Immunohistochemical analysis of the inflammatory reaction within the implantation bed of a collagen hemostatic biomaterial
Authors:   , Vizcaino Carlos Arturo Herrera 
Published: July 2021

Current research on medical biomaterials have shown that the physical and chemical characteristics of biomaterials determine the body inflammatory cellular reaction after their implantation. The aim of this study was to evaluate the individual effects of the physical characteristics over the initial biomaterial-cellular interaction and the inflammatory cellular reaction. For this purpose, an equine-derived collagen hemostatic sponge (E-CHS) was modified by pressing and evaluated using ex vivo, in vitro and in vivo methods. The E-CHS was pressed by applying constant pressure (6.47± 0.85 N) for 2 min using a sterile stainless-steel cylinder and cut in segments of 1cm2. Subsequently, E-CHS and the pressed equine-derived collagen hemostatic sponge (P-E-CHS) were studied as two independent biomaterials and compared to a control group (CG). A blood concentrate containing inflammatory cells known as platelet rich fibrin (PRF) was used to mimic the initial biomaterial-cell interaction and to measure the absorption coefficient of the biomaterials to liquid PRF (iPAC). Additionally, the biomaterials were cultivated together with PRF for 3 and 6 days to measure the induction of pro-inflammatory cytokines (TNF-α and IL-8). The results were obtained through enzyme-linked immunosorbent assay (ELISA) and histological methods. PRF cultivated without biomaterials served as the CG. Additionally, the biomaterials were evaluated in vivo using a subcutaneous model in Wistar rats and compared to sham operated animals (CG) representing physiologic wound healing. After 3, 15 and 30 days, the explanted samples were evaluated using histochemical and immunohistochemical (IHC) staining using the following markers: CD68 (pan macrophages), CCR7 (pro-inflammatory macrophages, M1), CD206 (pro-wound healing macrophages, M2) and α-Smooth Muscle Actin (α-SMA; vessel identification). After the mixture of liquid PRF with both biomaterials for 15 minutes, the ex vivo results showed that E-CHS was penetrated by cells, whereas P-E-CHS was cell-occlusive. Additionally, P-E-CHS induced a higher release of pro-inflammatory cytokines compared to liquid PRF alone (CG) and E-CHS after 3 days (P< 0.05). Although the biomaterial was pressed, the difference of the iPAC value did not show statistical differences. In vivo, the CG induced at day 3 a higher inflammatory response compared to the experimental groups (EG) (P< 0.05). The intergroup comparison showed that P-E-CHS induced a higher presence of macrophages (CD68+/CC7+) compared to E-CHS at day 3 (P< 0.05). Only CD68+/CCR7+ mononuclear cells (MNCs) were observed without multinucleated giant cells (MNGCs). After 15 days, the presence of macrophages (CD68+ P<0.01 /CCR7+ P<0.001 /CD206+ P<0.05) reduced considerably in the CG. On the contrary, the inflammatory response increased in the EGs (CD68+/CCR7+). The intergroup comparison showed that this increment was statistically significant when comparing E-CHS and P-E-CHS to the CG at day 15 (P<0.01 and P< 0.05 respectively). At this time point, a reduced number of MNGCs were observed in the EGs. In the CG no MNGCs were observed. Furthermore, E-CHS showed a faster degradation rate and was fully invaded by cells and vessels formed in its interior region. On the other hand, P-E-CHS remained occlusive to cell penetration and vessels were formed only in the periphery. After 30 days, the cellular reaction shifted to a higher number of M2 macrophages (CD260+) in all groups and a reduced presence of CD68+ and CCR7+ MNCs. Both biomaterials degraded and only small fragments were found in the implantation bed surrounded by MNGCs (CCR7+). These results are of high clinical relevance and show that changes in biomaterial properties have a significant impact on their interaction with the body. They also serve as insight into the possibility to develop versatile biomaterials with different applications. For example, E-CHs can be applied to support hemostasis in a bleeding alveolar socket and P-E-CHs by being cell occlusive and having a delayed degradation rate can be applied for guided bone and tissue regeneration.