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This study aims to fabricate PYA/PEG/Chitosan nanofiber scaffolds for skin tissue engineering. The scaffolds in the nanofiber structure closely match with the ECM structure of the skin tissue. PYA/PEG/Chitosan nanofibers were prepared by electrospinning technique with various compositions (v/v) % (95:5, 90:10, 85:15, 80:20). The scaffold surface morphology was characterized by scanning electron microscopy (SEM), and the functional groups were characterized by Fourier transform infrared (FTIR). The biodegradation test was carried out by immersing the sample in a simulated body fluid (SBF) solution with time variations of 1, 2, 3, and 4 weeks. The scaffolds have diameters in the range of 110-520 nm, which correspond to the skin ECM, and porosity in the range of 63-71%, which facilitates cell adhesion, and proliferation. The rate of biodegradation is faster in the composition (95:5). The surface morphology with random fiber diameter, porosity, and biodegradation are suitable for skin tissue scaffolding. [ABSTRACT FROM AUTHOR]

Nowadays, bone tissue engineering is developed rapidly along with better and faster healing needs. One application of bone tissue engineering is improvement in defects. This improvement was completed by regenerating the tissue through a skeleton called scaffold. In this study, nano-Hydroxyapatite (n-HAp)/PLA scaffold composites were successfully made with variations in composition. The basic ingredients for making n-HAp are from natural materials using the sonication method. Addition of PLA into the nHAp matrix was carried out with variations of 10, 20, 30, 40 and 50 wt%. Nano-HAp was characterized using XRD and SEM. n-HAp/PLA composites were characterized by SEM and porosity tests were carried out. The results showed the crystal size of HAp was 14.46 nm. The most optimal porosity test on composites with the composition of n-HAp: PLA; 90:10 wt%. [ABSTRACT FROM AUTHOR]

Hydroxyapatite (HAp) is a bioceramic that can be applied for bone tissue regeneration. The hydroxyapatite scaffold has poor biodegradation. To increase the biodegradation of HAp, we composited it with PVA, Chitosan, and PEG polymers, which have faster biodegradation properties. PVA/CS/PEG/HAp composites nanofibers as a scaffold in bone tissue engineering were prepared by electrospinning. The composition of HAp varied 0, 2, 3, 4, 5, and 6%. HAp was synthesized from natural deposits and characterized using X-Ray Diffraction (XRD) to obtain phase, crystallinity, and crystal size. Surface morphology and porosity of nanofiber composites were characterized by SEM-EDX. Previous studies without the addition of PEG produced less homogeneous nanofibers. Increasing the concentration of HAp and adding PEG could increase the average diameter of the nanofiber and reduce porosity. Composite biodegradation of PVA/CS/PEG/HAp was also evaluated. Biodegradation test was carried out by immersing the sample in Krebs solution prepared for 1-4 weeks, and the fastest mass reduction occurred in HAp (0%) and decreased with increasing concentration of HAp. This nanofiber HAp/CS/PEG/HAp composite can be applied as a scaffold in bone tissue engineering. [ABSTRACT FROM AUTHOR]

Ceramic/polymer composites are currently being developed by researchers because of their wide applications in biomedical. This work describes the synthesis of hydroxyapatite/polyethylene glycol (nHAp/PEG) composites by the co-precipitation method with a composition ratio of 80:20 wt% and temperature variations of 25, 50, 75 °C. HAp was synthesized from limestone using the co-precipitation method. The properties of HAp and nHAp/PEG composites were evaluated using XRD, SEM, EDX and hardness that was tested by Vickers hardness. Synthetic HAp has a crystal size of 28.89 nm. The co-precipitation temperature affected the porosity and hardness of the nHAp/PEG composites, respectively for porosity of 2.98, 5.88, 8.82% and for hardness of 0.07, 0.05, 0.04 GPa. SEM results show a microstructure with a narrow grain size distribution, which means it is almost homogeneous. Hardness values in the range 0.04-0.07 GPa are appropriate for dentin applications. [ABSTRACT FROM AUTHOR]