Biocompatibility Assessment of a New Biodegradable Vascular Graft via In Vitro Co-culture Approaches and In Vivo Model
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Following the implantation of biodegradable vascular grafts, macrophages and fibroblasts are the major two cell types recruited to the host-biomaterial interface. In-vitro biocompatibility assessment usually involves one cell type, predominantly macrophages. In this study, macrophage and fibroblast mono- and co-cultures, in paracrine and juxtacrine settings, were used to evaluate a new biodegradable thermoplastic polyurethane (TPU) vascular graft. Expanded-polytetrafluoroethylene (ePTFE) grafts served as controls. Pro/anti-inflammatory gene expression of macrophages and cytokines was assessed in vitro and compared to those of an in vivo rat model. Host cell infiltration and the type of proliferated cells was further studied in vivo. TPU grafts revealed superior support in cell attachment, infiltration and proliferation compared with ePTFE grafts. Expression of pro-inflammatory TNF-α/IL-1α cytokines was significantly higher in ePTFE, whereas the level of IL-10 was higher in TPU. Initial high expression of pro-inflammatory CCR7 macrophages was noted in TPU, however there was a clear transition from CCR7 to anti-inflammatory CD163 expression in vitro and in vivo only in TPU, confirming superior cell-biomaterial response. The co-culture models, especially the paracrine model, revealed higher fidelity to the immunomodulatory/biocompatibility behavior of degradable TPU grafts in vivo. This study established an exciting approach developing a co-culture model as a tool for biocompatibility evaluation of degradable biomaterials.
KeywordsVascular graft Biocompatibility Biodegradable polyurethane Fibroblast-macrophage co-culture
Despite considerable research in the field of small diameter vascular graft (SDVG) replacement, there is still no ideal alternative to autografts up to now. Numerous problems are associated to synthetic SDVGs such as, thrombogenicity and intimal hyperplasia.11 Therefore, developing new generations of such conduits has become a major focus of scientists. One new approach is designing cell-free degradable vascular grafts, which promote remodeling via fast host cell infiltration. Furthermore, permanent presence of the foreign material in the host tissue will be avoided in these grafts.22 In our previous study a new biodegradable thermoplastic polyurethane polymer (TPU) with ultimate mechanical and functional behavior was synthesized and characterized.4 However, the inflammatory potential of the graft, which may evoke acute/chronic inflammatory responses at the site of implantation, still needs to be fully characterized.
Inflammation is the primary phase of wound healing and the presence of macrophages has a critical role for a positive healing outcome.13 Beside the presence of the macrophages, their activation state has equal importance on remodeling outcome. Activated pro-inflammatory macrophages, M1, secret inflammatory cytokines such as IL-1b, IL-1α, TNF-α and IL-6. While, activated anti-inflammatory macrophages, M2, express high level of IL-10 cytokine.6 An in vitro macrophage mono-culture model is one common method for evaluation of the host-biomaterial response. However, the extent of host-biomaterial response is defined by complex cell-based soluble signaling interactions between activated macrophages and other recruited cell types such as fibroblasts and endothelial cells at the graft-host interface.23 Among these cells, macrophages and fibroblasts are the major cells concurrently synchronizing and reacting to the foreign material via complex synergistic autocrine, paracrine (indirect cell contacts) and juxtacrine (direct cell contacts) signaling.23 Therefore, for a better cell-biomaterial interaction assessment, the effect of fibroblasts on macrophage polarization and modulation should be considered. However, there are only few studies on cooperative behavior of fibroblasts and macrophages in vitro in just juxtacrine co-culture model in the presence of biomaterials.18,23 It was shown that the magnitudes of the expression of cytokines in fibroblast-macrophage juxtacrine co-cultures were different from those in fibroblast/macrophage mono-cultures.18,23 Therefore, a better understanding of fibroblast and macrophage functional behavior in vitro in the presence of our TPU vascular graft in both juxtacrine and paracrine settings, could provide a better cell-biomaterial interaction assessment tool to study the immunomodulatory effect of the TPU biomaterial.
Fast host cell infiltration is essential for sufficient remodeling of a bioresorbable prosthesis. Following implantation, the composition of host-graft interface changes constantly. This leads to a continuous adoption of cells at the interface till the end of remodeling.1,18 The biomaterial should support host cell migration and proliferation and enable the presence of specific cellular phenotype necessary for remodeling.
This study seeks to evaluate the immunomodulatory behavior of degradable TPU grafts via fibroblast-macrophage paracrine (FM-Para-CC) and juxtacrine co-culture (FM-Jux-CC) models. TPU graft was compared with ePTFE graft, which is a clinically applied non-degradable synthetic vascular substitute. In-vivo immunomodulatory behavior of the grafts was compared with in vitro results. Furthermore, host cell infiltration into the TPU graft and the type of the proliferated cells were studied in vivo.
Materials and Methods
As previously described, the prepolymer method was utilized to synthesize the new thermoplastic polyurethane polymer.2 TPUs are block copolymers containing hard- and soft-block sections with crystalline and amorphous domains. The material is based on classical poly(tetrahydrofuran) as soft-block and hexamethylene diisocyanate and bishydroxyethyl terephthalate as components for the hard-block in a molar ratio of 1:2:1. TPU grafts were fabricated via electrospinning and they were characterized morphologically and mechanically (fiber diameter; 1.39 ± 0.76 µm, porosity; 74 ± 1%, pore size; 4.6 µm, inner diameter; 1.6 mm, wall thickness; 78 ± 10 µm).4 EPTFE grafts (inner diameter; 1.5 mm, wall thickness; 100 μm, intermodal-distance; 5–25 µm, Zeuss, Orangeburg, USA) were used as controls. Samples were sterilized with ethylene oxide before cell seeding and implantation. All experiments involving animals or animal tissues were conducted in compliance with European and national legislation and were permitted by the Animal Ethics Committee of the Medical University of Vienna and the Austrian Federal Ministry of Science and Research.
Isolation of Primary Macrophages and Fibroblasts
Both macrophages and fibroblasts were isolated from four adult male Sprague–Dawley rats (350–400 g). Primary fibroblasts were isolated from rat skin biopsies as previously described.23 The skin samples were cut and placed on a petri dish with subcutaneous side down. Cells started to migrate out of the tissue after approximately 1 week incubation in UltraCULTURE™ medium (Lonza GmbH, Verviers, Belgium) including 10% fetal bovine serum (Millipore, Darmstadt, Germany) and 2% penicillin (Lonza GmbH, Basel, Switzerland). Subsequently, skin tissues were removed. The collected cells were passaged and passages 3–6 were used for the experiments. Isolated fibroblasts could be distinguished by their flat/spindle-shaped morphology and their branched cytoplasm surrounding an oval-shaped nucleus. Macrophages were isolated by a standard technique previously described.23 Briefly, peritoneal macrophages were obtained by lavage of the peritoneal cavity with 50 mL of cold phosphate-buffered saline (PBS, GIBCO®, Austria) and isolated by adherence on culture dishes for 1 h at 37 °C. Subsequently, cells were gently detached by rubber cell scraper and used for our studies.
Mono- and Co-culture Models
The isolated cells were seeded on the luminal side of the grafts with the concentration of 2 × 105 macrophages and 2 × 104 fibroblasts per well (24 well plate) for the macrophage and fibroblast mono-cultures. Mixtures of macrophages and fibroblasts (2 × 105 M + 2 × 104 F) were used for the juxtacrine co-culture models. For paracrine co-culture, 0.4 μm pore transwell® polyester membrane cell culture inserts (Corning, USA) for 24 well plates were utilized. 2 × 105 macrophages per well were seeded on the grafts and 2 × 104 fibroblasts were seeded on each transwell insert. Culture media that were used for all the mono and co-cultures were similar to the media used for cell isolations. Cells were cultured on NUC™ Thermanox™ plastic coverslips (Thermo Scientist, NY, USA) as control groups.
Cell Morphology Studies
Morphology and attachment of the macrophages and fibroblasts to the grafts were visualized via crystal violet (CV) staining and scanning electron microscopy (SEM, JEOL JSM-5400, JEOL Ltd., Japan) in mono- and co-cultured models after 7 and 21 days. Briefly, for CV staining, samples were fixed with paraformaldehyde (3.7%) and subsequently incubated with 0.05% crystal violet prior to microscopy. For SEM, samples were fixed in 2.5% glutaraldehyde. They were dried using hexamethyldisilazane (reagent grade ≥99%, Sigma Aldrich, Austria) and then sputter coated with gold prior to SEM.
Viability and Proliferation Studies
The proliferation of the fibroblasts in mono and co-cultures was investigated using a XTT cell viability and proliferation kit (Biomol, Hamburg, Germany) after 7, 14 and 21 days. 208 μL XTT was added, and the scaffolds including adherent cells were incubated for 20 h. Absorption of the reduced XTT was measured at 450 nm (reference wavelength 595 nm) on a Victor3 spectrophotometer (VICTOR3, Perkin Elmer, MA, USA). Grafts incubated with culture media without cells served as blank and data has been adjusted to the blank. All experiments were repeated independently 3 times (n = 3 per time-point per group).
Cell Distribution Study
3D distribution of the cells and population of the positive cells on the grafts was investigated using confocal laser-scanning microscope (CLSM 700, Zeiss, Germany) after 21 days. Mouse-anti-rat-CD68 (pan macrophages) and mouse-anti-rat-CD163 (M2 anti-inflammatory macrophages) primary antibodies (both from AbD Serotec, Duesseldorf, Germany) were utilized. Briefly, after fixing the cells with paraformaldehyde (3.7%), non-specific sites were blocked with 1.5% normal goat serum (Dako, Glostrup, Denmark) and then the samples were stained with the primary antibodies. Subsequently, the samples were incubated with secondary antibodies (Goat anti-mouse igG Alexa Fluor 488, abcam, Bristol, UK,) with the dilution of 1:300 in PBS. Nuclei of the cells were counterstained with DAPI using Prolong® Gold antifade embedding solution containing DAPI (Life Technologies, USA). For quantification of the positive cells, five random positions of each samples with the area of 2 mm × 2 mm and thickness of 100 µm have been selected and scanned (n = 3 per group).
Specifications of the primers used.
Amplicon Size (bp)
TPU and ePTFE grafts (ID: 1.5 mm, length: 2 cm) were implanted into the infrarenal aorta of male Sprague–Dawley rats (300–400 g, n = 8 animals per time-point per group) using microsurgical techniques as previously described.4 No anti-coagulation nor anti-platelet drugs were administered. TPU and ePTFE grafts were harvested after 1 week and 1 month for PCR and histological assessments (n = 4 per time-point per group for each assessment).
RNA isolation, CDNAs and PCR protocols were identical to that used in in vitro studies (“Real-Time PCR” section).
Following dehydration of formaldehyde-fixed samples, they were embedded in paraffin. Histological cross-sections (3 µm) were processed for hematoxylin and eosin (H&E) staining. For characterization of proliferated cells and macrophages, sections were incubated with the monoclonal mouse-anti-Ki67 (clone MM1, Leica Biosystems, Nussloch, Germany), monoclonal mouse-anti-rat CD 68 (clone ED1, AbD Serotec, Oxford, UK) and monoclonal mouse-anti-rat CD163 (clone ED2, AbD Serotec, Oxford, UK) primary antibodies. Following washing steps, slides were incubated with the secondary antibody BrightVision Poly-HRP-anti-mouse (Immunologic, Duiven, The Netherlands). Images were captured using an Olympus BX microscope.
Double immunofluorescence staining was carried out to specifically identify the number of Ki67, desmin, α-SMA, PDGF, VEGF positive cells and to assess the percentage of desmin/α-SMA/PDGF/VEGF positive cells within the proliferated Ki67+ cells. To do so, following primary antibodies in combination with Ki67 have been used: monoclonal mouse-anti-smooth muscle actin (clone 1A4, DAKO, Glostrup, Denmark), monoclonal mouse-anti-desmin (clone D33, DAKO, Glostrup, Denmark), polyclonal rabbit anti-vascular endothelial growth factor A (Santa Cruz Biotechnology, Dallas, USA) and polyclonal rabbit anti-platelet derived growth factor (PDGFBB, Abcam, Cambridge, UK). Stainings were visualized using AlexaFluor goat-anti-mouse 568 (Molecular Probes) dilution 1:100 in PBS (for Ki67 positive cells), AlexaFluor goat-anti-mouse 488 (Molecular Probes) diluted 1:100 in PBS for α-SMA and desmin positive cells and AlexaFluor goat-anti-rabbit 488 (Molecular Probes) diluted 1:100 in PBS for PDGF and VEGF positive cells. Nuclei were stained by incubating in 4′,6-diamidino-2-phenylindole (DAPI, Sigma Aldrich, St. Louis, MO, USA). Immunofluorescent double-stained sections were evaluated via a confocal laser-scanning microscope (Zeiss, Germany, LSM 700).
Quantification and Analyzes of the Images
Three sections of midgraft region from each sample were randomly selected. The TissueQuest Analysis software (TissueGnostics GmbH, Austria) was used to count Ki67, CD68, CD163, desmin, α-SMA, PDGF and VEGF positive cells. The percentage of double positive cells were assessed by detecting the positive staining in the cytoplasma within a ring mask, which was grown from the nucleus to a defined distance.
All data were expressed as mean ± standard deviation (SD). Statistical analyzes were performed using GraphPad Prism 6 software (GraphPad Software Inc., CA, USA). Two-way analysis of variance (ANOVA) using Bonferroni post hoc tests were applied for multiple and pair-wise comparisons between the groups. Statistical significance was defined for a p value of < 0.05.
Cell Attachment, Morphology, Viability and Proliferation
The influence of macrophages on proliferation of fibroblasts was further investigated (Figs. 1p–1r). Proliferation of fibroblasts increased significantly from day 7 till day 21 in all cultures in both TPU (p < 0.001 in all cultures) and ePTFE grafts (p < 0.001 in F-C and FM-Jux-CC and p < 0.05 in FM-Para-CC). In general, co-cultures showed higher proliferation compared to F mono-cultures. Comparing juxtacrine with paracrine co-cultures, the proliferation of the fibroblasts in paracrine co-culture was significantly higher than in juxtacrine at earlier time points (p < 0.001; day 7 and p < 0.05; day 14) in both grafts. This suggests that paracrine model could better support the fibroblast proliferation. Comparing TPU with ePTFE grafts, proliferation of fibroblasts was higher in F mono-culture and FM co-culture models in TPU grafts.
Cell Distribution Studies In Vitro
Comparison of FM Co-cultures vs. Mono-cultures
Expression of pro- and anti-inflammatory cytokines was not prominent in the fibroblast mono-cultures. However, the presence of fibroblasts in co-cultures had evident influence on expression of these cytokines. The expression of TNF-α and IL-1α pro-inflammatory cytokines was higher in FM co-culture models compared with M mono-cultures and this was more significant in paracrine co-cultures (TPU; M vs. FM-Para, TNF-α and IL-1α: 2, 24, 48, 72 h: p < 0.001), (ePTFE; M vs. FM-Para, TNF-α: 2, 24, 48, 72 h: p < 0.001, IL-1α: 2 h: p < 0.001, IL-1α: 24, 48, 72 h: p < 0.05).
Comparison of FM Paracrine vs. Juxtacrine Co-cultures
The trend of cytokines expressions was similar in both paracrine and juxtacrine co-cultures. However, in the paracrine model the expressions of TNF-α and IL-1α pro-inflammatory cytokines were higher at all time points compared to juxtacrine model (TPU; FM-Jux vs. FM-Para, TNF-α, IL-1α: 2, 24, 48 h: p < 0.001), (ePTFE; FM-Jux vs. FM-Para, TNF-α: 2, 24, 48 h: p < 0.001, IL-1α: 2, 24 h: p < 0.05). Expression of anti-inflammatory IL-10 did not show significant differences between paracrine and juxtacrine co-cultures.
Comparison of TPU vs. ePTFE Grafts
Both grafts showed high expression of pro-inflammatory cytokines at the beginning. These expressions were then followed by significant down-regulation of pro-inflammatory and up-regulation of anti-inflammatory IL-10 cytokines (after 24 h). The level of anti-inflammatory IL-10 was significantly higher in TPU grafts compared with ePTFE grafts in both M mono-culture (after 2, 48, 72 h) and FM co-cultures (after 2, 24, 72 h). Furthermore, level of pro-inflammatory IL-1α and TNF-α were significantly higher in ePTFE grafts compared with TPU in co-culture models, (IL-1α:2 h: p < 0.001, 72 h: p < 0.05 and TNF-α: 2, 48, 72 h: p < 0.001).
Macrophages Gene Expression Studies
Comparison of FM Co-cultures vs. Macrophage Mono-cultures
In ePTFE grafts, CCR7 pro-inflammatory expression was significantly higher at all time points in both juxtacrine and paracrine co-cultures compared with macrophage mono-cultures. While, in TPU grafts, only FM paracrine co-cultures expressed significantly higher CCR7 genes (p < 0.05) compared with macrophage mono-cultures after 7 and 14 days. The expression of anti-inflammatory CD163 macrophages was not statistically different in macrophage mono-cultures compared with FM co-cultures.
Comparison of FM Paracrine vs. Juxtacrine Co-cultures
Expressions of pro-inflammatory macrophages (CCR7) and pan macrophages (CD68) in paracrine co-culture models were significantly higher than in juxtacrine models at all time points in both ePTFE and TPU grafts (except after 21 days, CCR7 in TPU). All these confirmed that in FM co-cultures especially in paracrine co-cultures, pro-inflammatory macrophages have been more activated compared to M mono-cultures.
Comparison of TPU vs. ePTFE Grafts
High level of pro-inflammatory (CCR7) was present in both grafts at day 7. This expression decreased significantly in TPU grafts (p < 0.001), whereas, it remained up-regulated in ePTFE grafts at all time points in macrophage mono-cultures and fibroblast-macrophage co-cultures. Furthermore, the level of anti-inflammatory CD163 in TPU grafts was significantly higher than in ePTFE grafts at all time points in M and FM culture models (p < 0.05).
The CCR7/CD163 ratios were further calculated using the correspondent gene expression levels for each graft type. TPU grafts initially had M1 pro-inflammatory responses, however after 14 days there was a clear switch from M1 pro-inflammatory (CCR7) to M2 anti-inflammatory (CD163) in all cultures, confirming a constructive response in TPU grafts (Fig. 4b). The initial pro-inflammatory response in TPU grafts in paracrine co-cultures was significantly higher than in juxtacrine co-cultures. In ePTFE grafts, FM co-culture models, showed predominant M1 pro-inflammatory responses however, a negligible transition from M1 toward M2 response was observed in M mono-cultures.
Graft Retrieval and Macrophage Infiltration
In-Vivo Biocompatibility Evaluation and Gene Expression Studies
Cytokines release monitoring, revealed that only in TPU grafts, expressions of TNF-α and IL-1α pro-inflammatory cytokines were significantly lower than IL-10 anti-inflammatory cytokine after 1 month implantation. Comparing TPU vs. ePTFE grafts, expressions of pro-inflammatory TNF-α and IL-1α cytokines were significantly higher in ePTFE grafts, whereas level of IL-10 was significantly lower in these grafts after 1 month (Fig. 6c, (p < 0.05)).
Quantification and Phenotypic Characterisation of the Proliferated Cells
Promoting cell infiltration and regulating inflammatory response by an implanted material are the two major factors for positive remodeling outcome and successful tissue regeneration of degradable materials. However, it is evident that capability of the implanted material to modulate pro-inflammatory response of macrophages is a pre-requisite for cell infiltration and cell growth.5 In this study, primary macrophages in mono- and co-cultured with fibroblasts (paracrine and juxtacrine co-culture models) were recruited for evaluation of the recently developed biodegradable electrospun grafts.
TPU grafts had superior support for fibroblast and macrophage cell attachment and proliferation, compared to ePTFE grafts in both mono- and co-cultured systems. This could be due to individual surface chemistry of the grafts and less hydrophobicity of TPU compared to ePTFE.4 Macrophages stimulated the proliferation of fibroblasts in co-cultures. It is known that activated macrophages induce fibrogenic cytokines such as IL1-α, TNF-α, PDGF and FGF, which stimulate fibroblast growth and proliferation.8,24 Cytokine release studies showed that early expression of the IL-1α and TNF-α was evident in both TPU and ePTFE grafts and this could enhance fibroblast proliferation in the co-culture.
The inflammatory phase of healing is associated with a significant up-regulation of the inflammatory cytokines, especially IL-6, TNF-α, IL-1α and IL-1β.14 These cytokines could be involved in different processes such as evoking migration/proliferation of fibroblasts, deposition/degradation of ECM and regulation of foreign body response.23 In constructive remodeling, the initial burst of inflammatory cytokines and M1 response is followed by a transitional phase toward M2 response, which is associated with significant down-regulation of pro-inflammatory cytokines. This phase stimulates the formation of scar tissue and inhibits chronic inflammation.5,13 In our study, initial expression of M1 macrophages (CCR7) and pro-inflammatory cytokines (TNF-α, IL-1α) was prominent in both macrophage mono-culture and in fibroblast-macrophage co-cultures in TPU and ePTFE grafts. Paracrine co-culture models showed higher pro-inflammatory response compared with juxtacrine co-culture models. After this initial inflammatory response, only TPU grafts modulated macrophage polarization toward M2 phenotype. The extent of this modulation was significantly higher in the co-culture models especially in paracrine co-culture models. It was shown previously that expression of IL-1α and TNF-α occurs considerably earlier than 72 h in macrophage-involved cultures.23 In our in vitro investigation, significant expression of pro-inflammatory cytokines (IL-1α, TNF-α) was evident after 2 h. This early phase was followed by significant down-regulation of TNF-α after 48 h. This shows the possible capability of fibroblasts and macrophages to modulate the inflammatory response to a foreign implant via expression of IL-10 anti-inflammatory cytokine. This expression has a key role in limiting the synthesis of pro-inflammatory cytokines such as TNF-α, IL-3 and IL-2.7
Following the adherence of macrophages to the implanted grafts in a rat model, the initial expression of M1 occurs in both TPU and ePTFE grafts. However, only TPU grafts ultimately promoted macrophage phenotypic transition towards M2 after 1 month implantation to support tissue repair and to inhibit chronic inflammation. Expression of inflammatory cytokines (TNF-α and IL-1α) was significantly higher than anti-inflammatory cytokines (IL-10) in ePTFE grafts. Continuous release of these inflammatory cytokines may lead to chronic inflammation and chronic wounding in vivo.8,10,24 Co-cultures had higher fidelity to in vivo situation compared to individual mono-cultures. Among the co-cultures, paracrine models better represented the in vivo initial pro-inflammatory response compared to juxtacrine models in TPU grafts. They also better represented the extent of the immunomodulatory effect of the biomaterial on macrophage polarization.
Remodeling of a biodegradable graft in terms of endothelialization and ECM production is highly governed by the migration and infiltration of host cells into the construct. Migration of endothelial cells (from the anastomosis or from transmural capillary ingrowth) and endothelial progenitor cells in bloodstream, play major roles in endothelialization and antithrombotic characteristics of a vascular graft. As previously seen, TPU grafts were fully endothelialized after 1 month implantation.4 Apart from cell infiltration, even distribution of cells throughout prosthesis is required to have uniform remolding and ECM deposition. It was shown that migration of the inflammatory cells and α-SMA+ cells is the major kind of migration in remolding of a vascular graft.20 Our previous study showed slight graft remodeling after 1 month implantation, however the extensive cellular repopulation of the grafts occurred after 12 months implantation in a rat model. The wall thickness did not change due to a precise balance between polymer degradation and tissue remodeling.4
TPU graft highly supported cell infiltration and proliferation compared to ePTFE grafts. Major cell infiltration in TPU grafts occurred via migration of macrophage, α-SMA+ and desmin+ cells. After 1 week implantation, CD68+ macrophages and Ki67+ proliferated cells were present in TPU grafts but mainly localized at adventitial layer. After 1 month, these cells were more evenly distributed throughout grafts at a lower density. Presence of CD163+ anti-inflammatory cells inside TPU grafts and very limited number of CD163+ cells in the adjacent tissue of the ePTFE grafts suggest the superior characteristic of TPU in recruiting healing macrophages compared to ePTFE grafts in vivo.
α-SMA+ and desmin+ cells are contractile filaments. They are considered as markers for developing vascular mural cells.3,12 Abundant number of α-SMA+ and desmin+ cells evenly distributed in the graft could indicate the regeneration of a contractile media in TPU grafts. Presence of PDGF and especially endothelium release of PDGF could be responsible in part for recruitment and proliferation of the vascular smooth muscle cells.12,15 Luminal layers of TPU and ePTFE grafts were comprised of VEGF+ cells after 1 month implantation. VEGF is considered as specific mitogen of the vascular endothelial cells, which promotes endothelial cell proliferation and migration. They also act as a major regulator of angiogenesis and vasculogenesis.16 VEGF+ cells were also present at the TPU host-tissue interface. It is well known that VEGF could be also produced by non-endothelial cells such as macrophages, platelets and cardiac myofibroblasts.9 Identifying the type of these VEGF+ non-endothelial cells remains to be studied. Quantification of the co-expression of Ki67-desmin, Ki67-α-SMA, Ki67-PDGF and Ki67-VEGF revealed that TPU grafts significantly supported the proliferation of α-SMA+ and desmin+ cells. These cells are primarily responsible for control of blood pressure and blood flow by responding to biomechanical stimuli.17,21
This study highlighted that macrophages in co-culture with fibroblasts in a paracrine model was a better representative of in vivo condition for assessing immunomodulatory potential of the TPU grafts. However, the absence of other inflammatory cells might confine the in vitro approach. Therefore, further assessing the biocompatibility of the graft and its influences on innate and acquired immunity such as T cells, B cells, natural killer cells and granulocytes should be considered in cell-biomaterial interaction studies.19 Furthermore, long-term functionality of the TPU graft should be assessed under low blood flow conditions in a large animal model. Comparing TPU graft with ePTFE graft, degradable TPU material showed desirable immunomodulatory effects on macrophages activation state and it promoted the macrophage polarization toward the M2 phenotype. It also highly supported cell infiltration, which could promote constructive remodeling.
Morphology and structure of the TPU grafts supported attachment, viability and proliferation of the fibroblasts in mono and co-culture models. The extent of the inflammatory response was different in FM co-cultures compared to individual mono-cultures. Within the co-culture models, paracrine model better represented the initial pro-inflammatory response of the implanted TPU graft. Although, the co-culture models could not represent all the comprehensive aspects of the in vivo condition, it could provide a superior model to assess the in vivo behavior of the TPU graft prior to implantation. TPU grafts had superior characteristics in supporting cell infiltration and proliferation in vivo. A large number of α-SMA+ and desmin+ cells indicates the regeneration of a contractile media in TPU. TPU grafts also revealed an effective switch in macrophage polarization from M1 pro-inflammatory toward M2 anti-inflammatory in vitro and in vivo, which is a key component of constructive remodeling.
This work was supported by the Ludwig Boltzmann Cluster for Cardiovascular Research. The authors thank the core facility imaging of the Medical University of Vienna especially Marion Gröger for confocal microscopy and Claudia Höchsmann for technical assistance.
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