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. Author manuscript; available in PMC: 2018 Jun 11.

Published in final edited form as: Nat Biomed Eng. 2017 Oct 10;1:818–825. doi: 10.1038/s41551-017-0142-5

a, Braid elongation (modeled vs. experimental). Graphical representation of length-diameter relationship for biaxially braided sleeves. Changing braid pitch (defined by picks-per-inch (PPI)) creates unique elongation profiles for device tunability. Modeled braided sleeve behavior (curves) accurately reflects actual sleeve behavior (experimentally measured lengths: , , ) across range of braid profiles. b, ESPGS degradation profile under accelerated conditions for different polymer curing temperatures & durations. Degradation rate is significantly influenced by curing temperature (n = 3, mean ± s.d.). c, Young’s modulus of device with different PGS cores. Overall device modulus is affected by inner polymer curing. Increasing curing duration and curing at 155°C results in increased device strength. Device prototypes with 86-hour ESPGS have greater Young’s Modulus than commercially available surgical sutures (e.g. PTFE, polydioxanone (PDO)) (n = 3, mean ± s.d.). d, Representative cyclic tensile testing demonstrates no evidence of device fatigue following 1000 cycles (n = 3). e, ESPGS degradation profile under accelerated conditions with varying tensile stresses applied to overall device. Degradation rate is not significantly influenced by applied stress. (n = 3, mean ± s.d.)

Inline graphic — a, Braid elongation (modeled vs. experimental). Graphical representation of length-diameter relationship for biaxially braided sleeves. Changing braid pitch (defined by picks-per-inch (PPI)) creates unique elongation profiles for device tunability. Modeled braided sleeve behavior (curves) accurately reflects actual sleeve behavior (experimentally measured lengths: , , ) across range of braid profiles. b, ESPGS degradation profile under accelerated conditions for different polymer curing temperatures & durations. Degradation rate is significantly influenced by curing temperature (n = 3, mean ± s.d.). c, Young’s modulus of device with different PGS cores. Overall device modulus is affected by inner polymer curing. Increasing curing duration and curing at 155°C results in increased device strength. Device prototypes with 86-hour ESPGS have greater Young’s Modulus than commercially available surgical sutures (e.g. PTFE, polydioxanone (PDO)) (n = 3, mean ± s.d.). d, Representative cyclic tensile testing demonstrates no evidence of device fatigue following 1000 cycles (n = 3). e, ESPGS degradation profile under accelerated conditions with varying tensile stresses applied to overall device. Degradation rate is not significantly influenced by applied stress. (n = 3, mean ± s.d.)