laminin/YIGSR collagen fibres (θ, 100–150 µm) |
rat sciatic |
15 mm |
eight weeks |
laminin/YIGSR coated fibre groups significantly increased axonal density versus uncoated fibres. |
Itoh et al. [44] |
2000 × collagen filaments (θ, 20 µm) |
rat sciatic |
20 mm |
four, eight weeks |
critical gap bridged. No significant difference versus autograft at eight weeks. |
Yoshii & Oka [45] |
80 × laminin-coated collagen fibres (θ, 50 µm)/sponge |
canine peroneal |
80 mm |
12 months |
no significant difference in nerve regeneration or functional recovery seen between groups. |
Toba et al. [46] |
various densities of PLLA (θ, 40–100 µm) microfilaments |
rat sciatic |
10, 14, 18 mm |
10 weeks |
high filament densities inhibited nerve regeneration. Low filament densities increased nerve regeneration. |
Ngo et al. [47] |
2000 × PGA (θ, 14 µm) filaments |
dog sciatic |
30 mm |
six months |
critical gap bridged with similar functional recovery to autograft. |
Wang et al. [48] |
collagen gel |
rat peroneal |
15 mm |
12 weeks |
a critical nerve gap bridged without the addition of neurotrophic factors. |
Lee et al. [49] |
1/3 PAN-MA fibrous film configurations (θ, 400–600 nm). |
rat tibial |
14 mm |
six, 13 weeks |
functional nerve regeneration was significantly greater in the 1 film conduit versus that of the 3 film conduit. |
Clements et al. [39] |
fibrous (θ, 2–20 µm) keratin hydrogel |
mouse tibial |
4 mm |
six weeks |
keratin group showed significantly greater conduction delay than autograft group. |
Sierpinski et al. [50] |
1000 × PLGA fibres (θ, 14 µm) + MSCs |
dog sciatic |
50 mm |
six months |
critical gap bridged. Functional recovery significantly greater than a hollow conduit and less than autograft. |
Ding et al. [51] |