining a relatively stable electrochemical sensing performance within 7 days, enabling the monitoring of NaNO2 in complex environments. The successful preparation of the Pt@ApoF/Ti3C2 nanohybrid materials provides a new approach for constructing efficient electrochemical biosensors, offering a simple and rapid method for detecting NaNO2 in complex environments. Full article
(This article belongs to the Section Nano- and Micro-Technologies in Biosensors)
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<p>(<b>a</b>) Schematic of GA-crosslinked Pt@ApoF and Ti<sub>3</sub>C<sub>2</sub>; (<b>b</b>) AFM image of Ti<sub>3</sub>C<sub>2</sub> nanosheets, with the number and color line in red corresponding to the monolayer and bilayer thickness of the samples; (<b>c</b>) TEM image of Ti<sub>3</sub>C<sub>2</sub> nanosheets; (<b>d</b>) XRD image of Ti<sub>3</sub>C<sub>2</sub> and Ti<sub>3</sub>AlC<sub>2</sub>.</p>
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<p>(<b>a</b>) AFM image of ferritin; (<b>b</b>) TEM image of ApoF; (<b>c</b>) TEM image of Pt@ApoF; (<b>d</b>) XPS image of ferritin, ApoF, and Pt@ApoF.</p>
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<p>Characterizations of Pt@ApoF/Ti<sub>3</sub>C<sub>2</sub> nanohybrids: (<b>a</b>) AFM image; (<b>b</b>) TEM image; (<b>c</b>,<b>d</b>) TEM-based elemental mapping.</p>
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<p>(<b>a</b>) XPS spectra of Ti<sub>3</sub>C<sub>2</sub> and Pt@ApoF/Ti<sub>3</sub>C<sub>2</sub> nanohybrids; (<b>b</b>) XPS spectra of N in Ti<sub>3</sub>C<sub>2</sub> and Pt@ApoF/Ti<sub>3</sub>C<sub>2</sub> nanohybrids (N in Pt@ApoF/Ti<sub>3</sub>C<sub>2</sub> nanohybrids).</p>
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<p>Electrochemical tests of Pt@ApoF/Ti<sub>3</sub>C<sub>2</sub>/GCE in NaNO<sub>2</sub> detection: (<b>a</b>) CV curves of GCE, apoferritin/GCE, Pt@ApoF/GCE, and Pt@ApoF/Ti<sub>3</sub>C<sub>2</sub>/GCE; (<b>b</b>) current response of Pt@ApoF /Ti<sub>3</sub>C<sub>2</sub>/GCE toward NaNO<sub>2</sub> with different concentrations of 0–10 mM; (<b>c</b>) linear calibration of CV response with NaNO<sub>2</sub> concentration ranging from 0 to 10 mM.</p>
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<p>Electrochemical tests of Pt@ApoF/Ti<sub>3</sub>C<sub>2</sub>/GCE in NaNO<sub>2</sub> detection: (<b>a</b>) I–T response of 0–50 μm concentrations of NaNO<sub>2</sub>; (<b>b</b>) I–T response of different concentrations of NaNO<sub>2</sub>; (<b>c</b>) linear calibration of I–T response with NaNO<sub>2</sub> concentration ranging from 0–50 μm; (<b>d</b>) linear calibration of I–T response with NaNO<sub>2</sub> concentration ranging from 0–9 mM.</p>
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<p>Anti-interference ability and stability of Pt@ApoF/Ti<sub>3</sub>C<sub>2</sub>−based electrochemical platform. (<b>a</b>) Amperometric responses upon successive additions of NaNO<sub>2</sub>, NaCl, KCl, CaCl<sub>2</sub>, MgCl<sub>2</sub>, CuCl<sub>2</sub>, FeCl<sub>3</sub>, Na<sub>2</sub>CO<sub>3</sub>, KNO<sub>3</sub>, AgNO<sub>3</sub>, NH<sub>4</sub><sup>+</sup>, HCl, CH<sub>3</sub>COOH, Na<sub>2</sub>SO<sub>4</sub>, NaBr, Na<sub>2</sub>PHO<sub>4</sub>, and NaNO<sub>2</sub>; (<b>b</b>) stability of Pt@ApoF/Ti<sub>3</sub>C<sub>2</sub> electrochemical platform for 7 days; (<b>c</b>) current response of Pt@ApoF/Ti<sub>3</sub>C<sub>2</sub>/GCE toward NaNO<sub>2</sub> with different concentrations of 0–20 mM in milk; (<b>d</b>) linear calibration of CV response with NaNO<sub>2</sub> concentration ranging from 0 to 20 mM in milk.</p>
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<p>Schematic fabrication of electrochemical nitrite biosensors based on biomimetic Pt@ApoF/Ti<sub>3</sub>C<sub>2</sub>.</p>
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22 pages, 1716 KiB  
Article
Integration of Sensor Fusion to Enhance Quality Assessment of White Brine Cheeses
by Zlatin Zlatev, Tatjana Spahiu, Ira Taneva, Milen Dimov and Miroslav Vasilev
Dairy 2024, 5(2), 249-270; https://doi.org/10.3390/dairy5020021 - 30 Apr 2024
Viewed by 1135
Abstract
The article examines the main characteristics of white brine cheeses from different manufacturers and changes in their quality indicators. These characteristics include the active acidity, electrical conductivity, total dissolved solids, oxidation–reduction potential, and organoleptic assessment. In this context, the connection to biomimetics lies [...] Read more.
The article examines the main characteristics of white brine cheeses from different manufacturers and changes in their quality indicators. These characteristics include the active acidity, electrical conductivity, total dissolved solids, oxidation–reduction potential, and organoleptic assessment. In this context, the connection to biomimetics lies in the approach of integrating multiple sensory modalities, similar to how biological systems often use multiple senses to perceive and understand their environment. For this purpose, spectral, ultrasonic, and gas characteristics were used, from which informative indices were extracted, united at a later stage in a vector of features. Based on the classification, it was found that the optical characteristics of cheeses from different manufacturers overlap, thus making it possible to predict the main indicators for each type of cheese. The results show that the use of a multimodal approach combining features from different sensors contributes to a better understanding of the variations in cheese properties, while improving the predictive abilities of the created models. The obtained results give a clear idea of the quality of the cheese, thus enabling adequate decisions to be made during the production process. Full article
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<p>Early feature fusion steps.</p>
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<p>Spectral characteristics of cheese from three manufacturers.</p>
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<p>Gas characteristics for cheese from three manufacturers.</p>
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<p>Ultrasonic characteristics of cheese from three manufacturers.</p>
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<p>Classification examples between M1 and M2: (<b>a</b>) Naive Bayesian classifier, (<b>b</b>) discriminant analysis with quadratic function, and (<b>c</b>) SVM with quadratic function.</p>
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<p>Regression models—general view: (<b>a</b>) pH = f(LV<sub>1</sub>,LV<sub>2</sub>), (<b>b</b>) EC = f(LV<sub>1</sub>,LV<sub>2</sub>), (<b>c</b>) TDS = f(LV<sub>1</sub>,LV<sub>2</sub>), and (<b>d</b>) ORP = f(LV<sub>1</sub>,LV<sub>2</sub>).</p>
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<p>Distribution of actual and predicted cheese data: (<b>a</b>) pH, (<b>b</b>) EC, (<b>c</b>) TDS, and (<b>d</b>) ORP.</p>
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33 pages, 4183 KiB  
Review
Biominerals and Bioinspired Materials in Biosensing: Recent Advancements and Applications
by Mohamed A. A. Abdelhamid, Mi-Ran Ki and Seung Pil Pack
Int. J. Mol. Sci. 2024, 25(9), 4678; https://doi.org/10.3390/ijms25094678 - 25 Apr 2024
Cited by 4 | Viewed by 2101
Abstract
Inspired by nature’s remarkable ability to form intricate minerals, researchers have unlocked transformative strategies for creating next-generation biosensors with exceptional sensitivity, selectivity, and biocompatibility. By mimicking how organisms orchestrate mineral growth, biomimetic and bioinspired materials are significantly impacting biosensor design. Engineered bioinspired materials [...] Read more.
Inspired by nature’s remarkable ability to form intricate minerals, researchers have unlocked transformative strategies for creating next-generation biosensors with exceptional sensitivity, selectivity, and biocompatibility. By mimicking how organisms orchestrate mineral growth, biomimetic and bioinspired materials are significantly impacting biosensor design. Engineered bioinspired materials offer distinct advantages over their natural counterparts, boasting superior tunability, precise controllability, and the ability to integrate specific functionalities for enhanced sensing capabilities. This remarkable versatility enables the construction of various biosensing platforms, including optical sensors, electrochemical sensors, magnetic biosensors, and nucleic acid detection platforms, for diverse applications. Additionally, bioinspired materials facilitate the development of smartphone-assisted biosensing platforms, offering user-friendly and portable diagnostic tools for point-of-care applications. This review comprehensively explores the utilization of naturally occurring and engineered biominerals and materials for diverse biosensing applications. We highlight the fabrication and design strategies that tailor their functionalities to address specific biosensing needs. This in-depth exploration underscores the transformative potential of biominerals and materials in revolutionizing biosensing, paving the way for advancements in healthcare, environmental monitoring, and other critical fields. Full article
(This article belongs to the Special Issue New Trends in Molecular Biosensors)
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<p>(<b>A</b>) Schematic illustrating the process for mass-producing diatom biosilica from cultivated diatom microalgae. Potential applications of diatom-based triboelectric nanogenerators (TENGs) in (<b>B</b>) a tremor sensor; (<b>C</b>) a self-powered, biocompatible, innovative mask design; and (<b>D</b>) a skin-attachable power generation device. (<b>A</b>,<b>C</b>): Reproduced with permission from [<a href="#B38-ijms-25-04678" class="html-bibr">38</a>], Copyright 2021 American Chemical Society. (<b>B</b>): Reproduced with permission from [<a href="#B37-ijms-25-04678" class="html-bibr">37</a>], Copyright 2021 Elsevier Ltd. (<b>D</b>): Reproduced with permission from [<a href="#B39-ijms-25-04678" class="html-bibr">39</a>], Copyright 2020 Elsevier Ltd.</p>
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<p>Scanning electron microscopy (SEM) images of (<b>A</b>) a densely packed diatom assembly on a glass slide and (<b>B</b>) a single diatom frustule. (<b>C</b>) Schematic representation of a diatom-based immunoassay for NT-proBNP detection. (<b>A</b>–<b>C</b>): Reproduced with permission from [<a href="#B64-ijms-25-04678" class="html-bibr">64</a>], Copyright 2019 Elsevier B.V.</p>
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<p>Design and fabrication of DNA-silicified templates for Raman optical beacons (DNA-STROBE). (<b>A</b>) Schematic of DNA-mediated silicification for core–satellite gold assemblies. (<b>B</b>) SERS enhancement mapping for DNA–silica hybrid gold assemblies with different core-satellite distances, indicated by yellow numbers in nanometers. (<b>C</b>) Diffraction-limited and (<b>D</b>) super-resolution imaging of plasmonic hotspots on DNA-STROBE. (<b>A</b>–<b>D</b>): Reproduced with permission from [<a href="#B14-ijms-25-04678" class="html-bibr">14</a>], Copyright 2021 Wiley-VCH GmbH.</p>
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<p>Schematic representation of a biomimetic optosensor for nitrite detection. Silaffin R5 peptide-guided silica encapsulation of NAD(P)H and nitrite reductase (NNR) enzyme. Ruthenium complex (pH label) on the silica surface. Nitrite reduction by NNR leads to color change (from orange to yellow) via reflectance. Reproduced with permission from [<a href="#B44-ijms-25-04678" class="html-bibr">44</a>], Copyright 2022 MDPI (CC BY 4.0).</p>
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<p>Fabrication of a coccolith-modified electrochemical aptasensor. The process of creating a coccolith-modified electrodeposited (CME) onto a screen-printed gold electrode (SPGE) is shown. The CME-SPGE serves as the platform for a subsequent cognate pair aptamer-based electrochemical aptasensor. Reproduced with permission from [<a href="#B50-ijms-25-04678" class="html-bibr">50</a>], Copyright 2018 Elsevier B.V.</p>
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<p>Bioinspired calcium carbonate-based ionic skin. (<b>A</b>) Schematic of the biomimetic hydrogel (ACC/PAA/alginate). (<b>B</b>) SEM image of the porous hydrogel structure. (<b>C</b>) Shape-adaptable hydrogel for versatile sensor designs. (<b>D</b>) Working principle: charge accumulation at interfaces upon voltage application for pressure detection. (<b>E</b>) Photograph of a sensor fabricated with biocompatible hydrogel. (<b>F</b>) Finger motion sensor: hydrogel sensor responds to finger bending with real-time capacitance changes. (<b>G</b>) Blood pressure sensor design and real-time signal variation reflecting changes in arm pressure. (<b>A</b>–<b>G</b>): Reproduced with permission from [<a href="#B84-ijms-25-04678" class="html-bibr">84</a>], Copyright 2017 WILEY-VCH Verlag GmbH &amp; Co. KGaA, Weinheim.</p>
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<p>(<b>A</b>) Bioengineered SpyCatcher-functionalized magnetosomes from Magnetospirillum gryphiswaldense. (<b>B</b>) Transmission electron microscopy (TEM) images of isolated magnetosomes obtained from mutant <span class="html-italic">M. gryphiswaldense</span> cells. The organic shell, corresponding to the magnetosome membrane, is indicated by blue arrows. (<b>C</b>) Schematic depiction of the biocatalytic application. The engineered magnetosomes are coupled with SpyTag-fused dimeric phenolic acid decarboxylase (PAD-ST) to facilitate the conversion of p-coumaric acid to p-hydroxystyrene within a magnetic microreactor in flow. (<b>A</b>–<b>C</b>): Reproduced with permission from [<a href="#B99-ijms-25-04678" class="html-bibr">99</a>], Copyright 2022 American Chemical Society (CC BY 4.0).</p>
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<p>Bioengineered bacterial microrobots for multifunctionality. (<b>A</b>) Modular design using SpyCatcher/SpyTag for surface display of functional proteins (Cas12a for DNA detection, Mms6 for biomineralization) on bacterial microrobots. Specificity (<b>B</b>,<b>C</b>) and sensitivity (<b>D</b>,<b>E</b>) of detection of DIV1 and WSSV nucleic acid sequences, respectively. * <span class="html-italic">p</span> &lt; 0.05, ns not significant. Reproduced with permission from [<a href="#B58-ijms-25-04678" class="html-bibr">58</a>], Copyright 2023 American Chemical Society.</p>
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<p>Versatile biomimetic hydroxyapatite for biosensing applications. (<b>A</b>) Magnetic HAP-based electrochemical biosensor for label-free detection of miRNA Let-7a. (<b>B</b>) Piezoresponsive HAP patterns on a biomimetic platform facilitate sensitive recording of extracellular ion currents for studying cell-to-cell communication. (<b>C</b>) HAP-Au-modified electrode for selective detection of SARS-CoV-2 antibodies via an immunosensing approach. (<b>A</b>): Reproduced with permission from [<a href="#B61-ijms-25-04678" class="html-bibr">61</a>], Copyright 2023, American Chemical Society. (<b>B</b>): Reproduced with permission from [<a href="#B110-ijms-25-04678" class="html-bibr">110</a>], Copyright 2024 Elsevier Ltd. (CC BY-NC-ND 4.0). (<b>C</b>): Reproduced with permission from [<a href="#B62-ijms-25-04678" class="html-bibr">62</a>], Copyright 2024 American Chemical Society.</p>
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<p>Biomineralized multifunctional device for detection of paraoxon. Schematic illustration of (<b>A</b>) the fabrication process and (<b>B</b>) the paraoxon assay on the resulting M-OPH-loaded membrane. (<b>C</b>) Absorbance spectra of filtrates obtained from incubating the M-OPH-loaded membrane with different paraoxon concentrations (5–500 μM). (<b>D</b>) Calibration curve for paraoxon detection using the M-OPH-loaded membrane. (<b>A</b>–<b>D</b>): Reproduced with permission from [<a href="#B123-ijms-25-04678" class="html-bibr">123</a>], Copyright 2021 Elsevier B.V.</p>
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<p>Laccase–mineral hybrid microflowers for smartphone-based colorimetric detection. (<b>A</b>) Schematic illustration of the process for creating laccase–mineral hybrid microflowers (La-HMFs). (<b>B</b>–<b>D</b>) La-HMF-based smartphone-assisted colorimetric detection: (<b>B</b>) colorimetric image captured by a smartphone camera; (<b>C</b>) color selection using a color picker application; (<b>D</b>) extraction of red (P<sub>R</sub>), green (P<sub>G</sub>), and blue (P<sub>B</sub>) pixel values from the chosen color; (<b>E</b>) establishment of a linear calibration curve for quantitative analysis. (<b>A</b>–<b>E</b>): Reproduced with permission from [<a href="#B122-ijms-25-04678" class="html-bibr">122</a>], Copyright 2020 Elsevier B.V.</p>
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14 pages, 6833 KiB  
Article
Reducing Automotive Cooling System Complexity through an Adaptive Biomimetic Air Control Valve
by Thomas Thuilot, Moses-Gereon Wullweber, Matthias Fischer, Michael Bennemann and Tobias Seidl
Biomimetics 2024, 9(4), 207; https://doi.org/10.3390/biomimetics9040207 - 29 Mar 2024
Viewed by 1262
Abstract
Future automotive mobility is predominantly electric. Compared to existing systems, the requirements of subsystems change. Air flow for cooling components is needed predominantly when the car is in rest (i.e., charging) or at slow speeds. So far, actively driven fans consuming power and [...] Read more.
Future automotive mobility is predominantly electric. Compared to existing systems, the requirements of subsystems change. Air flow for cooling components is needed predominantly when the car is in rest (i.e., charging) or at slow speeds. So far, actively driven fans consuming power and generating noise are used in this case. Here we propose a passive adaptive system allowing for convection-driven cooling. The developed system is a highly adaptive flat valve derived from the bordered pit. It was developed through an iterative design process including simulations, both structural and thermodynamic. In hardwoods and conifers, bordered pits enable the challenging transport of vertical fluids by locally limiting damage. Depending on the structure, these can close at sudden pressure changes and take the function of valves. The result of the biomimetic abstraction process is a system-integrative, low-profile valve that is cheap to produce, long-lasting, lightweight, maintenance-free, and noise-free. It allows for the passive switching of air flow generation at the heat exchanger of the cooling between natural convection or an active airstream without the need for complex sensing and control systems. The geometric and material design factors allow for the simple tuning of the valve to the desired switching conditions during the design process. Full article
(This article belongs to the Special Issue Biological and Bioinspired Smart Adaptive Structures)
Show Figures

Figure 1

Figure 1
<p>(<b>a</b>) Microscopic image of a bordered pit (with kind permission of Prof. Dr. Gerhard Wanner). (<b>b</b>) Drawing of an opened (grey) and closed (green) bordered pit (drawing by Anastasiya Mironava based on [<a href="#B15-biomimetics-09-00207" class="html-bibr">15</a>]).</p>
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<p>FE mesh on biomimetic bordered pit valve. Meshing of arms and arm-adjacent base is highly refined to handle expected complex deformations in those areas.</p>
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<p>Technical design space. Based on the biological model, a functional technical design needs to also address requirements like desired function parameters, material, manufacturability, and cost (drawings by Anastasiya Mironava).</p>
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<p>(<b>a</b>) Drawing of the biological model (drawing by Anastasiya Mironava based on [<a href="#B15-biomimetics-09-00207" class="html-bibr">15</a>]). (<b>b</b>) Technical abstraction of the bordered pit. Highlighted in red: frame. Red: base. Blue: microfibrils. Green: torus plate.</p>
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<p>Design variants influence closing behavior. Membrane with one arm twists while closing (<b>a</b>). Optimized membrane with two arms (<b>b</b>) achieves symmetrical closing and hence higher process repeatability.</p>
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<p>Mechanical simulation of torus displacement. The plate has a thickness of 1 mm, a diameter of 22 mm, and a Young’s modulus of 35 MPa. Pressure is applied from below. The displacement is accompanied by a counterclockwise rotation of the torus.</p>
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<p>Displacement of the torus as a function of pressure and thickness. Closure is complete at 8 mm in the current design (red dashed line) while the total height of the valve is 10 mm.</p>
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<p>Opening and closing behavior depending on material used. Membranes tested were made from different materials (475K, 1534K, Z-Semiflex), in different thicknesses (0.2, 0.5, 1.0 mm), and mounted in different orientations, e.g., with the air-flow-exposed bottom being a smooth surface (sb) or the opposite, top side being smooth (st). In all cases, the encasing was 20 mm-thick and an exhaust chimney was situated on top of the setup.</p>
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<p>Plate displacement along a linear line. Despite the extreme displacement of 20 mm stress within the model, it remains fairly low and uniformly distributed along the structure. Peaks only occur at the end points of the spiral arms (stress point at the center of the torus plate results from force constraints during simulation).</p>
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<p>Simulation of plate displacement inside a rigid encasing. At 8 mm displacement, contact between both elements was achieved. Top 2 mm is dead space to compensate for tolerances.</p>
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<p>Stress–strain behavior of Z-Semiflex prototype material testing following DIN ISO 527-2. [<a href="#B21-biomimetics-09-00207" class="html-bibr">21</a>] Test specimen (type 1B) printed in massive material. Loading occurred at 100 mm/min; n = 6 experiments per direction.</p>
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<p>Controlling air tightness in closed configuration. While the original geometry (<b>a</b>) closes with a considerable leakage of air flow, the improved geometries (<b>b</b>,<b>c</b>) largely inhibit air flow. Variant (<b>c</b>) is costly to produce and hence (<b>b</b>) marks the final design.</p>
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<p>Setup for functional verification. For reliable verification, the use case is further narrowed down to a specific mid-range car model focusing on the forward right side. The front of the car is situated on the left side, and the front wheel on the right side of (<b>a</b>). In standstill, the valves are open and warm air exits the cooler at the top. (<b>b</b>) The existing design is extended with an air flow generator and—for manufacturing reasons—further modularized. (<b>c</b>) Air motion is generated by an array of 12 variable fans. The valve array is placed above the right-hand wheel arch cooler (<b>c</b>,<b>d</b>) and permits or prevents upwards air flow. Air flow is visualized by red wool threads in the final setup ((<b>d</b>), top right corner).</p>
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<p>Geometric design parameters used to adjust the behavior of the torus.</p>
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<p>Abstract design of chimney effect adjusted to the wheel arch cooler setup. Air flow with open valves is indicated by red and blue arrows. The chimney shape is a result of geometric constraints given in the application case [<a href="#B25-biomimetics-09-00207" class="html-bibr">25</a>], [adapted].</p>
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