Evaluation of the effect of stent strut profile on shear stress distribution using statistical moments
- Juan Mejia^{1, 4},
- Bilal Ruzzeh^{1},
- Rosaire Mongrain^{1, 4}Email author,
- Richard Leask^{2, 4} and
- Olivier F Bertrand^{3}
https://doi.org/10.1186/1475-925X-8-8
© Mejia et al; licensee BioMed Central Ltd. 2009
Received: 17 October 2008
Accepted: 30 April 2009
Published: 30 April 2009
Abstract
Background
In-stent restenosis rates have been closely linked to the wall shear stress distribution within a stented arterial segment, which in turn is a function of stent design. Unfortunately, evaluation of hemodynamic performance can only be evaluated with long term clinical trials. In this work we introduce a set of metrics, based on statistical moments, that can be used to evaluate the hemodynamic performance of a stent in a standardized way. They are presented in the context of a 2D flow study, which analyzes the impact of different strut profiles on the wall shear stress distribution for stented coronary arteries.
Results
It was shown that the proposed metrics have the ability to evaluate hemodynamic performance quantitatively and compare it to a common standard. In the context of the simulations presented here, they show that stent's strut profile significantly affect the shear stress distribution along the arterial wall. They also demonstrates that more streamlined profiles exhibit better hemodynamic performance than the standard square and circular profiles. The proposed metrics can be used to compare results from different research groups, and provide an improved method of quantifying hemodynamic performance in comparison to traditional techniques.
Conclusion
The strut shape found in the latest generations of stents are commonly dictated by manufacturing limitations. This research shows, however, that strut design can play a fundamental role in the improvement of the hemodynamic performance of stents. Present results show that up to 96% of the area between struts is exposed to wall shear stress levels above the critical value for the onset of restenosis when a tear-drop strut profile is used, while the analogous value for a square profile is 19.4%. The conclusions drawn from the non-dimensional metrics introduced in this work show good agreement with an ordinary analysis of the wall shear stress distribution based on the overall area exposed to critically low wall shear stress levels. The proposed metrics are able to predict, as expected, that more streamlined profiles perform better hemodynamically. These metrics integrate the entire morphology of the shear stress distribution and as a result are more robust than the traditional approach, which only compares the relative value of the local wall shear stress with a critical value of 0.5 Pa. In the future, these metrics could be employed to compare, in a standardized way, the hemodynamic performance of different stent designs.
Keywords
Introduction
Recently stent design was directly linked to in-stent restenosis rates [1]. For example, the corrugated ring stent design was found to result in smaller tissue proliferation than tubular slotted stent design suggesting that vessel response is dependent on stent design [2–6]. Since then a great deal of effort has been invested to improve stent designs. In general, the overall aim has been set toward improving the hemodynamic compatibility of stents.
A factor that has proved to be a strong predictor of in-stent restenosis is the stent's strut thickness, where thicker struts result in higher restenosis rates when compared to thinner strut designs [7]. Other studies have found a link between stent and neointimal thickening observed in human and animal experiments after vascular remodeling occurred [8, 9].
Work on the effect of wall shear stress (WSS) on the arterial wall have been able to find a strong relationship between abnormal regions of WSS with the generation of mitogens that can lean to neointimal hyperplasia (NIH), which can cause in-stent restenosis [10–12]. It has also been shown that the stent's presence can result in recirculation and reattachment regions between individual struts, and that the characteristics of these flow stagnation regions are dependent on strut spacing and geometry [13–22]. Moore et al. suggested that zones of recirculation and stagnant blood flow created by stenting are precursors of restenosis [23].
Moreover, it has been suggested that very high shear stress created along the stent's struts is a factor that could potentially cause in-stent restenosis [24] due to the alteration of blood constituents [25]. All these observations suggest that improvements of stent design could potentially lead to a decrease in restenosis rates.
In this paper, we study the impact of strut cross-sectional profile on the wall shear stress distribution along a stented segment of a coronary artery. Four different strut cross-sectional profiles (square, circular, elliptical, and tear-drop) are investigated. Simple metrics are suggested to assess the deviation of the shear stress distribution along the wall from the reference condition – i.e. an unstented arterial segment. It is shown that the proposed metrics are coherent with the fact that more streamlined profiles perform better than the more blunt profiles hemodynamically.
Methods
Mathematical Model
where ρ is the blood density (kg/m^{3}), μ is the blood dynamic viscosity (Pa·s), p is the pressure (Pa), and is the velocity field of the blood (m/s).
Numerical Model
Summary of boundary conditions.
Boundary Conditions | |
---|---|
Computational Domain | V_{ θ }= 0 |
Inlet | V_{ r }= 0 |
V_{ z }= 0.265(1 - (r/R)^{2}) (parabolic velocity profile) | |
Symmetry Line | V_{ r }= 0 |
Wall-blood interface | V_{ z }= 0 (no-slip condition) |
V_{ r }= 0 (non-porous wall) |
Shear Stress Metrics
where μ is the dynamic viscosity and s_{ ij }the shear rate tensor. Therefore, for a Newtonian fluid, the shear stress and shear rate plots exhibit the same general morphology.
Quantitatively, the global WSS distributions can be compared using statistical moments such as the mean, standard deviation, and kurtosis. We have limited our present analysis to the region between the first and second strut, while assuming that results obtained within this region remain for the entire stented arterial segment.
where x is the spatial dimension along which τ is evaluated. With this definition, the first central moment about zero is the mean of the function. the second central moment about the mean is the variance, the square root of which is the standard deviation. The third central moment is a measure of the lopsidedness of the distribution; a perfectly symmetric distribution will have a third central moment of zero. The third central moment is not employed here as it is assumed that the overall shift of the WSS is not as important as its flatness and elevation, which are measured by the first, second, and third statistical moments. Finally, the fourth central moment, also referred to as the kurtosis, is a measure of whether the distribution is tall and skinny (leptokurtosis), or short and squat (platokurtosis). The kurtosis is defined as the standardized fourth central moment. For a flat distribution (Poiseuille shear stress distribution), the average value at the wall is constant, the standard deviation is zero, and the skewness and kurtosis are zero. In fact, this approach is borrowed from tribology where similar metrics are employed to characterize surface roughness [32].
The first and second statistical moments, the mean and standard deviation respectively, have units of Pascals. We have non-dimensionalized them by dividing the first statistical moment by the average WSS of a normal artery (2.5 Pa as calculated with a Poiseuille flow) and by dividing the second statistical moment by the first – also known as the coefficient of variation.
For the case of a non-stented artery the last term of (5) is 1, in which case the kurtosis and the kurtosis coefficient are identical. When the mean changes – due to the presence of the stent – the kurtosis is greater than the kurtosis coefficient. Therefore, (5) is a measure of the distribution's flatness as well as its overall elevation.
Results
Statistical moments.
Non-embedded struts | |||
---|---|---|---|
Profile | Non-dimensional Mean | Coefficient of Variation | Kurtosis Coefficient |
Square | 0.0936 | 1.0212 | 0.2099 |
Circle | 0.0865 | 0.8908 | 0.1355 |
Ellipse | 0.3034 | 0.9404 | 0.4176 |
Tear Drop (1:3) | 0.4732 | 0.7715 | 0.6091 |
Statistical moments.
Half-embedded struts | |||
---|---|---|---|
Profile | Non-dimensional Mean | Coefficient of Variation | Kurtosis Coefficient |
Square | 0.2618 | 0.8395 | 0.3916 |
Circle | 0.3851 | 0.6817 | 0.5797 |
Ellipse | 0.6259 | 0.4496 | 1.6703 |
Tear Drop (1:3) | 0.7679 | 0.3127 | 4.7543 |
Discussion
Present results show that the proposed metrics correctly assess the hemodynamic performance of different strut profiles. Indeed they confirm that the tear-drop and elliptical strut profile perform best in both the non-embedded and half-embedded scenarios. The results revealed that the stent strut profile has a significant impact on the wall shear stresses both on the struts and in between struts. It also showed that slender and streamlined profiles provide better results in terms of peak stress. Tear-drop and elliptical profiles have better performance than the classical square and circular profiles. Furthermore, the current work suggests that appropriate strut apposition can lead to a significant improvement in terms of the hemodynamic performance of a stent.
The authors feel there is a need for appropriate data reduction analysis, and standardization, in the field of stent design, because of the complexity of the numerical studies and the various ways of assessing the hemodynamic performance available in the literature, which render comparison amongst studies difficult. Such considerations provided the motivation for this study, resulting in a set of metrics that have the capability of assessing the global WSS morphology and comparing it to a common standard.
Results showed that the metrics proposed here are in agreement with the traditional qualitative ways of evaluating hemodynamic performance. In almost all cases, the non-dimensional mean increases as the strut profile becomes more streamlined. The only exception is observed when the strut profile changes from a square to a circle in the non-embedded case. This exception can be explained by the fact that a circular profile comes into contact with the arterial wall further upstream than the square profile as the distance from the center of the strut is always constant for the circular geometry. Assuming that restenosis rates are reduced when the flow within the stented region is as similar to physiological values as possible the ideal stent would have a non-dimensional mean of 1. As such an ideal stent does not exist, it is assumed that the higher the non-dimensional mean the less likely it is that restenosis will occur. A similar argument is true for the kurtosis coefficient. A high kurtosis coefficient implies that the distribution is both relatively flat and contains, on average, high values of WSS. Therefore, a stent design with high kurtosis coefficient is desirable. It is not sufficient, however, to take into account the non-dimensional mean without the kurtosis coefficient as the first statistical moment is sensitive to extreme isolated values. Finally, the coefficient of variation of WSS within the stented region for a normal unstented artery is naturally low, which implies that a stent design with low coefficient of variation is desirable. Results from Tables 2 and 3 support this argument as the WSS distributions obtained with the elliptical and tear-drop profiles have the lowest coefficient of variation.
A stent design with a low coefficient of variation, high coefficient of kurtosis, and high non-dimensional mean is superior to a stent design with high coefficient of variation, high coefficient of kurtosis, and high non-dimensional mean as the latter probably has a high outlying value which is influencing the results, while it is possible that the overall WSS is relatively low. In general, when comparing stent designs in terms of their resulting WSS distributions a stent with high non-dimensional mean, high coefficient of kurtosis, and low coefficient of variation is assumed desirable. In the past, several studies have described the overall morphology of the WSS within a stented region [26, 27, 33] but as of yet a quantitative method of evaluating the global WSS distribution has not been presented.
Percentage of area over critical value.
Non-embedded struts | |
---|---|
Profile | % of area over threshold value |
Square | 19.4 |
Circle | 9.7 |
Ellipse | 50 |
Tear Drop (1:3) | 61.3 |
Percentage of area over critical value.
Half-embedded struts | |
---|---|
Profile | % of area over threshold value |
Square | 45 |
Circle | 67.7 |
Ellipse | 90.3 |
Tear Drop (1:3) | 96.2 |
The principal objective of this study was to develop the general methodology and simple metrics to assess the shear stress distribution associated with various stent strut designs. The present work shows that the proposed metrics are effective as they confirm that more streamlined cross-sectional strut profiles have better hemodynamic performance. Presently, struts with square cross-sectional profiles are common, but current results show that this type of profile might hamper hemodynamic performance. Elliptical profiles, which perform better according to the metrics proposed here, can be manufactured by chemically etching rectangular profiles obtained from conventional laser cut tubes. More complex profiles, such as the tear drop profile, would require more elaborate manufacturing processes. The tear drop profile was used because of its well known fluid dynamic properties. These properties provide a way to assess the proposed metrics for comparison purposes. In fact, the conclusions drawn from this study would not change if a tear-drop profile with a blunt trailing edge would have been used. Indeed, the circular, elliptical, and tear drop profiles have been investigated in the past in terms of their shear stress distribution [36]. In that reference it was shown that elliptical profiles have very close properties to the tear drop profile.
Valuable insight has been obtained by analyzing the present two-dimensional model. Although future work should also include more complicated model of the stented vessel (e.g. including curvature and compliance) there are still important lessons that can be learned from relatively simple simulations, as was also recently demonstrated by Kolachalama et al. and Borghi et al. [37, 38].
Consequently, the proposed metrics can be calculated on a two-dimensional section of a three-dimensional model, or over a three-dimensional surface.
This work assumed that blood can be modeled as a Newtonian fluid. However, recent studies have suggested that the non-Newtonian nature of blood can have a non-negligible impact on WSS levels [44]. Therefore, future work should include the non-Newtonian behavior of blood into the model. The present work also assumed rigid vessel walls, which could potentially alter WSS distributions and should also be investigated in the future.
Conclusion
In this work, we presented simple metrics to assess and compare the shear stress levels associated with various stent strut profiles. The metrics are defined with respect to the reference values of the corresponding normal unstented arterial segment. In other words, we globally assess the difference of the shear stress distribution between the stented and the unstented conditions. Although there are several methods presented in the literature to asses stent performance – such as those used by Moore et al. and Balossino et al. [17, 34] – the proposed metrics introduce the first standardized method of assessing hemodynamic performance in terms of WSS distribution.
As expected, results suggest that more streamlined strut profiles exhibit better hemodynamic performance.
In addition, when comparing the non-embedded and the half-embedded scenarios the latter exhibits more favorable WSS distributions for the same strut profile, which is also to be expected. In terms of the proposed metrics, both the streamlined profiles and the half-embedded struts perform better. Therefore, it is concluded that the metrics introduced in this work can be later used to assess the impact of more complex factors – such as stent cell geometry, inter-strut distance, strut thickness, etc. – on WSS distribution. Although these metrics were proposed here in the context of a 2D model they can be directly applied to any WSS distribution regardless of how it is obtained (i.e. 3D numerical model, in-vitro model, or in-vivo). Future work should include dedicated clinical trials to provide a direct link between the proposed metrics and restenosis rates.
Declarations
Acknowledgements
This work has been supported in part by research grants from the Natural Sciences and Engineering Research Council of Canada (NSERC), Fonds de Recherche de l'Institut de Cardiologie de Montreal, Fondation de l'Institut de Cardiologie de Quebec and by an equipment grant from the Canadian Foundation for Innovation (CFI).
Authors’ Affiliations
References
- Kastrati A, Mehilli J, Dirschinger J, Dotzer F, Schuhlen H, Neumann FJ, Fleckenstein M, Pfafferott C, Seyfarth M, Schomig A: Intracoronary stenting and angiographic results: strut thickness effect on restenosis outcome (ISAR-STEREO) trial. Circulation 2001,103(23):2816–21.View ArticleGoogle Scholar
- Kastrati A, Schomig A, Elezi S, Schuhlen H, Dirschinger J, Hadamitzky M, Wehinger A, Hausleiter J, Walter H, Neumann FJ: Predictive factors of restenosis after coronary stent placement. Journal of the American College of Cardiology 1997,30(6):1428–36. 10.1016/S0735-1097(97)00334-3View ArticleGoogle Scholar
- Rogers C, Edelman ER: Endovascular stent design dictates experimental restenosis and thrombosis. Circulation 1995,91(12):2995–3001.View ArticleGoogle Scholar
- Jonas M, Resnic FS, Levin AD, Arora N, Rogers CD: Transition from bare metal to drug eluting stenting in contemporary US practice: Effect on incidence and predictors of clinically driven target lesion revascularization. Catheter Cardiovasc Interv 2007,70(2):175–183. 10.1002/ccd.21123View ArticleGoogle Scholar
- Eric Larose CDRDIS: When size matters: Lessons learned from left main stent embolization and retrieval. Journal of Interventional Cardiology 2006,19(4):350–355. 10.1111/j.1540-8183.2006.00160.xView ArticleGoogle Scholar
- Choi G, Cheng CP, Wilson NM, Taylor CA: Methods for quantifying three-dimensional deformation of arteries due to pulsatile and nonpulsatile forces: Implications for the design of stents and stent grafts. Annals of Biomedical Engineering 2009, 37: 14–33. 10.1007/s10439-008-9590-0View ArticleGoogle Scholar
- Briguori C, Sarais C, Pagnotta P, Liistro F, Montorfano M, Chieffo A, Sgura F, Corvaja N, Albiero R, Stankovic G, Toutoutzas C, Bonizzoni E, Di Mario C, Colombo A: In-stent restenosis in small coronary arteries: Impact of strut thickness. Journal of the American College of Cardiology 2002,40(3):403–409. 10.1016/S0735-1097(02)01989-7View ArticleGoogle Scholar
- Garasic JM, Edelman ER, Squire JC, Seifert P, Williams MS, Rogers C: Stent and artery geometry determine intimal thickening independent of arterial injury. Circulation 2000,101(7):812–818.View ArticleGoogle Scholar
- Hoffmann R, Jansen C, Konig A, Haager PK, Kerckhoff G, vom Dahl J, Klauss V, Hanrath P, Mudra H: Stent design related neointimal tissue proliferation in human coronary arteries; an intravascular ultrasound study. European Heart Journal 2001,22(21):2007–14. 10.1053/euhj.2001.2606View ArticleGoogle Scholar
- Carlier SG, van Damme LCA, Blommerde CP, Wentzel JJ, van Langehove G, Verheye S, Kockx MM, Knaapen MWM, Cheng C, Gijsen F, Duncker DJ, Stergiopulos N, Slager CJ, Serruys PW, Krams R: Augmentation of wall shear stress inhibits neointimal hyperplasia after stent implantation: inhibition through reduction of inflammation? Circulation 2003,107(21):2741–2746. 10.1161/01.CIR.0000066914.95878.6DView ArticleGoogle Scholar
- Liu SQ, Goldman J: Role of blood shear stress in the regulation of vascular smooth muscle cell migration. IEEE Trans Biomed Eng 2001,48(4):474–483. 10.1109/10.915714View ArticleGoogle Scholar
- Liu SQ, Tieche C, Tang D, Alkema P: Pattern formation of vascular smooth muscle cells subject to nonuniform fluid shear stress: role of PDGF-beta receptor and Src. Am J Physiol Heart Circ Physiol 2003,285(3):H1081-H1090.View ArticleGoogle Scholar
- Berry J, Santamarina A, Moore J, Roychowdhury S, Routh W: Experimental and computational flow evaluation of coronary stents. Annals of Biomedical Engineering 2000,28(4):386–398. 10.1114/1.276View ArticleGoogle Scholar
- Henry F: Flow in Stented Arteries. Intra- and Extracorporeal Cardiovascular Fluid Dynamics. Volume 333–364. Boston: WIT Press; 2000.Google Scholar
- Moore JE, Berry JL: Fluid and Solid Mechanical Implications of Vascular Stenting. Annals of Biomedical Engineering 2002,30(4):498–508. 10.1114/1.1458594View ArticleGoogle Scholar
- Schachter L, Barakat A: Computational study of arterial flow disturbance induced by intravascular stents. 2001.Google Scholar
- Duraiswamy N, Cesar JM, Schoephoerster RT, Moore JE Jr: Effects of stent geometry on local flow dynamics and resulting platelet deposition in an in vitro model. Biorheology 2008,45(5):547–561.Google Scholar
- Dehlaghi V, Shadpoor MT, Najarian S: Analysis of wall shear stress in stented coronary artery using 3D computational fluid dynamics modeling. Journal of Materials Processing Technology 2008,197(1–3):174–181. 10.1016/j.jmatprotec.2007.06.010View ArticleGoogle Scholar
- Dehlaghi V, Najarian S, Shadpour MT: Effect of the stent design properties on restenosis in stented human coronary artery. Heart, Lung and Circulation 2008,17(Supplement 1):S12-S13. 10.1016/j.hlc.2007.11.031View ArticleGoogle Scholar
- Dehlaghi V, Najarian S, Shadpour MT: Effect of stent geometry on phase shift between pressure and flow waveforms in stented human coronary artery. American Journal of Applied Sciences 2008,5(4):340–6.View ArticleGoogle Scholar
- Wentzel JJ, Gijsen FJH, Stergiopulos N, Serruys PW, Slager CJ, Krams R: Shear stress, vascular remodeling and neointimal formation. Journal of Biomechanics 2003,36(5):681–688. 10.1016/S0021-9290(02)00446-3View ArticleGoogle Scholar
- LaDisa J, Olson L, Douglas H, Warltier D, Kersten J, Pagel P: Alterations in regional vascular geometry produced by theoretical stent implantation influence distributions of wall shear stress: analysis of a curved coronary artery using 3D computational fluid dynamics modeling. BioMedical Engineering OnLine 2006, 5: 40. 10.1186/1475-925X-5-40View ArticleGoogle Scholar
- Moore JJE, Xu C, Glagov S, Zarins CK, Ku DN: Fluid wall shear stress measurements in a model of the human abdominal aorta: oscillatory behavior and relationship to atherosclerosis. Atherosclerosis 1994,110(2):225–40. 10.1016/0021-9150(94)90207-0View ArticleGoogle Scholar
- Faik I: 3D characterization of the hemodynamic parameters in a stented coronary artery. PhD thesis. McGill University; 2005.Google Scholar
- Yeleswarapu KK, Antaki JF, Kameneva MV, Rajagopal KR: A mathematical model for shear-induced hemolysis. Artificial Organs 1995,19(7):576–82. 10.1111/j.1525-1594.1995.tb02384.xView ArticleGoogle Scholar
- Seo T, Schachter LG, Barakat AI: Computational study of fluid mechanical disturbance induced by endovascular stents. Annals of Biomedical Engineering 2005,V33(4):444–456. 10.1007/s10439-005-2499-yView ArticleGoogle Scholar
- Xu Y, MW C: Fluid Dynamics in stents. In Endoluminal stenting, sigwart u, ed. edition. London: WB Saunders Co, Ltd; 1996:52–59.Google Scholar
- Kajiya F, Matsuoka S, Ogasawara Y, Hiramatsu O, Kanazawa S, Wada Y, Tadaoka S, Tsujioka K, Fujiwara T, Zamir M: Velocity profiles and phasic flow patterns in the non-stenotic human left anterior descending coronary artery during cardiac surgery. Cardiovascular Research 1993,27(5):845–50. 10.1093/cvr/27.5.845View ArticleGoogle Scholar
- Serruys PW, Rensing BJ: Handbook of Coronary Stents. MARTIN DUNITZ LTD; 2002.Google Scholar
- Baroldi G, Bigi R, Cortigiani L: Ultrasound imaging versus morphopathology in cardiovascular diseases. Coronary atherosclerotic plaque. Cardiovasc Ultrasound 2004, 2: 29. 10.1186/1476-7120-2-29View ArticleGoogle Scholar
- He X, Ku DN: Pulsatile flow in the human left coronary artery bifurcation: average conditions. Journal Biomechanical Engineering 1996, 118: 74–82. 10.1115/1.2795948View ArticleGoogle Scholar
- Tayebi N, Polycarpou AA: Modeling the effect of skewness and kurtosis on the static friction coefficient of rough surfaces. Tribology international 2003,37(6):491–505. 10.1016/j.triboint.2003.11.010View ArticleGoogle Scholar
- Rajamohan D, Banerjee RK, Back LH, Ibrahim AA, Jog MA: Developing pulsatile flow in a deployed coronary stent. Journal of Biomechanical Engineering 2006,128(3):347–359. 10.1115/1.2194067View ArticleGoogle Scholar
- Balossino R, Gervaso F, Migliavacca F, Dubini G: Effects of different stent designs on local hemodynamics in stented arteries. Journal of Biomechanics 2008,41(5):1053–1061. 10.1016/j.jbiomech.2007.12.005View ArticleGoogle Scholar
- LaDisa JJF, Meier HT, Olson LE, Kersten JR, Warltier DC, Pagel PS: Antegrade iliac artery stent implantation for the temporal and spatial examination of stent-induced neointimal hyperplasia and alterations in regional fluid dynamics. Journal of Pharmacological and Toxicological Methods 2005,51(2):115–121. 10.1016/j.vascn.2004.08.001View ArticleGoogle Scholar
- Schlichting H, Gersten K: Boundary-layer theory. 8th rev. and enl. edition. Berlin; New York: Springer; 2000.View ArticleGoogle Scholar
- Kolachalama VB, Tzafriri AR, Arifin DY, Edelman ER: Luminal flow patterns dictate arterial drug deposition in stent-based delivery. Journal Control Release 2009, 133: 24–30. 10.1016/j.jconrel.2008.09.075View ArticleGoogle Scholar
- Borghi A, Foa E, Balossino R, Migliavacca F, Dubini G: Modelling drug elution from stents: effects of reversible binding in the vascular wall and degradable polymeric matrix. Computer Methods in Biomechanics and Biomedical Engineering 2008,11(4):367–77. 10.1080/10255840801887555View ArticleGoogle Scholar
- Faik I, Mongrain R, Leask RL, Rodes-Cabau J, Larose E, Bertrand O: Time-dependent 3D simulations of the hemodynamics in a stented coronary artery. Biomedical Materials 2007, 2: S28–37. 10.1088/1748-6041/2/1/S05View ArticleGoogle Scholar
- Mejia J, Mongrain DR, Leask R, Rodes J, Bertrand O: The significance of flow unsteadiness on the near-wall flow of a stented artery. In 4th European Congress for Medical and Biomedical Engineering. Antwerp, Belgium: IFMBE; 2008.Google Scholar
- Plante S: Expandable intravascular stent. 1999.Google Scholar
- Mongrain DR, Faik I, Bulman-Fleming N, Tardiff JC, Plante S, Bertrand O: Numerical simulations of local pharmacokinetics of a drug delivered from an eluting stent. In Advanced Materials for Biomedical Applications. Edited by: Mantovani D. Montreal, Canada: Met Soc; 2002:213–223.Google Scholar
- Ventzel H: Theorie de Probabilities. Moscous: Mir; 1982.Google Scholar
- Benard N, Perrault R, Coisne D: Computational approach to estimating the effects of blood properties on changes in intra-stent flow. Annals of Biomedical Engineering 2006,V34(8):1259–1271. 10.1007/s10439-006-9123-7View ArticleGoogle Scholar
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