Spinal cord injury repair is a complex and challenging problem that will require a combinatorial treatment strategy involving, for example, the use of cells and a biomaterial to provide a favorable microenvironment for transplanted cell function and axon regeneration at the site of injury. Hemisection1,2,3,4,5,6,7,8,9 and complete transection10,11,12,13,14,15,16,17,18,19,20,21,22 models are frequently used to assess the effects of biomaterial-based bridging therapies. The advantage of using a hemisection model is that it provides more stability for the bridging construct compared to complete transection. However, in hemisection models, it is difficult to prove axon regeneration as an outcome of the applied therapeutic method due to the presence of spared tissue. The complete transection model is the most rigorous method to demonstrate axon regeneration.
Various natural and synthetic materials have been studied for use as an injectable gel, a pre-formed gel placed in contusion or hemisection models, or as a structured conduit into hemisection or complete transection models (detailed in the reviews23,24,25). In situ gelling of an injectable matrix/SC mixture creates a more permissive interface between the transplant and the host cord for axon crossing26,27 compared to pre-gelled matrix/SC implants5,18,19,28. In situ gelling allowed the matrix to contour around the irregular host interfaces whereas a more rigid and structured conduit or a less moldable pre-formed gel could not. A structured conduit often provides contact guidance and implant stability in contrast to an injectable matrix. The protocols presented here describe a surgical procedure that takes advantage of both an injectable basement membrane matrix (e.g., matrigel, see the Table of Materials, referred to as injectable matrix here) and a structured conduit to evaluate axon regeneration in the most rigorous spinal cord injury model.
Electrospun poly-vinylidenedifluoride-trifluoroethylene (PVDF-TrFE) aligned fibrous hollow conduits are used in our experimental approach. PVDF-TrFE is a piezoelectric polymer that generates a transient charge when mechanically deformed and has been shown to promote neurite extension and axon regeneration both in vitro29,30 and in vivo31. Electrospinning is a common scaffold fabrication method that can rapidly produce reliable fibrous scaffolds using a variety of polymers with controllable properties such as fiber alignment, fiber diameter, and thickness of the scaffold for neural and other applications32,33,34.
Numerous studies of rat SCs transplanted into spinal cord injury sites have demonstrated treatment efficacy5,9,18,19,20,21,26. These transplants are neuroprotective for tissue surrounding the lesion, reduce lesion cavity size, and promote axon regeneration into the lesion/transplant site and myelination of the regenerated axons. Human SCs can be autologously transplanted, an advantage when compared to most other neural-related cells24. After a peripheral nerve biopsy, SCs can be isolated and purified and will proliferate to the desired amount for transplantation into humans. Autologous SC transplantation for spinal cord injured patients has been proven to be safe in Iran35,36,37,38, China39,40, and the United States41,42. SCs are known to secrete numerous neurotrophic factors and extracellular matrix proteins important for axon growth and to play an essential role in axon regeneration after peripheral nerve injury. Our goal here is to describe methods which can investigate conduit designs to improve the outcome of SC transplantation in a complete rat spinal cord transection model.