Biomedical Engineering Reference
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Figure 9.7
(a) Scaffold implanted into intervertebral disc. (b) Harvested motion
segment; PCL-TCP scaffold
þ
rhBMP-2 show bone overgrowth. (c) Re-
constructed m-CT images of scaffold
þ
rhBMP-2 and autograft bone.
(d) Representative histological sections (sagittal view) of explant. Note
the fairly well aligned columns of trabecular bone formed in scaf-
fold
þ
rhBMP-2 implant group.
Adapted from Abbah et al.
68
.
20 mm ulnar segmental defects in rabbits. Groups consisted of PCL scaf-
folds, PCL-fibrin scaffolds, and animals with empty defects serving as
controls. At 1, 2 and 3 months post-implantation, the explanted tissue-
scaffold constructs were analysed with X-ray radiograph imaging, m-CT
imaging and histological H&E staining.
69
Three months post-implantation,
all control groups showed minimal bone formation, whilst in PCL-BMSCs-
BMP2 treatment groups defect bridging was already apparent 2 months
post-implantation, with complete defect bridging achieved at 3 months
post-implantation. PCL-BMP2 and PCL-BMSCs treatment groups indicated
defect bridging only after 3 months post-implantation. This study indicated
that combinations of BMSCs and BMP-2 with PCL scaffolds can enhance
bone healing ecacy.
69
This supports the general opinion that a combin-
ation of scaffold, bioactive molecules and cells will provide the most ther-
apeutically ecacious constructs.
Reichert et al.
70
explored a combination of MSCs or rhBMP-7 with PCL-
TCP (80 : 20) scaffolds in comparison to autologous cancellous bone grafts
(ABG). MSCs and rhBMP-7 were loaded onto the scaffolds using platelet rich
plasma (PRP) and bovine collagen type I as carrier matrices, prior to im-
plantation into 3 cm mid-diaphysial tibial segmental defects using an ovine
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