Abstract
With the goal of mimicking the mechanical properties of a given native tissue, tissue engineers seek to culture replacement tissues with compositions similar to those of native tissues. In this report, differences between the mechanical properties of engineered arteries and native arteries were correlated with differences in tissue composition. Engineered arteries failed to match the strengths or compliances of native tissues. Lower strengths of engineered arteries resulted partially from inferior organization of collagen, but not from differences in collagen density. Furthermore, ultimate strengths of engineered vessels were significantly reduced by the presence of residual polyglycolic acid polymer fragments, which caused stress concentrations in the vessel wall. Lower compliances of engineered vessels resulted from minimal smooth muscle cell contractility and a lack of organized extracellular elastin. Organization of elastin and collagen in engineered arteries may have been partially hindered by high concentrations of sulfated glycosaminoglycans. Tissue engineers should continue to regulate cell phenotype and promote synthesis of proteins that are known to dominate the mechanical properties of the associated native tissue. However, we should also be aware of the potential negative impacts of polymer fragments and glycosaminoglycans on the mechanical properties of engineered tissues.
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Acknowledgments
This work was funded by NIH R-1 HL63766. The authors wish to thank Jay Humphrey for discussions about stress concentrations.
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Appendix
Appendix
Calculation of Stress Concentrations Caused by Polymer Fragments
At the suture line, regions of densely packed PGA fragments (e.g., circled area in Fig. 4) were approximated as a single circular stress concentration in the vessel wall. The behavior of this stress concentration during mechanical testing was assumed to be analogous to a void within a plate being pulled in tension.3
To calculate the maximum local stress seen by engineered tissue bordering a polymer “void,” vessel wall thickness, h, and radius of the polymer void, r void, were used to calculate the thickness of the vessel wall not containing polymer, d:
The ratio r void/d was used to calculate a stress concentration factor, K T, which ranged from 2.0 to 3.0:
where σmax was the maximum stress seen by a tissue at a void edge, and σavg was the average stress across d (Fig. 5).
For a void space covering 15% of the vessel area, r void/d = 0.118, and thus, K T = 2.5.3 With
where r i was the vessel inner radius, and
where length was the axial length of the tested vessel segment, σmax could be calculated from Eq. (A2). The ratio σmax/σo described the factor of increased stress seen by engineered tissue near the polymer void (Table 3). Thus, in the absence of polymer fragments at the suture line and elsewhere, engineered tissues may withstand pressures and stresses greater than 3 times their reported burst pressures and maximum stresses.
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Dahl, S.L.M., Rhim, C., Song, Y.C. et al. Mechanical Properties and Compositions of Tissue Engineered and Native Arteries. Ann Biomed Eng 35, 348–355 (2007). https://doi.org/10.1007/s10439-006-9226-1
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DOI: https://doi.org/10.1007/s10439-006-9226-1