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Host Response to Biomaterials
Published in Claudio Migliaresi, Antonella Motta, Scaffolds for Tissue Engineering, 2014
Sangeetha Srinivasan, Julia E. Babensee
An interesting, biomaterial chemistry-based angiogenesis approach has been described wherein porous bulk polymerised SCs prepared from n-butyl methacrylic acid-methyl methacrylate (MMA) co-polymer demonstrated an ability to promote angiogenesis within a 30-day period when implanted in rats.169 This approach is interesting since the angigogenic observation is dependent solely on a unique material-chemistry (methacrylic acid [MAA] containing) without the additional of any exogenous factors such as angiogenic growth factors. Beads made of the same material were used to treat skin grafts in rodents with an observed benefit on graft engraftment.170 This was associated with a significantly increased microvessel density and thickness of panniculus carnosus muscle 11 days post implantation. In a similar study, poly(MAA-co-MMA) (45 mol% MAA) beads enhanced wound closure and vascularization in diabetic mice within a 21-day period.171 Another study compared the effect of surface charge properties on angiogenesis. Surface-modified polymer fibers were plasma coated with either negatively charged MAA, positively charged N,N-dimethyl-aminoethyl methacrylate, or neutral hexafluoropropylene.172-174 In vivo implantation showed that MAA-coated constructs promoted angiogenesis better than the other groups. This suggests a possible dependence of angiogenic behavior on the negative charge carried by MAA. Furthermore, other material properties such as polymer fiber diameter and fiber spacing within SC mesh were shown to directly impact the development of neovascular structures.
Epidermal stimulating factors-gelatin/polycaprolactone coaxial electrospun nanofiber: ideal nanoscale material for dermal substitute
Published in Journal of Biomaterials Science, Polymer Edition, 2021
Li Yan, Haoyu Wang, Hui Xu, Rui Zheng, Zhengyu Shen
The recovery of healthy epidermal and dermal structure in our treated tissues was assessed by measuring the epidermal thickness using haematoxylin and eosin (H&E) staining and Masson's trichrome staining tissue sections. The thickness of epidermal was calculated between two lines (Supplementary material Figure S3A). Lower line was drawn at the interface of the dermis and the stratum basal, and the upper line was positioned above the stratum granulosum, disregarding the stratum corneum as it flaked off during staining. The thickness of dermal was calculated between the stratum basal and the lower margin of the coherently arrayed collagens (Supplementary material Figure S3B) which can be stained blue by Masson’s trichrome staining. The thickness was measured manually using ImageJ image analysis software. The mean thickness was calculated by the area of epidermal or dermal versus the wound length. The wound edges were defined by determining the position of the underlying panniculus carnosus muscle tissue.