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18 pages, 9457 KiB  
Article
Novel Injectable Collagen/Glycerol/Pullulan Gel Promotes Osteogenic Differentiation of Mesenchymal Stem Cells and the Repair of Rat Cranial Defects
by Xin Wang, Satoshi Komasa, Yoshiro Tahara, Shihoko Inui, Michiaki Matsumoto and Kenji Maekawa
Gels 2024, 10(12), 775; https://doi.org/10.3390/gels10120775 - 28 Nov 2024
Viewed by 359
Abstract
Bone tissue engineering is a technique that simulates the bone tissue microenvironment by utilizing cells, tissue scaffolds, and growth factors. The collagen hydrogel is a three-dimensional network bionic material that has properties and structures comparable to those of the extracellular matrix (ECM), making [...] Read more.
Bone tissue engineering is a technique that simulates the bone tissue microenvironment by utilizing cells, tissue scaffolds, and growth factors. The collagen hydrogel is a three-dimensional network bionic material that has properties and structures comparable to those of the extracellular matrix (ECM), making it an ideal scaffold and drug delivery system for tissue engineering. The clinical applications of this material are restricted due to its low mechanical strength. In this investigation, a collagen-based gel (atelocollagen/glycerol/pullulan [Col/Gly/Pul] gel) that is moldable and injectable with high adhesive qualities was created by employing a straightforward technique that involved the introduction of Gly and Pul. This study aimed to characterize the internal morphology and chemical composition of the Col/Gly/Pul gel, as well as to verify its osteogenic properties through in vivo and in vitro experiments. When compared to a standard pure Col hydrogel, this material is more adaptable to the complexity of the local environment of bone defects and the apposition of irregularly shaped flaws due to its greater mechanical strength, injectability, and moldability. Overall, the Col/Gly/Pul gel is an implant that shows great potential for the treatment of complex bone defects and the enhancement of bone regeneration. Full article
(This article belongs to the Special Issue Development of Nanogels/Microgels for Regenerative Medicine)
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Graphical abstract

Graphical abstract
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<p>(<b>A</b>) Fourier-transform infrared spectra: (a) pullulan (Pul), (b) atelocollagen (Col), (c) Col/Gly/Pul gel, and (d) glycerol (Gly). (<b>B</b>,<b>C</b>) Thixotropic studies of Col/Gly/Pul gel and standard liquid. (<b>D</b>) Swelling behavior of the Col/Gly/Pul gel. (<b>E</b>) Amplitude-strain, (<b>F</b>) frequency, and (<b>G</b>) tan δ (<span class="html-italic">G</span>″/<span class="html-italic">G</span>′) of frequency sweeps. LVR, linear viscoelastic region. (<b>H</b>) Images showing the moldability and injectability of the Col/Gly/Pul gel.</p>
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<p>(<b>A</b>) Scanning electron micrographs, and (<b>B</b>) pore size distribution. (<b>C</b>) The cell viability of rBMSCs initial adherent to the control, Col gel, and Col/Gly/Pul gel. Not significant (ns): <span class="html-italic">p</span> ≥ 0.05; ***: <span class="html-italic">p</span> &lt; 0.001; ****: <span class="html-italic">p</span> &lt; 0.0001. (<b>D</b>) In vitro degradation of the Col/Gly/Pul gel and Col gel.</p>
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<p>Morphology of rBMSCs attached to the control, Col gel, and Col/Gly/Pul gel after 24 h of incubation. Nuclei were labeled with DAPI (blue), and actin filaments stained with Phalloidin (green). Images obtained at a lower magnification (<b>A</b>) show the number and distribution of cells (scale bars = 100 µm), whereas those obtained at a higher magnification (<b>B</b>) show the connections among cells attached to the different samples (white arrows indicate interactions among cells; scale bars = 50 µm).</p>
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<p>(<b>A</b>–<b>C</b>) The real-time PCR analysis of specific osteogenesis-related gene expression on the control, Col gel, and Col/Gly/Pul gel. (<b>D</b>) Alkaline phosphatase (ALP) activity and (<b>E</b>) calcium deposition on the control, Col gel, and Col/Gly/Pul gel. Not significant (ns): <span class="html-italic">p</span> ≥ 0.05; *: <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; ****: <span class="html-italic">p</span> &lt; 0.0001. (<b>F</b>) Alizarin Red staining of the control, Col gel, and Col/Gly/Pul gel (white arrows indicate bone nodules).</p>
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<p>Effect of the Col/Gly/Pul gel on bone formation in a rat cranial defect model. (<b>A</b>) Treatment protocol for cranial bone defects in rats. Briefly, after separating the periosteum, a 5 mm cylinder-shaped bone defect was prepared on both sides of the sagittal midline of the rat parietal bone and then treated with or without gel. (<b>B</b>) Reconstructed three-dimensional micro-CT images of bone tissues after eight weeks. (<b>C</b>) Bone mineral density (BMD), (<b>D</b>) bone volume-to-total volume ratio (BV/TV), (<b>E</b>) trabecular number (Tb. N), (<b>F</b>) bone surface-to-bone volume ratio (BS/BV), and (<b>G</b>) trabecular separation (Tb. Sp) around the control, Col gel, and Col/Gly/Pul gel after eight weeks. Not significant (ns): <span class="html-italic">p</span> ≥ 0.05; *: <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; ****: <span class="html-italic">p</span> &lt; 0.0001.</p>
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<p>Sirius red stain sections of bone tissues after eight weeks around the (<b>A,a,b</b>) Control, (<b>B,c,d</b>) Col gel, and (<b>C,e,f</b>) Col/Gly/Pul gel. Mature, regular fibrous groups were marked by white arrows; immature, disorganized fibrous tissues marked by blue arrows; and the boundary between the old and new bone marked by black arrows.</p>
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<p>Schematic illustration of the principle of the Col/Gly/Pul gel to promote bone regeneration and repair. (<b>A</b>) Col/Gly/Pul gel provides a scaffold for cell growth. (<b>B</b>) Col/Gly/Pul gel provides mechanical stimuli to the cells and facilitates the diffusion of nutrients. (<b>C</b>) Col/Gly/Pul gel promotes osteogenic differentiation through multiple signaling pathways. (<b>D</b>) Regeneration of new bone tissue with degradation of the Col/Gly/Pul gel. This figure was drawn using Figdraw.</p>
Full article ">Scheme 1
<p>Schematic diagram of the design and preparation of an injectable gel composed of atelocollagen, glycerol, and pullulan (Col/Gly/Pul). (<b>A</b>) Col, Gly, and Pul were stirred at room temperature (23–25 °C) for 5 h. (<b>B</b>) The mixture was frozen at −80 °C for 30 min. (<b>C</b>) The material was dried with a freeze dryer for 12 h. (<b>D</b>) Injectable state of the Col/Gly/Pul gel. (<b>E</b>) Col/Gly/Pul gel before swelling. (<b>F</b>) Network of the swollen Col/Gly/Pul gel.</p>
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31 pages, 9924 KiB  
Review
Hyaluronic Acid-Based Dynamic Hydrogels for Cartilage Repair and Regeneration
by Mingshuo Zhang, Qianwen Ye, Zebo Zhu, Shuanglian Shi, Chunming Xu, Renjian Xie and Yumei Li
Gels 2024, 10(11), 703; https://doi.org/10.3390/gels10110703 - 30 Oct 2024
Cited by 1 | Viewed by 1374
Abstract
Hyaluronic acid (HA), an important natural polysaccharide and meanwhile, an essential component of extracellular matrix (ECM), has been widely used in tissue repair and regeneration due to its high biocompatibility, biodegradation, and bioactivity, and the versatile chemical groups for modification. Specially, HA-based dynamic [...] Read more.
Hyaluronic acid (HA), an important natural polysaccharide and meanwhile, an essential component of extracellular matrix (ECM), has been widely used in tissue repair and regeneration due to its high biocompatibility, biodegradation, and bioactivity, and the versatile chemical groups for modification. Specially, HA-based dynamic hydrogels, compared with the conventional hydrogels, offer an adaptable network and biomimetic microenvironment to optimize tissue repair and the regeneration process with a striking resemblance to ECM. Herein, this review comprehensively summarizes the recent advances of HA-based dynamic hydrogels and focuses on their applications in articular cartilage repair. First, the fabrication methods and advantages of HA dynamic hydrogels are presented. Then, the applications of HA dynamic hydrogels in cartilage repair are illustrated from the perspective of cell-free and cell-encapsulated and/or bioactive molecules (drugs, factors, and ions). Finally, the current challenges and prospective directions are outlined. Full article
(This article belongs to the Special Issue Hydrogel for Tissue Regeneration (2nd Edition))
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Figure 1
<p>HA hydrogels based on Schiff base bonding. (<b>A</b>). (<b>i</b>) HA/PRP/BM injectable hydrogel prepared by Schiff base reaction synergistically treats OA by viscosity enhancement, eliminating ROS, relieving inflammation, and promoting cartilage repair. (<b>ii</b>) Images of hydrogel gelation and self-healing process. (<b>iii</b>) Step strain test of hydrogel with fixed shear frequency of 1 Hz at 37 °C. (<b>iv</b>) Hydrogel can be injected through a 29-gauge needle without clogging. Reproduced with permission from ref. [<a href="#B56-gels-10-00703" class="html-bibr">56</a>], copyright, Elsevier. (<b>B</b>). (<b>i</b>) Preparation of double cross-linked OHA/HTCCMA hydrogel for articular cartilage repair. (<b>ii</b>) The O<sub>8</sub>H<sub>2</sub> hydrogel was cut in half and re-attached. (<b>iii</b>) Alternate step strain test of O<sub>8</sub>H<sub>2</sub> hydrogel. Reproduced with permission from ref. [<a href="#B53-gels-10-00703" class="html-bibr">53</a>], copyright, Elsevier.</p>
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<p>HA hydrogels based on acylhydrazone bonds. (<b>A</b>). (<b>i</b>) Schematic diagram of the hydrogel. (<b>ii</b>) Photograph of the healing process after cut disruption. (<b>iii</b>) Alternating step strain scanning curves of AMD-2 hydrogel and AMD + UV-2 hydrogel. (<b>iv</b>) Gel formation curves. Reproduced with permission from ref. [<a href="#B63-gels-10-00703" class="html-bibr">63</a>], copyright, Elsevier. (<b>B</b>). (<b>i</b>) Diagram of cross-linking mechanism of DN network. (<b>ii</b>) Scheme of the double cross-linking process (dynamic covalent acylhydrazone bonds labeled in red and Diels–Alder bonds chemically labeled in blue). (<b>iii</b>) Gel behavior of double crosslinked hydrogels. (<b>iv</b>) Self-healing properties of DN hydrogels (<b>a</b>–<b>c</b>). Reproduced with permission from ref. [<a href="#B65-gels-10-00703" class="html-bibr">65</a>], copyright, ACS Publications.</p>
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<p>HA hydrogel based on borate bonding. (<b>A</b>). (<b>i</b>) A scheme of a pH-controlled cross-linked hydrogel system. (<b>ii</b>) Self-healing properties of the hydrogel verified by tensile tests. (<b>iii</b>) Injectability test of hydrogel (with methylene blue) in a single syringe system. Reproduced with permission from ref. [<a href="#B67-gels-10-00703" class="html-bibr">67</a>], copyright, ACS Publications. (<b>B</b>). (<b>i</b>) Schematic diagram of dynamic HA hydrogel crosslinked with gelatin formation. (<b>ii</b>) Variation in storage modulus (G′) and loss modulus (G″) with time for different hydrogels. (<b>iii</b>) Shear recovery properties of gelatin cross-linked dynamic HA hydrogels. Reproduced with permission from ref. [<a href="#B71-gels-10-00703" class="html-bibr">71</a>], copyright, IOP Publishing.</p>
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<p>HA hydrogels based on disulfide bonds. (<b>A</b>). (<b>i</b>) Preparation and application process of composite hydrogels. (<b>ii</b>) Macroscopic morphology and gelling time measured by rheological test. (<b>iii</b>) Internal microstructure of the hydrogel measured by scanning electron microscopy. Reproduced with permission from ref. [<a href="#B74-gels-10-00703" class="html-bibr">74</a>], copyright, Royal Society of Chemistry. (<b>B</b>). (<b>i</b>) Schematic diagram of the synthesis process of HB-PBHE, HA-SH, and the generated HA-SH/HB-PBHE hydrogel. (<b>ii</b>) Dynamic time-scanning measurements. (<b>iii</b>) Variation in G′ and G″ with angular frequency for HA-SH/HB-PBHE hydrogel. Reproduced with permission from ref. [<a href="#B75-gels-10-00703" class="html-bibr">75</a>], copyright, Elsevier.</p>
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<p>Physically crosslinked dynamic HA hydrogel. (<b>A</b>). (<b>i</b>) Schematic design of an injectable composite hydrogel. (<b>ii</b>) Macroscopic photographs of the hydrogel at different temperatures. (<b>iii</b>) Injectability, thermal sensitivity, and shape adaptation. (<b>iv</b>) Rheological recovery behavior of composite hydrogels. Reproduced with permission from ref. [<a href="#B58-gels-10-00703" class="html-bibr">58</a>], copyright, KeAi. (<b>B</b>). (<b>i</b>) Schematic diagram of dual network hydrogel. (<b>ii</b>) Self-healing behavior of the samples when low (1%) and high (100%, 300%, and 500%) strain cycles are applied alternately. (<b>iii</b>) Schematic of adhesion measurement. Reproduced with permission from ref. [<a href="#B76-gels-10-00703" class="html-bibr">76</a>], copyright, Nature Portfolio.</p>
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<p>HA hydrogels based on multiple dynamic cross-links. (<b>A</b>). (<b>i</b>) Microstructural fusion of fast gel AHA/CMC hydrogel print constructs based on dynamic imine bonds. (<b>ii</b>) Preparation of AHA/PEG-SG slow gels through the formation of stable amide bonds. (<b>iii</b>) TSHSP hydrogels prepared by complementary AHA/ CMC and GEL/PEG-SG. Reproduced with permission from ref. [<a href="#B82-gels-10-00703" class="html-bibr">82</a>], copyright, Elsevier. (<b>B</b>). (<b>i</b>) Preparation scheme of PBNPs@OBG hydrogels. (<b>ii</b>) Schematic structure of a hydrogel consisting mainly of imine and borate bonds. Reproduced with permission from ref. [<a href="#B19-gels-10-00703" class="html-bibr">19</a>], copyright, BMC. (<b>C</b>). Scheme for the formation of double dynamic bond crosslinked hydrogels (HPP). Reproduced with permission from ref. [<a href="#B54-gels-10-00703" class="html-bibr">54</a>], copyright, Wiley. (<b>D</b>). Schematic diagram of ADQ hydrogel preparation. Reproduced with permission from ref. [<a href="#B85-gels-10-00703" class="html-bibr">85</a>], copyright, Elsevier.</p>
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<p>Illustration articular cartilage structure and composition (<b>A</b>) and the tissue engineering method for cartilage repair and regeneration (<b>B</b>). Reproduced with permission from reference [<a href="#B86-gels-10-00703" class="html-bibr">86</a>], copyright, RSC Publishing.</p>
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<p>Dynamic HA hydrogel for the treatment of OA. (<b>A</b>). Cartilage repairing effect of double crosslinked OHA/HTCCMA hydrogel. (<b>i</b>) Photographs of the gross appearance of healed rabbit articular cartilage within 56 days. (<b>ii</b>) H and E staining, (<b>iii</b>) SO/FG staining images of cartilage tissue. Reproduced with permission from ref. [<a href="#B53-gels-10-00703" class="html-bibr">53</a>], copyright, Elsevier. (<b>B</b>). In vivo therapeutic effect of intra-articular injection of double dynamic bond cross-linked hydrogel (HPP) on OA in mice. (<b>i</b>) CT reconstruction model of femoral condyle. (<b>ii</b>) Representative images of SF and H and E stained mouse joints. Reproduced with permission from ref. [<a href="#B54-gels-10-00703" class="html-bibr">54</a>], copyright, Wiley.</p>
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<p>Cell-loaded HA hydrogel for the treatment of OA. (<b>A</b>). (<b>i</b>) (<b>a</b>) Osteochondral defect of rabbit knee joint, untreated (sham operation). Arrow points to the defect site. (<b>b</b>) Implant a separate gel at the defect site. (<b>c</b>) Allogeneic chondrocyte coated gel was implanted at the defect site. Arrows point to gel/gel + cells at the defect site. (<b>ii</b>) General appearance of the joint 12 weeks after implantation. Arrows point to regenerated tissue and circles indicate enlarged areas of regenerated cartilage. Reproduced with permission from ref. [<a href="#B97-gels-10-00703" class="html-bibr">97</a>], copyright, Elsevier. (<b>B</b>). (<b>i</b>) Arthroscopic examination 1 year after human umbilical cord blood-derived MSC-HA hydrogel composite transplantation reveals good surface reconstruction at the defect site, with smooth surface of the regenerated cartilage and good fusion with the surrounding cartilage. (<b>ii</b>) Biopsy samples were taken from the regenerated cartilage. (<b>iii</b>) Histological presentation of the regenerated cartilage. Histological analysis of the biopsy samples showed that the staining pattern of the regenerated cartilage was similar to that of normal articular hyaline cartilage. (<b>iv</b>) MRI of cartilage regeneration after transplantation of hUCB-MSCs-HA hydrogels at 3 years. Reproduced with permission from ref. [<a href="#B101-gels-10-00703" class="html-bibr">101</a>], copyright, Oxford Academic.</p>
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<p>Drug-encapsulated HA hydrogel for the treatment of OA. (<b>A</b>). Schematic diagram of the surgical procedure for the formation of an injectable SF/HA hydrogel scaffold and regeneration of cartilage tissue. Reproduced with permission from ref. [<a href="#B55-gels-10-00703" class="html-bibr">55</a>], copyright, Elsevier. (<b>B</b>). (<b>i</b>) Schematic diagram of the synthesis of HA/PRP/BM injectable hydrogels. (<b>ii</b>) Therapeutic effect of each hydrogel treatment group on OA model. (a) HE staining, (b) SO/FG staining and (c) collagen II protein immunohistochemical staining. Reproduced with permission from ref. [<a href="#B56-gels-10-00703" class="html-bibr">56</a>], copyright, Elsevier. (<b>C</b>). (<b>i</b>) Development and application of SHA@KGN/TGF-β<sub>1</sub> multifunctional hydrogel. (<b>ii</b>) Schematic diagram of the synergistic interaction between KGN and TGF-β<sub>1</sub>. (<b>iii</b>) Arthroscopic in situ implantation of various hydrogels for repairing articular cartilage for 8 weeks. Figure (<b>a</b>) shows a schematic diagram of arthroscopic ACD repair. Figures (<b>b1</b>,<b>b2</b>), (<b>c1</b>,<b>c2</b>), (<b>d1</b>,<b>d2</b>) and (<b>e1</b>,<b>e2</b>) are gross and microscopic images after repair. Figures (<b>b3</b>–<b>b7</b>), (<b>c3</b>–<b>c7</b>), (<b>d3</b>–<b>d7</b>) and (<b>e3</b>–<b>e7</b>) show the staining of each group. Reproduced with permission from ref. [<a href="#B57-gels-10-00703" class="html-bibr">57</a>], copyright, Elsevier.</p>
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<p>HA hydrogel loaded with metal ions for the treatment of OA. (<b>A</b>). (<b>i</b>) Chemical structure of prepared calcium hyaluronate complex (HA@Ca) and its injectable hydrogel. (<b>ii</b>) Schematic representation of the enhanced remodeling hydrogel mechanism. (<b>iii</b>) Schematic and application of HA based biphasic hydrogels for selective hyaline and calcified cartilage regeneration. (<b>iv</b>) Nucleic acid and f-actin staining of samples taken from in vivo experiments in a simulated in vivo model of cartilage regeneration to confirm whether phosphorylated HA affects chondrocyte morphology. * <span class="html-italic">p</span> &lt; 0.05 and **** <span class="html-italic">p</span> &lt; 0.0001 Reproduced with permission from ref. [<a href="#B115-gels-10-00703" class="html-bibr">115</a>], copyright, Wiley. (<b>B</b>). (<b>i</b>) Mg-PC@Dop-HA/F127 hydrogel repair cartilage by regulating the inflammatory environment and controlling the release of Mg-PC. (<b>ii</b>) Reconstruction of the proximal humerus in rats and acquisition of coronal images at 4 and 8 weeks post-surgery using CT technology. (<b>iii</b>) Morphological analysis of the newly formed tendon-bone interface tissue after treatment. Reproduced with permission from ref. [<a href="#B58-gels-10-00703" class="html-bibr">58</a>], copyright, KeAi.</p>
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<p>Research methods for the treatment of articular cartilage and regeneration.</p>
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16 pages, 5528 KiB  
Article
Bioactive Hydrogels Based on Tyramine and Maleimide Functionalized Dextran for Tissue Engineering Applications
by Lin Zhong, Alma Tamunonengiofori Banigo, Bram Zoetebier and Marcel Karperien
Gels 2024, 10(9), 566; https://doi.org/10.3390/gels10090566 - 30 Aug 2024
Cited by 1 | Viewed by 998
Abstract
Hydrogels are widely used in tissue engineering due to their ability to form three-dimensional (3D) structures that support cellular functions and mimic the extracellular matrix (ECM). Despite their advantages, dextran-based hydrogels lack intrinsic biological activity, limiting their use in this field. Here, we [...] Read more.
Hydrogels are widely used in tissue engineering due to their ability to form three-dimensional (3D) structures that support cellular functions and mimic the extracellular matrix (ECM). Despite their advantages, dextran-based hydrogels lack intrinsic biological activity, limiting their use in this field. Here, we present a strategy for developing bioactive hydrogels through sequential thiol–maleimide bio-functionalization and enzyme-catalyzed crosslinking. The hydrogel network is formed through the reaction of tyramine moieties in the presence of horseradish peroxidase (HRP) and hydrogen peroxide (H2O2), allowing for tunable gelation time and stiffness by adjusting H2O2 concentrations. Maleimide groups on the hydrogel backbone enable the coupling of thiol-containing bioactive molecules, such as arginylglycylaspartic acid (RGD) peptides, to enhance biological activity. We examined the effects of hydrogel stiffness and RGD concentration on human mesenchymal stem cells (hMSCs) during differentiation and found that hMSCs encapsulated within these hydrogels exhibited over 88% cell viability on day 1 across all conditions, with a slight reduction to 60–81% by day 14. Furthermore, the hydrogels facilitated adipogenic differentiation, as evidenced by positive Oil Red O staining. These findings demonstrate that DexTA–Mal hydrogels create a biocompatible environment that is conducive to cell viability and differentiation, offering a versatile platform for future tissue engineering applications. Full article
(This article belongs to the Special Issue Biopolymer-Based Gels for Drug Delivery and Tissue Engineering)
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<p>Synthesis and characterization of DexTA–Mal. (<b>A</b>) Schematic of synthesis route for DexTA–Mal, (<b>B</b>) <sup>1</sup>H-NMR spectra of DexTA–Mal (<b>i</b>), and DexTA–bNH<sub>2</sub> (<b>ii</b>) in DMSO-d<sub>6</sub>, the dextran region is shaded and the letters corresponding to the protons are marked in the chemical structures above. TFA, trifluoroacetic acid; bNH<sub>2</sub>, butylamine; boc, tert-butyloxycarbonyl; AMAS, n-(α-maleimidoacetoxy)succinimide ester [<a href="#B32-gels-10-00566" class="html-bibr">32</a>].</p>
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<p>Schematic representation of the DexTA–Mal polymers, capable of forming a hydrogel (<b>A</b>) with PEG dithiol (<b>B</b>) or via enzymatic crosslinking of the tyramine moieties. Biofunctionalization is demonstrated with (<b>C</b>) a fluorescent peptide (<b>i</b>) SDS-PAGE gel analysis and fluorescence visualization of FITC-labeled peptide after conjugating to DexTA-Mal (<b>ii</b>) bright-field and (<b>iii</b>) fluorescence imaging of FITC-labeled peptide in hydrogel (<b>D</b>) and with BSA (<b>i</b>) Coomassie blue-stained SDS-PAGE gel analysis of BSA after conjugating to DexTA-Mal, (<b>ii</b>) digital photograph of BSA-loaded hydrogel before and (<b>iii</b>) after coomassie blue staining. (Pep: FITC-labeled peptide; Cys: cysteine; Polymer-Mal: DexTA-Mal) [<a href="#B32-gels-10-00566" class="html-bibr">32</a>].</p>
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<p>Characterization of DexTA–Mal hydrogels. (<b>A</b>) Storage modulus and (<b>B</b>) swelling ratio of hydrogels as a function of polymer concentration. Hydrogels were prepared using 4 U/mL of HRP and a H<sub>2</sub>O<sub>2</sub>/TA molar ratio of 0.5. (<b>C</b>) Storage modulus and (<b>D</b>) swelling ratio of 10% (<span class="html-italic">w</span>/<span class="html-italic">v</span>) hydrogels as a function of degree of crosslinking, and (<b>E</b>) gelation time based on HRP concentration [<a href="#B32-gels-10-00566" class="html-bibr">32</a>].</p>
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<p>(<b>A</b>) Gelation time and (<b>B</b>) storage moduli of DexTA–Mal, depending on crosslinking density and RGD addition.</p>
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<p>(<b>A</b>,<b>B</b>) Viability of hMSCs on days 1, 7, and 14, (Live (green) and dead (red) cells are stained).and (<b>C</b>) morphology of hMSCs on day 7 in injectable DexTA–Mal hydrogel compositions with 10% or 20% crosslinking, 1.0 U/mL HRP with or without RGD (Actin filaments (green) and nucleus (blue) are stained). Scale bar is 100 μm.</p>
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<p>Adipogenic differentiation: (<b>A</b>) percentage of cells stained by Oil Red O in representative samples of DexTA–Mal hydrogels ± RGD, with 10 or 20% crosslinking density and hMSCs cultured for 14 days in bipotential medium. (<b>B</b>) Micrographs of representative samples of DexTA–Mal hydrogels ± RGD, with 10 or 20% crosslinking density and hMSCs cultured for 14 days in bipotential medium, stained with Oil Red O (red colour indicates fat deposition). Black scale bar: 100 inches.</p>
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19 pages, 6385 KiB  
Article
Osteoblastic Cell Sheet Engineering Using P(VCL-HEMA)-Based Thermosensitive Hydrogels Doped with pVCL@Icariin Nanoparticles Obtained with Supercritical CO2-SAS
by Rubén García-Sobrino, Isabel Casado-Losada, Carmen Caltagirone, Ana García-Crespo, Carolina García, Juan Rodríguez-Hernández, Helmut Reinecke, Alberto Gallardo, Carlos Elvira and Enrique Martínez-Campos
Pharmaceutics 2024, 16(8), 1063; https://doi.org/10.3390/pharmaceutics16081063 - 13 Aug 2024
Viewed by 1337
Abstract
New clinical strategies for treating severe bone and cartilage injuries are required, especially for use in combination with implant procedures. For this purpose, p(VCL-co-HEMA) thermosensitive hydrogels have been activated with icariin-loaded nanoparticles to be used as bone-cell-harvesting platforms. Supercritical CO2-SAS technology [...] Read more.
New clinical strategies for treating severe bone and cartilage injuries are required, especially for use in combination with implant procedures. For this purpose, p(VCL-co-HEMA) thermosensitive hydrogels have been activated with icariin-loaded nanoparticles to be used as bone-cell-harvesting platforms. Supercritical CO2-SAS technology has been applied to encapsulate icariin, a small molecule that is involved in osteoblastic differentiation. Thus, physical-chemical analysis, including swelling and transmittance, showed the impact of HEMA groups in hydrogel composition. Moreover, icariin (ICA) release from p(VCL-co-HEMA) platforms, including pVCL@ICA nanoparticles, has been studied to evaluate their efficacy in relevant conditions. Finally, the thermosensitive hydrogels’ cell compatibility, transplant efficiency, and bone differentiation capacity were tested. This study identifies the optimal formulations for icariin-activated hydrogels for both control and HEMA formulations. Using this technique, osteoblastic sheets that were rich in collagen type I were successfully transplanted and recultivated, maintaining an optimal extracellular matrix (ECM) composition. These findings suggest a new cell-sheet-based therapy for bone regeneration purposes using customized and NP-activated pVCL-based cell platforms. Full article
(This article belongs to the Special Issue Supercritical Techniques for Pharmaceutical Applications)
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<p>Scheme of the proposal evaluated in this work.</p>
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<p>(<b>a</b>) Bright-field images of C2C12-GFP premyoblastic cell transplants 24 h after the cell transplant stage; (scale bar: 200 µm). (<b>b</b>) Metabolic activity (Alamar Blue) of cell transplants at 24 h. Significant differences were indicated as follows: * (<span class="html-italic">p</span> ≤ 0.05) and ** (<span class="html-italic">p</span> ≤ 0.01).</p>
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<p>SEM micrograph evaluation: temperature optimization process at 40 (<b>a</b>) and 35 °C (<b>b</b>). Pressure optimization process at 100 (<b>c</b>) and 200 bar (<b>d</b>). pVCL-ICA concentrations at 20 (<b>e</b>) and 30 mg/mL (<b>f</b>). ICA load at 5 (<b>g</b>) and 20 wt.% (<b>h</b>). The scale bar for (<b>a</b>) is 10 µm and (<b>b</b>–<b>h</b>) is 2 µm.</p>
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<p>(<b>a</b>) ICA release profile (mg) from the nanoparticles (NP5, 10, and 20) at 37 °C. (<b>b</b>) ICA release from the hydrogels (mg) at 37 °C, using PBS as a medium. (<b>c</b>) Release percentage of ICA from the hydrogels, also at 37 °C.</p>
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<p>MC3T3−E1 osteoblastic cell cultures, proliferating over hydrogels at day 14 (scale bar: 200 µm).</p>
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<p>(<b>a</b>) PicroSirius Red staining (collagen I) from MC3T3−E1 osteoblastic transplants from hydrogels at day 8 after transplant; (scale bar: 200 µm). (<b>b</b>) PicroSirius Red quantification. Significant differences were indicated as follows: ** (<span class="html-italic">p</span> ≤ 0.01).</p>
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13 pages, 1752 KiB  
Article
Customizable Hydrogel Coating of ECM-Based Microtissues for Improved Cell Retention and Tissue Integrity
by Shani Elgin, Eric Silberman, Assaf Shapira and Tal Dvir
Gels 2024, 10(8), 515; https://doi.org/10.3390/gels10080515 - 5 Aug 2024
Viewed by 1303
Abstract
Overcoming the oxygen diffusion limit of approximately 200 µm remains one of the most significant and intractable challenges to be overcome in tissue engineering. The fabrication of hydrogel microtissues and their assembly into larger structures may provide a solution, though these constructs are [...] Read more.
Overcoming the oxygen diffusion limit of approximately 200 µm remains one of the most significant and intractable challenges to be overcome in tissue engineering. The fabrication of hydrogel microtissues and their assembly into larger structures may provide a solution, though these constructs are not without their own drawbacks; namely, these hydrogels are rapidly degraded in vivo, and cells delivered via microtissues are quickly expelled from the area of action. Here, we report the development of an easily customized protocol for creating a protective, biocompatible hydrogel barrier around microtissues. We show that calcium carbonate nanoparticles embedded within an ECM-based microtissue diffuse outwards and, when then exposed to a solution of alginate, can be used to generate a coated layer around the tissue. We further show that this technique can be fine-tuned by adjusting numerous parameters, granting us full control over the thickness of the hydrogel coating layer. The microtissues’ protective hydrogel functioned as hypothesized in both in vitro and in vivo testing by preventing the cells inside the tissue from escaping and protecting the microdroplets against external degradation. This technology may provide microtissues with customized properties for use as sources of regenerative therapies. Full article
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<p>Overall schematic. Cells (brown) and nanoparticles of CaCO<sub>3</sub> (gray) were encapsulated within an ECM-based hydrogel (red), and a microfluidic system was used to generate microtissues. When the microdroplets were subsequently suspended in a solution of sodium alginate (yellow), the calcium ions crosslinked the alginate and generated a customizable protective shell around the microgel. Created with BioRender.com.</p>
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<p>Controlling the Alginate Capsule. (<b>a</b>) The 3D confocal imaging revealed that the alginate shell completely surrounded the microdroplet from all sides. For visualization, FITC liposomes were incorporated in the ECM-based hydrogel and alginate was tagged with fluorescent moieties. (<b>b</b>) Representative images of alginate barriers with varying thickness and integrity. For visualization, fluorescent microparticles were incorporated in the alginate layer. (<b>c</b>) The thickness of the alginate capsule varies proportionally with the concentration of <sup>np</sup>CaCO<sub>3</sub> used. (<b>d</b>) Increasing the concentration of alginate in which the microdroplets were submersed increases the thickness of the capsule. (<b>e</b>) Using longer alginate chains (Protanal<sup>®</sup> LF 200 FTS vs. Protanal<sup>®</sup> LF 10/60 FT) led to an increase in capsule thickness. (<b>f</b>) Increasing the time during which the reaction was allowed to proceed led to an increase in the thickness of the alginate layer. Scale bars = 20 µm.</p>
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<p>Functionality and biocompatibility of the alginate coating. (<b>a</b>) The addition of <sup>np</sup>CaCO<sub>3</sub> caused no significant changes in the rheological properties of the ECM-based hydrogel. (<b>b</b>) The cell-coating protocol had no negative impact on cell viability, and, indeed, showed a positive increase in cell viability after a week of cultivation. (<b>c</b>) The presence of the alginate coating did not impair cell viability. In fact, because the coating acted to protect the microtissue, coated microtissues remained larger and thus were able to accommodate larger and more active cell populations. (<b>d</b>) Representative images showing cells that had escaped from the droplet and adhered to the well plate on Day 3 in both uncoated (left) and coated-then-enzymatically-degraded (center) droplets. Droplets with an intact alginate barrier showed negligible cell escape (right). Scale bars = 100 µm. (<b>e</b>) The presence of the coating almost entirely halted the ability of the cells to migrate out of and away from the microtissue. The impact of the alginate was further verified by enzymatically degrading the alginate, which led to unimpaired “cell escape”.</p>
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<p>Integrity of alginate barrier. (<b>a</b>) The alginate barrier prevented water molecules and even collagenase enzymes from degrading the hydrogel, while unprotected droplets rapidly degraded. (<b>b</b>) Representative images showing the thickness and integrity of the alginate shell before (left) and after (right) being injected through a hypodermic needle. Scale bar = 100 µm. (<b>c</b>) Quantification of the barrier integrity showed no significant change as a result of injection.</p>
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<p>Injection of microtissues into in vivo murine model. (<b>a</b>) Immunofluorescent staining performed on Day 0 of the in vivo experiment confirms that the microtissues were successfully deployed within the murine muscle. (<b>b</b>) Immunofluorescent staining on Day 0 of the microtissues containing the protective alginate shell. (<b>c</b>) On Day 5, unprotected microtissues had largely been degraded and injected cells had escaped or been removed from the area. (<b>d</b>) Microtissues that contained a protective alginate coating maintained their integrity and, more importantly, maintained high cell concentrations at the site of injection. Scale bars = 100 µm.</p>
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19 pages, 9265 KiB  
Article
Injectable Biodegradable Chitosan–PEG/PEG–Dialdehyde Hydrogel for Stem Cell Delivery and Cartilage Regeneration
by Xiaojie Lin, Ruofan Liu, Jacob Beitzel, Yang Zhou, Chloe Lagadon and Miqin Zhang
Gels 2024, 10(8), 508; https://doi.org/10.3390/gels10080508 - 1 Aug 2024
Viewed by 1311
Abstract
Stem cell-based therapy holds promise for cartilage regeneration in treating knee osteoarthritis (KOA). Injectable hydrogels have been developed to mimic the extracellular matrix (ECM) and facilitate stem cell growth, proliferation, and differentiation. However, these hydrogels face limitations such as poor mechanical strength, inadequate [...] Read more.
Stem cell-based therapy holds promise for cartilage regeneration in treating knee osteoarthritis (KOA). Injectable hydrogels have been developed to mimic the extracellular matrix (ECM) and facilitate stem cell growth, proliferation, and differentiation. However, these hydrogels face limitations such as poor mechanical strength, inadequate biocompatibility, and suboptimal biodegradability, collectively hindering their effectiveness in cartilage regeneration. This study introduces an injectable, biodegradable, and self-healing hydrogel composed of chitosan–PEG and PEG–dialdehyde for stem cell delivery. This hydrogel can form in situ by blending two polymer solutions through injection at physiological temperature, encapsulating human adipose-derived stem cells (hADSCs) during the gelation process. Featuring a 3D porous structure with large pore size, optimal mechanical properties, biodegradability, easy injectability, and rapid self-healing capability, the hydrogel supports the growth, proliferation, and differentiation of hADSCs. Notably, encapsulated hADSCs form 3D spheroids during proliferation, with their sizes increasing over time alongside hydrogel degradation while maintaining high viability for at least 10 days. Additionally, hADSCs encapsulated in this hydrogel exhibit upregulated expression of chondrogenic differentiation genes and proteins compared to those cultured on 2D surfaces. These characteristics make the chitosan–PEG/PEG–dialdehyde hydrogel–stem cell construct suitable for direct implantation through minimally invasive injection, enhancing stem cell-based therapy for KOA and other cell-based treatments. Full article
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<p>Polymer structure and characterizations. Synthesis routes and chemical structures of (<b>a</b>) mPEG–acid, (<b>b</b>) chitosan–PEG, and (<b>c</b>) PEG–dialdehyde. (<b>d</b>) <sup>1</sup>H NMR spectra of chitosan and chitosan–PEG. (<b>e</b>) <sup>1</sup>H NMR spectra of PEG-2000 and PEG–dialdehyde.</p>
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<p>Hydrogel injectability, chemical structure, gelation, morphologies, and self-healing capability. (<b>a</b>) Illustration of the double-barrel syringe filled with chitosan–PEG and PEG–dialdehyde solutions for creating hydrogels. (<b>b</b>) Chemical structure of crosslinked chitosan–PEG/PEG–dialdehyde hydrogel. (<b>c</b>) Gelation process: photos of chitosan–PEG before (sol) and after (gel) adding PEG–dialdehyde. (<b>d</b>) SEM photograph of freeze-dried chitosan–PEG/PEG–dialdehyde hydrogel; scale bar represents 20 μm. (<b>e</b>) Images demonstrating the self-healing capability of chitosan–PEG/PEG–dialdehyde hydrogel: (1) A 700 μL aliquot of freshly prepared hydrogel was divided into two pieces with one of them stained with Trypan Blue for identification purposes; (2) following this, the two pieces were brought together at room temperature for 3 min; (3) resulting in the formation of a single hydrogel piece through spontaneous fusion, which was then picked up using tweezers.</p>
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<p>Rheological analysis of chitosan–PEG/PEG–dialdehyde hydrogels. (<b>a</b>) The storage modulus (G’, filled symbols) and loss modulus (G”, empty symbols) were recorded under the strain sweep at 37 °C and 1 Hz for chitosan–PEG/PEG–dialdehyde hydrogels with different concentrations (1.3% and 2.5%, <span class="html-italic">w</span>/<span class="html-italic">v</span>), showing that strain at 0.1% was within the linear viscoelastic regime (LVR) with less noise. (<b>b</b>) The G’ and G” were recorded under the time sweep for chitosan–PEG/PEG–dialdehyde hydrogels with different concentrations (1.3% and 2.5%, <span class="html-italic">w</span>/<span class="html-italic">v</span>) right after injection, showing the crossover point of G’ and G” for verification of gelation (G’ &gt; G”). (<b>c</b>) The G’ and G” were recorded under increasing shear stress for chitosan–PEG and chitosan–PEG/PEG–dialdehyde hydrogels with different concentrations (1.3% and 2.5%, <span class="html-italic">w</span>/<span class="html-italic">v</span>) at 37 °C to compare the strength of different hydrogels. (<b>d</b>) The G’ and G” were recorded under increasing temperatures for chitosan–PEG and chitosan–PEG/PEG–dialdehyde hydrogels with different concentrations (1.3% and 2.5%, <span class="html-italic">w</span>/<span class="html-italic">v</span>) at 37 °C to show their thermosensitivity.</p>
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<p>Hydrogel swelling and degradation behaviors. (<b>a</b>) Swelling ratio and (<b>b</b>) degradation of chitosan–PEG/PEG–dialdehyde hydrogels incubated in complete human mesenchymal stem cell medium or DPBS and maintained at 37 °C. The hydrogels were prepared by mixing chitosan–PEG (2.5%, <span class="html-italic">w</span>/<span class="html-italic">v</span>) and PEG–dialdehyde (1 g/mL) at a volume mixing ratio of 6:1.</p>
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<p>The effect of culture environment on hADSC viability. Fluorescence images of hADSCs cultured in chitosan–PEG/PEG–dialdehyde hydrogels (2.5%, <span class="html-italic">w</span>/<span class="html-italic">v</span>, 3D hydrogel) and on regular 2D surfaces (2D control) on days 1, 3, 5, 7, and 10. hADSCs were stained with Calcein-AM (green, for live) and propidium iodide (red, for dead). Short scale bar represents 200 μm, and long scale bar represents 100 μm.</p>
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<p>(<b>a</b>) The diameter of cell spheroids in chitosan–PEG/PEG–dialdehyde hydrogels (2.5%, <span class="html-italic">w</span>/<span class="html-italic">v</span>) on day 1, 3, 5, and 7. One-way ANOVA followed by Tukey’s multiple comparison test was used to determine whether the differences were statistically significant (mean ± SD, <span class="html-italic">n</span> &gt; 5; **** <span class="html-italic">p</span> &lt; 0.0001; ns, nonsignificant). (<b>b</b>) Cell proliferation results tested by the alamarBlue assay on day 1, 3, 5, 7, and 10 days for hADSCs cultured in chitosan–PEG/PEG–dialdehyde hydrogels (2.5%, <span class="html-italic">w</span>/<span class="html-italic">v</span>) (<span class="html-italic">n</span> = 3).</p>
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<p>Gene expression associated with chondrogenic differentiation. Relative expression of RNA: (<b>a</b>) ACAN, (<b>b</b>) SOX9, and (<b>c</b>) Col-II contents in hADSCs cultured on 2D TCPS and in 3D hydrogels in chondrogenic differentiation medium for a 10-day culture period. Gene expression was first normalized to glyceraldehyde 3-phosphate dehydrogenase (GAPDH) (reference gene) and then normalized to the expression associated with 2D TCPS culture on day 0 (set as 1-time). One-way ANOVA followed by Tukey’s multiple comparison test was used to determine whether the differences were statistically significant (mean ± SD, <span class="html-italic">n</span> = 3; * <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; 0.0001; ns, nonsignificant). Legend: 2D = hADSCs cultured on 2D TCPS in the complete cell culture medium, 2D-d = hADSCs cultured on 2D TCPS in the chondrogenic differentiation medium, 3D-d = hADSCs cultured in 3D hydrogels in the chondrogenic differentiation medium.</p>
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<p>Protein expression associated with chondrogenic differentiation of hADSCs encapsulated in hydrogels. Immunofluorescence staining was applied for Aggrecan (ACAN, green), SRY-Box Transcription Factor 9 (SOX9, red), and cell nuclei (DAPI, blue). hADSCs were cultured in chitosan–PEG/PEG–dialdehyde hydrogels (2.5%, <span class="html-italic">w</span>/<span class="html-italic">v</span>) in the chondrogenic differentiation medium (3D-d) for a 10-day culture period. hADSCs cultured on 2D TCPS surface in both chondrogenic differentiation medium (2D-d) and normal cell culture medium (2D) were used as a control. The short scale bar represents 200 μm, and the long scale bar represents 100 μm.</p>
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<p>Schematic illustration of an injectable and biological compatible stem cell-laden hydrogel at a cartilage defect site for knee cartilage repair.</p>
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25 pages, 3615 KiB  
Review
Biomechanical Properties and Cellular Responses in Pulmonary Fibrosis
by Andong He, Lizhe He, Tianwei Chen, Xuejin Li and Chao Cao
Bioengineering 2024, 11(8), 747; https://doi.org/10.3390/bioengineering11080747 - 24 Jul 2024
Viewed by 1707
Abstract
Pulmonary fibrosis is a fatal lung disease affecting approximately 5 million people worldwide, with a 5-year survival rate of less than 50%. Currently, the only available treatments are palliative care and lung transplantation, as there is no curative drug for this condition. The [...] Read more.
Pulmonary fibrosis is a fatal lung disease affecting approximately 5 million people worldwide, with a 5-year survival rate of less than 50%. Currently, the only available treatments are palliative care and lung transplantation, as there is no curative drug for this condition. The disease involves the excessive synthesis of the extracellular matrix (ECM) due to alveolar epithelial cell damage, leading to scarring and stiffening of the lung tissue and ultimately causing respiratory failure. Although multiple factors contribute to the disease, the exact causes remain unclear. The mechanical properties of lung tissue, including elasticity, viscoelasticity, and surface tension, are not only affected by fibrosis but also contribute to its progression. This paper reviews the alteration in these mechanical properties as pulmonary fibrosis progresses and how cells in the lung, including alveolar epithelial cells, fibroblasts, and macrophages, respond to these changes, contributing to disease exacerbation. Furthermore, it highlights the importance of developing advanced in vitro models, based on hydrogels and 3D bioprinting, which can accurately replicate the mechanical and structural properties of fibrotic lungs and are conducive to studying the effects of mechanical stimuli on cellular responses. This review aims to summarize the current understanding of the interaction between the progression of pulmonary fibrosis and the alterations in mechanical properties, which could aid in the development of novel therapeutic strategies for the disease. Full article
(This article belongs to the Section Biomechanics and Sports Medicine)
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<p>(<b>A</b>) A schematic view of a healthy and fibrotic lung [<a href="#B4-bioengineering-11-00747" class="html-bibr">4</a>]; (<b>B</b>) the major cellular response and pathological activities as pulmonary fibrosis develops; and (<b>C</b>) a schematic representation of changes in the mechanical microenvironment and cell phenotype before and after the onset of pulmonary fibrosis. The elasticity, viscosity, and surface tension contribute to maintaining the homeostasis of healthy lung tissue. As pulmonary fibrosis develops, the elastic and viscous properties of the tissue become altered, along with elevated shear stress and surface tension, which in turn induce the apoptosis of epithelial cells and the activation of immune cells and fibroblasts. The activated fibroblasts then synthesize an excessive amount of the ECM, thereby aggravating the pulmonary fibrosis [<a href="#B14-bioengineering-11-00747" class="html-bibr">14</a>].</p>
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<p>(<b>A</b>) Immunostaining of collagen I in murine lung parenchyma treated with either saline (left) or bleomycin (right, for pulmonary fibrosis induction), as well as the corresponding AFM elastograph of the region of interest as highlighted with dashed squares. Scale = 100 μm [<a href="#B28-bioengineering-11-00747" class="html-bibr">28</a>]. (<b>B</b>) The scheme of investigating the Young’s modulus of lung using an AFM, and the Young’s modulus of lungs of different regions in control and Cdc42-null mice following sham surgery or post-lung lobe resection (PNX) [<a href="#B29-bioengineering-11-00747" class="html-bibr">29</a>]. Reprinted and adapted from references [<a href="#B28-bioengineering-11-00747" class="html-bibr">28</a>,<a href="#B29-bioengineering-11-00747" class="html-bibr">29</a>] with permissions. NS: <span class="html-italic">p</span> &gt; 0.05, *** <span class="html-italic">p</span> &lt; 0.001 for Student’s t test.</p>
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<p>(<b>A</b>) Intraesophageal pressure–volume loops of a healthy adult (A), healthy child (B), and patient with pulmonary fibrosis (C). The work against vicious lung tissue resistance was highlighted with shaded areas [<a href="#B38-bioengineering-11-00747" class="html-bibr">38</a>]; (<b>B</b>) changes in the relaxation time, migration speed of cells, and cell migration persistence coefficient of a collagen-based substrate with and without treatment with LOX [<a href="#B44-bioengineering-11-00747" class="html-bibr">44</a>], * <span class="html-italic">p</span> &lt; 0.05, *** <span class="html-italic">p</span> &lt; 0.001 for Welch’s <span class="html-italic">t</span>-test; (<b>C</b>) the scheme of decomposing the viscoelastic properties of lung tissue via a self-similar model, with E representing elasticity, J as a composite (viscoelastic) building block, and η as cytoplasm viscosity, respectively; (<b>D</b>) an ROC analysis of how the power-law exponents (α<sub>short</sub> and α<sub>long</sub> for exponents within 0.01–1 s and 1–10 s, respectively) and the elasticity at the cytoplasm (E<sub>1</sub>), cellular (E<sub>2</sub>), and tissue (E<sub>3</sub>) levels, as well as the cytoplasm viscosity are effective in distinguishing the lung tissues of different conditions (healthy control, fibrotic, or MSC-transplanted after fibrosis). A higher value indicates greater effectiveness in distinguishing the lung tissues [<a href="#B49-bioengineering-11-00747" class="html-bibr">49</a>]. Reprinted and adapted from references [<a href="#B38-bioengineering-11-00747" class="html-bibr">38</a>,<a href="#B44-bioengineering-11-00747" class="html-bibr">44</a>,<a href="#B49-bioengineering-11-00747" class="html-bibr">49</a>] with permissions.</p>
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<p>A schematic view of how elevated tension in fibrotic lung tissue exacerbates pulmonary fibrosis [<a href="#B29-bioengineering-11-00747" class="html-bibr">29</a>]. The elevated tension in fibrotic lung tissue activates AT2 cells in the peripheral lung tissue to secrete TGF-β, which subsequently activates the fibroblast to exacerbate pulmonary fibrosis.</p>
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<p>A scheme of cells differentiating into fibroblasts and participating in fibrosis progression [<a href="#B88-bioengineering-11-00747" class="html-bibr">88</a>]. (<b>A</b>) Different types of mesenchymal cells in lung tissue, including alveolar fibroblasts, lipofibroblasts, and pericytes, can be activated and transformed into myofibroblasts upon stimulus; (<b>B</b>) the extensive deposition of the ECM activates the transformation of fibroblasts into myofibroblasts in lung fibrosis, thereby exacerbating the condition.</p>
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<p>A scheme illustrating the major pathways in which mechanical stimuli regulate the polarization of macrophages through mechanoreceptors [<a href="#B111-bioengineering-11-00747" class="html-bibr">111</a>]. The activation of mechanoreceptors in macrophages transduces mechanical signals to the nucleus through different downstream response proteins, mediating the polarization of macrophages into the M2 phenotype.</p>
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<p>The strategies employed in constructing in vitro models of fibrotic lungs. (<b>A</b>) Conventional two-dimensional cell cultures for high-throughput drug screening. No mechanical stimulus is applied to the cells; (<b>B</b>) hydrogel-based three-dimensional constructs for cell cultures, where the mechanical properties of the hydrogel can be modulated by adjusting the hydrogel concentration, and drug screening is performed in the presence of mechanical stimuli in this setup; (<b>C</b>) a collagen-based hydrogel system with time-evolving stiffness endowed with mTG cross-linking [<a href="#B121-bioengineering-11-00747" class="html-bibr">121</a>]; (<b>D</b>) 3D bioprinting technology employed in the fabrication of a viable construct that recapitulates the healthy and fibrotic cardiac tissue (characterized by significant vimentin expression) [<a href="#B123-bioengineering-11-00747" class="html-bibr">123</a>]; and (<b>E</b>) a biomimetic, bioprinted hydrogel alveolar model. Deoxygenated blood was injected from the upper entry, and became oxygenated after acquiring oxygen from the air sacs, with the oxygen being supplied from the air duct via tidal ventilation [<a href="#B125-bioengineering-11-00747" class="html-bibr">125</a>]. Reprinted and adapted from references [<a href="#B121-bioengineering-11-00747" class="html-bibr">121</a>,<a href="#B123-bioengineering-11-00747" class="html-bibr">123</a>,<a href="#B125-bioengineering-11-00747" class="html-bibr">125</a>] with permissions.</p>
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21 pages, 4003 KiB  
Article
Fabrication and Characterization of Porous PEGDA Hydrogels for Articular Cartilage Regeneration
by Silvia Gonella, Margarida F. Domingues, Filipe Miguel, Carla S. Moura, Carlos A. V. Rodrigues, Frederico Castelo Ferreira and João C. Silva
Gels 2024, 10(7), 422; https://doi.org/10.3390/gels10070422 - 26 Jun 2024
Cited by 2 | Viewed by 2470
Abstract
Functional articular cartilage regeneration remains an unmet medical challenge, increasing the interest for innovative biomaterial-based tissue engineering (TE) strategies. Hydrogels, 3D macromolecular networks with hydrophilic groups, present articular cartilage-like features such as high water content and load-bearing capacity. In this study, 3D porous [...] Read more.
Functional articular cartilage regeneration remains an unmet medical challenge, increasing the interest for innovative biomaterial-based tissue engineering (TE) strategies. Hydrogels, 3D macromolecular networks with hydrophilic groups, present articular cartilage-like features such as high water content and load-bearing capacity. In this study, 3D porous polyethylene glycol diacrylate (PEGDA) hydrogels were fabricated combining the gas foaming technique and a UV-based crosslinking strategy. The 3D porous PEGDA hydrogels were characterized in terms of their physical, structural and mechanical properties. Our results showed that the size of the hydrogel pores can be modulated by varying the initiator concentration. In vitro cytotoxicity tests showed that 3D porous PEGDA hydrogels presented high biocompatibility both with human chondrocytes and osteoblast-like cells. Importantly, the 3D porous PEGDA hydrogels supported the viability and chondrogenic differentiation of human bone marrow-derived mesenchymal stem/stromal cell (hBM-MSC)-based spheroids as demonstrated by the positive staining of typical cartilage extracellular matrix (ECM) (glycosaminoglycans (GAGs)) and upregulation of chondrogenesis marker genes. Overall, the produced 3D porous PEGDA hydrogels presented cartilage-like mechanical properties and supported MSC spheroid chondrogenesis, highlighting their potential as suitable scaffolds for cartilage TE or disease modelling strategies. Full article
(This article belongs to the Special Issue Functional Gels Applied in Tissue Engineering)
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<p>Macroscopic view of a porous PEGDA scaffold produced via gas foaming and UV-based crosslinking and a traditional non-porous PEGDA scaffold. (<b>A</b>) Top view. (<b>B</b>) Lateral view.</p>
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<p>Characterization of porous PEGDA scaffolds. Scanning Electron Microscopy analysis of porous PEGDA scaffolds with different (<b>A</b>) gas foaming parameters and (<b>B</b>) photoinitiator concentrations. Scale bars: (<b>A</b>) 100 µm, (<b>B</b>) 1 mm (top) and 100 µm (bottom). (<b>C</b>) Size distribution of the pore diameter of scaffolds with different photoinitiator concentrations (<span class="html-italic">n</span> = 50).</p>
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<p>Characterization of porous PEGDA scaffolds with different initiator concentrations (0.1%, 0.45% and 0.95% <span class="html-italic">v</span>/<span class="html-italic">v</span>). (<b>A</b>) μ-CT analysis of PEGDA porous hydrogels. (<b>B</b>) Porosity and interconnectivity of the three scaffold formulations.</p>
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<p>Assessment of 20% <span class="html-italic">v</span>/<span class="html-italic">v</span> PEGDA hydrogels’ properties. (<b>A</b>) Water content and (<b>B</b>) swelling behavior of non-porous and porous hydrogels with different photoinitiators concentrations (0.1%, 0.45% and 0.95% <span class="html-italic">v</span>/<span class="html-italic">v</span>) (<span class="html-italic">n</span> = 3).</p>
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<p>Mechanical properties of porous and non-porous PEGDA scaffolds under uniaxial compression. (<b>A</b>) Compressive modulus (kPa) and (<b>B</b>) compressive strength (kPa) and elastic recovery (%) of four 20% <span class="html-italic">v</span>/<span class="html-italic">v</span> PEGDA scaffold formulations, after fabrication and after 1h of swelling: non-porous (0.95% <span class="html-italic">v</span>/<span class="html-italic">v</span> photoinitiator) and porous scaffolds (0.1, 0.45 and 0.95% <span class="html-italic">v</span>/<span class="html-italic">v</span> photoinitiator concentrations) (<span class="html-italic">n</span> = 3). # Hydrogels broke. &amp; Hydrogels did not break. *** <span class="html-italic">p</span> &lt; 0.001; **** <span class="html-italic">p</span> &lt; 0.0001.</p>
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<p>Biocompatibility of non-porous and porous PEGDA scaffolds. (<b>A</b>) MTT assay results and (<b>B</b>) direct contact test images of porous and non-porous PEGDA scaffolds with human MG-63 osteoblasts and chondrocytes. Scale bar: 100 µm (<span class="html-italic">n</span> = 3), **** <span class="html-italic">p</span> &lt; 0.0001.</p>
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<p>Experimental setup for the development of MSC-spheroid-seeded porous PEGDA hydrogel scaffolds for AC TE. (<b>A</b>) Production and seeding of spheroids on porous PEGDA hydrogel scaffolds, fabricated with the gas-foaming technique. (<b>B</b>) Pore size of porous PEGDA hydrogels (SEM images, left) and spheroid diameters (brightfield image, right) (<span class="html-italic">n</span> = 50). Scale bar: 100 µm.</p>
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<p>Evaluation of chondrogenic differentiation of MSC spheroids seeded in porous PEGDA scaffolds. (<b>A</b>) Live/Dead (green: live cells, red: dead cells), Alcian Blue and Safranin-O stainings of MSC spheroids at day 21 post-seeding. (<b>B</b>) qRT-PCR analysis of <span class="html-italic">COL1A1</span>, <span class="html-italic">COL2A1</span>, <span class="html-italic">SOX9</span> and <span class="html-italic">ACAN</span> in 2D cultures (control), 3D spheroids (day 1) and in 3D spheroids cultured on PEGDA porous hydrogels (day 21 post-seeding). Gene expression levels were normalized to that of glyceraldehyde 3-phosphate dehydrogenase (<span class="html-italic">GAPDH,</span> endogenous control) and calculated as fold-change relative to the control sample (2D MSC cultures at day 0, before spheroid formation and scaffold seeding). (<span class="html-italic">n</span> = 3), * <span class="html-italic">p</span> &lt; 0.05, ** <span class="html-italic">p</span> &lt; 0.01.</p>
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21 pages, 7137 KiB  
Article
Screening of MMP-13 Inhibitors Using a GelMA-Alginate Interpenetrating Network Hydrogel-Based Model Mimicking Cytokine-Induced Key Features of Osteoarthritis In Vitro
by Qichan Hu, Steven L. Williams, Alessandra Palladino and Melanie Ecker
Polymers 2024, 16(11), 1572; https://doi.org/10.3390/polym16111572 - 1 Jun 2024
Cited by 2 | Viewed by 1225
Abstract
Osteoarthritis (OA) is a chronic joint disease characterized by irreversible cartilage degradation. Current clinical treatment options lack effective pharmaceutical interventions targeting the disease’s root causes. MMP (matrix metalloproteinase) inhibitors represent a new approach to slowing OA progression by addressing cartilage degradation mechanisms. However, [...] Read more.
Osteoarthritis (OA) is a chronic joint disease characterized by irreversible cartilage degradation. Current clinical treatment options lack effective pharmaceutical interventions targeting the disease’s root causes. MMP (matrix metalloproteinase) inhibitors represent a new approach to slowing OA progression by addressing cartilage degradation mechanisms. However, very few drugs within this class are in preclinical or clinical trial phases. Hydrogel-based 3D in vitro models have shown promise as preclinical testing platforms due to their resemblance to native extracellular matrix (ECM), abundant availability, and ease of use. Metalloproteinase-13 (MMP-13) is thought to be a major contributor to the degradation of articular cartilage in OA by aggressively breaking down type II collagen. This study focused on testing MMP-13 inhibitors using a GelMA-alginate hydrogel-based OA model induced by cytokines interleukin-1 beta (IL-1β) and tumor necrosis factor alpha (TNF-α). The results demonstrate a significant inhibition of type II collagen breakdown by measuring C2C concentration using ELISA after treatment with MMP-13 inhibitors. However, inconsistencies in human cartilage explant samples led to inconclusive results. Nonetheless, the study highlights the GelMA-alginate hydrogel-based OA model as an alternative to human-sourced cartilage explants for in vitro drug screening. Full article
(This article belongs to the Special Issue Polymer-Based Biomaterials for Tissue Engineering Applications)
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<p>Synthesis of GelMA-alginate IPN hydrogels. (<b>a</b>) Schematic diagram of the synthesis of a GelMA-alginate IPN hydrogel. GelMA polymer chains, sodium alginate, Na<sup>+</sup>, and Ca<sup>2+</sup> are represented by green, red, yellow, and blue colors, respectively. (<b>b</b>) Increasing opacity of GelMA-alginate IPN hydrogels corresponds to incremental increases in sodium alginate concentration.</p>
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<p>Characteristics of GelMA-alginate hydrogels with variation in sodium alginate content. (<b>a</b>) Microstructure of GelMA-alginate hydrogels. The scale bar is 100 μm. (<b>b</b>) Compressive modulus of GelMA-alginate hydrogels. (<b>c</b>) Swelling degree of GelMA-alginate hydrogels. Data are presented as mean ± SD with statistical significance indicated as * <span class="html-italic">p</span> &lt; 0.05 and ** <span class="html-italic">p</span> &lt; 0.01.</p>
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<p>Evaluation of cell viability of TC28a2 chondrocytes in GelMA-alginate hydrogels on days 1 and 7. (<b>a</b>) Live/dead staining of chondrocytes. Green fluorescence indicates viable cells whereas red fluorescence indicates dead cells. The scale bar is 100 μm. (<b>b</b>) Metabolic activity of chondrocytes assessed by alamarBlue™ assay. Data are presented as mean ± SD, with statistical significance indicated as * <span class="html-italic">p</span> &lt; 0.05 and ** <span class="html-italic">p</span> &lt; 0.01.</p>
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<p>Evaluation of different chondrogenic differentiation media. (<b>a</b>) Staining of Alcian blue (upper row) and Sirius red (lower row) on days 7, 14, and 21. The culture medium in each group from left to right is CCM + AA2P + DXM, CCM + AA2P + DXM + TGF-β1, CCM + AA2P + DXM + TGF-β1 + ITS Premix, and CCM only (control). (<b>b</b>) Quantification of Alcian blue staining and Sirius red staining. Data are presented as mean ± SD with statistical significance indicated as * <span class="html-italic">p</span> &lt; 0.05 and ** <span class="html-italic">p</span> &lt; 0.01.</p>
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<p>Confirmation of chondrogenesis in GelMA-alginate hydrogel. (<b>a</b>) qRT-PCR analysis of gene expression of chondrogenic markers. Gene expression is normalized to GAPDH and expressed relative to the control group (Day 0). Data are presented as mean ± SD with statistical significance indicated as * <span class="html-italic">p</span> &lt; 0.05 and ** <span class="html-italic">p</span> &lt; 0.01. (<b>b</b>) Immunofluorescence staining of type II collagen (green) in cryosections. The scale bar is 100 μm. (<b>c</b>) Alcian blue/nuclear fast red staining of sulfated glycosaminoglycans (sGAGs) in paraffin sections. Nuclei, cytoplasm, and sGAGs are stained dark pink to red, pale pink, and blue, respectively. The scale bar is 100 μm.</p>
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<p>Evaluation of cytokines for MMP-13 induction in monolayer TC28a2 chondrocytes. (<b>a</b>) Cell viability using MTT assay 24 h post-treatment with inflammatory cytokines. (<b>b</b>) Measurement of MMP-13 concentration by ELISA in cell supernatant 2 d post-cytokine induction. (<b>c</b>) Immunofluorescence staining of MMP-13 2 d post-cytokine induction. The scale bar is 100 μm. Data are presented as mean ± SD with statistical significance indicated as * <span class="html-italic">p</span> &lt; 0.05 and ** <span class="html-italic">p</span> &lt; 0.01.</p>
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<p>Evaluation of MMP-13 inhibitors. (<b>a</b>) Cell viability of TC28a2 chondrocytes using MTT assay 24 h post-treatment with MMP-13 inhibitors. (<b>b</b>) Comparison of inhibitory effects of inhibitors using a fluorogenic substrate assay. Data are presented as mean ± SD with statistical significance indicated as * <span class="html-italic">p</span> &lt; 0.05 and ** <span class="html-italic">p</span> &lt; 0.01.</p>
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<p>Screening of MMP-13 inhibitors using GelMA-alginate cartilage constructs with OA-like conditions. (<b>a</b>) Evaluation of MMP-13 expression in TC28a2 chondrocytes using immunofluorescence staining 3 d post-treatment with IL-1β and TNF-α. The scale bar is 100 μm. (<b>b</b>) Fluorescence intensity of MMP-13 expression in TC28a2 chondrocytes analyzed by ImageJ (version 1.54 g). (<b>c</b>) Measurement of active MMP-13 concentration by ELISA in cell supernatant. (<b>d</b>) Measurement of C2C concentration for type II collagen cleavage by ELISA in cell supernatant. Data are presented as mean ± SD with statistical significance indicated as * <span class="html-italic">p</span> &lt; 0.05 and ** <span class="html-italic">p</span> &lt; 0.01.</p>
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<p>Histological analysis of human articular cartilage by staining of H&amp;E, Safranin O, and Alcian blue, and IHC staining of type II collagen. The scale bar is 100 μm.</p>
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35 pages, 8715 KiB  
Review
Exploring the Progress of Hyaluronic Acid Hydrogels: Synthesis, Characteristics, and Wide-Ranging Applications
by Iman Gholamali, Trung Thang Vu, Sung-Han Jo, Sang-Hyug Park and Kwon Taek Lim
Materials 2024, 17(10), 2439; https://doi.org/10.3390/ma17102439 - 18 May 2024
Cited by 3 | Viewed by 3595
Abstract
This comprehensive review delves into the world of hyaluronic acid (HA) hydrogels, exploring their creation, characteristics, research methodologies, and uses. HA hydrogels stand out among natural polysaccharides due to their distinct features. Their exceptional biocompatibility makes them a top choice for diverse biomedical [...] Read more.
This comprehensive review delves into the world of hyaluronic acid (HA) hydrogels, exploring their creation, characteristics, research methodologies, and uses. HA hydrogels stand out among natural polysaccharides due to their distinct features. Their exceptional biocompatibility makes them a top choice for diverse biomedical purposes, with a great ability to coexist harmoniously with living cells and tissues. Furthermore, their biodegradability permits their gradual breakdown by bodily enzymes, enabling the creation of temporary frameworks for tissue engineering endeavors. Additionally, since HA is a vital component of the extracellular matrix (ECM) in numerous tissues, HA hydrogels can replicate the ECM’s structure and functions. This mimicry is pivotal in tissue engineering applications by providing an ideal setting for cellular growth and maturation. Various cross-linking techniques like chemical, physical, enzymatic, and hybrid methods impact the mechanical strength, swelling capacity, and degradation speed of the hydrogels. Assessment tools such as rheological analysis, electron microscopy, spectroscopy, swelling tests, and degradation studies are employed to examine their attributes. HA-based hydrogels feature prominently in tissue engineering, drug distribution, wound recovery, ophthalmology, and cartilage mending. Crafting HA hydrogels enables the production of biomaterials with sought-after qualities, offering avenues for advancements in the realm of biomedicine. Full article
(This article belongs to the Special Issue Synthesis and Characterization of Hydrogels)
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<p>Exploring the reaction mechanism between HA and EDC.</p>
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<p>Schematic reaction between HA and BIED and a representative image of BIED-cross-linked HA gels with MW of 1.2 MDa. (<b>a</b>) Cross-linked HA demonstrates the formation of urethane bonds between the isocyanate and hydroxyl groups. (<b>b</b>) Formulation four maintains its shape. (<b>c</b>) Formulation three shows inadequate structural stability. (<b>d</b>) Representative FTIR spectra of HA and HA-BIED-cross-linked gel displaying characteristic urethane bridges. Reprinted with permission from ref. [<a href="#B52-materials-17-02439" class="html-bibr">52</a>]. 2020, Elsevier.</p>
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<p>The hydrogel formulation was depicted through schematic representations, illustrating the swift cross-linking reaction with HA-Mal, Gel-Mal, and PEGDSH in PBS. Reprinted with permission from ref. [<a href="#B27-materials-17-02439" class="html-bibr">27</a>]. 2021, MDPI.</p>
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<p>Chemical structures and proposed cross-linking mechanism of Gantrez<sup>®</sup> S97 and sodium hyaluronate. Reprinted with permission from ref. [<a href="#B29-materials-17-02439" class="html-bibr">29</a>]. 2018, Elsevier.</p>
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<p>Illustrates the schematic representation of FA-conj-HA gel. The synthesis route of FA-conj-HA polymers is shown in (<b>a</b>), while the cross-linking route of FA-conj-HA gel is depicted in (<b>b</b>). In (<b>c</b>), the FA-conj-HA solution undergoes cross-linking using 4-arm-PEG2000-Mal through a D-A reaction, leading to the creation of viscoelastic hydrogels. Reprinted with permission from ref. [<a href="#B31-materials-17-02439" class="html-bibr">31</a>]. 2024, Elsevier.</p>
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<p>The schematic illustrates the design and the impact of photo-cross-linking hydrogels on wound healing. Reprinted with permission from ref. [<a href="#B66-materials-17-02439" class="html-bibr">66</a>]. 2022, MDPI.</p>
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<p>The amidation reactions of the -COOH group in chemical modifications of HA. Reprinted with permission from ref. [<a href="#B36-materials-17-02439" class="html-bibr">36</a>]. 2024, Elsevier.</p>
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<p>Oxidation of HA and hydrogel formation via hydrazone cross-linking.</p>
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<p><sup>1</sup>H NMR characterization of the precursor of HA-Nb in D<sub>2</sub>O. Reprinted with permission from ref. [<a href="#B83-materials-17-02439" class="html-bibr">83</a>]. 2022, Elsevier.</p>
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<p><sup>13</sup>C-NMR spectra (400 MHz) of (<b>a</b>,<b>b</b>) HA–furan/TA and (<b>c</b>) HA/PEG hydrogel are solid, indicating the presence of both D-A click chemistry and enzymatic cross-linking processes. Reprinted with permission from ref. [<a href="#B86-materials-17-02439" class="html-bibr">86</a>]. 2014, RSC.</p>
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<p>The schematic of HA-PNIPAAm demonstrates the amide groups of PNIPAAm forming hydrogen bonds with water below the LCST (lower critical solution temperature) and forming hydrogen bonds with each other above the LCST, thereby the formation of hydrophobic microdomains and the transformation of the material into a physically cross-linked hydrogel. Reprinted with permission from ref. [<a href="#B41-materials-17-02439" class="html-bibr">41</a>]. 2018, Wiley.</p>
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<p>An Overview of Dynamic Covalent Bonding and their biomedical application. Reprinted with permission from ref. [<a href="#B105-materials-17-02439" class="html-bibr">105</a>]. 2020, Elsevier.</p>
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<p>The moduli of HA/Coumarin-25 and HA/Coumarin-100 hydrogels were measured in two ways. Firstly, their moduli were measured as a function of step time (<b>a</b>,<b>b</b>), and secondly, their moduli were measured as a function of angular frequency (<b>c</b>,<b>d</b>). Reprinted with permission from ref. [<a href="#B64-materials-17-02439" class="html-bibr">64</a>]. 2023, Elsevier.</p>
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<p>The coumarin-functionalized HA hydrogels with different molar ratios (50:100, 100:100 with respect to Nb/Tz). Reprinted with permission from ref. [<a href="#B64-materials-17-02439" class="html-bibr">64</a>]. 2023, Elsevier.</p>
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<p>SEM images of HA hydrogel films. Cross-section image (<b>a</b>) of HA dried hydrogel film; (<b>b</b>) cross-section image of HA hydrogel film in swelling status. Reprinted with permission from ref. [<a href="#B132-materials-17-02439" class="html-bibr">132</a>]. 2000, Elsevier.</p>
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<p>The X-ray diffraction (XRD) patterns of microspheres made of carboxymethyl chitosan and loaded with HA/gelatin hydrogels were analyzed. Reprinted with permission from ref. [<a href="#B79-materials-17-02439" class="html-bibr">79</a>]. 2021, Elsevier.</p>
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<p>TGA analysis of HA-Alg-PVA hydrogel membrane. Reprinted with permission from ref. [<a href="#B139-materials-17-02439" class="html-bibr">139</a>]. 2023, Elsevier.</p>
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<p>Tissue engineering strategies for regeneration can involve different approaches. In acellular methods, recipient-derived or artificial biomaterial structures without any cells are placed into the patient’s body to enhance natural regeneration processes. Cellular techniques utilize patient-specific or donor cells to populate and develop a framework before implantation. Cell therapy, on the other hand, involves administering intended cell types and biological populations directly to the patient without the use of scaffolds. Reprinted with permission from ref. [<a href="#B141-materials-17-02439" class="html-bibr">141</a>]. 2020, Elsevier.</p>
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<p>Polysaccharide-Based Hydrogels and Their Application as Drug Delivery Systems in Cancer Treatment. Reprinted with permission from ref. [<a href="#B159-materials-17-02439" class="html-bibr">159</a>]. 2023, MDPI.</p>
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<p>Illustration outlining the process and roles of injectable multifunctional hydrogel. Reprinted with permission from ref. [<a href="#B164-materials-17-02439" class="html-bibr">164</a>]. 2022, Elsevier.</p>
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<p>(<b>a</b>) A formulation of hydrogel; (<b>b</b>) creating a bioink (hydrogel) based on HA; (<b>c</b>) illustration depicting the process of 3D bioprinting for articular cartilage engineering. Reprinted with permission from ref. [<a href="#B172-materials-17-02439" class="html-bibr">172</a>]. 2020, Elsevier.</p>
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28 pages, 5331 KiB  
Article
Synthesis and Physicochemical Characterization of Gelatine-Based Biodegradable Aerogel-like Composites as Possible Scaffolds for Regenerative Medicine
by Silvana Alfei, Paolo Giordani and Guendalina Zuccari
Int. J. Mol. Sci. 2024, 25(9), 5009; https://doi.org/10.3390/ijms25095009 - 3 May 2024
Cited by 4 | Viewed by 1455
Abstract
Regenerative medicine is an interdisciplinary field aiming at restoring pathologically damaged tissues and whole organs by cell transplantation in combination with proper supporting scaffolds. Gelatine-based ones are very attractive due to their biocompatibility, rapid biodegradability, and lack of immunogenicity. Gelatine-based composite hydrogels, containing [...] Read more.
Regenerative medicine is an interdisciplinary field aiming at restoring pathologically damaged tissues and whole organs by cell transplantation in combination with proper supporting scaffolds. Gelatine-based ones are very attractive due to their biocompatibility, rapid biodegradability, and lack of immunogenicity. Gelatine-based composite hydrogels, containing strengthening agents to improve their modest mechanical properties, have been demonstrated to act as extracellular matrices (ECMs), thus playing a critical role in “organ manufacturing”. Inspired by the lysyl oxidase (LO)-mediated process of crosslinking, which occurs in nature to reinforce collagen, we have recently developed a versatile protocol to crosslink gelatine B (Gel B) in the presence or absence of LO, using properly synthesized polystyrene- and polyacrylic-based copolymers containing the amine or aldehyde groups needed for crosslinking reactions. Here, following the developed protocol with slight modifications, we have successfully crosslinked Gel B in different conditions, obtaining eight out of nine compounds in high yield (57–99%). The determined crosslinking degree percentage (CP%) evidenced a high CP% for compounds obtained in presence of LO and using the styrenic amine-containing (CP5/DMAA) and acrylic aldehyde-containing (CPMA/DMAA) copolymers as crosslinking agents. ATR-FTIR analyses confirmed the chemical structure of all compounds, while optical microscopy demonstrated cavernous, crater-like, and labyrinth-like morphologies and cavities with a size in the range 15–261 µm. An apparent density in the range 0.10–0.45 g/cm3 confirmed the aerogel-like structure of most samples. Although the best biodegradation profile was observed for the sample obtained using 10% CP5/DMAA (M3), high swelling and absorption properties, high porosity, and good biodegradation profiles were also observed for samples obtained using the 5–10% CP5/DMAA (M4, 5, 6) and 20% CPMA/DMAA (M9) copolymers. Collectively, in this work of synthesis and physicochemical characterization, new aerogel-like composites have been developed and, based on their characteristics, which fit well within the requirements for TE, five candidates (M3, M4, M5, M6, and M9) suitable for future biological experiments on cell adhesion, infiltration and proliferation, to confirm their effective functioning, have been identified. Full article
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<p>Copolymers prepared according to Alfei et al. [<a href="#B8-ijms-25-05009" class="html-bibr">8</a>,<a href="#B63-ijms-25-05009" class="html-bibr">63</a>], which were successful in crosslinking Gel B. CP = copolymer; <b>5</b> = aminobutyl styrene hydrochloride; <b>11b</b> = <span class="html-italic">N</span>-acryloyl-1,4-diaminobutane hydrochloride; <b>11c</b> = <span class="html-italic">N</span>-acryloyl-1,6-diaminohexane hydrochloride.</p>
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<p>ATR-FTIR spectra of Gel B (black plot) and of crosslinked gelatines (colored plots).</p>
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<p>Optical images captured with a 10× objective of M1 (<b>a</b>,<b>b</b>) and M2 (<b>c</b>,<b>d</b>).</p>
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<p>Optical images captured of M3 (<b>a</b>), M4 (<b>b</b>), and M6 (<b>c</b>) with a 40× objective and of M9 (<b>d</b>) with a 10× objective.</p>
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<p>Plots of the cumulative swelling rate values of the crosslinked gelatines vs. time.</p>
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<p>Cumulative mass loss percentage curves of developed crosslinked gelatines and Gel B.</p>
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<p>Korsmeyer–peppas kinetic model.</p>
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<p>Pseudo-second-order (PSO) kinetic model.</p>
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<p>Cumulative water loss (%) over time. Error bars not detectable.</p>
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<p>Curve of shear stress vs. shear rate (<b>a</b>) and viscosity vs. shear rate (<b>b</b>) of M1–M6 and M9 from rheological experiments performed in triplicate. Error bars not detectable.</p>
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<p>Score plot of PC2 vs. PC1 from PCA of samples M1–M6 and M9.</p>
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<p>Reactions that can occur during the LO-assisted crosslinking of gelatine [<a href="#B8-ijms-25-05009" class="html-bibr">8</a>].</p>
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24 pages, 3440 KiB  
Article
Graphene Oxide (GO)-Based Bioink with Enhanced 3D Printability and Mechanical Properties for Tissue Engineering Applications
by Katarzyna Kosowska, Paulina Korycka, Kamila Jankowska-Snopkiewicz, Joanna Gierałtowska, Milena Czajka, Katarzyna Florys-Jankowska, Magdalena Dec, Agnieszka Romanik-Chruścielewska, Maciej Małecki, Kinga Westphal, Michał Wszoła and Marta Klak
Nanomaterials 2024, 14(9), 760; https://doi.org/10.3390/nano14090760 - 26 Apr 2024
Cited by 3 | Viewed by 1944
Abstract
Currently, a major challenge in material engineering is to develop a cell-safe biomaterial with significant utility in processing technology such as 3D bioprinting. The main goal of this work was to optimize the composition of a new graphene oxide (GO)-based bioink containing additional [...] Read more.
Currently, a major challenge in material engineering is to develop a cell-safe biomaterial with significant utility in processing technology such as 3D bioprinting. The main goal of this work was to optimize the composition of a new graphene oxide (GO)-based bioink containing additional extracellular matrix (ECM) with unique properties that may find application in 3D bioprinting of biomimetic scaffolds. The experimental work evaluated functional properties such as viscosity and complex modulus, printability, mechanical strength, elasticity, degradation and absorbability, as well as biological properties such as cytotoxicity and cell response after exposure to a biomaterial. The findings demonstrated that the inclusion of GO had no substantial impact on the rheological properties and printability, but it did enhance the mechanical properties. This enhancement is crucial for the advancement of 3D scaffolds that are resilient to deformation and promote their utilization in tissue engineering investigations. Furthermore, GO-based hydrogels exhibited much greater swelling, absorbability and degradation compared to non-GO-based bioink. Additionally, these biomaterials showed lower cytotoxicity. Due to its properties, it is recommended to use bioink containing GO for bioprinting functional tissue models with the vascular system, e.g., for testing drugs or hard tissue models. Full article
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<p>The models of printable structures to evaluate printability in (<b>A</b>) fiber fusion test and (<b>B</b>) fiber collapse test.</p>
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<p>Results of rheology testing, where (<b>A</b>) shows gelation point, (<b>B</b>) shows complex modulus and (<b>C</b>) shows viscosity of biomaterials.</p>
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<p>The results for water absorbability: the weight of absorbed water (<b>A</b>) and the weight of absorbed water per mg of biomaterial (<b>B</b>).</p>
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<p>The printability of graphene bioinks. (<b>A</b>) The fiber fusion test results along with printing parameters; (<b>B</b>) the photographs of prints from the fiber fusion test; (<b>C</b>) the fiber collapse test results on the platform—fiber collapse rate; (<b>D</b>) the photos of fibers printed on the platform.</p>
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<p>The results from the static compression test. (<b>A</b>) Stress–strain behavior. (<b>B</b>) Mechanical parameters: I, mechanical strength; II, Young’s modulus; III, elastic limit.</p>
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<p>The effect of GO-enhanced biomaterial extracts on L-929 cell line in an indirect MTT assay. The blue line indicates the guidelines established by ISO 10993-5:2009(E), according to which &gt;70% cell viability of the L-929 cell line determines the absence of cytotoxicity of the test biomaterial.</p>
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<p>The influence of GO-based biomaterials on the viability of L-929 cell lines. The effect was measured using an LDH assay. (<b>A</b>) LDH assay, (<b>B</b>) statistical analysis; red: statistically significant differences, black: no statistically significant differences.</p>
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<p>The influence of GO-based biomaterials on the proliferation of L-929 cell lines. The effect was measured using the Alamar Blue assay.</p>
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<p>The relative expression of immune response-associated genes in mouse fibroblast cell lines after exposure to the BGO1 biomaterial. This analysis focuses on the measuring of the gene expression on the first day of incubation (<b>A</b>) and after seven days of incubation (<b>B</b>). Additionally, we assess the fold change in gene expression between the first and seventh day of incubation (<b>C</b>) comparing these to the control cells from the first day of incubation. The image was generated using software available at <a href="http://www.software.broadinstitute.org/morpheus/" target="_blank">www.software.broadinstitute.org/morpheus/</a> (accessed on 14 August 2023). Here, lower values correspond to a reduction in gene expression (bright blue color), while higher values indicate an increase in gene expression (dark blue color).</p>
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<p>The correlation of proteins between immune response-associated genes. The assessment of immune response-associated genes to acquire protein–protein interaction network diagram was created on the STRING program. (<b>A</b>,<b>C</b>,<b>E</b>) illustrate the protein functional dependence network. Network nodes represent proteins: splice isoforms or post-translational modifications are collapsed, i.e., each node represents all the proteins produced by a single, protein-coding gene locus. Node color: colored nodes represent query proteins and the first shell of interactors. White nodes: the second shell of interactions. Empty nodes: proteins of unknown 3D structure. Filed nodes: some 3D structures are known or predicted. The edges represent protein–protein associations: associations are meant to be specific and meaningful, i.e., proteins jointly contribute to a shared function; this does not necessarily mean they are physically binding to each other. Known interactions: blue—from curated databases; pink—experimentally determined. Predicted interactions: green—gene neighborhood; red—gene fusions; dark blue—gene co-occurrence. Others: yellow—text mining; black—co-expression; violet—protein homology. (<b>B</b>,<b>D</b>,<b>F</b>) illustrate co-expression predicts functional association. In the triangle matrices above, the intensity of color indicates the level of confidence that two proteins are functionally associated, given the overall expression data in the mouse organism.</p>
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22 pages, 2207 KiB  
Review
Biomimetic Scaffolds—A Novel Approach to Three Dimensional Cell Culture Techniques for Potential Implementation in Tissue Engineering
by Tomasz Górnicki, Jakub Lambrinow, Afsaneh Golkar-Narenji, Krzysztof Data, Dominika Domagała, Julia Niebora, Maryam Farzaneh, Paul Mozdziak, Maciej Zabel, Paweł Antosik, Dorota Bukowska, Kornel Ratajczak, Marzenna Podhorska-Okołów, Piotr Dzięgiel and Bartosz Kempisty
Nanomaterials 2024, 14(6), 531; https://doi.org/10.3390/nano14060531 - 16 Mar 2024
Cited by 13 | Viewed by 3643
Abstract
Biomimetic scaffolds imitate native tissue and can take a multidimensional form. They are biocompatible and can influence cellular metabolism, making them attractive bioengineering platforms. The use of biomimetic scaffolds adds complexity to traditional cell cultivation methods. The most commonly used technique involves cultivating [...] Read more.
Biomimetic scaffolds imitate native tissue and can take a multidimensional form. They are biocompatible and can influence cellular metabolism, making them attractive bioengineering platforms. The use of biomimetic scaffolds adds complexity to traditional cell cultivation methods. The most commonly used technique involves cultivating cells on a flat surface in a two-dimensional format due to its simplicity. A three-dimensional (3D) format can provide a microenvironment for surrounding cells. There are two main techniques for obtaining 3D structures based on the presence of scaffolding. Scaffold-free techniques consist of spheroid technologies. Meanwhile, scaffold techniques contain organoids and all constructs that use various types of scaffolds, ranging from decellularized extracellular matrix (dECM) through hydrogels that are one of the most extensively studied forms of potential scaffolds for 3D culture up to 4D bioprinted biomaterials. 3D bioprinting is one of the most important techniques used to create biomimetic scaffolds. The versatility of this technique allows the use of many different types of inks, mainly hydrogels, as well as cells and inorganic substances. Increasing amounts of data provide evidence of vast potential of biomimetic scaffolds usage in tissue engineering and personalized medicine, with the main area of potential application being the regeneration of skin and musculoskeletal systems. Recent papers also indicate increasing amounts of in vivo tests of products based on biomimetic scaffolds, which further strengthen the importance of this branch of tissue engineering and emphasize the need for extensive research to provide safe for humansbiomimetic tissues and organs. In this review article, we provide a review of the recent advancements in the field of biomimetic scaffolds preceded by an overview of cell culture technologies that led to the development of biomimetic scaffold techniques as the most complex type of cell culture. Full article
(This article belongs to the Special Issue Moving toward Biomimetic Tissue Engineered Scaffolds)
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<p>Types of direct and indirect co-culture systems. Created with BioRender.com.</p>
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<p>Steps of cell aggregation and spheroid formation (ECM, extracellular matrix). Created with BioRender.com.</p>
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<p>Main 3D printing technologies (abb. SLS, stereolitography; SLA, selective laser sintering; FDM, fused deposition modeling). Created with BioRender.com.</p>
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<p>Synthetic and natural route of proceeding biomimetic scaffolds. Created with BioRender.com.</p>
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25 pages, 1111 KiB  
Review
Hydrogel-Based Skin Regeneration
by Zohreh Arabpour, Farshad Abedi, Majid Salehi, Seyed Mahbod Baharnoori, Mohammad Soleimani and Ali R. Djalilian
Int. J. Mol. Sci. 2024, 25(4), 1982; https://doi.org/10.3390/ijms25041982 - 6 Feb 2024
Cited by 14 | Viewed by 5360
Abstract
The skin is subject to damage from the surrounding environment. The repair of skin wounds can be very challenging due to several factors such as severe injuries, concomitant infections, or comorbidities such as diabetes. Different drugs and wound dressings have been used to [...] Read more.
The skin is subject to damage from the surrounding environment. The repair of skin wounds can be very challenging due to several factors such as severe injuries, concomitant infections, or comorbidities such as diabetes. Different drugs and wound dressings have been used to treat skin wounds. Tissue engineering, a novel therapeutic approach, revolutionized the treatment and regeneration of challenging tissue damage. This field includes the use of synthetic and natural biomaterials that support the growth of tissues or organs outside the body. Accordingly, the demand for polymer-based therapeutic strategies for skin tissue defects is significantly increasing. Among the various 3D scaffolds used in tissue engineering, hydrogel scaffolds have gained special significance due to their unique properties such as natural mimicry of the extracellular matrix (ECM), moisture retention, porosity, biocompatibility, biodegradability, and biocompatibility properties. First, this article delineates the process of wound healing and conventional methods of treating wounds. It then presents an examination of the structure and manufacturing methods of hydrogels, followed by an analysis of their crucial characteristics in healing skin wounds and the most recent advancements in using hydrogel dressings for this purpose. Finally, it discusses the potential future advancements in hydrogel materials within the realm of wound healing. Full article
(This article belongs to the Special Issue Sustainable Approaches in Skin Conditions 2.0)
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<p>Schematic diagram of wound healing mechanism: (<b>A</b>) damaged blood vessel; (<b>B</b>) hemostasis platelet activation; (<b>C</b>) hemostasis fibrin clot; (<b>D</b>) inflammatory phase; (<b>E</b>) proliferation phase; (<b>F</b>) remodeling phase.</p>
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<p>Categorization of the wound care market based on application.</p>
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32 pages, 3676 KiB  
Review
Micro- and Nanostructured Fibrous Composites via Electro-Fluid Dynamics: Design and Applications for Brain
by Nergis Zeynep Renkler, Stefania Scialla, Teresa Russo, Ugo D’Amora, Iriczalli Cruz-Maya, Roberto De Santis and Vincenzo Guarino
Pharmaceutics 2024, 16(1), 134; https://doi.org/10.3390/pharmaceutics16010134 - 19 Jan 2024
Viewed by 1963
Abstract
The brain consists of an interconnected network of neurons tightly packed in the extracellular matrix (ECM) to form complex and heterogeneous composite tissue. According to recent biomimicry approaches that consider biological features as active components of biomaterials, designing a highly reproducible microenvironment for [...] Read more.
The brain consists of an interconnected network of neurons tightly packed in the extracellular matrix (ECM) to form complex and heterogeneous composite tissue. According to recent biomimicry approaches that consider biological features as active components of biomaterials, designing a highly reproducible microenvironment for brain cells can represent a key tool for tissue repair and regeneration. Indeed, this is crucial to support cell growth, mitigate inflammation phenomena and provide adequate structural properties needed to support the damaged tissue, corroborating the activity of the vascular network and ultimately the functionality of neurons. In this context, electro-fluid dynamic techniques (EFDTs), i.e., electrospinning, electrospraying and related techniques, offer the opportunity to engineer a wide variety of composite substrates by integrating fibers, particles, and hydrogels at different scales—from several hundred microns down to tens of nanometers—for the generation of countless patterns of physical and biochemical cues suitable for influencing the in vitro response of coexistent brain cell populations mediated by the surrounding microenvironment. In this review, an overview of the different technological approaches—based on EFDTs—for engineering fibrous and/or particle-loaded composite substrates will be proposed. The second section of this review will primarily focus on describing current and future approaches to the use of composites for brain applications, ranging from therapeutic to diagnostic/theranostic use and from repair to regeneration, with the ultimate goal of providing insightful information to guide future research efforts toward the development of more efficient and reliable solutions. Full article
(This article belongs to the Special Issue Nanofibrous Scaffolds Application in Biomedicine)
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<p>Schematic representation of multiple approaches for scaling devices fabricated via EFDTs from micro- to sub-micrometric size.</p>
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<p>Basic scheme of the electrospinning process and setup implementation by tailored needles/collectors.</p>
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<p>Schematic map of materials and main process parameters used to control the morphological properties of products via electrospinning and electrospraying techniques. Pictures were adapted with permission from [<a href="#B45-pharmaceutics-16-00134" class="html-bibr">45</a>,<a href="#B46-pharmaceutics-16-00134" class="html-bibr">46</a>].</p>
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<p>Different routes to design multicomponent and/or composite fibrous platforms via EFDTs.</p>
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<p>Different technological setups to impart (<b>a</b>) biochemical and/or (<b>b</b>) topographical cues in blended fibers to support brain regeneration. Pictures adapted with permission from [<a href="#B87-pharmaceutics-16-00134" class="html-bibr">87</a>].</p>
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<p>Co-electrospinning to fabricate nanoparticle decorated fibers. Particles can be collected contextually by the fibers by varying the process conditions (e.g., solution viscosity, deposition rate) to create controlled spatial gradients of drugs/molecules as a function of the particle density entrapped into the fiber network. Portions of the pictures adapted with permission from [<a href="#B101-pharmaceutics-16-00134" class="html-bibr">101</a>].</p>
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<p>(<b>a</b>) Morphological characterization of 2D adECM–PLA and 2D adECM–PLA PDA–rGO nanofibrous platforms by SEM analysis. Morphological analysis of cytoskeleton and nuclei in NSCs grown on 2D adECM–PLA and 2D adECM–PLA PDA-rGO nanofibrous platforms by (<b>b</b>) SEM analysis (7 days post-seeding) and (<b>c</b>) immunocytochemistry (14 days post-seeding) by using phalloidin-red (actin filaments) and DAPI (nuclei). (<b>d</b>) NSC spontaneous and RA-induced differentiation on 2D adECM–PLA and 2D adECM–PLA PDA–rGO nanofibrous platforms by means of immunocytochemistry using Tuj1 (green) as neuronal marker, GFAP (blue) as astrocyte marker and DAPI (blue) for nuclei. Pictures were adapted with permission from [<a href="#B119-pharmaceutics-16-00134" class="html-bibr">119</a>].</p>
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<p>Different ways of adding electrospun nanofibers into neat and nanocomposite hydrogels to produce fibrous hydrogels: multilayer approach. (<b>Left</b>) Example of multilayer fibrous hydrogel: optical micrographs of random and aligned electrospun polycaprolactone (PCL) fibers on gelatin hydrogels. Scale bars: 100 μm. Adapted from Mungenast et al. [<a href="#B151-pharmaceutics-16-00134" class="html-bibr">151</a>]. (<b>Right</b>) Example of injectable/scaffold fibrous hydrogel. SEM images of (<b>Left</b>) xyloglucan gel with poly-D-lysine, (<b>Middle</b>) poly(L-lactide) (PLLA) short fibers, and (<b>Right</b>) the fibrous hydrogel, including PLLA short fibers within the xyloglucan gel. Scale bars: 5 μm. Adapted with permission from Wang et al. [<a href="#B152-pharmaceutics-16-00134" class="html-bibr">152</a>].</p>
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