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Polymeric textile stents: Prototypi...

Irsale, Swagat Appasaheb.

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Polymeric textile stents: Prototyping and modeling.

紀錄類型:	書目-語言資料,印刷品 : Monograph/item
正題名/作者:	Polymeric textile stents: Prototyping and modeling./
作者:	Irsale, Swagat Appasaheb.
面頁冊數:	166 p.
附註:	Director: Sabit Adanur.
Contained By:	Dissertation Abstracts International66-12B.
標題:	Engineering, Biomedical. -
電子資源:	http://pqdd.sinica.edu.tw/twdaoapp/servlet/advanced?query=3201447
ISBN:	9780542465994

Polymeric textile stents: Prototyping and modeling.
Irsale, Swagat Appasaheb.

Polymeric textile stents: Prototyping and modeling. - 166 p.

Director: Sabit Adanur.

Thesis (Ph.D.)--Auburn University, 2005.

Although metal stents have been implanted for more than a decade, performance deficiencies still exist. The current study focuses on prototyping and modeling of braided structures to be used as stents, hence called 'textile stents'. Textile stents are self-expanding stents. The objective is to establish guidelines for commercial manufacturing of textile stents which can become major substitutes for metal stents. Textile stents and bifurcated textile stents were manufactured. Manufacturing variables braid angle, braid diameter, and heatset time had statistically significant effects (p = 0.0001) on the compression force of textile stents. A chart is compiled which categorizes factors affecting the performance of textile stents. Strong correlation (adjusted R 2 = 0.9999) between radial and in vitro (unidirectional) compressions of textile stents was observed. Agreement between values of Young's modulus of textile stents derived by the mechanical model (strain energy method) to those of the experimental was good (adjusted R2 = 0.7955). Stress-strain curves were obtained by strip testing of textile stents on an InstronRTM. The empirical model showed strong correlation between theoretical and experimental values of compression force for 1.27 cm (adjusted R2= 0.8669) and 1.9 cm (adjusted R2 = 0.9251) diameter textile stents. Two-Factor ANOVA showed statistically significant effect (p = 0.00051 for 0.4 cm artery diameter, p = 0.00013 for 0.8 cm artery diameter, p = 0.01716 for 1.2 cm artery diameter, p = 0.01240 for 1.6 cm artery diameter, p = 0.0309 for 2.5 cm artery diameter) of blood input velocity on exit velocity, determined by AnsysRTM FLOTRAN. Monofilament denier also showed statistically significant effect (p = 0.04395 for 0.4 cm, p = 0.03814 for 0.8 cm, p = 0.01491 for 1.2 cm) on exit velocity for all mentioned artery diameters except 1.6 and 2.5 cm. Textile stent entrance and exit effects and blood flow behavior in textile stented artery segment were helpful in understanding restenosis. Application of textile stents as substitute to metal stents is feasible.

ISBN: 9780542465994Subjects--Topical Terms:

1017684
Engineering, Biomedical.

Polymeric textile stents: Prototyping and modeling.
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245 1 0 $a Polymeric textile stents: Prototyping and modeling.
300 $a 166 p.
500 $a Director: Sabit Adanur.
500 $a Source: Dissertation Abstracts International, Volume: 66-12, Section: B, page: 6904.
502 $a Thesis (Ph.D.)--Auburn University, 2005.
520 $a Although metal stents have been implanted for more than a decade, performance deficiencies still exist. The current study focuses on prototyping and modeling of braided structures to be used as stents, hence called 'textile stents'. Textile stents are self-expanding stents. The objective is to establish guidelines for commercial manufacturing of textile stents which can become major substitutes for metal stents. Textile stents and bifurcated textile stents were manufactured. Manufacturing variables braid angle, braid diameter, and heatset time had statistically significant effects (p = 0.0001) on the compression force of textile stents. A chart is compiled which categorizes factors affecting the performance of textile stents. Strong correlation (adjusted R 2 = 0.9999) between radial and in vitro (unidirectional) compressions of textile stents was observed. Agreement between values of Young's modulus of textile stents derived by the mechanical model (strain energy method) to those of the experimental was good (adjusted R2 = 0.7955). Stress-strain curves were obtained by strip testing of textile stents on an InstronRTM. The empirical model showed strong correlation between theoretical and experimental values of compression force for 1.27 cm (adjusted R2= 0.8669) and 1.9 cm (adjusted R2 = 0.9251) diameter textile stents. Two-Factor ANOVA showed statistically significant effect (p = 0.00051 for 0.4 cm artery diameter, p = 0.00013 for 0.8 cm artery diameter, p = 0.01716 for 1.2 cm artery diameter, p = 0.01240 for 1.6 cm artery diameter, p = 0.0309 for 2.5 cm artery diameter) of blood input velocity on exit velocity, determined by AnsysRTM FLOTRAN. Monofilament denier also showed statistically significant effect (p = 0.04395 for 0.4 cm, p = 0.03814 for 0.8 cm, p = 0.01491 for 1.2 cm) on exit velocity for all mentioned artery diameters except 1.6 and 2.5 cm. Textile stent entrance and exit effects and blood flow behavior in textile stented artery segment were helpful in understanding restenosis. Application of textile stents as substitute to metal stents is feasible.
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