The current treatments for cartilage loss include autologous chondrocyte transplantation procedure, arthroscopic lavage and debridement, the subchondral bone microfracture technique, and osteochondral allograft. These procedures may relieve the symptoms temporarily, but are often associated with problems such as donor site morbidity, loss of chondrocyte phenotype during in vitro expansion, fibrocartilage formation, and cartilage degeneration. As stated previously, iPSCs are free of ethical issues because they are obtained from reprogrammed somatic cells, yet resemble ESCs in their multipotency and selfrenewal capacity. Diverse strategies have been employed to optimize the in vivo and in vitro chondrogenic induction of the two cell types, including direct differentiation via EB formation, high-density micromass induction, and co-culture with chondroprogenitor cells. The high-density micromass method displayed a chondrogenic efficacy superior to that of direct plating of EBs, which is in agreement with the classic pellet method for chondrogenic induction of BMSCs or expansion of chondrocytes in vitro. This superiority is possibly due to the chondrogenic differentiation of ESCs being a context-dependent process and enhanced by 3D-culture systems, such as the pellet and high-density micromass systems. Such 3D systems facilitate interactions between cells as well as between cells and the matrix, simulating the development of limb buds in which chondrogenesis is induced following condensation and consolidation of mesenchymal stem cells. An effective cell therapy for cartilage defects requires support from biomaterials or scaffolds. In the restoration of tissue defects, scaffolds can deliver cells or growth factors, provide a structure to which cells can attach and form tissue, and promote cell growth into the implant, both in vitro and in vivo. These properties account for the superiority of scaffolds over plating cultures or 2D systems in terms of tissue structure restoration and function. Furthermore, 3D systems with a fiber-deposited structure are superior to structures with a compress-molded feature or homogenous material. Additionally, such scaffolds composed of randomly aligned fibers with evenly distributed diameters of hundreds of nanometers to several microns are readily fabricated by electrospinning methods. In the in vitro chondrogenic induction experiment the levels of chondrogenic markers were notably elevated in the scaffold group. This could be attributed to the unique properties of nanofibrous scaffolds; i.e., their high porosity and specialized surface area that degraded over 2 months. These features facilitate cartilage restoration as this is an ongoing process requiring an extended period of time. Scaffold biocompatibility can also be affected by its components. Scaffolds composed of synthetic materials such as PLGA, PCL, or PLLA may have better mechanical properties but low biocompatibility. Alternatively, natural materials such as gelatin, collagen, or fibrin are more biocompatible but less mechanically supportive. A combination of the two types of material could create a bioscaffold with a balanced profile. SEM images Y-27632 showed cell attachment to the scaffold surface. Compared with cells in natural cartilaginous tissue, the cells cultured on a scaffold with nanofibrous structure displayed different morphological features characterized by protrusions stretching along the fibers. The chondrogenically induced iPSCs were attached to the scaffolds either in the form of clusters or were present individually separated by space, although seeded at a high density. A portion of the cells moved into the spaces between the fibers.