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Search Results (9,443)

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Keywords = 3D printing

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17 pages, 3212 KiB  
Article
Tunable Alginate-Polyvinyl Alcohol Bioinks for 3D Printing in Cartilage Tissue Engineering
by Alexandra Hunter Aitchison, Nicholas B. Allen, Kishen Mitra, Bijan Abar, Conor N. O’Neill, Kian Bagheri, Albert T. Anastasio and Samuel B. Adams
Gels 2024, 10(12), 829; https://doi.org/10.3390/gels10120829 (registering DOI) - 14 Dec 2024
Viewed by 355
Abstract
This study investigates 3D extrusion bioinks for cartilage tissue engineering by characterizing the physical properties of 3D-printed scaffolds containing varying alginate and polyvinyl alcohol (PVA) concentrations. We systematically investigated the effects of increasing PVA and alginate concentrations on swelling, degradation, and the elastic [...] Read more.
This study investigates 3D extrusion bioinks for cartilage tissue engineering by characterizing the physical properties of 3D-printed scaffolds containing varying alginate and polyvinyl alcohol (PVA) concentrations. We systematically investigated the effects of increasing PVA and alginate concentrations on swelling, degradation, and the elastic modulus of printed hydrogels. Swelling decreased significantly with increased PVA concentrations, while degradation rates rose with higher PVA concentrations, underscoring the role of PVA in modulating hydrogel matrix stability. The highest elastic modulus value was achieved with a composite of 5% PVA and 20% alginate, reaching 0.22 MPa, which approaches that of native cartilage. These findings demonstrate that adjusting PVA and alginate concentrations enables the development of bioinks with tailored physical and mechanical properties, supporting their potential use in cartilage tissue engineering and other biomedical applications. Full article
(This article belongs to the Special Issue Hydrogel for Tissue Regeneration (2nd Edition))
15 pages, 1725 KiB  
Article
Preparation and Characterization of Ultrasonically Modified Peanut Protein–Guar Gum Composite Emulsion Gels for 3D Printing
by Hong-Yan Yan and Shao-Bing Zhang
Gels 2024, 10(12), 828; https://doi.org/10.3390/gels10120828 (registering DOI) - 14 Dec 2024
Viewed by 168
Abstract
This study aimed to prepare ultrasonically modified peanut protein–guar gum composite emulsion gels for 3D printing. The composition of the composite emulsion gels was determined in single-factor and orthogonal experiments. The results revealed that the optimal composite emulsion gels consisted of 6% peanut [...] Read more.
This study aimed to prepare ultrasonically modified peanut protein–guar gum composite emulsion gels for 3D printing. The composition of the composite emulsion gels was determined in single-factor and orthogonal experiments. The results revealed that the optimal composite emulsion gels consisted of 6% peanut protein, 50% oil and 0.2% guar gum. After crushing pretreatment for 45 s, the printing deviation of the composite emulsion gels was reduced to 8.58 ± 0.20%. Moreover, after ultrasonic treatment (200 W for 20 min) of peanut proteins, the obtained composite emulsion gels presented the highest yield stress, hardness and G’ values, as well as a denser and more homogeneous microstructure. After protein ultrasonic modification (200 W or 600 W for 20 min), the printing accuracy and self-supporting properties of the composite emulsion gels for printing complex shapes significantly improved, which was attributed to their stronger textural and rheological properties; however, ultrasonically modified peanut protein–guar gum composite emulsion gels were not suitable for printing products with smooth surfaces. Full article
(This article belongs to the Special Issue Recent Trends in Gels for 3D Printing)
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11 pages, 2707 KiB  
Article
Path Planning Method for Wire-Based Additive Manufacturing Processes
by Alexey Shcherbakov, Alexander Gudenko, Andrey Sliva, Daria Gaponova, Artem Marchenkov and Alexey Goncharov
Modelling 2024, 5(4), 2040-2050; https://doi.org/10.3390/modelling5040105 (registering DOI) - 14 Dec 2024
Viewed by 194
Abstract
The relevance of creating specialized computer programs that convert a virtual 3D model of an object into machine code (G-code) for controlling the process of 3D printing products from wire raw materials is substantiated. It is shown that for wire-based additive technologies, a [...] Read more.
The relevance of creating specialized computer programs that convert a virtual 3D model of an object into machine code (G-code) for controlling the process of 3D printing products from wire raw materials is substantiated. It is shown that for wire-based additive technologies, a fundamentally important requirement is to ensure the continuity of the surfacing trajectory within one section. A method for determining a continuous surfacing trajectory is proposed, the implementation of which requires two stages: performing a numerical analysis of a two-dimensional region with boundary conditions describing this section; and running a heuristic algorithm for the movement of the surfacing head, in which the direction of movement is selected based on the results of the analysis. The procedure for setting boundary conditions and an algorithm for numerically solving the boundary value problem of determining the field of the “height” function for each section are described. The principles of operation of the heuristic algorithm for selecting the direction of head movement based on the calculated height field and continuous determination of the proximity of adjacent layers and section boundaries are disclosed. An analysis of the algorithm operation is carried out using a section with holes as an example, and the potential of using numerical methods to calculate the change in the temperature field during the surfacing process is shown. Full article
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<p>Deviation of layer height at the initial and final sections of formation: (<b>a</b>) photographs of typical multilayer thin walls; (<b>b</b>) schematic representation in section.</p>
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<p>Path strategies for generating continuous trajectories: (<b>a</b>) zigzag [<a href="#B13-modelling-05-00105" class="html-bibr">13</a>]; (<b>b</b>) spiral [<a href="#B14-modelling-05-00105" class="html-bibr">14</a>]; (<b>c</b>) contour parallel [<a href="#B14-modelling-05-00105" class="html-bibr">14</a>]; (<b>d</b>) hybrid [<a href="#B16-modelling-05-00105" class="html-bibr">16</a>]; (<b>e</b>) pixel [<a href="#B12-modelling-05-00105" class="html-bibr">12</a>,<a href="#B14-modelling-05-00105" class="html-bibr">14</a>]; (<b>f</b>) convex polygon decomposition [<a href="#B16-modelling-05-00105" class="html-bibr">16</a>]; (<b>g</b>) medial axis transformation [<a href="#B17-modelling-05-00105" class="html-bibr">17</a>]; (<b>h</b>) level set [<a href="#B18-modelling-05-00105" class="html-bibr">18</a>].</p>
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<p>Graphical view of the solution of the boundary value problem for <span class="html-italic">h</span>(<span class="html-italic">x</span>,<span class="html-italic">y</span>).</p>
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<p>Illustration of defining a destination point with coordinates <span class="html-italic">x<sub>n</sub></span>, <span class="html-italic">y<sub>n</sub></span>: (<b>a</b>) formation of a bead with constant <span class="html-italic">h</span> value; (<b>b</b>) transition to the next layer of the contour (the direction is chosen so that there is no overlap with the deposited bead, and the change in <span class="html-italic">h</span> value is minimal).</p>
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<p>The results of planning the welding path with the calculation of the temperature (°C) distribution for different moments of time: (<b>a</b>) 0.5 s; (<b>b</b>) 62 s; (<b>c</b>) 124 s; (<b>d</b>) 186 s; (<b>e</b>) 248 s; (<b>f</b>) 310 s; electron beam surfacing process photo (<b>g</b>); and the section deposited on the ELA-15I electron-beam installation (<b>h</b>).</p>
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<p>Computational results of trajectory planning for sections with no geometric similarity between the inner and outer boundaries: (<b>a</b>) section from <a href="#modelling-05-00105-f004" class="html-fig">Figure 4</a> with a rectangular hole; (<b>b</b>) section considered in [<a href="#B16-modelling-05-00105" class="html-bibr">16</a>]; (<b>c</b>,<b>d</b>) experimental trajectories of the electron beam movement on the surface of AISI 316L steel plate, treated without feeding filler wire.</p>
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15 pages, 7940 KiB  
Article
Study on Fatigue Behavior and Fracture Mechanism of LMD Ti-6.5Al-3.5Mo-1.5Zr-0.3Si Alloy Based on Microstructure
by Yuxue Wu, Yongxin Wang, Yunmei Lu and Chenxi Zhao
Materials 2024, 17(24), 6112; https://doi.org/10.3390/ma17246112 (registering DOI) - 13 Dec 2024
Viewed by 281
Abstract
This study explores the fatigue behavior and fracture mechanisms of TC11 titanium alloy formed by laser metal deposition (LMD) and subjected to double annealing. The research focuses on how the alloy’s unique microstructure, consisting of alternating equiaxed and columnar crystals, influences its fatigue [...] Read more.
This study explores the fatigue behavior and fracture mechanisms of TC11 titanium alloy formed by laser metal deposition (LMD) and subjected to double annealing. The research focuses on how the alloy’s unique microstructure, consisting of alternating equiaxed and columnar crystals, influences its fatigue performance. The microstructure’s basket-like α’ phase, made up of both plate-shaped and needle-like structures, leads to variations in crack growth behavior, as shown in the relationship between the crack growth rate and the stress intensity. An analysis of slip patterns reveals that equiaxed crystals undergo more frequent deformation, accelerating crack propagation compared to the more evenly distributed deformation in columnar crystals. These findings suggest a new approach for improving the fatigue resistance of 3D-printed titanium alloys by optimizing their microstructure. This study provides valuable insights for enhancing material toughness and extending the lifespan of titanium alloys in applications such as aerospace and biomedical engineering. Full article
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<p>Heat treatment process of deposited specimen.</p>
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<p>(<b>a</b>) Schematic illustration of the deposition direction. Schematic representation of specimens: (<b>b1</b>) Fatigue crack extension specimen, (<b>b2</b>) Fatigue tensile specimen.</p>
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<p>Fitting diagram of S-N curves in two different forming directions of Kt = 1 and Kt = 3.</p>
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<p>T1 sample crack source morphology (<b>a</b>); dimple morphology (<b>a1</b>); stable propagation zone morphology (<b>a2</b>); T2 sample crack source morphology (<b>b</b>); dimple morphology (<b>b1</b>); stable propagation zone morphology (<b>b2</b>).</p>
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<p>Schematic representation of the fatigue tensile fracture location (<b>a</b>); schematic representation of the wire-cut sampling (<b>b</b>); schematic representation of the macroscopic micro-morphology of the sample (<b>c</b>).</p>
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<p>Partial SEM diagrams of T1 (<b>a</b>) and T2 (<b>b</b>) crack propagation path.</p>
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<p>Columnar crystal region Euler diagram (<b>a</b>) and its corresponding orientation difference diagram (<b>c</b>) and equiaxed crystal region Euler diagram (<b>b</b>) and its corresponding orientation difference diagram(<b>d</b>).</p>
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<p>SEM diagrams of grain boundaries and secondary cracks along the crack propagation path. (a,b) Equiaxed and columnar grain boundary morphology (c) Secondary crack.</p>
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<p>Metallographic structure diagram of the boundary area between the equiaxed crystals and columnar crystals (<b>a</b>). 200 times metallographic structure diagram (<b>b</b>). Internal metallographic structure diagram of grains (<b>c</b>).</p>
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<p>Schematic diagram of fatigue crack growth path in L-T direction (<b>a</b>) and T-L direction (<b>b</b>).</p>
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<p>da/dN~ΔK diagram (<b>a</b>) and da/dN~a diagram (<b>b</b>) of L-T and T-L crack propagation specimens.</p>
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<p>Columnar intracrystalline IPF pattern (<b>a</b>). Polar pattern α (<b>a1</b>) β (<b>a2</b>) and equiaxed intracrystalline IPF pattern (<b>b</b>). Polar pattern α (<b>b1</b>) β (<b>b2</b>).</p>
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<p>SF statistics of columnar and equiaxed crystals.</p>
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<p>Columnar crystal phase distribution diagram (<b>a</b>). KAM part hcp crystal bcc crystal orientation diagram (<b>b</b>) and equiaxed crystal phase distribution diagram (<b>c</b>). KAM part hcp crystal bcc crystal orientation diagram (<b>d</b>).</p>
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12 pages, 1522 KiB  
Article
Unifocalization of Major Aortopulmonary Collateral Arteries (MAPCAs) and Native Pulmonary Arteries in Infancy—Application of 3D Printing and Virtual Reality
by Jacek Kolcz, Anna Rudek-Budzynska and Krzysztof Grandys
J. Cardiovasc. Dev. Dis. 2024, 11(12), 403; https://doi.org/10.3390/jcdd11120403 - 13 Dec 2024
Viewed by 342
Abstract
Background. Major aortopulmonary collateral arteries (MAPCAs) are rare remnants of pulmonary circulation embryological development usually associated with complex congenital anomalies of the right ventricular outflow tract and pulmonary arteries. Effective management requires surgical unifocalization of MAPCAs and native pulmonary arteries (NPAs). Traditional imaging [...] Read more.
Background. Major aortopulmonary collateral arteries (MAPCAs) are rare remnants of pulmonary circulation embryological development usually associated with complex congenital anomalies of the right ventricular outflow tract and pulmonary arteries. Effective management requires surgical unifocalization of MAPCAs and native pulmonary arteries (NPAs). Traditional imaging may lack the spatial clarity needed for precise surgical planning. Aim. This study evaluated the feasibility of integrating three-dimensional (3D) printing and virtual reality (VR) into preoperative planning to improve surgical precision, team communication, and parental understanding. In a prospective cohort study, nine infants undergoing MAPCA unifocalization were included. Four patients underwent conventional imaging-based planning (control), while five were additionally assessed using VR and 3D-printed models (intervention). The outcomes measured included operative times, team confidence, collaboration, and parental satisfaction. Statistical analysis was performed using standard tests. Results. The intervention group had shorter operative and cardiopulmonary bypass times compared to the control group. Intraoperative complications were absent in the VR/3D group but occurred in the control group. Medical staff in the VR/3D group reported significantly improved understanding of anatomy, surgical preparedness, and team collaboration (p < 0.05). Parents also expressed higher satisfaction, with better comprehension of their child’s anatomy and surgical plan. Conclusions. VR and 3D printing enhanced preoperative planning, surgical precision, and communication, proving valuable for complex congenital heart surgery. These technologies offer promising potential to improve clinical outcomes and patient–family experiences, meriting further investigation in larger studies. Full article
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<p>An example of a 3D-printed model of a patient with tetralogy of Fallot and multiple major aortopulmonary collateral arteries (MAPCAs). A prominent circumflex vessel is visible, originating from the right subclavian artery, along with MAPCAs branching from the descending aorta.</p>
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<p>Three-dimensional reconstruction of the heart and lungs showcasing the topography of all detected MAPCAs. This model provides a comprehensive view of the vascular pathways, clearly delineating the origins, routes, and connections of each MAPCA with the native pulmonary arteries, offering a precise anatomical map to aid in preoperative planning and intraoperative guidance. L: Refers to “Left”; I: Refers to “Inferior”; R: Refers to “Right”; S: Refers to “Superior”.</p>
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<p>Virtual reality model, meticulously constructed from computed tomography images of a patient diagnosed with tetralogy of Fallot (TOF), pulmonary trunk agenesis, multiple MAPCAs, and non-confluent pulmonary arteries following a right-sided modified Blalock–Taussig shunt to the right pulmonary artery (RPA) and stenting of the arterial duct to supply the left pulmonary artery (LPA). (<b>A</b>): Anterior view showing the stented arterial duct that supplies the non-confluent LPA, a key anatomical feature providing crucial blood flow to the left lung; (<b>B</b>): Posterior view highlighting the MAPCAs originating from the descending aorta, which are primarily responsible for the blood supply to the right lung; (<b>C</b>): Anterior view detailing the blood supply to the right lung. [#1] Modified Blalock–Taussig shunt linking the RPA to the proximal segment of the brachiocephalic trunk. [#2] Right-sided MAPCA originating from the proximal left subclavian artery and connecting to the native RPA in the right lung hilum (marked in green). [#3.1] A partially visible MAPCA segment arising from the descending aorta; (<b>D</b>): Anterior view further illustrating the MAPCA from the descending aorta ([#3]), which divides proximally into two right-sided branches ([#3.1] and [#3.2]), supplying the same area as the native RPA. Additionally visible are the following: [#4] A distal segment of an R-MAPCA from the right subclavian artery to the right lung’s upper lobe. [#1] Partially visible native RPA. [#2] MAPCA from the left subclavian artery to the right lung. [#4] Distal segment of the MAPCA from the right subclavian artery to the right lung. (<b>E</b>): Posterior view displaying the MAPCA from the descending aorta ([#3]), dividing into branches ([#3.1] and [#3.2]) that converge at the right hilum, overlapping with the area supplied by the native RPA. Also seen are [#2] MAPCA originating from the left subclavian artery. [#4] Middle and distal segments of the MAPCA from the right subclavian artery. L—left, R—right, S—superior, I—inferior.</p>
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17 pages, 1875 KiB  
Review
Addressing the Challenges in Pediatric Facial Fractures: A Narrative Review of Innovations in Diagnosis and Treatment
by Gabriel Mulinari-Santos, Amanda Paino Santana, Paulo Roberto Botacin and Roberta Okamoto
Surgeries 2024, 5(4), 1130-1146; https://doi.org/10.3390/surgeries5040090 - 13 Dec 2024
Viewed by 308
Abstract
Background/Objectives: Pediatric facial fractures present unique challenges due to the anatomical, physiological, and developmental differences in children’s facial structures. The growing facial bones in children complicate diagnosis and treatment. This review explores the advancements and complexities in managing pediatric facial fractures, focusing on [...] Read more.
Background/Objectives: Pediatric facial fractures present unique challenges due to the anatomical, physiological, and developmental differences in children’s facial structures. The growing facial bones in children complicate diagnosis and treatment. This review explores the advancements and complexities in managing pediatric facial fractures, focusing on innovations in diagnosis, treatment strategies, and multidisciplinary care. Methods: A narrative review was conducted, synthesizing data from English-language articles published between 2001 and 2024. Relevant studies were identified through databases such as PubMed, Scopus, Lilacs, Embase, and SciELO using keywords related to pediatric facial fractures. This narrative review focuses on anatomical challenges, advancements in diagnostic techniques, treatment approaches, and the role of interdisciplinary teams in management. Results: Key findings highlight advancements in imaging technologies, including three-dimensional computed tomography (3D CT) and magnetic resonance imaging (MRI), which have improved fracture diagnosis and preoperative planning. Minimally invasive techniques and bioresorbable implants have revolutionized treatment, reducing trauma and enhancing recovery. The integration of multidisciplinary teams, including pediatricians, psychologists, and speech therapists, has become crucial in addressing both the physical and emotional needs of patients. Emerging technologies such as 3D printing and computer-assisted navigation are shaping future treatment approaches. Conclusions: The management of pediatric facial fractures has significantly advanced due to innovations in imaging, surgical techniques, and the growing importance of interdisciplinary care. Despite these improvements, long-term follow-up remains critical to monitor potential complications. Ongoing research and collaboration are essential to refine treatment strategies and improve long-term outcomes for pediatric patients with facial trauma. Full article
18 pages, 4752 KiB  
Article
Three-Dimensionally Printed Bionic Hydroxyapatite (HAp) Ceramic Scaffolds with Different Structures and Porosities: Strength, Biocompatibility, and Biomedical Application Potential
by Peng Zhang, Qing Zhou and Rujie He
Materials 2024, 17(24), 6092; https://doi.org/10.3390/ma17246092 - 13 Dec 2024
Viewed by 252
Abstract
Bionic bioceramic scaffolds are essential for achieving excellent implant properties and biocompatible behavior. In this study, inspired by the microstructure of natural bone, bionic hydroxyapatite (HAp) ceramic scaffolds with different structures (body-centered cubic (BCC), face-centered cubic (FCC), and gyroid Triply Periodic Minimal Surfaces [...] Read more.
Bionic bioceramic scaffolds are essential for achieving excellent implant properties and biocompatible behavior. In this study, inspired by the microstructure of natural bone, bionic hydroxyapatite (HAp) ceramic scaffolds with different structures (body-centered cubic (BCC), face-centered cubic (FCC), and gyroid Triply Periodic Minimal Surfaces (TPMSs)) and porosities (80 vol.%, 60 vol.%, and 40 vol.%) were designed, 3D-printed, and characterized. The effects of structure and porosity on the morphology, mechanical properties, and in vitro biocompatibility properties of the HAp scaffolds were studied and compared with each other. Interestingly, the HAp scaffold with a porosity of 80 vol.% and a TPMS structure had the best combination of compressive strength and in vitro biocompatibility, and demonstrated a great biomedical application potential for bone repair. We hope this study can provide a reference for the application and development of HAp scaffolds in the field of bone repair engineering. Full article
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<p>Bionic design of HAp scaffolds with different structures and porosities.</p>
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<p>Design and flow chart of this study.</p>
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<p>Photographs and high-magnification microstructures of 3D-printed HAp BCC scaffolds with different porosities: (<b>a</b>–<b>c</b>) B80; (<b>d</b>–<b>f</b>) B60; (<b>g</b>–<b>i</b>) B40.</p>
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<p>Photographs and high-magnification microstructures of 3D-printed HAp FCC scaffolds with different porosities: (<b>a</b>–<b>c</b>) F80; (<b>d</b>–<b>f</b>) F60; (<b>g</b>–i) F40.</p>
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<p>Photographs and high-magnification microstructures of 3D-printed HAp TPMS scaffolds with different porosities: (<b>a</b>–<b>c</b>) T80; (<b>d</b>–<b>f</b>) T60; (<b>g</b>–<b>i</b>) T40.</p>
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<p>Compressive strength of 3D-printed HAp scaffolds with different porosities: (<b>a</b>,<b>b</b>) 80 vol.%; (<b>c</b>,<b>d</b>) 60 vol.%; (<b>e</b>,<b>f</b>) 40 vol.%. These graphs show that TPMS structures have the highest compressive strength.</p>
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<p>CCK-8 cell viability assay for 3D-printed HAp scaffolds with different structures and porosities: (<b>a</b>) 1 day; (<b>b</b>) 4 days; (<b>c</b>) 7 days. (Note: asterisk indicates a statistically significant difference between the two groups; N: no statistically significant difference; ***: <span class="html-italic">p</span> &lt; 0.001; ****: <span class="html-italic">p</span> &lt; 0.0001.)</p>
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<p>Fluorescence images of live/dead cell staining on various 3D-printed HAp scaffolds: (<b>a</b>) B80; (<b>b</b>) F80; (<b>c</b>) T80; (<b>d</b>) B60; (<b>e</b>) F60; (<b>f</b>) T60.</p>
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<p>Expression of cellular alkaline phosphatase activity on days (<b>a</b>) 1, (<b>b</b>) 4, and (<b>c</b>) 7 (Note: asterisk indicates statistical differences between the two groups; N: no statistically significant difference; *: <span class="html-italic">p</span> &lt; 0.05; **: <span class="html-italic">p</span> &lt; 0.01; ***: <span class="html-italic">p</span> &lt; 0.001).</p>
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<p>Effects of porosity on cellular alkaline phosphatase activity of 3D-printed HAp scaffolds.</p>
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1 pages, 171 KiB  
Retraction
RETRACTED: Bas et al. Embedded Sensors with 3D Printing Technology: Review. Sensors 2024, 24, 1955
by Joan Bas, Taposhree Dutta, Ignacio Llamas Garro, Jesús Salvador Velázquez-González, Rakesh Dubey and Satyendra K. Mishra
Sensors 2024, 24(24), 7957; https://doi.org/10.3390/s24247957 - 13 Dec 2024
Viewed by 183
Abstract
The Sensors Editorial Office retracts the article, “Embedded Sensors with 3D Printing Technology: Review” [...] Full article
1 pages, 24225 KiB  
Article
Multiscale Concurrent Topology Optimization and Mechanical Property Analysis of Sandwich Structures
by Zihao Li, Shiqiang Li and Zhihua Wang
Materials 2024, 17(24), 6086; https://doi.org/10.3390/ma17246086 - 12 Dec 2024
Viewed by 437
Abstract
Based on the basic theoretical framework of the Bi-directional Evolutionary Structural Optimization method (BESO) and the Solid Isotropic Material with Penalization method (SIMP), this paper presents a multiscale topology optimization method for concurrently optimizing the sandwich structure at the macro level and the [...] Read more.
Based on the basic theoretical framework of the Bi-directional Evolutionary Structural Optimization method (BESO) and the Solid Isotropic Material with Penalization method (SIMP), this paper presents a multiscale topology optimization method for concurrently optimizing the sandwich structure at the macro level and the core layer at the micro level. The types of optimizations are divided into macro and micro concurrent topology optimization (MM), macro and micro gradient concurrent topology optimization (MMG), and macro and micro layered gradient concurrent topology optimization (MMLG). In order to compare the multiscale optimization method with the traditional macroscopic optimization method, the sandwich simply supported beam is illustrated as a numerical example to demonstrate the functionalities and superiorities of the proposed method. Moreover, several samples are printed through micro-nano 3D printing technology, and then the static three-point bending experiments and the numerical simulations are carried out. The mechanical properties of the optimized structures in terms of deformation modes, load-bearing capacity, and energy absorption characteristics are compared and analyzed in detail. Finally, the multiscale optimization methods are extended to the design of 2D sandwich cantilever beams and 3D sandwich fully clamped beams. Full article
(This article belongs to the Section Advanced Materials Characterization)
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<p>A 2D two-scale structure.</p>
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<p>2D rectangular base cell model.</p>
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<p>Flowchart of multiscale concurrent topology optimization.</p>
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<p>Optimization model and initial microstructure, (<b>a</b>) initial optimization model of sandwich simply supported beam, (<b>b</b>) initial microstructure.</p>
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<p>MM structure optimization history. (<b>a</b>) Macrostructure optimization history chart, (<b>b</b>) microstructure optimization history chart.</p>
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<p>MMG structure optimization history. (<b>a</b>) Macrostructure optimization history chart. (<b>b</b>) Microstructure optimization history chart.</p>
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<p>MMG structure topology optimization result.</p>
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<p>MMLG structure topology optimization.</p>
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<p>MMLG structure topology optimization history. (<b>a</b>) Macrostructure optimization history chart. (<b>b</b>) Microstructure optimization history chart.</p>
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<p>MMLG structure topology optimization result.</p>
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<p>Comparison of efficiency of different multiscale concurrent topology optimization algorithms [<a href="#B31-materials-17-06086" class="html-bibr">31</a>,<a href="#B38-materials-17-06086" class="html-bibr">38</a>,<a href="#B50-materials-17-06086" class="html-bibr">50</a>,<a href="#B51-materials-17-06086" class="html-bibr">51</a>,<a href="#B52-materials-17-06086" class="html-bibr">52</a>].</p>
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<p>Optimization design and initial microstructure. (<b>a</b>) Initial optimization model of sandwich simply supported beam. (<b>b</b>) Initial microstructure.</p>
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<p>MMG structure topology optimization result.</p>
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<p>MMLG structure topology optimization result.</p>
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<p>A 3D fully clamped beam structure.</p>
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<p>MM structure topology optimization result.</p>
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<p>MMG structure topology optimization result (the volume fraction of five microstructures varies from large to small, with values of 1, 0.8, 0.6, 0.4, and 0.2).</p>
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<p>MMLG structure topology optimization result.</p>
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<p>3D printing model preparation and results. (<b>a</b>) Printing direction. (<b>b</b>) Finished product status. (<b>c</b>) M structure. (<b>d</b>) MM structure. (<b>e</b>) MMG structure. (<b>f</b>) MMLG structure.</p>
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<p>(<b>a</b>) Material stress–strain curve. (<b>b</b>) Load displacement curve of 5 structures.</p>
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<p>Comparison of experimental and numerical deformation modes of 5 structures.</p>
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<p>(<b>a</b>) Comparison of force–displacement curves between experimental and numerical values of five structures. (<b>b</b>) Comparison of peak force and effective bearing displacement of five structures.</p>
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<p>Displacement of 5 structures. (<b>a</b>) S structure specimen displacement. (<b>b</b>) M structure specimen displacement. (<b>c</b>) MM structure specimen displacement. (<b>d</b>) MMG structure specimen displacement. (<b>e</b>) MMLG structure specimen displacement.</p>
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<p>Displacement of 5 structures. (<b>a</b>) S structure specimen displacement. (<b>b</b>) M structure specimen displacement. (<b>c</b>) MM structure specimen displacement. (<b>d</b>) MMG structure specimen displacement. (<b>e</b>) MMLG structure specimen displacement.</p>
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<p>Deformation modes of 4 structural specimens: (<b>a</b>) M structure <span class="html-italic">w</span> = 4 mm deformation mode; (<b>b</b>) MM structure <span class="html-italic">w</span> = 7 mm deformation mode; (<b>c</b>) MMG structure <span class="html-italic">w</span> = 7 mm deformation mode; (<b>d</b>) MMLG structure <span class="html-italic">w</span> = 7 mm deformation mode.</p>
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<p>Specific energy absorption and energy absorption proportion of 5 structures.</p>
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14 pages, 5812 KiB  
Article
Three-Dimensionally Printed Dual-Slot-Fed Dielectric Resonator Antenna with Rectangular and Irregular Elements for 5G Applications
by Zhenyi Shou, Zhipeng Wu, Hanyang Wang, Hai Zhou and Meng Hou
Electronics 2024, 13(24), 4903; https://doi.org/10.3390/electronics13244903 (registering DOI) - 12 Dec 2024
Viewed by 338
Abstract
In this paper, a novel dual-slot-fed dielectric resonator antenna (DRA) with rectangular and irregular elements, designed for 5G wireless applications, is presented. The DRA achieves wideband capability by combining the resonant modes of the rectangular and irregular DRA elements, which is a less [...] Read more.
In this paper, a novel dual-slot-fed dielectric resonator antenna (DRA) with rectangular and irregular elements, designed for 5G wireless applications, is presented. The DRA achieves wideband capability by combining the resonant modes of the rectangular and irregular DRA elements, which is a less common feature in conventional designs. A frequency ratio adjustment technique, based on the concept of inductive de-loading, is uniquely proposed for the independent frequency adjustment of the irregular DRA. Unlike traditional methods, an equivalent circuit presentation was developed to interpret the impedance characteristics of single-element DRAs, and to provide new insights into the presence of inductive de-loading from a circuit perspective. For verification, a dual-slot-fed prototype was fabricated through digital light processing (DLP)-based 3D printing technology, with the aim of customizable design and low-cost fabrication. The measured and simulated results of reflection coefficients and radiation patterns showed good agreements, with a measured bandwidth of 51.6% (2.96–5.02 GHz), effectively covering the desired 5G n77–n79 (3.3–5.0 GHz) frequency bands. Full article
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<p>(<b>a</b>) Theoretical <span class="html-italic">H<sub>y</sub></span> fields of TE<sup>y</sup><sub>111</sub> mode in <span class="html-italic">y</span> = 0 plane; (<b>b</b>) theoretical <span class="html-italic">H<sub>y</sub></span> fields of TE<sup>y</sup><sub>211</sub> mode in <span class="html-italic">y</span> = 0 plane; (<b>c</b>) configuration of the basic RDRA (DRA-00); (<b>d</b>) configuration of the irregular DRA (DRA-20).</p>
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<p>(<b>a</b>) Front cut of the irregular DRA-20 with different <span class="html-italic">R<sub>x</sub></span>; (<b>b</b>) simulated reflection coefficients of the DRA-00 and the DRA-20 for different <span class="html-italic">R<sub>x</sub></span>.</p>
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<p>Simulated <span class="html-italic">H<sub>y</sub></span> field plots of the DRAs in <span class="html-italic">y</span> = 0 plane and <span class="html-italic">z</span> = 0 plane: (<b>a</b>) TE<sup>y</sup><sub>111</sub> mode of the DRA-00 at 3.43 GHz; (<b>b</b>) TE<sup>y</sup><sub>211</sub> mode of the DRA-00 at 3.93 GHz; (<b>c</b>) quasi-TE<sup>y</sup><sub>111</sub> mode of the DRA-20 with <span class="html-italic">R<sub>x</sub></span> = 7.8 mm at 3.9 GHz; (<b>d</b>) quasi-TE<sup>y</sup><sub>211</sub> mode of the DRA-20 with <span class="html-italic">R<sub>x</sub></span> = 7.8 mm at 5.005 GHz.</p>
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<p>Simulated radiation patterns of the DRAs on a dB scale: (<b>a</b>) TE<sup>y</sup><sub>111</sub> mode of DRA-00 at 3.43 GHz; (<b>b</b>) TE<sup>y</sup><sub>211</sub> mode of DRA-00 at 3.93 GHz; (<b>c</b>) quasi-TE<sup>y</sup><sub>111</sub> mode of DRA-20 with <span class="html-italic">R<sub>x</sub></span> = 7.8 mm at 3.9 GHz; (<b>d</b>) quasi-TE<sup>y</sup><sub>211</sub> mode of DRA-20 with <span class="html-italic">R<sub>x</sub></span> = 7.8 mm at 5.005 GHz.</p>
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<p>Equivalent circuit presentation of DRA-00 and DRA-20 in ADS.</p>
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<p>Simulated reflection coefficients of DRA-00 and DRA-20 in CST and ADS.</p>
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<p>Configuration of the wideband dual-slot-fed DRA: (<b>a</b>) perspective view; (<b>b</b>) bottom view.</p>
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<p>(<b>a</b>) Simulated reflection coefficients of the DRA-00, DRA-20, and the proposed dual-slot-fed DRA; (<b>b</b>) simulated reflection coefficients of the dual-slot-fed DRA for different <span class="html-italic">R<sub>x</sub></span>.</p>
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<p>Simulated <span class="html-italic">H<sub>y</sub></span> field distributions of the DRA in <span class="html-italic">z</span> = 0 plane: (<b>a</b>) first mode at 3.43 GHz; (<b>b</b>) second mode at 3.93 GHz; (<b>c</b>) third mode at 4.91 GHz.</p>
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<p>(<b>a</b>) Ceramic slurry preparation; (<b>b</b>) 3D printer; (<b>c</b>) 3D-printed transition film on the platform; (<b>d</b>) 3D-printed DRA elements on the transition film; (<b>e</b>) post-curing of DRA elements; (<b>f</b>) perspective view of the assembled DRA; (<b>g</b>) microstrip feed structure.</p>
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<p>(<b>a</b>) Keysight 85070E dielectric probe kit; (<b>b</b>) measurement setup of radiation patterns in an anechoic chamber.</p>
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<p>(<b>a</b>) Measured dielectric constants of the resin and DRA elements; (<b>b</b>) measured and simulated reflection coefficients of the proposed DRA.</p>
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<p>Simulated and measured <span class="html-italic">E</span>-plane and <span class="html-italic">H</span>-plane radiation patterns: (<b>a</b>) 1st mode at 3.43 GHz; (<b>b</b>) 2nd mode at 3.93 GHz; (<b>c</b>) 3rd mode at 4.91 GHz and 4.83 GHz.</p>
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14 pages, 6220 KiB  
Article
Post-Processing of AM-EBM Ti6Al4V for Biomedical Applications: Evolution of Mechanical Properties as a Function of Surface Roughness
by Andrea Valencia-Cadena, Ude Hangen and Joan Josep Roa Rovira
Metals 2024, 14(12), 1423; https://doi.org/10.3390/met14121423 - 12 Dec 2024
Viewed by 316
Abstract
Post-processing, and particularly the dry electropolishing process, is essential for improving the surface quality of 3D-printed Ti6Al4V samples, with specific emphasis on reducing roughness over extended polishing times while preserving mechanical properties. Reducing surface roughness enhances the reliability of hardness measurements and improves [...] Read more.
Post-processing, and particularly the dry electropolishing process, is essential for improving the surface quality of 3D-printed Ti6Al4V samples, with specific emphasis on reducing roughness over extended polishing times while preserving mechanical properties. Reducing surface roughness enhances the reliability of hardness measurements and improves the consistency of elastic modulus measurements, as prolonged polishing time stabilizes the full width at half maximum values, thereby minimizing variability due to uniaxial indentation. This stability is crucial for maintaining the structural integrity and uniformity of mechanical properties, facilitating better performance and reliability in biomedical applications. Additionally, under service-like working conditions, solid electrolyte particles undergo dehydration due to the Joule effect, introducing a dynamic aspect to the system as the particle structure degrades with thermal cycling. EDX cross-sectional analysis reveals that TiO2 informs the particle’s surface, with an oxygen-to-titanium ratio that confirms the oxide’s composition. This TiO2 oxide layer demonstrates the progressive surface oxidation occurring under the post-processing process, further modifying the particle’s surface chemistry. This dual effect of roughness reduction and controlled surface chemistry highlights the role of dry electropolishing in enhancing the functional lifespan and mechanical reliability of Ti6Al4V components. Full article
(This article belongs to the Special Issue Novel Materials and Techniques for Dental Implants)
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<p>(<b>a</b>) Image of the Arcan<sup>®</sup> A3 EBM machine (Amsterdam, The Netherlands) used and (<b>b</b>) Image of the 3D-printed Ti6-Al4-V workpieces.</p>
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<p>(<b>a</b>) Image of the DLyte 100 PRO machine used to dry electropolish the two 3D-printed investigated specimens and (<b>b</b>) schematic representation of the electrical cycle used. The total number of cycles can be obtained as follows: N<sub>total</sub> = total dry electropolishing time/time of 1 cycle (labeled as N in <a href="#metals-14-01423-f002" class="html-fig">Figure 2</a>b).</p>
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<p>Representative Element Evolution for the Ti6Al4V specimen 3D printed by using the EBM technique: (<b>a</b>) <span class="html-italic">R<sub>a</sub></span> vs. scan area and (<b>b</b>) FE-SEM micrographs for a small and large scanned area, labeled as b1 and b2 in <a href="#metals-14-01423-f003" class="html-fig">Figure 3</a>a, respectively.</p>
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<p><span class="html-italic">R<sub>a</sub></span> evolution as a function of the dry electropolishing time for the Ti6Al4V specimen 3D printed by using the EBM technique.</p>
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<p>FE-SEM microstructural evolution as a function of the post-processing time: (<b>a</b>) initial state (t = 0 min); and after being dry-electropolished during (<b>b</b>) 5 min, (<b>c</b>) 40 min, and (<b>d</b>) magnification for the regions marked with a dashed rectangle in <a href="#metals-14-01423-f005" class="html-fig">Figure 5</a>b and <a href="#metals-14-01423-f005" class="html-fig">Figure 5</a>c, respectively.</p>
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<p>FE-SEM micrograph after being post-processed for 5 min showing the duplex, <span class="html-italic">α-</span> and <span class="html-italic">β-</span>, microstructure.</p>
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<p><span class="html-italic">H</span>- and <span class="html-italic">E<sub>r</sub></span>-maps as a function of the dry electropolishing time.</p>
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<p>Mechanical properties distribution through histogram representation for the (<b>a</b>) <span class="html-italic">H</span>- and (<b>b</b>) <span class="html-italic">E<sub>r</sub></span>- properties performed for both dry electropolishing times investigated.</p>
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<p>(<b>a</b>) Visual image of the solid electrolyte after being dry-electropolished the Ti6Al4V specimen; (<b>b</b>) FE-SEM micrograph of a solid particle at the initial state (<span class="html-italic">t =</span> 0 min) and after being dry-electropolished, the desired specimen for 40 min; (<b>c</b>) FIB-cross-section conducted through an induced oxide, marked as a white dash square in <a href="#metals-14-01423-f009" class="html-fig">Figure 9</a>b. The yellow line highlights the region where the chemical composition is analyzed and (<b>d</b>) the chemical profile representation through the solid electrolyte (label a) to the oxide generated along the dry electropolishing process (label b) for the main constitutive chemical elements.</p>
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23 pages, 10166 KiB  
Article
The Mechanical Properties and Energy Absorption of AuxHex Structures
by Robert Panowicz, Adam Jeschke, Tomasz Durejko, Marcin Zachman and Marcin Konarzewski
Materials 2024, 17(24), 6073; https://doi.org/10.3390/ma17246073 - 12 Dec 2024
Viewed by 204
Abstract
Based on a combination of hexagonal honeycomb and re-entrant honeycomb cells, the concept of novel hybrid cell structures was developed. Experimental studies and numerical analyses of the behaviour of the analysed structures under in-plane compression in two compression directions were carried out. Explicit [...] Read more.
Based on a combination of hexagonal honeycomb and re-entrant honeycomb cells, the concept of novel hybrid cell structures was developed. Experimental studies and numerical analyses of the behaviour of the analysed structures under in-plane compression in two compression directions were carried out. Explicit finite element analyses with an explicit integration scheme, incorporating plastic deformation and ductile damage evolution models, were employed to analyse the entire deformation process, including plastic and damage stages. Good agreement was obtained between the results of the numerical analyses and the experimental studies. Full article
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<p>Basic cells (t = 1.05 mm, l = 4 mm) and analysed structures. <span class="html-italic">x</span> and <span class="html-italic">y</span> index indicates the compression direction defined concerning the structure.</p>
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<p>Reduced size 1BA sample (Unit: mm).</p>
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<p>Sample mounted on the test stand with visible extensometer.</p>
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<p>Structure mounted on the test stand.</p>
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<p>Cellular stress–strain curve; (<b>a</b>) brittle material; (<b>b</b>) initial range of the stress–strain curve with a distinct (curve 1) and without a distinct (curve 2) yield stress. The Y and fps indices denote the yield and the first peak, respectively; σ<span class="html-italic"><sub>C pl</sub></span> is plateau stress.</p>
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<p>Energy absorption efficiency.</p>
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<p>Schematic diagram of the <span class="html-italic">EA</span>−<span class="html-italic">l</span> curve with the method of determining ε<sub>D</sub>; l<sub>0</sub> is the initial height of the sample.</p>
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<p>Engineering stress vs. engineering strain for ULTEM during tensile test.</p>
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<p>The force vs. change in length curves with the area of variation marked in grey for the (<b>a</b>) <span class="html-italic">a<sub>x</sub></span> structure and (<b>b</b>) <span class="html-italic">b<sub>x</sub></span> structure.</p>
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<p>Numerical model of the experimental study.</p>
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<p>Curves used in the numerical analyses (<b>a</b>) the plastic true stress–strain curve; (<b>b</b>) material softening curve.</p>
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<p>Compression stress–strain curve of experimental and FE analysis results for <span class="html-italic">a<sub>x</sub></span> structure (<b>left</b>) and corresponding deformation behaviours at selected compression strains (<b>right</b>).</p>
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<p>Compression stress–strain curve of experimental and FE analysis results for <span class="html-italic">a<sub>y</sub></span> structure (<b>left</b>) and corresponding deformation behaviours at selected compression strains (<b>right</b>).</p>
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<p>Compression stress–strain curve of experimental and FE analysis results for <span class="html-italic">b<sub>x</sub></span> structure (<b>left</b>) and corresponding deformation behaviours at selected compression strains (<b>right</b>).</p>
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<p>Compression stress–strain curve of experimental and FE analysis results for <span class="html-italic">b<sub>y</sub></span> structure (<b>left</b>) and corresponding deformation behaviours at selected compression strains (<b>right</b>).</p>
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<p>Compression SEA curve of experimental and FE analysis results for (<b>a</b>) <span class="html-italic">a<sub>x</sub></span> structure and (<b>b</b>) <span class="html-italic">a<sub>y</sub></span> structure.</p>
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<p>Compression SEA curve of experimental and FE analysis results for (<b>a</b>) <span class="html-italic">b<sub>x</sub></span> structure and (<b>b</b>) <span class="html-italic">b<sub>y</sub></span> structure.</p>
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<p>Comparison between the simulation and experimental results of the EA for all of the studied structures.</p>
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<p>Normalised Young’s modulus vs. relative density.</p>
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<p>Normalised stress plateau vs. relative density.</p>
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<p>Normalised EA vs. relative density.</p>
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<p>Normalised SEA vs. relative density.</p>
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<p>Comparison of SEA under in-plane compression. Additional structures from literature: s<sub>1</sub> [<a href="#B52-materials-17-06073" class="html-bibr">52</a>], s<sub>2</sub> [<a href="#B53-materials-17-06073" class="html-bibr">53</a>], s<sub>3</sub> [<a href="#B55-materials-17-06073" class="html-bibr">55</a>], s<sub>4</sub> [<a href="#B56-materials-17-06073" class="html-bibr">56</a>] and s<sub>5</sub> [<a href="#B57-materials-17-06073" class="html-bibr">57</a>].</p>
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13 pages, 2469 KiB  
Article
Effect of Heat Treatment on Gelatin Properties and the Construction of High Internal Phase Emulsions for 3D Printing
by Yixiao Wang, Ling Zhang, Geng Cao, Zhaorui Li and Ming Du
Foods 2024, 13(24), 4009; https://doi.org/10.3390/foods13244009 - 11 Dec 2024
Viewed by 403
Abstract
The effect of tilapia skin gelatin properties on the characteristics of high internal phase emulsions (HIPEs) and the quality of 3D printing remains unidentified. In this work, HIPEs were constructed by gelatin with various properties that were obtained by heat treatment. The results [...] Read more.
The effect of tilapia skin gelatin properties on the characteristics of high internal phase emulsions (HIPEs) and the quality of 3D printing remains unidentified. In this work, HIPEs were constructed by gelatin with various properties that were obtained by heat treatment. The results indicated that the gelatin undergoes degradation gradually with an increase in heating intensity. The highest values of intrinsic fluorescence intensity, surface hydrophobicity, and emulsification were obtained when the heating time was 5 h. The gel strength and hardness of gelatin hydrogels were negatively correlated with heat treatment temperature. HIPEs constructed by gelatin extracted at 70 °C demonstrated a suitable material for 3D printing. The storage modulus (G′) and viscosity of HIPEs exhibited a similar tendency as the gel strength of gelatin. The microstructure of HIPEs revealed that gelatin established a gel network around oil droplets, and the higher G′ of HIPEs corresponded to a more compact network structure. This study elucidated the correlation between the structure and properties of gelatin, offering essential insights for the formulation of HIPEs by natural gelatin, which is suitable for applications across several domains. Full article
(This article belongs to the Special Issue Fish Protein Gel: Preparation, Characterization and Quality Control)
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<p>Structure and properties of gelatins extracted at different temperatures and times. (<b>A</b>) Sodium dodecyl sulfate-polyacrylamide gel electrophoresis (SDS-PAGE), (<b>B</b>) Fourier transform spectroscopy (FTIR), (<b>C</b>) Intrinsic fluorescence spectroscopy measurements, (<b>D</b>) Surface hydrophobicity (H<sub>0</sub>), (<b>E</b>) Emulsifying activity index (EAI), (<b>F</b>) Emulsifying stability index (ESI). Note: Different letters indicate the significant difference between samples (<span class="html-italic">p</span> &lt; 0.05).</p>
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<p>Gel strength (<b>A</b>) and hardness (<b>B</b>) of hydrogels stabilized by gelatins extracted at different temperatures and times.</p>
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<p>3D printing photographs of high internal phase emulsions (HIPEs) stabilized by gelatins extracted at different temperatures and times.</p>
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<p>Rheological behavior of HIPEs stabilized by gelatins extracted at different temperatures and times. (<b>A</b>) Frequency sweep test of storage modulus (G′), (<b>B</b>) Frequency sweep test of loss modulus (G″), (<b>C</b>) 3ITT curves, (<b>D</b>), Cyclic shear ramp test.</p>
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<p>Microstructure of HIPEs stabilized by gelatins extracted at different temperatures and times.</p>
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14 pages, 3716 KiB  
Technical Note
Mandibular Reconstruction with Osseous Free Flap and Immediate Prosthetic Rehabilitation (Jaw-in-a-Day): In-House Manufactured Innovative Modular Stackable Guide System
by Matthias Ureel, Pieter-Jan Boderé, Benjamin Denoiseux, Pasquier Corthouts and Renaat Coopman
Bioengineering 2024, 11(12), 1254; https://doi.org/10.3390/bioengineering11121254 - 11 Dec 2024
Viewed by 379
Abstract
Background: Head and neck reconstruction following ablative surgery results in alterations to maxillofacial anatomy and function. These postoperative changes complicate dental rehabilitation. Methods: An innovative modular, stackable guide system for immediate dental rehabilitation during mandibular reconstruction is presented. The virtual surgical planning was [...] Read more.
Background: Head and neck reconstruction following ablative surgery results in alterations to maxillofacial anatomy and function. These postoperative changes complicate dental rehabilitation. Methods: An innovative modular, stackable guide system for immediate dental rehabilitation during mandibular reconstruction is presented. The virtual surgical planning was performed in Materialise Innovation Suite v26 and Blender 3.6 with the Blenderfordental add-on. The surgical guides and models were designed and manufactured at the point of care. Results: The duration of the surgery was 9 h and 35 min. Good implant stability (>35 Ncm) and a stable occlusion were achieved. After 9 months of follow-up, the occlusion remained stable, and a mouth opening of 25 mm was registered. The dental implants showed no signs of peri-implant bone loss. Superposition of the preoperative planning and postoperative position of the fibula parts resulted in an average difference of 0.70 mm (range: −1.9 mm; 5.4 mm). Conclusions: The in-house developed stackable guide system resulted in a predictive workflow and accurate results. The preoperative virtual surgical planning was time-consuming and required extensive CAD/CAM and surgical expertise. The addition of fully guided implant placement to this stackable guide system would be beneficial. More research with longer follow-ups is necessary to validate these results. Full article
(This article belongs to the Special Issue Computer-Assisted Maxillofacial Surgery)
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<p>VSP in Enlight<sup>®</sup> 2.0 (Materialise, Leuven, Belgium). (<b>A</b>) Position of the two fibula parts in between the remaining mandible after virtual resection of the tumor. The height and rotation of the fibula parts are essential parameters to allow optimal implant placement. Purple: remaining mandible parts; translucent orange: resected mandible; green + yellow: two-piece fibula for mandibular reconstruction. (<b>B</b>) Visualization of the right tibia and fibula bones. In yellow and green, the corresponding fibula parts are visible. The measurements of each part and the distance to the lateral malleolus and fibula head are visualized (red text boxes).</p>
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<p>VSP of cutting guides and templates designed in 3-Matic<sup>®</sup> 18.0 (Materialise, Leuven, Belgium). (<b>A</b>,<b>B</b>) Cutting guides for the right and left mandibular osteotomy. (<b>C</b>) Positioning model with vertical support for positioning of the fibula segments. (<b>D</b>) Neomandible for prebending of the reconstruction plate. (<b>E</b>) Neomandible and intra-oral scan of the dentition for height estimation of the fibula segments. The dental implant position is visualized with 5 mm diameter cylinders. (<b>F</b>) Initial cutting guide for fibula osteotomies.</p>
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<p>Design of the base plate, attachment cylinders (blue), and connecting arms (brown) in Blender v3.6 with the Blenderfordental add-on. (<b>A</b>,<b>C</b>) Connecting 3 attachment cylinders with three connecting arms to position the fibula guide and fibula parts in a correct position. (<b>B</b>,<b>D</b>) Connecting two attachment cylinders with two connecting arms and an extension towards the native dentition to position the provisional prosthesis.</p>
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<p>Modular, stackable guide system. (<b>A</b>) Base plate with three attachment cylinders to connect the fibula cutting guide for optimal positioning of the fibula segments. The same attachment cylinders are used for positioning the stackable guides for implant placement and prosthesis positioning. A supporting sleeve, bridging the remaining native mandibular parts, allows correct vertical positioning of the fibula segments. (<b>B</b>) Base plate with stackable implant drill guide connected to the attachment cylinders and to the right mandibular teeth using a dental extension. This guide holds occlusal drill holes for positioning the dental implants in the fibula segments. (<b>C</b>) Base plate with stackable prosthesis guide (white) and the provisional prosthesis positioned in the correct vertical dimension. (<b>D</b>,<b>E</b>) Fibula guide with sufficient contact surface to provide accurate positioning on the fibula; fixation holes for fixation to the fibula with 1.5 mm screws; 2 mm arch bridges to connect both superior and inferior surface areas; 5 mm arch bridge connecting the two fibula guide parts; flanges serving as cutting guides; connection arms for positioning of the fibula segments on the base plate.</p>
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<p>Prebending of the 2.3 KLS Martin reconstruction plate: (<b>A</b>) A 3D model of the neomandible. (<b>B</b>) The reconstruction plate is placed on the neomandible model, starting from the condyle. (<b>C</b>) The plate is adjusted using a surgical marker and folding pliers. (<b>D</b>) The prebent reconstruction plate is fixed to the fibula segments that are positioned by the superior surface parts of the fibula guide.</p>
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<p>Surgical steps for guide positioning. (<b>A</b>) The fibula guide was fixed on the right fibula with 1.5 mm screws. Skin island attached to the fibula. (<b>B</b>,<b>C</b>) After performing the fibula osteotomies, the 2 mm arch bars were cut to remove the inferior parts of the fibula guide. (<b>D</b>) Positioning of the fibula parts by connecting the connection arms of the fibula guide to the attachment cylinders of the base plate. Fixation of the prebent 2.3 mm KLS Martin reconstruction plate with locking and non-locking screws. (<b>E</b>) After the removal of the superior part of the fibula guide, the stackable implant guide for dental implant placement was placed. An extension was made for support of the remaining dentition for stability reasons. (<b>F</b>) Placement of the stackable prosthetic guide to check implant position before connecting the provisional prosthesis.</p>
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<p>Incorporation of the fibula construct. (<b>A</b>) Neomandible with fibula segments positioned and fixed to the reconstruction plate. Temporary prosthesis fixed to three Bredent classic SKY 4.0 × 10 mm dental implants. The fibula construct is still attached to the pedicle. (<b>B</b>) Fibula construct after sectioning of the pedicle with attached skin island and flexor hallucis longus muscle flap for transfer to the patient’s mouth. (<b>C</b>) The fibula construct is positioned in occlusion and fixed with locking and non-locking screws to the mandible.</p>
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<p>Postoperative clinical images 2 (<b>A</b>,<b>B</b>) and 9 (<b>C</b>,<b>D</b>) months after surgery. (<b>A</b>) Good temporomandibular function with interincisal mouth opening of approximately 25 mm. (<b>B</b>) Provisional dental prosthesis fixed on dental implants with stable occlusion. (<b>C</b>) Stable temporomandibular function after radiochemotherapy. (<b>D</b>) Stable occlusion with the final prosthesis in place.</p>
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<p>Superimposition of preoperative planning and postoperative result. Mean difference of 0.70 mm (range: −1.9940 mm; 5.4144 mm).</p>
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15 pages, 9156 KiB  
Article
Antisolvent 3D Printing of Gene-Activated Scaffolds for Bone Regeneration
by Andrey Vyacheslavovich Vasilyev, Irina Alekseevna Nedorubova, Viktoria Olegovna Chernomyrdina, Anastasiia Yurevna Meglei, Viktoriia Pavlovna Basina, Anton Vladimirovich Mironov, Valeriya Sergeevna Kuznetsova, Victoria Alexandrovna Sinelnikova, Olga Anatolievna Mironova, Ekaterina Maksimovna Trifanova, Igor Ivanovich Babichenko, Vladimir Karpovich Popov, Anatoly Alekseevich Kulakov, Dmitry Vadimovich Goldshtein and Tatiana Borisovna Bukharova
Int. J. Mol. Sci. 2024, 25(24), 13300; https://doi.org/10.3390/ijms252413300 - 11 Dec 2024
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Abstract
The use of 3D-printed gene-activated bone grafts represents a highly promising approach in the fields of dentistry and orthopedics. Bioresorbable poly-lactic-co-glycolic acid (PLGA) scaffolds, infused with adenoviral constructs that carry osteoinductive factor genes, may provide an effective alternative to existing bone grafts for [...] Read more.
The use of 3D-printed gene-activated bone grafts represents a highly promising approach in the fields of dentistry and orthopedics. Bioresorbable poly-lactic-co-glycolic acid (PLGA) scaffolds, infused with adenoviral constructs that carry osteoinductive factor genes, may provide an effective alternative to existing bone grafts for the reconstruction of extensive bone defects. This study aims to develop and investigate the properties of 3D scaffolds composed of PLGA and adenoviral constructs carrying the BMP2 gene (Ad-BMP2), both in vitro and in vivo. The elastic modulus of the disk-shaped PLGA scaffolds created using a specialized 3D printer was determined by compressive testing in both axial and radial directions. In vitro cytocompatibility was assessed using adipose-derived stem cells (ADSCs). The ability of Ad-BMP2 to transduce cells was evaluated. The osteoinductive and biocompatible properties of the scaffolds were also assessed in vivo. The Young’s modulus of the 3D-printed PLGA scaffolds exhibited comparable values in both axial and radial compression directions, measuring 3.4 ± 0.7 MPa for axial and 3.17 ± 1.4 MPa for radial compression. The scaffolds promoted cell adhesion and had no cytotoxic effect on ADSCs. Ad-BMP2 successfully transduced the cells and induced osteogenic differentiation in vitro. In vivo studies demonstrated that the 3D-printed PLGA scaffolds had osteoinductive properties, promoting bone formation within the scaffold filaments as well as at the center of a critical calvarial bone defect. Full article
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<p>SEM images of the filament structure and internal structure of PLG scaffold formed by anti-solvent 3D printing.</p>
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<p>Means of Young’s modulus at radial and axial compression of PLGA scaffold.</p>
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<p>Viability of ADSCs at 1 and 7 days after incubation with scaffolds, MTT test.</p>
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<p>Adhesion of ADSCs on the surface of scaffolds. Fluorescence microscopy.</p>
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<p>Transduction efficiency of Ad-BMP2 incorporated into PLGA-based 3D scaffolds. Relative expression of osteogenic marker genes RT-PCR; osteogenic marker proteins production, ELISA. * <span class="html-italic">p</span> &lt; 0.001.</p>
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<p>Osteogenic differentiation of ADSCs after incubation with scaffolds: relative expression of osteogenic marker genes, RT-PCR; osteogenic marker proteins production, ELISA; enzyme activity, spectrophotometry. * <span class="html-italic">p</span> &lt; 0.001 (relative to control).</p>
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<p>Histological study of a critical-size rat calvarial bone defect after implantation; H&amp;E or Masson’s trichrome staining. CT—connective tissue, MF—macrophage, NB—new bone, SC—scaffold.</p>
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<p>Connective tissue and immune cells in the area of the defect and between the scaffold filaments. H&amp;E. MF—macrophage, GC—giant cell, BV—blood vessel.</p>
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<p>Results of morphometrical study of a critical-size rat calvarial bone defect after implantation in control, PLGA, PLGA+Ad-BMP2 groups. * 0.05 &gt; <span class="html-italic">p</span> &gt; 0.01; *** <span class="html-italic">p</span> &lt; 0.001.</p>
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<p>Immunohistochemical study of regenerate in the area of critical rat calvarial defect after implantation. Staining for osteopontin (Opn) and alkaline phosphatase (Alpl) (brown).</p>
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<p>Laboratory 3D printer, process of layer-by-layer antisolvent printing and optical microscopy image of printed and cross-sectioned scaffold.</p>
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<p>PLGA scaffold mechanical test load scheme.</p>
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