Ping Yi1†
Jiadi Liang2†Futing Huang1Zuodong Zhao1Xiaohui Zhou1
Qianya Gao1Min Huang1Baoyi Chen1
Zhenzhao Guo3
Chang Liu1*- 1Guangzhou Key Laboratory of Basic and Applied Research of Oral Regenerative Medicine, Department of Orthodontics, Affiliated Stomatology Hospital of Guangzhou Medical University, Guangzhou, China
- 2Center of Stomatology, Shunde Hospital of Southern Medical University, Foshan, China
- 3Guangzhou Key Laboratory of Basic and Applied Research of Oral Regenerative Medicine, Affiliated Stomatology Hospital of Guangzhou Medical University, Guangzhou, China
Tissue engineering is a promising approach to restore or replace a damaged temporomandibular joint (TMJ) disc. However, constructing a scaffold that can mimic biomechanical and biological properties of the natural TMJ disc remains a challenge. In this study, three-dimensional (3D) printing technology was used to fabricate polycaprolactone (PCL)/polyurethane (PU) scaffolds and PU scaffolds to imitate the region-specific biomechanical properties of the TMJ disc. The scaffolds were coated with polydopamine (PDA) and combined with a decellularized matrix (dECM). Then, rat costal chondrocytes and mouse L929 fibroblasts, respectively, were suspended on the composite scaffolds and the biological functions of the cells were studied. The properties of the scaffolds were characterized by scanning electron microscopy (SEM), X-ray photoelectron spectroscopy (XPS), contact angle analysis, and biomechanical testing. To verify the biocompatibility of the scaffolds, the viability, proliferation, and extracellular matrix (ECM) production of the cells seeded on the scaffolds were assessed by LIVE/DEAD staining, Cell Counting Kit-8 assay, biochemical content analysis, immunofluorescence staining, and qRT-PCR. The functionalized hybrid scaffolds were then implanted into the subcutaneous space of nude mice for 6 weeks, and the regenerated tissue was evaluated by histological staining. The biomechanical properties of PCL/PU and PU scaffolds were comparable to that of the central and peripheral zones, respectively, of a native human TMJ disc. The PDA-coated scaffolds displayed superior biomechanical, structural, and functional properties, creating a favorable microenvironment for cell survival, proliferation, ECM production, and tissue regeneration. In conclusion, 3D-printed polymer scaffolds coated with PDA and combined with dECM hydrogel were found to be a promising substitute for TMJ disc tissue engineering.
Introduction
Temporomandibular disorder (TMD) has been reported to affect 10%–15% of the population, and only 5% of patients seek treatment (Lim and Sbhalang, 2010; Gonçalves et al., 2011). As a major component of the temporomandibular joint (TMJ), the disc usually undergoes degenerative changes, such as displacement without reduction and perforation in patients with severe TMD, and these pathological changes greatly compromise normal jaw movement and functions, including the ability to eat and speak (Eiji and Theo, 2003). The TMJ disc has poor regeneration capability due to the limited vascularization. At the advanced stage of TMD, the only option for the treatment of the damaged disc is surgical resection (Miloro and Henriksen, 2010; Renapurkar, 2018). Though discectomy can partially relieve symptoms, permanent recovery will not occur due to the development of condylar remodeling (Eriksson and Westesson, 1992; Abdala-Junior et al., 2018). To avoid progressive degenerative changes of the affected TMJ, placement of an interpositional material is highly recommended. However, replacement of the damaged disc with alloplastic or autogenous graft leads to a range of complications, which considerably limit the clinical application (Dolwick, 2007; Dimitroulis, 2011).
Tissue engineering is emerging as a promising approach to attenuate symptoms of TMD, even repair or potentially replace the injured discs. Scaffolding materials play a crucial role in providing mechanical support and biochemical signals for tissue regeneration. Until now, numerous natural materials and synthetic polymers have been used to engineer the disc (Wu et al., 2014; Kobayashi et al., 2015; Bousnaki et al., 2018; Wang et al., 2018; Moura et al., 2020). Natural scaffolds, especially the tissue-specific decellularized extracellular matrix (dECM), generally possess high biocompatibility and recognition domains to facilitate cell adhesion, proliferation, and differentiation through inherent biochemical cues within native tissues, while the poor mechanical strength impedes its application in regenerating load-bearing tissues (Brown et al., 2012; Liang et al., 2020). On the other hand, the lack of mechanical properties of these biomaterials can be overcome by combining them with synthetic polymers to form composite structures with superior mechanical strength, biocompatibility, and biodegradability (Pina et al., 2019).
At present, the main methods used to prepare scaffolds are electrospinning, freeze-drying, three-dimensional (3D) printing, and so on (Acri et al., 2019). 3D printing technology is an ideal way to fabricate biomimetic scaffolds with a desired shape, suitable mechanical properties, and a well-controlled microstructure to facilitate cell infiltration and distribution (Legemate et al., 2016; Tamay et al., 2019). Various synthetic polymers, including poly(lactic-co-glycolic acid) (PLGA), polylactic acid (PLA), polycaprolactone (PCL), and polyurethane (PU), have been used for printing soft and hard tissues due to their fine-tunable properties (Daly et al., 2017). Recently, PCL and PU have been widely investigated for regeneration of cartilaginous tissue because they possess excellent biocompatibility and adequate mechanical properties, which can be maintained for a long time (Bahcecioglu et al., 2019; Theodoridis et al., 2019; Wen et al., 2019). However, scaffolds made of these materials have smooth surfaces, are hydrophobic, and lack cell recognition sites; thus, their ability to promote cell adhesion, proliferation, and differentiation is poor (Zhu et al., 2002). To address this challenge, various surface modification techniques have been developed to mediate cell adhesion and subsequent cell responses (Richbourg et al., 2019). Recently, functionalizing biomaterials with different biomacromolecules, such as proteins, peptides, or growth factors, has attracted much attention since this approach may evoke cell- and tissue-specific reactions (Lee et al., 2014; Tarafder et al., 2016; Capellato et al., 2020). Compared to other chemical conjugation methods, the polydopamine (PDA) coating tends to be nontoxic, solvent-free, and time-saving (Qiu et al., 2018). This innovative surface modification method has therefore been extensively explored for applications in engineering various hard and soft tissues, such as bone, cartilage, blood vessels, nerves, and muscle (Qian et al., 2018; Bock et al., 2020; Godoy-Gallardo et al., 2020; Wei et al., 2020).
In the present study, we aimed to develop a biomimetic composite scaffold of 3D printed synthetic polymers and tissue-specific dECM hydrogel to repair the TMJ disc. The composite scaffold developed can provide an ideal physical and biochemical microenvironment to promote cell attachment, proliferation, differentiation, and tissue regeneration by combining PDA-coated PCL/PU and PU scaffolds with tissue-specific decellularized ECM hydrogel derived from porcine TMJ discs. Therefore, this biomimetic composite scaffold holds potential to be a promising approach for TMJ disc tissue engineering.
Materials and Methods
Fabrication of the 3D Printed Scaffolds
Based on the region-specific mechanical properties of TMJ disc, 3D printed scaffolds were fabricated using a mixture of PCL (Sigma, USA) and PU (Tecoflex, EG-100A, United States) at a ratio of 1:1, according to the results of our pilot study. PCL and PU particles were heated at 100°C for 30 min in the miniature twin screw extruder (MiniJet, HAAKE MiniJet, Germany), then the mixture was extruded at a speed of 100 r/min at a temperature of 140°C. PCL/PU and PU scaffolds with a pore size of about 350 μm were fabricated using a 3D printer (Regenovo, China). The materials were melted at 170°C in printing chamber, printed through a 22 gauge metal needle at pressure 0.45 Mpa and deposition speed of 0.5 mm/s. Printed scaffolds were immersed in a dopamine solution (2 mg/ml, pH 8.5) at room temperature for 16 h under continuous stirring (Jo et al., 2013) and then rinsed several times with deionized water. Samples were used after vacuum drying for 24 h. Scaffolds coated with PDA were classified as “modified” groups and were referred to as PDA-PCL/PU and PDA-PU scaffolds, respectively. The scaffolds without PDA coating were classified as “original” groups.
Characterization of 3D Printed Scaffolds
The morphology of the scaffolds was visualized by scanning electron microscopy (SEM, Thermo Fisher Scientific, United States). Samples were sputter-coated with gold at 20 mA for 60 s, mounted on aluminum stubs, fixed with carbon tape, and observed under a SEM at an accelerating voltage of 10 kV. The chemical composition of the scaffolds was analyzed by X-ray photoelectron spectroscopy (XPS, Thermo Fisher K-Aloha, United States). The containment C1s hydrocarbon peak at 284.7 eV was applied to calibrate the binding energies, and the sensitivity factors of C1s, N1s, and O1s were quantitatively calculated. The water contact angle of the scaffolds was used to evaluate the hydrophobicity of the scaffolds. Briefly, the same amount of water was dropped onto the surface of each scaffold at room temperature, and the image was captured using a contact angle analyzer (JY-PH, JINHE, China).
Preparation of the Composite Scaffolds
Preparation of the Hydrogel
The decellularization process of TMJ disc was carried out as described in prior study (Liang et al., 2020). Briefly, the minced tissue pieces were placed into a hypotonic Tris-HCl buffer followed by four cycles of freezing and thawing. These samples were treated with 0.5% trypsin solution for 24 h and then with nuclease solution (50 U/ml DNase and 1 U/ml RNase, pH 7.5) at room temperature for 4 h. Afterward, these samples were treated with 1% Triton X-100 for 48 h and washed with deionized water for at least 3 days. The dECM powder was digested with 0.1% pepsin in 0.01 M HCl at room temperature for 48 h. The flowable solution was neutralized by adding 0.1 M NaOH, followed by adding 10 × PBS to adjust the physiological acidity and salinity. The pregel solution was diluted to the predetermined concentration (8 mg/ml) using 1 × PBS for subsequent study, since this concentration has been proven to be the most cells-friendly concentration in a preceding study (Liang et al., 2020).
Fabrication of the Composite Scaffolds
The dECM solution (8 mg/ml) was infused into the 3D printed scaffolds using a dropper and then incubated in a 37°C incubator for 30 min to complete the gelation of the hydrogel. The size of the scaffolds used in the subsequent cell experiments corresponded to the size of the well plates, e.g., when a cell experiment was performed with 48-well plates, the scaffold size was matched to that of the 48-well plate size. A schematic illustration of the preparation procedure of scaffolds is presented in Figure 1.
FIGURE 1. Schematic illustration of the construction process of the composite scaffolds of the experimental design.
Mechanical Tests of the Composite Scaffolds
Mechanical tests were performed as described previously (Legemate et al., 2016), using Instron mechanical testing instrument (Instron 3,342, Instron, Norwood, MA, United States). Cylinders with 5 mm diameter and 3 mm height were prepared for compression test. Bone-shaped scaffolds with 1 mm thickness and 25 mm length were printed for tensile test. All scaffolds tested were combined with dECM hydrogel. Compression and tensile mechanical tests were performed at 0.25 mm/min after samples had been preconditioned with 15 cycles with strain ranging from 0 to 10% strain.
Cell Culture Experiments
Cells Culture
L929 cells (i-CELL, China) were cultured in Dulbecco’s Modified Eagle’s Medium (DMEM) (Hyclone, China) supplemented with 10% FBS and 1% penicillin-streptomycin in an atmosphere containing 5% CO2 at 37°C. Primary rat chondrocytes isolated from 4-week-old specific pathogen free rat (SPF), according to an established method (Barbero et al., 2004). Briefly, costal cartilage fragments were digested with 0.2% collagenase at 37°C overnight. Cells were collected from the digested solution and cultured using DMEM/F-12 (Hyclone, China) supplemented with 10% FBS and 1% penicillin-streptomycin in a humidified incubator with 5% CO2 at 37°C. Cells at passage 2 were used for all experiments. All animal experiments were approved by Guangzhou Medical University (No. GY2020-044) and conducted according to standard guidelines for the use and care of laboratory animals.
Cell Seeding onto Scaffolds and Viability Assay
The sterilized composite scaffolds were placed in 48-well plates. L929 and chondrocytes, respectively, were implanted at a density of 1.0 × 104 cells/scaffold to construct cell-laden composite scaffolds and cultured with the growth medium suitable for growth of each type of cells. The viability of the cells on the composite scaffolds was evaluated using a LIVE/DEAD staining kit (BestBio, China) at 1 and 7 days of culture following the manufacturer protocol. The stained cells were observed by confocal laser scanning microscope (Leica TCS SP8, Germany). Cell proliferation was quantified by the Cell Counting Kit-8 assay (CCK8, Dojindo, Japan) at 1, 4, and 7 days of culture and measured at 450 nm wavelength in a microplate reader (Thermo Scientific, Shanghai, China).
Differentiation and Maturation of Cells
Gene Expression Analysis
Cell-loaded composite scaffolds were cultured in 6-well plates for 14 days, then total RNA was extracted using a TaKaRa MiniBEST Universal RNA Extraction Kit (TaKaRa Biotechnology, Japan). The content and purity of RNA were measured using NanoDrop 2000 (Thermo Fisher, United States). Total RNA (1 μg) was reverse-transcribed into cDNA using a PrimeScript TM RT reagent Kit (TaKaRa Biotechnology, Japan). Reverse-transcribed cDNA was subjected to quantitative real-time PCR (SYBR Premix Ex Taq, TaKaRa, Japan) using specific primers targeting Sox 9, collagen type II (ColII), collagen type I (ColI), and GAPDH according to the manufacturer’s instructions. GAPDH was used as a housekeeping gene. The primer sequences of the target genes are shown in Table 1.
TABLE 1. Primer of qPCR.
Immunofluorescence Staining and Analysis
Cell-loaded composite scaffolds were cultured in 24-well plates for 14 days, then immunofluorescence staining was used to visualize the deposition of Col I and Col II, respectively. Briefly, the samples were gently washed 3 times with PBS, fixed in 4% paraformaldehyde (PFA) for 15 min, and immersed in 0.1% Triton X-100 for 20 min. Then the samples were blocked with 5% bovine serum albumin (BSA) for 30 min and incubated overnight in a primary antibody solution diluted with 1% BSA in PBS with rabbit anti-Col I and rabbit anti-Col II (1:100, Abcam, USA) at 4°C. After washing 3 times with PBS, the scaffolds were incubated in the dark with the secondary antibody (1:200, Goat anti-rabbit IgG (H + L), Affinity, China) for 30 min. Finally, samples were stained with 4ʹ,6-diamidino-2-phenylindole (Dapi, Beyotime, China) for 15 min in the dark. The images were taken using a confocal laser scanning microscope (Leica TCS SP8, Germany).
Biochemical Content Analysis
Cell-laden composite scaffolds were cultured in 24-well plates for 14 days, and the biochemical content of sulfated glycosaminoglycans (GAG) and collagen was assessed as described in a previous study (Romanazzo et al., 2018). Briefly, the scaffolds were digested in 1 ml of papain mixture (125 µg/ml papain in 0.1 M sodium acetate, 5 mM L-cysteine HCL, and 0.05 M EDTA) at 65°C for 18 h and then were centrifuged at 10,000 rpm for 10 min to collect supernatant for quantification tests. Using a chondroitin sulphate standard, the dimethylmethylene blue dye binding assay was utilized to quantify sulfated GAG. Total collagen was determined by measuring the hydroxyproline content. Samples were hydrolyzed at 110°C for 18 h in 38% HCl diluted in H2O and then examined using a chloramine-T assay with a hydroxyproline:collagen ratio of 1:7.69.
Scaffolds Implantation and In Vivo Analysis
Cell-loaded composite scaffolds were implanted into subcutaneous pockets in the dorsal surface of 4-week-old female nude mice to compare the ability of chondrogenesis and fibrogenesis between modified groups and original groups. Briefly, cylindrical composite scaffolds with 5 mm in diameter and 1 mm in height were prepared as described above, and 2 × 106 cells were seeded on each scaffold to construct cell-laden composite scaffold. At 6 weeks after implantation, the mice were sacrificed and all implants were retrieved. Prior to sectioning, the implants were embedded in optimal cutting temperature (OCT) compound (Tissue-Tek®, Sakura, Japan) and then sectioned transversely at a thickness of 10 μm. Tissue sections were stained with Alcian blue (AB) and Picrosirius red (PR) to evaluate chondrogenesis and fibrogenesis of the scaffolds, respectively.
Statistical Analysis
All values were reported as mean ± standard deviation (mean ± SD). At least three samples per group were selected for statistical analysis. Statistical analysis was performed with GraphPad Prism 7 (GraphPad Software, Inc., La Jolla, CA). Statistical significance was analyzed using Student’s t-test. The significant difference for all statistical analyses was defined as p < 0.05.
Results
Characterization of the Scaffolds
A color change to dark brown in the modified groups indicated the successful surface modification with PDA coating. Microscopically, SEM analysis showed that surface morphology of the original scaffolds was remarkably altered after PDA coating (Figure 2A). Compared with the smooth surfaces of original groups, spherical aggregates were observed on the surfaces in the modified groups.
FIGURE 2. Characterization of the 3D printed scaffolds. (A) SEM micrographs and gross images of the scaffolds: (A) PU; (B) PDA-PU; (C) PCL/PU; (D) PDA-PCL/PU. The gross images at the upper right corner. (B) XPS spectra of scaffolds. (C) Water contact angle of scaffolds (n = 3, *p < 0.05).
The surface chemical compositions of the scaffolds were analyzed by XPS. The spectra showed the existence of carbon (C1s, 284.5 eV), oxygen (O1s, 531.0 eV), and nitrogen (N1s, 399.6 eV) atoms in all scaffolds (Figure 2B). The nitrogen/carbon (N/C) ratio in the modified groups was higher than that in the original groups, mainly because PDA contains a large number of nitrogen atoms (Table 2).
TABLE 2. Surface chemical composition of scaffolds.
The water contact angle was measured to evaluate the efficiency of PDA attachment on original scaffolds. The surfaces of PCL/PU and PU scaffolds became relatively hydrophilic as shown with the significant decrease in water contact angle from 80.20° to 29.13° and 89.67° to 44.70°, after PDA coating (Figure 2C).
The tensile modulus and compressive modulus of the modified groups were significantly higher than those of the original groups (p < 0.05). The compression modulus of PDA-PCL/PU (15.970 Mpa) and PDA-PU (6.617 Mpa) scaffolds was similar to that of the middle region (about 15 Mpa) and the surrounding area (about 5 Mpa) of human TMJ disc, respectively (Figure 3).
FIGURE 3. Compressive and tensile modulus of the scaffolds. (A) Graphical representation of the compressive test specimen. (B) Graphical representation of the tensile test specimen. (C) Compressive modulus of the scaffolds. (D) Tensile modulus of the scaffolds. (* Comparison between groups, n = 5, *p < 0.05).
Biocompatibility of the Scaffolds
The results of cell viability examined by LIVE/DEAD staining are shown in Figure 4A. The living cells, colored green, were the dominant population of seeded cells and primarily resided in the hydrogel at day 1 and day 7. As determined by the amount of green fluorescence, the cell density in the modified groups remarkably increased after 7 days of culture. The proliferation of costal chondrocytes and L929 cells in the scaffolds was evaluated by the CCK-8 assay (Figures 4B,C). The optical density (OD) values increased from day 1 to 7 in all groups, suggesting the composite scaffolds were suitable for cell growth and nutrient transmission. Significantly higher OD values can be found in modified groups compared to original groups at 4 and 7 days (p < 0.05), indicating that cell proliferation was enhanced by the PDA coating.
FIGURE 4. Cell viability of the scaffolds. (A) LIVE/DEAD staining of the scaffolds: (a)-(h) chondrocyte, (i)-(p) L929. (B,C) Cell proliferation of the scaffolds. (*Comparison between original groups and modified groups, n = 3, *p < 0.05, **p < 0.01).
Cell Differentiation and Maturation
The expression level of chondrocyte and fibroblast marker genes was evaluated with qPCR after 14 days of culture. The modified groups exhibited significant upregulation of the chondrogenic-specific markers (Sox 9 and Col II) and fibrous-specific marker (Col I) compared with the original groups (p < 0.05) (Figure 5). These results indicated that the cell differentiation and maturation were promoted in the modified groups.
FIGURE 5. Genes expression of the scaffolds. (A)COL I, (B)COL II, and (C)SOX 9. (*Comparison between original groups and modified groups, n = 3, *p < 0.05, **p < 0.01).
Immunofluorescence Staining and Biochemical Study
The presence of collagens in the cell-laden composite scaffolds after 14 days of culture was visualized by immunofluorescence staining. (Figure 6: Col-I [green] and Col-II [red]). The number of cells positive for Col I and Col II in the modified groups was remarkably higher than that in the original groups, suggesting larger amounts of collagens were synthesized in the modified groups. Quantification of collagen and GAG content was carried out using biochemical analysis and the result was shown in Figure 7. There were significantly greater amounts of collagen and GAG deposition in the modified groups than the original groups (p < 0.05). These results indicated that the surface modification with PDA was beneficial to the secretion of these two major components of the extracellular matrix.
FIGURE 6. Immunofluorescence staining images of the scaffolds. (A) COL I and (B) COL II.
FIGURE 7. Biochemical analysis for collagen and GAG quantification. (A) Collagen content of the scaffolds; (B) GAG content of the scaffolds. (*Comparison between original groups and modified groups, n = 3, *p < 0.05, **p < 0.01).
In Vivo Cartilage and Fibrous Tissue Regeneration
Sirius red and Alcian blue are common methods for staining the extracellular matrix to identity fibroblasts and cartilage. Significant histological differences were observed between the modified and original groups at 6 weeks after implantation (Figure 8). The areas of hydrogel were filled with loose reticular red-stained fibroblast tissue or blue-stained cartilage tissue in the original groups. While the same areas in the modified groups were filled with regular dense fibrous or cartilage tissues, suggesting the PDA coating improved both chondrogenesis and fibrogenesis in vivo.
FIGURE 8. Histological analysis of the scaffolds retrieved from nude mice. (A) Picrosirius red staining. (B) Alcian blue staining. (a) PU-dECM; (b) PDA-PU- dECM; (c) PCL/PU-dECM; (d) PDA-PCL/PU- dECM. Orange arrows, 3D printed scaffolds framework lines; green arrows, collagen positively stained red with Picrosirius red; grey arrows, GAG positively stained blue with Alcian blue.
Discussion
The goal of tissue engineering is to construct ideal scaffolds which can provide a microenvironment that facilitates the proliferation and differentiation of implanted cells by mimicking the natural ECM and that can provide suitable mechanical strength to meet the requirements of various tissues (Acri et al., 2019). The TMJ disc is a load-bearing tissue and subjected to complex mechanical forces during function, thus, the ability of an engineered disc to withstand anisotropic physiological forces is essential to successful regeneration. In this study, we fabricated a biomimetic composite system of 3D-printed synthetic polymers and dECM hydrogel for the reconstruction of TMJ disc. The compressive modulus of the PCL/PU and PU scaffolds was comparable to that of the central and peripheral zone of a native human TMJ disc, respectively. The PDA-coated composite constructs promoted chondrocyte and fibroblast attachment, proliferation, differentiation, and tissue regeneration. Therefore, the biomimetic composite system developed has the potential to be a promising substitute for damaged TMJ disc.
It has been reported that a tissue-specific ECM environment plays a critical role in regulating the cellular behaviors of cells, such as cell attachment, proliferation, and differentiation (Acri et al., 2019). In our prior study, porcine TMJ disc was processed into tissue-specific hydrogel that possessed outstanding biological properties and biocompatibility; however, weak mechanical strength prevented it from withstanding compression when implanted into a TMJ disc defect (Liang et al., 2020). Synthetic polymers are typically associated with improved mechanical properties and usually used as scaffolds to regenerate hard tissues (Aljohani et al., 2018). Recently, hybridization of natural and synthetic polymer materials is proven to be a promising approach to construct tissue-engineered scaffolds which combines the advantages of both materials and meets diverse requirements (Setayeshmehr et al., 2019). This strategy has been applied to fabricate a variety of hybrid scaffolds to regenerate various hard tissues (Haaparanta et al., 2014; Chen et al., 2019a; Chen et al., 2019b). Therefore, in this study we chose polymer materials as the backbone of the composite scaffolds due to their excellent physical properties and TMJ disc-derived dECM hydrogel as a cell delivery system because of its superior biological properties, to engineer TMJ discs.
Compared with conventional approaches, 3D printing can produce specific implantable devices with architectural complexity that mimics that of the target tissue (Kumar et al., 2013). Although parameters vary according to the target tissue, pore sizes ranging from 200 to 350 μm are necessary to promote cellular activities such as cell proliferation, migration, and differentiation (Kim et al., 2018; Li et al., 2019). Thus, we constructed 3D printed scaffolds with a pore size of about 350 μm. 3D printed PU and PCL scaffolds have been widely used in hard tissue engineering because of their excellent biological performance and desirable physical properties which can be tailored for specific applications (Wen et al., 2019; Han et al., 2020). However, PCL and PU exhibit poor cell attachment due to their hydrophobic properties and lack of biological cell recognition. Recently, it has been suggested that PDA coating can improve the hydrophobicity of PCL and PU and also significantly facilitate cell adhesion (Ghorbani et al., 2020). In this study, we modified the surface of the scaffolds with PDA coating to provide a more cell-friendly polymeric surface, and success of surface modification was confirmed by SEM and XPS. Previous studies indicated that increased surface roughness can be ascribed to the thorough distribution of submicron-sized particulates following PDA coating by atomic force microscopic analysis (Ju et al., 2011; Shin et al., 2011). The increased nitrogen/carbon ratio in modified groups was also confirmed by a previous study which revealed the presence of nitrogen peaks corresponding to primary amine groups present in the polydopamine structure (Shin et al., 2011). The decreased static contact angle in modified groups manifested that PDA coating led to improved hydrophilicity of the materials. Actually, the hydrophilicity can be increased independent of the underlying substrate’s surface chemistry (Madhurakkat Perikamana et al., 2015). The enhanced mechanical properties in modified groups can be explained by the fact that DOPA contributes to cohesive strength through self-polymerization, which improves the overall mechanical strength of the composite scaffold (Zhao et al., 2018). In addition, a 600 nm PDA layer formed on scaffold surface maintained the optimal pore size of scaffold to facilitate cell infiltration and nutrition supply (Ma et al., 2016). Therefore, PDA coating is a promising approach to functionalize biomaterials by changing their physiochemical properties.
Chondrocytes, fibroblasts, and a combination of both have been widely used to evaluate the suitability of scaffolds for fibrocartilage tissue repair and regeneration (Vanderploeg et al., 2004; Singh et al., 2011). Thus, in this study rat costal chondrocytes and L929 fibroblasts were used to evaluate the biofunctions and biocompatibility of the composite scaffolds in vitro and in vivo. The LIVE/DEAD test and CCK-8 assay showed that surface modification significantly enhanced cell adhesion and proliferation in modified groups. Previous studies have confirmed that the adhesion and proliferation of chondroblasts and fibroblasts can be improved by topological changes of the material surface (den Braber et al., 1995; Boyan et al., 1996). It was suggested that amine groups contained in PDA confer hydrophilicity and positive charge to substrates (Madhurakkat Perikamana et al., 2015). Furthermore, highly reactive amine groups can undergo secondary conjugation with various biomacromolecules in the culture medium and TMJ disc dECM hydrogel, which further facilitate cell adhesion and other biofunctions. Therefore, the deposition of polydopamine on the scaffold surface provided a favorable biomimetic ECM microenvironment, improving a range of cell metabolic functions.
The TMJ disc contains a heterogeneous collection of morphologically variable cells with characteristics of fibroblasts and chondrocytes. Selection of cell sources is of paramount importance for TMJ disc tissue engineering (Donahue et al., 2019). Besides various stem cells used to engineer the TMJ disc, the combination of costal cartilage and fibroblast was advocated to be a promising cell source due to relative tissue abundance and surgical accessibility (Huwe et al., 2018; Vapniarsky et al., 2018). In our study, the enhanced gene expression and protein deposition of collagens in modified groups were verified by qPCR and immunofluorescence staining. Collagen I and II are considered as the phenotypic markers of fibroblasts and chondrocytes, and the expression levels can be used to represent the differentiation and maturation of these two cells. As a pivotal transcription factor that plays a dominant role in chondrogenesis and chondrocyte differentiation pathways, Sox9 is required to enhance chondrocyte survival, maintain expression of cartilage-specific markers already active, such as Col II, and activate markers of overtly differentiated chondrocytes (Lefebvre and Dvir-Ginzberg, 2017). The elevated expression of these tissue-specific markers in modified groups indicated the increased fibrogenesis and chondrogenesis following PDA coating. Collagen and GAG are the primary biochemical constituents that impart tensile and compressive strength to the TMJ disc (Lowe and Almarza, 2017). Thus, the higher level of collagen and GAG deposition can be associated to reinforced mechanical properties of the cell-laden composite scaffolds in the modified groups. Increased fibrogenesis and chondrogenesis in vivo can also be observed in the modified groups with Sirius red and Alcian blue staining. These histological results were consistent with our previous results which revealed enhanced cell adhesion, proliferation, differentiation, and maturation following PDA coating.
Although we have constructed a biomimetic cell-laden composite scaffold for engineering of TMJ disc, there are still some hurdles that need to be overcome to achieve ideal TMJ disc regeneration. First, polymeric scaffolds mimicking the complex geometric shape and region-specific mechanical properties of TMJ disc should be tailored by multiple-tool biofabrication strategies based on the image of MRI (Barbieri et al., 2020). Second, we have confirmed the fibrogenesis and chondrogenesis of the cell-laden composite scaffolds in nude mice; however, the successful regeneration of TMJ disc should be evaluated in physiologically mechanical environment by orthotopic implantation of these scaffolds in big animal model, such as mini pig (Helgeland et al., 2018). Third, the degradation velocity and mechanical strength of the polymeric scaffolds and hydrogel did not match each other perfectly, and these discrepancies probably compromised the biological and mechanical performance of the composite scaffolds in functional environment in vivo. Therefore, further study should focus on improving physical properties of these biomaterials to construct an ideal biomimetic substitute for TMJ disc tissue engineering (Kundu et al., 2015; Rothrauff et al., 2018).
Conclusion
In this study, a biomimetic composite scaffold was developed by combining 3D printed polymeric scaffolds and TMJ disc dECM hydrogel, and the biological and biomechanical properties of this scaffold were characterized. PDA-coated composite scaffolds possessed superior biomechanical properties and created a favorable microenvironment for cell adhesion, proliferation, differentiation, and maturation. The increased fibrogenesis and chondrogenesis of the cell-laden composite scaffolds in vitro and in vivo provided evidence of a promising strategy for TMJ disc regeneration. Overall, these results demonstrated that the biomimetic composite scaffold has therapeutic potential for TMJ disc engineering and regeneration.
Data Availability Statement
The raw data supporting the conclusions of this article will be made available by the authors, without undue reservation.
Ethics Statement
The animal study was reviewed and approved by Guangzhou Medical University.
Author Contributions
CL contributed to conception and design of the study; PY performed most of the experiments; JL carried out data analysis. All authors participated in drafting of the manuscript and critical revision of the draft. All authors have read and approved the final version of the manuscript.
Funding
This work was supported by the National Natural Science Foundation of China (31900946).
Conflict of Interest
The authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.
Acknowledgments
The authors thank the Laboratory of Stomatology Hospital of Guangzhou Medical University for technical support.
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Keywords: temporomandibular joint disc, tissue engineering, decellularized extracellular matrix, three-dimensional (3D), polydopamine
Citation: Yi P, Liang J, Huang F, Zhao Z, Zhou X, Gao Q, Huang M, Chen B, Guo Z and Liu C (2021) Composite System of 3D-Printed Polymer and Acellular Matrix Hydrogel to Repair Temporomandibular Joint Disc. Front. Mater. 8:621416. doi: 10.3389/fmats.2021.621416
Received: 09 November 2020; Accepted: 15 January 2021;
Published: 12 March 2021.
Edited by:
Jianxun Ding, Chinese Academy of Sciences, ChinaReviewed by:
Xianghong Luan, Texas A&M University, United StatesHe Liu, Jilin University, China
Jinlin Song, Chongqing Medical University, China
Copyright © 2021 Yi, Liang, Huang, Zhao, Zhou, Gao, Huang, Chen, Guo and Liu. This is an open-access article distributed under the terms of the Creative Commons Attribution License (CC BY). The use, distribution or reproduction in other forums is permitted, provided the original author(s) and the copyright owner(s) are credited and that the original publication in this journal is cited, in accordance with accepted academic practice. No use, distribution or reproduction is permitted which does not comply with these terms.
*Correspondence: Chang Liu, changliudentist@gzhmu.edu.cn
†These authors have contributed equally to this work and share first authorship