In nerve injuries, the proximal and distal nerve stumps are often prevented from direct realignment of nerve fascicles due to the lesion site 1-2. Normally, axon tracts are composed of highly ordered and aligned bundles of axons, which form complex networks of connectivity. However, nerve regeneration is a chaotic process due to poorly organized axon alignment 3-4. Therefore, to generate a sufficient number of regenerating axons that bridge the lesion site, it is necessary to induce well organized axonal alignment. Additionally, demyelination accompanies nerve injuries due to death of the myelinating cells at the injury site. Since demyelination strongly impairs the conductive capacity of surviving axons, treatments targeting demyelination or promoting remyelination are significant for functional recovery after nerve injury 5. Thus the goal of this protocol is to illustrate an engineering approach that addresses these two issues of nerve regeneration.
Surface anisotropy, which is defined as a difference, when measured along different axes, in a material's physical or mechanical properties, has been applied to influence cell alignment, growth, and migration 6-7. In addition to topography, there are other methods to induce anisotropy. Previously, we investigated surface anisotropy induced by mechanical static pre-stretch of poly-dimethyl-siloxane (PDMS) membrane. The theory of "small deformation super imposed on large" predicted that the effective stiffness the cells sense in the stretched direction differs from the perpendicular direction, and this difference in effective stiffness is due to surface anisotropy 8. Mesenchymal stem cells (MSCs) cultured on a pre-stretched PDMS membrane are able to sense the anisotropy by actively pulling the surface and as a result, align in the pre-stretched direction 9. Similarly, an anisotropic surface arising from a mechanical pre-stretched surface affects the alignment, as well as growth and myelination of dorsal root ganglion (DRG) axons 10. Here we provide a protocol for inducing surface anisotropy on a static pre-stretched PDMS substrate to enhance axon regeneration 10.
To elicit axon alignment, topological features with desired patterns, reported to provide contact guidance through aligned fibers and channels 6,11-12, were demonstrated to facilitate axon alignment 11,13. However, reported techniques for inducing axon alignment through topological features, such as fibers, channels and patterning, were unable to lengthen and increase the thickness of the axons. In contrast, gradual mechanical stretching led to axon alignment in the stretch direction with longer and thicker axons that increased with the magnitude of the stretch 14. However, incorporating a powered motor device in vivo is not feasible. In contrast, static pre-stretched induced anisotropy is less complicated and can be more readily incorporated into future scaffold designs for in vivo applications.
In this protocol, a static pre-stretched cell culture system is used to induce surface anisotropy without topological features. The pre-stretched culture system is composed of a PDMS membrane, a stretchable frame and a stretching stage, whereupon the membrane is fixed onto the frame and a predetermined stretch magnitude is applied on the stretching stage. Freshly isolated DRG neurons cultured on the pre-stretched surface for up to 21 days are monitored for axon alignment and thickness. Subsequently, Schwann cells (SCs) co-cultured with the aligned axons are monitored for myelination. By incorporating pre-stretch induced surface anisotropy we were able to enhance cell alignment-differentiation and axon alignment-growth of MSCs and DRG neurons 9-10, respectively.