PubMed · 11731302
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G Szekely. 2001. Soft tissue deformation.. https://doi.org/10.1016/s1361-8415(01)00054-8
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Precise control over scaffold material, porosity, and internal pore architecture is essential for tissue engineering. By coupling solid free form (SFF) manufacturing with conventional sponge scaffold fabrication procedures, we have developed methods for casting scaffolds that contain designed and controlled locally porous and globally porous internal architectures. These methods are compatible with numerous bioresorbable and non-resorbable polymers, ceramics, and biologic materials. Phase separation, emulsion-solvent diffusion, and porogen leaching were used to create poly(L)lactide (PLA) scaffolds containing both computationally designed global pores (500, 600, or 800 microm wide channels) and solvent fashioned local pores (50-100 microm wide voids or 5-10 microm length plates). Globally porous PLA and polyglycolide/PLA discrete composites were made using melt processing. Biphasic scaffolds with mechanically interdigitated PLA and sintered hydroxyapatite regions were fabricated with 500 and 600 microm wide global pores. PLA scaffolds with complex internal architectures that mimicked human trabecular bone were produced. Our indirect fabrication using casting in SFF molds provided enhanced control over scaffold shape, material, porosity and pore architecture, including size, geometry, orientation, branching, and interconnectivity. These scaffolds that contain concurrent local and global pores, discrete material regions, and biomimetic internal architectures may prove valuable for multi-tissue and structural tissue interface engineering.
The fibril reinforced poroelastic models have been found successful in describing some mechanical behaviors of articular cartilage in unconfined compression that were not understood previously, including the strong and nonlinear transient response, the strain-magnitude and strain-rate dependent cartilage stiffness and the depth-varying stresses and strains. It has been demonstrated that a better description for the mechanical behavior of cartilage is obtained by introducing a fibrillar matrix into a poroelastic model, in addition to the nonfibrillar matrix and water. This paper reports the development of the nonlinear fibril reinforced homogeneous and nonhomogeneous models and further explores the potentials of the models for investigation of cartilage mechanical response. Some comments are made in regard to further applications of the models and improved accuracy of the material representation.
There is a clinical need for the tissue engineering of a small diameter blood vessel substitute. Ideally such a vascular substitute should possess the functional attributes of the native vessel which it will replace. This means not only having the appropriate mechanical properties, but also being non-thrombogenic and exhibiting vasoactivity. In each of these there is in some way a role of mechanics. For thrombogenicity, an "endothelial-like" lining is required, one which is responsive to its mechanical environment in a manner similar to that of the normal vascular endothelium. If vasoactivity is exhibited, then this lining must also serve as a signal transduction interface, communicating with the underlying smooth muscle cells which themselves must be of a contractile phenotype if they are to carry out the biomechanical function resulting in contraction and dilation. Having appropriate mechanical properties means not only exhibiting sufficient strength, but also a viscoelasticity which allows for a compliance that matches that of the vascular system into which the vascular substitute is to be placed. Finally, once implanted the biological responses which will occur at least in part are regulated by biomechanical factors. Thus, the proper incorporation of biomechanics into the design of a vascular substitute is critical to achieving success.