ORIGINAL RESEARCH article
Improved Osteogenesis by Mineralization Combined With Double-Crosslinked Hydrogel Coating for Proliferation and Differentiation of Mesenchymal Stem Cells
- 1Department of Orthopaedic Surgery, Zhongshan Hospital, Fudan University, Shanghai, China
- 2Hospital Infection Management Department, Affiliated Wuxi People’s Hospital of Nanjing Medical University, Wuxi, China
- 3Department of Orthopaedic Surgery, Zhongshan Hospital, Fudan University (Xiamen Branch), Xiamen, China
In consideration of improving the interface problems of poly-L-lactic acid (PLLA) that hindered biomedical use, surface coatings have been explored as an appealing strategy in establishing a multi-functional coating for osteogenesis. Though the layer-by-layer (LBL) coating developed, a few studies have applied double-crosslinked hydrogels in this technique. In this research, we established a bilayer coating with double-crosslinked hydrogels [alginate–gelatin methacrylate (GelMA)] containing bone morphogenic protein (BMP)-2 [alginate-GelMA/hydroxyapatite (HA)/BMP-2], which displayed great biocompatibility and osteogenesis. The characterization of the coating showed improved properties and enhanced wettability of the native PLLA. To evaluate the biosafety and inductive ability of osteogenesis, the behavior (viability, adherence, and proliferation) and morphology of human bone mesenchymal stem cells (hBMSCs) on the bilayer coatings were tested by multiple exams. The satisfactory function of osteogenesis was verified in bilayer coatings. We found the best ratios between GelMA and alginate for biological applications. The Alg70-Gel30 and Alg50-Gel50 groups facilitated the osteogenic transformation of hBMSCs. In brief, alginate-GelMA/HA/BMP-2 could increase the hBMSCs’ early transformation of osteoblast lineage and promote the osteogenesis of bone defect, especially the outer hydrogel layer such as Alg70-Gel30 and Alg50-Gel50.
The treatment of bone defects still needs further exploration because of the unsatisfactory clinical outcome. With the increased understanding of tissue engineering and degeneration, polymeric material grafts have been tailored highly biocompatible and widely available so as to reduce rehabilitation time (Rai et al., 2016; Sobolev et al., 2019). Among them, poly-L-lactic acid (PLLA), one of the most applied bioresorbable polymers, opens up a great deal of possibilities in bone substitutes. However, the acidic degradation products released from PLLA may cause an aseptic inflammatory response in bone repair microenvironment and impede bone healing (Kaito et al., 2005). Kandziora et al. (2004) used a fusion cage made of PLLA to treat cervical and lumbar spine diseases. During follow-up, osteolysis occurred around the fusion cage, which is predictive of bone non-union. In order to overcome the shortcoming, several strategies have been designed to modify PLLA, especially the interface between PLLA and adjacent tissues. Based on the potential application in bone engineering, PLLA is usually combined with apatite ceramics, such as hydroxyapatite or tricalcium phosphate, to improve this polymer’s property. The strengthened osteoconductivity and better bone-binding ability provide the conditions for bone regeneration. In vitro experiments showed that the hydrophilicity of the PLLA increased and the cell attachment and proliferation enhanced as well (Szustakiewicz et al., 2021; Tan et al., 2021). All this is possible thanks to the component and microstructural similarity between the apatite ceramics and native bone.
Apatite ceramics can also be doped onto the interface of PLLA, which is called biomineralization. It means inorganic crystal, such as hydroxyapatite (HA), is induced to wrap the organic materials. Simulated body fluid (SBF) is widely applied to develop hydroxyapatite coating over PLLA. However, the interface bonding force between HA and PLLA is relatively poor and may last for several weeks. In order to form a negative charge to bind constituents of HA, the surface of PLLA is always pretreated for hydrolysis of carboxyl group. Therefore, polydopamine coating inspired by mussels’ adhesive mechanism has been introduced as the medium to “fix” HA (Lee, Dellatore, Miller, & Messersmith, 2007). The polydopamine coating is tightly bound to the material surface by the exhaustively repeated 3,4-dihydroxy-L-phenylalanine-lysine motif and is easy to administer in alkaline solutions of dopamine. On the other hand, nanoclusters of HA can be secondarily “grown” on polydopamine films (Tsai et al., 2011), and subsequent studies have further increased the generation rate of HA (Tas and Bhaduri, 2004). Chen et al. (2019) used polydopamine (PDA) to biomineralize electrospinning PLLA fibrous membrane, which was excellent for bone tissue repair. A previous study revealed that an organic–inorganic hybrid coating is able to reduce cytotoxicity and improve cell viability, thus prolonging the time of osteogenesis (Li et al., 2016). Hsu et al. (2020) reported that the composition of chlorine-substituted hydroxyapatite/polydopamine on a titanium-64 surface strengthened the osteointegration in vivo. Nevertheless, even loose inorganic structures are still unsatisfactory for controlled release of growth factors that induce bone formation.
Except for good biocompatibility and mimicking natural extracellular matrices, hydrogel was found to be the superior carrier for growth factors (Liang et al., 2020). Alginate, a natural polymer, includes (1-4)-linked b-D-mannuronic acid and a-L-guluronic acid with good biocompatibility (Drury et al., 2004; Ahn et al., 2021). With the participation of divalent cations (e.g., Ca2+), rapid ionic crosslinking can be achieved in sodium alginate (Ahn et al., 2021). Sodium alginate has been approved by the U.S. Food and Drug Administration (FDA) for medical use, because there is no toxic medium in the sodium alginate gel preparation process (Wang et al., 2020). However, the lack of stem cell adhesion and the uncontrolled degradative kinetics must be addressed (Nair et al., 2020). These defects hampered the proliferation and functionality of the encapsulated cells. Many binding motifs and polymers have been studied, such as matrix metalloproteinase (MMP)-sensitive degradation sequences and collagen, to adjust the compliance with the extracellular matrix (ECM) (Kraehenbuehl et al., 2008; Gregurec et al., 2016). Additionally, a layer-by-layer assembly of chitosan and alginate was applied to modify surface chemistry and expedite the adhesion of human umbilical vein endothelial cells (Silva, Garcia, Reis, Garcia, & Mano, 2017).
Studies have illustrated that modified alginate hydrogels can act as a desired “soil” for the target cells to proliferate and differentiate to the expected phenotypes (Silva et al., 2017; Simo, Fernandez-Fernandez, Vila-Crespo, Ruiperez, & Rodriguez-Nogales, 2017). The gelatin–alginate coating is capable to withstand cyclic compression and even retain proteins entrapped in hydrogel (Pacelli, Basu, Berkland, Wang, & Paul, 2018). Gelatin methacrylate (GelMA), a newly developed photo-crosslinkable hydrogel, has been applied in wound healing and controlled drug release and as a cell culture substrate. For example, Chen et al. (2021) grafted GelMA hydrogel on the surface of expanded nanofiber scaffolds and photo-crosslinked the hydrogel to fit invasive surgery such as laparoscopy and thoracoscopy. Ashwin et al. (2020) made PLLA scaffolds coated with GelMA that were loaded with mucic acid and demonstrated the controlled release of mucic acid and potential capability of osteoblast differentiation. In order to combine gel strength with drug loading performance; achieve better simulation of the biomechanical properties of natural ECM; and improve stem cell adhesion, encapsulation, and differentiation to target phenotypes, a hydrogel coating that is double crosslinked with GelMA and alginate may be a good choice for promoting high-quality bone tissue regeneration.
In consideration of a layer-by-layer (LBL) assembly technique as a successful measurement, it has been explored as an appealing strategy in establishing the multi-functional coating for osteogenesis (Blatchley et al., 2021; Piluso et al., 2021). It could not only regulate local and extended drug release on the surface of PLLA acting as seal barrier but it could also orient the osteogenic differentiation of bone mesenchymal stem cells (BMSCs) and bone formation (Lin, Hsieh, Tseng, & Hsu, 2016; Tsai et al., 2015). Therefore, the aim of this research was to establish a coating to induce osteogenesis of bone mesenchymal stem cells by a combination of alginate and GelMA DN structure for controllable bone morphogenic protein (BMP)-2 release and to check the behavior (adhesion, proliferation, and differentiation) of human bone mesenchymal stem cells (hBMSCs) in the hydrogel platform and its underlying mechanism.
Materials and Methods
PLLA were purchased from Jufukai Biotechnology Co. (Shangdong, China). Sodium alginate, gelatin, dopamine, and Igracure 2959 were purchased from Sigma-Aldrich (St. Louis, MO, United States). Yuanxiang Medical Instrument Co. (Shanghai, China) provided CCK-8 assay kit, alkaline phosphatase (ALP) assay kit, and Dulbecco’s Modified Eagle Medium (DMEM). PCR primers were supplied by Sangon Biotech Co. (Shanghai, China). Total RNA Kit, rhodamine phalloidin, and 4,6-diamidino-2-phenylindole (DAPI) solution were bought from Yeason Biotechnology Co. (Shangdong, China).
Substrate Preparation and Polydopamine/HA Modification
PLLA composite substrate was synthesized according to our previous report (Cao et al., 2012). Substrate films were dried at −30°C for 24 h after being cast in custom-made Teflon molds. Then, these films were divided into small squares (10 mm in length and 1 mm in thickness) and were stored at room temperature. For biomedical use, the substrate was washed in distilled water ultrasonically and then sterilized with gamma irradiation at 25 kGy.
The prepared substrates were dipped into 2 mg/ ml dopamine alkaline solution in which the pH value was adjusted to 8.5 with 10 mmol Tris-HCl buffer. The solution was stirred carefully to ensure sufficient contact with the PLLA substrate for 24 h. Then, these sheets were washed by distilled water three times to get rid of the free dopamine. The polydopamine-modified PLLA membranes were then dried at 40°C before further use.
Biomineralization was performed largely according to a previous study (Zhang, Zhang, Bao, & Chen, 2014). For rapid synthesis of the HA on polydopamine, first, a simulated body fluid solution, which was used to form HA coating, was prepared according to the work of Tas & Bhaduri (2004) and the pH adjusted to 4.0–4.5 prior to the coating procedure. Second, the polydopamine-modified PLLA membranes were dipped in the above solution with a pH value 6.5 for a certain period; finally, these membranes were denoted as PLLA-PDA-HA, respectively.
Preparation of Double-Crosslinked Hydrogel Coatings
Sodium alginate was dissolved in phosphate-buffered saline (PBS) at a certain concentration according to Table 1. GelMA was synthesized according to a previous study (Nichol et al., 2010). Next, freeze-dried GelMA and the photoinitiator (Irgacure 2959, Sigma-Aldrich) were dissolved in the prepared sodium alginate solution in a given proportion. The concentration of GelMA solution was set at 0.5%, 1.5%, 2.5%, 3.57, and 4.5% w/v, respectively. Consequently, BMP-2 (10 μg/ml) was dissolved in the alginate-GelMA solution at 37°C before gel formation. The PLLA-PDA-HA films were dipped into the alginate-GelMA solution for 60 s and withdrawn at a speed of 3,000 rpm for 30 s. The prepared films were dried at room temperature and ionically crosslinked in 100 mM CaCl2 solution for 5 min, following irradiation by UV for 15 s with an OmniCure S2000 UV lamp. Finally, the formed double-crosslinked platform was ultrasonically cleaned and sterilized by ultraviolet irradiation for 30 min before cell experiment. According to various component ratios of hydrogel, the samples were denoted as Alg90-Gel10, Alg70-Gel30, Alg50-Gel50, Alg30-Gel70, and Alg10-Gel90 (Table 1). All of them were kept at 4 C overnight.
The morphology of the prepared samples with predetermined LBL coating was observed by field emission scanning electron microscopy (FE-TEM, HT7700, Japan). Atomic force microscopy (AFM, MFP-3D-BIO, Asylum Research, United States) was applied to observe the microstructure and surface roughness. The chemical structures of the double-crosslinked hydrogel were measured by Fourier transform infrared (FTIR) spectroscopy (PerkinElmer Spectrum Two) in the 400–4,000 cm−1 range. Energy-dispersive spectrometry was performed by EDS (Oxford Instruments, United Kingdom). Surface hydrophilicity is another factor affecting cell attachment, and it was measured by surface water contact angles by a surface roughness meter (Perthometer M1, Mahr, Germany).
Cell Culture and BMP-2 Release
hBMSC line was purchased from the Chinese Academy of Sciences (Shanghai, China). The hBMSCs were maintained in culture with Dulbecco’s Modified Eagle’s Medium with low glucose (Low/DMEM) (HyClone, Tauranga, New Zealand) containing 10% fetal bovine serum (FBS, Gibco, United States). It was supplemented with antibiotics (100 U ml−1 penicillin and 100 μg ml−1 streptomycin) (Gibco BRL) in a humidified incubator with a 5% CO2 atmosphere at 37°C. The medium was changed every 2 days. When the cell density exceeded 85%, the cells were digested with trypsin and passed to the cultured cells in a ratio of 1:3.
The cumulative of BMP-2 release was a representative study on the release of growth factor in this double-crosslinked hydrogel (Niu et al., 2009). Five groups of hydrogels (Alg90-Gel10, Alg70-Gel30, Alg50-Gel50, Alg30-Gel70, and Alg10-Gel90) carrying BMP-2 (10 μg per sample) were put in a 2-ml PBS system (pH = 7.4). The solution stayed in a sustained shaking condition at 120 rpm and 37°C for 14 days. At specified time points, 1 ml of solution was sucked out and an equal volume of PBS was added. The measurement of released BMP-2 from each hydrogel samples was carried out by BCA method. The final cumulative release of BMP-2 (%) was calculated as follows: BMP-2 (%) = (total release of BMP2 / total load of BMP2 in the sample) × 100%).
Cell adhesion is the first step in facilitating osteogenesis in the scaffold. To check the adhesive effect, the GelMA-alginate hydrogel coating films were put into 24-well plates after sterilization by UV. Then, the hBMSCs were seeded in each hole at a density of 5 × 104/hole for 4 h. Cell viability was determined using Cell Counting Kit-8 (CCK-8) assay. The suspension was transferred into 96-well plates to detect absorbance value.
To verify the morphology of the hBMSCs attached on the coating, the GelMA-alginate hydrogel coating films were co-cultured with hBMSCs for 4 h. The films were gently washed to get rid of impurities and were fixed with 4% paraformaldehyde. Then, the samples were successively stained with 50 mg/ml rhodamine phalloidin for 60 min and with DAPI for 5 min at 4°C. Images were captured by confocal microscopy (Olympus, LX81-ZDC, Japan).
For transmission electron microscopy (TEM) detection, hBMSCs were incubated with GelMA-alginate hydrogel coating films for 4 h at 37°C. Subsequently, after fixing with 4% glutaraldehyde, the fixed samples were dehydrated with a gradient concentration of alcohol (from 30% to 99.5%). The films were dried and sputtered with platinum to test by TEM (HT7700, Hitachi, Japan), respectively.
The hBMSCs were seeded on different surfaces of the films at a density of 5 × 104 cells/hole in 24-well plates. The samples were cleaned by PBS and stained with live and dead cells for 5 min at 3 days, respectively. The images were captured with a fluorescence microscope. Quantitation of cell proliferation was performed by the CCK-8 test, and optical density (OD) was measured at 450 nm on a microplate reader.
After seeding hBMSCs for 7 days, the Total RNA Kit was used to extract total RNA of the cells according to the manufacturer’s protocol. Then, the first strand cDNA kits were applied to reverse-transcribe the collected total RNA. Real-time PCR (qPCR) with the Bio-Rad CFX Manager system was performed according to the standard procedure. Amplification was realized by two-step cycling. Melting curves were recorded at a temperature range from 65°C to 95°C. The primers in this study are presented in Table 2.
Alkaline Phosphatase Activity Assay
The hBMSCs were seeded on different surfaces of the films at a density of 5 × 104 cells/hole in 24-well plates until the hBMSCs in each group adhered to the films. Subsequently, the osteogenic medium was prepared consisting of 0.2 mmol/ l ascorbic acid, 100 nmol/ l dexamethasone, and 10 mmol/ l β-glycerol phosphate and applied to the hBMSCs. The medium was changed every 2 days. ALP activity was measured at 4 and 7 days after the use of osteogenic medium by a BCIP/NBT ALP Color Development Kit (Beyotime, China).
Alizarin Red Staining
The samples were incubated for 28 days with osteogenic medium and fixed with 4% paraformaldehyde for 10 min at 4°C. Alizarin red (pH = 4.2) staining was carried out at 25°C. Images were captured by microscopy.
Data were recorded as mean ± standard deviation (SD). Student’s t-test was used for assessing the difference between two groups, while one-way analysis of variance (ANOVA) was used for evaluating the significance among multiple groups. All the statistical analyses were applied with SPSS 13.0 software (SPSS Inc., United States). Differences were regarded significant if p < 0.05.
Results and Discussion
In our research, polydopamine coating is firstly formed on PLLA films in alkaline and weak oxidation environment, which has an affinity for hydroxyapatite (Wu, Zhang, Zhang, & Chen, 2021). Relevant research found that hydroxyapatite grown on the surface of dopamine in simulated body fluid is more uniform and more consistent with the extracellular environment of bone tissues than hydroxyapatite mixed in hydrogel (Li et al., 2016; Z.; Wang, Chen, Wang, Chen, & Zhang, 2016). Meanwhile, the outer-layer alginate/GelMA pairs provide enough strength to contain growth factors. The design has obvious advantages: firstly, the microstructure of hydroxyapatite is helpful for achieving the three-dimension-stimulating bone environment for osteogenic-associated cells to grow in. Secondly, the covering alginate/GelMA DN, acting as a barrier, would be beneficial for sustained release of BMP-2, resulting in extending its biofunction toward hBMSCs in a relatively long term (Hu et al., 2012).
Scanning electron microscopy (SEM) and AFM were used to observe the surface morphology of PLLA substrates. As shown in Figure 1A, the native PLLA displayed a relatively flat surface feature. The synthesis of polydopamine on the PLLA surface formed an eruptive microporous structure. With the assistance of strengthened simulated body fluid, well-aligned and highly ordered HA clusters were gradually constructed onto the PLLA films. The piles of HA cluster increased with the prolonged time of simulated body fluid on the PLLA. The pore diameter of the HA was approximately 1–5 μm and was distributed at regular intervals. After covering the alginate/GelMA DN outer layer in different proportions, the sample surfaces were scattered with various degrees of projections (Figure 1B). As sodium alginate is more viscous than GelMA at the same concentration, the protuberance on substrate surface becomes more obvious as the proportion of sodium alginate in the outer coating decreases.
FIGURE 1. SEM images of (A) synthesis of composite coatings: PLLA, PLLA-PD, PLLA-PD-HA (1 h), PLLA-PD-HA (3 h), and PLLA-PD-HA (6 h) and (B) different ratios of alginate and GelMA. SEM, scanning electron microscopy; PLLA, poly-L-lactic acid; PD, polydopamine; HA, hydroxyapatite; GelMA, gelatin methacrylate.
To measure the distribution of element of the coatings, SEM-EDS was performed for hydrogel analysis. As presented in Figure 2A, the hydrogel coatings displayed largely characteristic C, O, H, and Ca elements. The Ca element was derived from hydroxyapatite. In each group, the amount of Ca was presented ∼3%. Meanwhile, with the increase of GelMA in the outer layer, the peak of C and O element content gradually accumulated, attributing to the substitution of the methacrylic anhydride for the amino groups of GelMA molecules (Table 3). The result of SEM-EDS indirectly manifested the successful coverage of multilayer coating on the PLLA films.
FIGURE 2. (A) SEM-EDS and (B) FTIR spectra for Alg90-Gel10, Alg70-Gel30, Alg50-Gel50, Alg30-Gel70, and Alg10-Gel90. (C) Contact angle measurement of water on the surface of different samples. FTIR, Fourier transform infrared.
To further verify the double-crosslinked hydrogel, FTIR spectra (Figure 2B) showed a similar trend in the hybrid hydrogel composed of GelMA and alginate. The characteristic band peaks of the alginate range of 1,460–1,649 cm−1 correspond to carboxylate ions and those of 935–1,107 cm−1 relate to C–O of the pyranose ring (Golafshan, Kharaziha, & Fathi, 2017; Craciun, Barhalescu, Agop, Ochiuz, & Medicine, 2019). In addition, the spectrum of GelMA consisted of the peak of C=O at 1,630, 1,548, and 1,240 cm−1. The C–N–H at 1,500–1,570 cm−1 could also be recognized. These characters illustrated the reaction of anhydride methacrylate with free amine groups of gelatin (Rahali et al., 2017). The spectrum of Alg90-Gel10, Alg70-Gel30, Alg50-Gel50, Alg30-Gel70, and Alg10-Gel90 presents broad band peaks at 1,621 and 1,557 cm−1 probably because of overlapping with the functional groups of the GelMA and alginate composition, implying the successful introduction of the double-crosslinked hydrogel on the surface of PLLA sheets. Moreover, it semi-quantitatively analyzes specific reference bands of functional groups according to the two components of the coatings, which were less affected by the chemical reaction.
Hydrophilicity is another necessary requirement for the osteoblast-related cells to access bone tissue implants (Oliveira et al., 2021). Figure 2C displays the water contact angles on the surfaces of the substrate and customized coatings, of which, native PLLA showed a contact angle of 101.40°, while mineralization showed an obviously hydrophilic contact angle of 68.12°. After incorporation of hydrogel, there was a further decrease of contact angle to 51.86°–44.24°. In addition, various proportions of hydrogel components did not affect the change of the contact angle. The result may reflect the corresponding deposition of alginate-GelMA/HA bilayers. The hierarchical microstructure may promote hydrophilicity in a progressive behavior, which has a capillary function to facilitate the drop spreading and coincides with a previous report (Xing et al., 2020). These results demonstrate the successful construction of alginate-GelMA/HA bilayer coating on the PLLA films.
Cell Viability, Attachment, and Proliferation
Cell adhesion, growth, and differentiation are dependent on the degree of biocompatibility. To evaluate the cytotoxicity of the coated samples, the survival rate of cells on the coating surface of each group was determined at the same magnification by staining with dead cells on the third day (green dot: live cells; red dot: dead cells) (Figure 3A). Cell viability was assessed by fluorescence microscopy. Although the proportion of dead cells increased slightly in the PLLA group, there were no significant dead cells in each group, indicating that the bilayer coatings in each group had good biosafety and provided an appropriate growth environment for hBMSCs (Figure 3B). It is remarkable, however, that there were fewer viable cells in the native PLLA films than in the coatings, which may result in short-term cell adhesion and relative long-term cell proliferation.
FIGURE 3. (A) Cell viability of human bone mesenchymal stem cells (hBMSCs) on the different samples (scale: 50 μm) and (B) statistical analysis. (C) The short-term cell adhesion at hour 2 and (D) cell proliferation at days 1, 3, and 7 on the PLLA and bilayer coatings (*p < 0.05 compared with the control).
After seeding the cells on the samples for 2 h, quantification was performed to measure the cell attachment according to a previous study (Zhang et al., 2018) (Figure 3C). Notably, the bilayer coatings facilitated the cells adhering on the substrate rather than the bare PLLA film. The OD values of CCK-8 had nearly identical results in the Alg90-Gel10, Alg70-Gel30, Alg50-Gel50, Alg30-Gel70, and Alg10-Gel90 groups, but were higher than those in the PLLA group. To further evaluate the proliferation of cells in each samples, the number of live hBMSCs was measured by CCK-8 test on days 1, 3, and 7 (Figure 3D). Cell numbers increased in all groups, indicating that not only all the bilayer coatings but also the native PLLA provided a suitable microenvironment for cell growth. There were no differences in hBMSCs among the groups on the first day. The proliferative rate in the bilayer groups began to present higher than that in the PLLA alone on day 3. Finally, on day 7, the cell proliferation in the Alg70-Gel30 and Alg50-Gel50 groups did an outstanding performance than that in the other five groups, among which the cell growth of the Alg90-Gel10, Alg30-Gel70, and Alg10-Gel90 groups was far superior to that of the PLLA group. These results illustrated that the double-crosslinked hydrogel combined with HA has the advantage to attract osteoblast-related cells more rapidly to adhere to the surface of the substrate.
Additionally, the function of hBMSCs corresponds with a well-ordered morphology. Immunofluorescence detection at hour two showed the intracellular microstructure on the surface of the PLLA sheet and bilayer coatings in different proportions. The cytoskeleton was stained with rhodamine-labeled phalloidin, and nuclei were stained with DAPI by confocal microscopy (Figure 4A). Most of the hBMSCs that adhered to the PLLA film seemed spherical, while the cells on the bilayer coatings had many obvious cytoskeleton/microfilaments, as well as clear intercellular connections. Particularly, a better directional rearrangement of the cell cytoskeleton was displayed in the Alg70-Gel30 and Alg50-Gel50 groups.
FIGURE 4. (A) Confocal microscopy images of hBMSCs on different groups at 2 h (red, rhodamine phalloidin; blue, DAPI for nucleus) (scale: 15 μm). (B) SEM images of hBMSCs in different groups at 3 days.
To avoid the interference of fluorescence on cell microstructure, SEM was applied to observe the activity of cells on the coating after 3 days of seeding on the samples (Figure 4B). At higher magnification, there were a few hBMSCs on the surface of the native PLLA, and their morphology tended to be elongated. Intercellular connections between cells were not detected. Cells in the Alg90-Gel10 and Alg10-Gel90 groups began to develop a typical fusiform shape and clearly extend their pseudopods, but the cell size was smaller and the intercellular filaments were still not as clear. In the Alg70-Gel30, Alg50-Gel50, and Alg30-Gel70 groups, we found a longer irregular fusiform structure; the pseudopods were normal size, and the number of cells on the surface of the material increased significantly. For the Alg70-Gel30 and Alg50-Gel50 groups, the extended microstructure with some cell–cell interactions was easy to observe, and the pseudopods tended to extend to the microspores in multiple directions. These results showed that the adhesion and migration of hBMSCs in the Alg70-Gel30 and Alg50-Gel50 groups were significantly better than those in other double-crosslinked coatings, especially in the PLLA group.
Sustained Release of BMP-2 and Expression of Gene
Figure 5A shows an in vitro BMP-2 release curve from different ratios of double-crosslinked hydrogels. All the hydrogel systems displayed a sustained release for 2 weeks. In the first 2 days, the release curve of each group showed a relatively steep but not a burst release. The next 5 days, all the groups exhibited a “plateau” release curves and then entered a process of steady and moderate release. The total BMP-2 release of Alg90-Gel10, Alg70-Gel30, Alg50-Gel50, Alg30-Gel70, and Alg10-Gel90 reached 74.08%, 57.12%, 52.84%, 67.81%, and 71.64%, respectively. Then, the additional release of BMP-2 was less than 10%. Since the BMP-2 was kept inside the hydrogel, it is helpful for hBMSCs and osteoblasts attached or grown into the coatings to proliferate, differentiate, and induce bone formation. Moreover, the results seemed to show the higher crosslinking hydrogel as a barrier against growth factor release. On 2 weeks, the BMP-2 loading capacity of five samples was 18.44%, 29.65%, 38.64%, 27.55%, and 22.70%, respectively, and the drug encapsulation efficiency of Alg50-Gel50 hydrogels was 20.20% and 16.94% higher than that of the Alg90-Gel10 and Alg10-Gel90 groups.
FIGURE 5. (A) Release curves of BMP-2 from different double-crosslinked hydrogels. The mRNA levels of (B) BMP-2, (C) OCN, (D) RUNX-2, and (E) OPN were quantified from hBMSCs cultured in various substrates (*p < 0.05 compared with the control).
The differentiation of hBMSCs toward osteoblast lineage could be valued by specific osteoblast mRNA expression. The expression of the four osteogenic-related genes (RUNX-2, BMP-2, OCN, and OPN) was detected by RT-PCR experiments on day 14 (Table 3). The cells cultured on PLLA films in DMEM were set as negative control for each experiment, which failed to extract osteogenic-specific genes. In the positive control group, an osteogenic medium, which replaced DMEM, was used to culture hBMSCs on PLLA films. We detected osteogenic-specific gene expression in the positive control group that we treated as reference for other groups. By the 14th day, the expression levels of RUNX-2 and BMP-2, which are the markers of early osteoblast differentiation and bone formation, was higher in the Alg70-Gel30 and Alg50-Gel50 groups than in other bilayer coatings. Meanwhile, the expression of OCN and OPN, which represents late osteogenic formation, showed a similar trend (Figure 5).
To reveal the sustained promotion of osteogenesis of hBMSCs on the coatings, alkaline phosphatase staining was applied to detect ALP expression. After hBMSCs were seeded on the surface of different double-crosslinked coatings and constantly induced with osteogenic medium, the staining was carried out on day 4 and day 7 (Figure 6A). From the perspective of density, the samples in the Alg70-Gel30 and Alg50-Gel50 groups are more deeply stained compared with the other coating groups and the PLLA group. It indicates that early-stage differentiation could occur in Alg70-Gel30 and Alg50-Gel50 bilayer coatings. To accurately depict the early osteogenesis in these groups, the ALP activity was used in quantification. The ALP expression activity in each group enhanced as the time went on. Among them, the highest was in the Alg70-Gel30 and Alg50-Gel50 groups, which coincided with the result of staining (Figure 6C).
FIGURE 6. (A) ALP staining at 4 and 7 days (scale: 100 μm). (B) Alizarin red staining images at 28 days (scale: 100 μm). Quantitative results of (C) ALP activity and (D) Alizarin red staining (*p < 0.05). ALP, alkaline phosphatase.
At the end stage of osteoblast differentiation, the formation of mineralized nodules is a crucial phenomenon that indicates the maturation of osteoblasts. To evaluate this, Alizarin red staining was used to quantify the degree of mineralization by measuring the number of calcium nodules (stained red spots). Alizarin red staining was conducted on day 28 (Figure 6B). The Alg70-Gel30 and Alg50-Gel50 groups had significantly more nodules compared to every other groups (Figure 6D). The poor performance of mineral nodules in the PLLA group may result from the lack of BMP-2 release “barrier layer.” In consideration of the controlled release of BMP-2 in the hydrogel layer, long-term osteogenic differentiation of hBMSCs can be sustained, which probably has a key role in the formation of mineralized nodules (Feng et al., 2019). In addition, the crosslinked layer of hydrogels provides suitable biological strength for cell adhesion, infiltration, and proliferation (Zhang et al., 2018). In brief, double-crosslinked coating/HA could promote the greatest amount of osteogenesis, especially the outer hydrogel layer such as Alg70-Gel30 and Alg50-Gel50.
In this research, we established a bilayer coating with double-crosslinked hydrogels (alginate-GelMA) containing BMP-2 proteins (alginate-GelMA/HA/BMP-2), which displayed great biocompatibility and osteogenesis. The characterization of the coating improved the properties and enhanced the wettability of the native PLLA. To evaluate the biosafety and inductive ability of osteogenesis, the behavior (viability, adherence, and proliferation) and morphology of hBMSCs on the bilayer coatings were tested by multiple exams. The satisfactory function of osteogenesis was verified in bilayer coatings, especially in the specific ratio of alginate to GelMA. We found the best ratios between GelMA and alginate for biological applications. The Alg70-Gel30 and Alg50-Gel50 groups facilitated the osteogenic transformation of hBMSCs. In brief, alginate-GelMA/HA/BMP-2 could increase the hBMSCs’ early transformation of osteoblast lineage and promote the osteogenesis of bone defect, especially the outer hydrogel layer such as Alg70-Gel30 and Alg50-Gel50.
Data Availability Statement
The original contributions presented in the study are included in the article/Supplementary Material, and further inquiries can be directed to the corresponding authors.
YM and YY made the same contribution to this work. All authors contributed to the article and approved the submitted version.
This study was funded by the Shanghai “Rising Stars of Medical Talent” Youth Development Program (Shanghai Municipal Health Commission 2019–72) and the Shanghai Sailing Program (No. 18YF1404400).
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.
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Keywords: hydrogel coating, gelatin methacrylate (GelMA), alginate, double crosslink, mesenchymal stem cells
Citation: Ma Y, You Y, Cao L, Liang B, Tian B, Dong J and Lin H (2021) Improved Osteogenesis by Mineralization Combined With Double-Crosslinked Hydrogel Coating for Proliferation and Differentiation of Mesenchymal Stem Cells. Front. Bioeng. Biotechnol. 9:706423. doi: 10.3389/fbioe.2021.706423
Received: 07 May 2021; Accepted: 06 October 2021;
Published: 30 November 2021.
Edited by:Jingxiao Chen, Jiangnan University, China
Reviewed by:Sanjun Shi, Chengdu University of Traditional Chinese Medicine, China
Guofeng Luo, Hebrew University of Jerusalem, Israel
Copyright © 2021 Ma, You, Cao, Liang, Tian, Dong and Lin. 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.