Tailor-Made and Biodegradable Vascular Scaffolds - Microsurgery: Advances, Simulations, and Applications - page 289

We chose PLCL in terms of bioactivity [43] and mechanoactivity
[44] for future application in vascular tissue engineering. Initially,
we tried to assemble MSPs around the cylindrical surface by using a
cylindrical bar magnet. However, theoretically it is almost impossible
to generate a uniform magnetic ield all over the surface, especially
if its axial length becomes longer than 1 cm. When we consider the
application in vascular tissue engineering, this method of winding
a sheet with use of MSPs will be the better way to control the pore
layout and porosity inside a small-diameter vascular graft.

a) b)

5 mm

5 mm

Figure 8.26 (a) PLCL tubular scaffold with porous structure all over the
inner surface (b) PLCL tubular scaffold with polka-dot pattern
of pores.
So far, straight cylindrical vascular grafts have been fabricated by
electrospinning [25, 26, 43, 44] or excimer laser ablation. In the case
of electrospinning, it is very dificult to control pore layout to the axial
direction. In the case of excimer laser ablation, they spent 8 hours to
fabricate a 2 cm-long vascular graft. Compared with these methods,
our method can create patterned porous coniguration in 2D plane
by use of patterned magnetic ield and 2D sheets can be easily rolled
to tubes in a short time regardless of tube size (total fabrication time
<4 hours). The maximum axial length and minimum inner diameter
available by this method are 4 cm and 1 mm, respectively.

8.7.6 Cell Culture for Confirmation of Biocompatibility

and Safeness of Fabrication Methods

8.7.6.1 General cell culture
A humidiied incubator at 37 ° C and 5% CO 2 was used for cell culture.
HUVECs were cultured on plastic culture dishes in Humedia-EG2.
Sub-conluent cells were washed in PBS and detached from dishes