The restoration of full-thickness cartilage defects with BMSCs and TGF-beta 1 loaded PLGA/fibrin gel constructs
Introduction
The arthritis is mostly caused by cartilage deficiency. The injured cartilage can hardly repair automatically and lead to further degeneration. Some conventional methods such as debridement, microfracture, osteochondral grafting and autologous chondrocytes implantation (ACI) are thus developed and used in clinic [1]. As an alternative treatment, tissue engineering has been demonstrated a promising approach to restore the cartilage defects too. The success of this technique relies critically on the seed cells and scaffolds and thereby the structure and functions of the regenerated cartilage.
Among the various scaffolds used, the hybrid scaffold prepared by filling soft hydrogel into hard sponge is very promising for the cartilage regeneration since their advantages can be maintained while the shortcomings can be avoided [2], [3], [4], [5], [6]. Apart from the more even distribution of cells and maintenance of the cell phenotype, bioactive factors such as functional genes and growth factors are conveniently loaded into the filled hydrogel with preserved bioactivity. These factors are known to regulate the proliferation and differentiation of the seed cells, which is particularly important when stem cells are used. Actually, the use of stem cells, in particular the bone mesenchymal marrow stem cells (BMSCs) has a lot of advantages over the autologous chondrocytes, and has achieved great success in cartilage and bone repair [7], [8], [9], [10]. Particularly, both the cartilage and bone can be simultaneously repaired when the BMSCs are used, and result in better remodelling and integration with the host surface zone [11], [12].
It is known that differentiation of the BMSCs requires suitable stimuli, which can be achieved with a large variety of different growth factors. Transforming growth factor-β1 (TGF-β1) is one of the most powerful growth factors and is routinely used to induce BMSCs to chondrocytes in vitro. There are two ways to construct the hybrid scaffold which has the ability to regulate the stem cell differentiation in vivo: direct loading of the growth factors, and loading of functional genes encoding the growth factors. In a previous study, plasmid DNA encoding TGF-β1 was loaded into the fibrin gel filled poly(lactide-co-glycolide) (PLGA) sponge. In vivo experiment demonstrated that the cartilage defects were successfully restored in the rabbit knees [13]. However, the safety of the gene therapy still remains a big concern, especially for a long term application. In contrast, the biofunctions and biosafety of the growth factors are more definite with a limited function time.
In this study, recombinant protein TGF-β1 is encapsulated into the fibrin gel and then filled into the PLGA sponges to obtain a composite construct for articular cartilage repair in vivo. Attention is paid to the in vivo degradation of the PLGA and fibrin gel, the function of the fibrin gel on the cartilage repair, and the overall repair effect by the composite constructs.
Section snippets
Materials
PLGA with a copolymer ratio of 75/25 (lactide/glycolide) was purchased from China Textile Academy. Its weight-average (Mw) and number-average (Mn) molecular weights were 154 kDa and 76 kDa respectively. The fibrinogen was isolated from fresh human plasma (the Blood Centre of Zhejiang Province of China) by a freezing–thawing cycle [14].
Dulbecco’s modified Eagle’s medium (DMEM) and fetal bovine serum (FBS) were obtained from Gibco. Millipore water was used throughout the study. All other reagents
Properties of the hybrid scaffold
The PLGA sponges used in this work was prepared by a porogen leaching method using gelatin spheres with a size of 280–450 μm as the porogen (Fig. 1a). The PLGA sponges had an average pore diameter of 350 μm calculated from one hundred pores on the SEM images (Fig. 1b). Fig. 1b shows also the even distribution of the pores and good interconnectivity in the sponge. Besides the big pores, there are small pores on the pore walls, which were formed by thermally induced phase separation during the
Discussion
It is being a primary focus to develop reliable approaches for the repair or regeneration of damaged articular cartilage in orthopaedic [23], [24], [25], [26], [27], [28]. Tissue engineering and regenerative medicine has shown its great promise in this regard by implantation of 3D constructs, loaded with either chondrocytes or stem cells. In this study, PLGA/fibrin gel/BMSCs constructs loaded with TGF-β1 were fabricated and used to repair the articular cartilage defects in a rabbit model (
Conclusion
Herein a composite construct of PLGA/fibrin gel/BMSCs/TGF-β1 was designed and manufactured for osteochondral restoration, whose biological performance was evaluated in a rabbit model. The PLGA sponge degraded much faster in vivo than in vitro, but was still remained after implantation in rabbit knees for 12 wk. Moreover, the fast released fibrin gel in vitro could be still detected after 12 wk in vivo. Transplantation of the TGF-β1 absent constructs into full-thickness cartilage defects of
Acknowledgements
This study is financially supported by the Natural Science Foundation of China (20934003), the Science Technology Program of Zhejiang Province (2009C14003), Ph.D. Programs Foundation of Ministry of Education of China (20090101110049), the Major State Basic Research Program of China (2005CB623902), and the National High-tech Research and Development Program (2006AA03Z442).
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2020, Acta BiomaterialiaCitation Excerpt :Poly(lactic acid) (PLA) and poly(lactic-co-glycolic acid) (PLGA) are also widely used in the medical field, as both are biocompatible, with good mechanical properties, with PLGA having a much faster degradation rate than PCL [54–56]. They have been used for drug/ growth factor delivery, as porous scaffolds [49,57–59] and can be 3D printed [60]. One drawback of PLA/PLGA materials, however, is that their melting temperatures are much higher than PCL (~130 °Celsius for PLGA and ~180 °Celsius for PLA), which can render the co-printing of live cells with PLA/PLGA a challenge.