Content uploaded by Philippe Sucosky
Author content
All content in this area was uploaded by Philippe Sucosky on Sep 16, 2018
Content may be subject to copyright.
Full Terms & Conditions of access and use can be found at
http://www.tandfonline.com/action/journalInformation?journalCode=gcmb20
Download by: [Philippe Sucosky] Date: 07 October 2016, At: 05:34
Computer Methods in Biomechanics and Biomedical
Engineering
ISSN: 1025-5842 (Print) 1476-8259 (Online) Journal homepage: http://www.tandfonline.com/loi/gcmb20
Aortic valve leaflet wall shear stress
characterization revisited: impact of coronary flow
K. Cao & P. Sucosky
To cite this article: K. Cao & P. Sucosky (2016): Aortic valve leaflet wall shear stress
characterization revisited: impact of coronary flow, Computer Methods in Biomechanics and
Biomedical Engineering, DOI: 10.1080/10255842.2016.1244266
To link to this article: http://dx.doi.org/10.1080/10255842.2016.1244266
View supplementary material
Published online: 07 Oct 2016.
Submit your article to this journal
View related articles
View Crossmark data
COMPUTER METHODS IN BIOMECHANICS AND BIOMEDICAL ENGINEERING, 2016
http://dx.doi.org/10.1080/10255842.2016.1244266
Aortic valve leaet wall shear stress characterization revisited: impact of
coronary ow
K. Caoa and P. Sucoskyb
aDepartment of Aerospace and Mechanical Engineering, University of Notre Dame, Notre Dame, IN, USA; bDepartment of Mechanical and
Materials Engineering, Wright State University, Dayton, OH, USA
ABSTRACT
Computational characterizations of aortic valve hemodynamics have typically discarded the eects
of coronary ow. The objective of this study was to complement our previous uid–structure
interaction aortic valve model with a physiologic coronary circulation model to quantify the impact
of coronary ow on aortic sinus hemodynamics and leaet wall shear stress (WSS). Coronary ow
suppressed vortex development in the two coronary sinuses and altered WSS magnitude and
directionality on the three leaets, with the most substantial dierences occurring in the belly and
tip regions.
1. Introduction
Aortic valve (AV) leaets are sensitive to their surround-
ing hemodynamic stress environment. While physiologic
ow promotes AV homeostasis, wall shear stress (WSS)
abnormalities trigger pathological cascades that may lead
ultimately to calcic aortic valve disease (CAVD) (Sucosky
et al. 2009; Hoehn et al. 2010; Sun et al. 2012, 2013; Sun &
Sucosky 2015). is hypothetical hemodynamic etiology of
valvular disease has motivated the characterization of the
native leaet WSS environment using uid–structure inter-
action (FSI) modeling (Chandra et al. 2012; Cao & Sucosky
2015; Gilmanov & Sotiropoulos 2016; Cao & Sucosky
forthcoming 2016). While those studies have shed new light
on valvular mechanics and function, the impact of the cor-
onary circulation on valvular ow has been discarded. As
observed experimentally, the coronary ow established dur-
ing diastole generates complex vortex dynamics in the aortic
sinus, which interacts with the leaets and may alter their
regional stress distribution (Moore & Dasi 2015). e aim
of this study was to complement our previous FSI AV model
with a physiologic coronary circulation model to quantify
the impact of coronary ow on AV ow and leaet WSS.
2. Materials and methods
Our previous FSI AV model (Cao et al. 2016) was used
as the basis for this study. e aortic root geometry was
modied to include the coronary ostia and the proximal
segments of the coronary arteries. e le- and right-cor-
onary ostia were modeled as circular (diameter: 4.0 and
3.2mm, respectively) and were positioned 18mm above
the valve annulus (Waller et al. 1992) (Figure 1(a)). e
proximal le- and right-coronary arteries (LCA and RCA,
respectively) were modeled as cylindrical extensions
(length: 6.0mm) with a wall thickness of 0.4mm (Dong et
al. 2015). e coronary arteries were approximated as iso-
tropic linear elastic materials (Young’s modulus: 0.4MPa,
Claes et al. 2010).
Two Windkessel models were implemented to pre-
scribe realistic LCA and RCA ow rates (Q):
where P is the aortic pressure, R1 is the coronary arterial
resistance, R2 is the coronary venous resistance and C is
the coronary arterial compliance (Figure 1(b)) (Westerhof
et al. 2009). Each model was calibrated using two sets of
parameters (Table 1) to generate physiologic human cor-
onary ow rates during systole and diastole, respectively
(Koeppen & Stanton 2009) (Figure 1(c)).
Arbitrary Lagrangian Eulerian simulations were car-
ried out in ANSYS 15.0 over three cardiac cycles and all
results were extracted during the last cycle. All model
parameters, numerical treatments and mesh sensitivity
analyses have been described in our previous FSI AV
(1)
CR
1
dQ
dt+
(
1+
R
1
R
2)
Q=CdP
dt+1
R
2
P
,
KEYWORDS
Aortic valve; coronary flow;
fluid–structure interaction;
hemodynamics; wall shear
stress; aortic sinus
ARTICLE HISTORY
Received 4 May 2016
Accepted 29 September 2016
© 2016 Informa UK Limited, trading as Taylor & Francis Group
CONTACT P. Sucosky philippe.sucosky@wright.edu
The supplementary material for this paper is available online at http://dx.doi.org/10.1080/10255842.2016.1244266.
2 K. CAO AND P. SUCOSKY
3. Results
Coronary ow resulted in asymmetric hemodynamics in
the aortic sinuses during diastole, marked by recirculation
and intense vorticity in the non-coronary sinus and more
moderate vorticity in the coronary sinuses (Figure 2(a)
and Supplemental Material – video.mp4). Quantication
of the peak-systolic valve geometric orice area (GOA)
revealed a 7% increase in the presence of coronary ow
model (Cao et al. 2016). Valvular ow was characterized in
terms of vorticity and velocity. Regional WSS magnitude
and directionality were quantied in terms of temporal
shear magnitude (TSM) and oscillatory shear index (OSI)
in the base, belly and tip of the non-, right- and le-cor-
onary leaets (i.e. NC, RC and LC leaets, respectively)
and compared to those captured by our previous model
in the absence of coronary ow (REF leaet).
Figure 1.Model setup: (a) AV geometry; (b) Windkessel electrical analog; and (c) coronary flow rates generated by the Windkessel models
at the LCA and RCA outlets (physiologic values adapted from Koeppen & Stanton 2009).
Table 1.Windkessel parameters.
Systole Diastole
R1 (kg/(m4s) R2 (kg/(m4s) C (m4s2/kg) R1 (kg/(m4s) R2 (kg/(m4s) C (m4s2/kg)
LCA 5.7 × 1091.9 × 1011 4.9 × 10−11 3.8 × 1092.1 × 1011 9.7 × 10−11
RCA 1.7 × 1010 5.7 × 1011 1.6 × 10−11 3.9 × 1010 1.9 × 1011 9.6 × 10−12
Figure 2.Comparison of AV hemodynamics without and with coronary flow: (a) diastolic velocity and vorticity fields; (b) TSM and (c) OSI
regional distributions on the leaflet fibrosa.
COMPUTER METHODS IN BIOMECHANICS AND BIOMEDICAL ENGINEERING 3
relative to our previous model (Supplemental Material
– Figure S1), demonstrating the benecial impact of the
coronary circulation on valvular function.
As compared to our previous model, coronary ow
generated an overall increase in WSS magnitude and uni-
directionality on the leaet brosa (up to 30% increase
in TSM, up to 0.10 decrease in OSI vs. REF leaet), with
the most apparent changes occurring in the belly and
tip regions (Figure 2(b) and (c)). e asymmetry in vor-
ticity dynamics introduced by the coronary circulation
translated into discrepancies in WSS magnitude and
directionality between the three leaets. e LC and RC
leaets were subjected to WSS overloads (30 and 15%
increase, respectively) relative to the NC leaet. While
this increase aected the belly and tip of the LC leaet, it
only occurred in the tip of the RC leaet. Coronary ow
also generated asymmetric and spatially-dependent OSI
distributions on the leaets, with mixed directionality in
the base (0.26<OSI<0.30), more pronounced bidirec-
tionality in the belly (OSI>0.31) and strong unidirec-
tionality in the tip (OSI<0.15). While WSS directionality
was essentially similar in the base of all three leaets, it
was markedly more bidirectional in the belly of the RC
and NC leaets (0.13 and 0.12 OSI increase, respectively)
relative to the LC leaet and more unidirectional in the
tip of the LC and RC leaets (0.09 OSI decrease) relative
to the NC leaet.
4. Discussion
In summary, coronary ow suppressed vortex devel-
opment in the coronary sinuses and promoted valvular
function. ose results are consistent with particle image
velocimetry measurements of aortic sinus ow with phys-
iologic coronary ow (Moore & Dasi 2015). Coronary
ow resulted in contrasted WSS patterns on the three
leaets, with the most substantial dierences occurring
in the belly and tip regions. e distinctly lower and more
bidirectional WSS on the NC leaet may explain its higher
vulnerability to calcication (Freeman & Otto 2005). To
conclude, coronary ow impacts the leaet WSS environ-
ment and should be accounted for in the characterization
of the native valvular hemodynamic stresses.
Disclosure statement
No potential conict of interest was reported by the authors.
Funding
is work supported by Division of Civil, Mechanical and Man-
ufacturing Innovation, National Science Foundation [grant
number CMMI-1148558], [grant number CMMI-1550144];
American Heart Association [grant number 14PRE18940010].
References
Cao K, Sucosky P. 2015. Eect of bicuspid aortic valve cusp
fusion on aorta wall shear stress: preliminary computational
assessment and implication for aortic dilation. World J
Cardiovasc Dis. 5:129–140.
Cao K, Sucosky P. Forthcoming 2016. Computational comparison
of regional stress and deformation characteristics in tricuspid
and bicuspid aortic valve leaets. Int J Numer Method Biomed
Eng. Epub ahead of print. doi: 10.1002/cnm.2798
Cao K, Bukač M, Sucosky P. 2016. ree-dimensional macro-
scale assessment of regional and temporal wall shear stress
characteristics on aortic valve leaets. Comput Methods
Biomech Biomed Engin. 19:603–613.
Chandra S, Rajamannan NM, Sucosky P. 2012. Computational
assessment of bicuspid aortic valve wall-shear stress:
implications for calcic aortic valve disease. Biomech Model
Mechanobiol. 11:1085–1096.
Claes E, Atienza JM, Guinea GV, Rojo FJ, Bernal JM, Revuelta
JM, Elices M. 2010. Mechanical properties of human
coronary arteries. Conf Proc Annu Int Conf IEEE Eng Med
Biol Soc IEEE Eng Med Biol Soc Annu Conf. 2010:3792–
3795.
Dong J, Sun Z, Inthavong K, Tu J. 2015. Fluid–structure
interaction analysis of the le coronary artery with variable
angulation. Comput Methods Biomech Biomed Engin.
18:1500–1508.
Freeman RV, Otto CM. 2005. Spectrum of calcic aortic valve
disease: pathogenesis, disease progression, and treatment
strategies. Circulation. 111:3316–3326.
Gilmanov A, Sotiropoulos F. 2016. Comparative hemodynamics
in an aorta with bicuspid and trileaet valves. eor Comput
Fluid Dyn. 30: 1–19.
Hoehn D, Sun L, Sucosky P. 2010. Role of pathologic shear
stress alterations in aortic valve endothelial activation.
Cardiovasc Eng Technol. 1:165–178.
Koeppen B, Stanton B. 2009. Berne & Levy physiology. 6th ed.
Philadelphia, PA: Mosby Elsevier.
Moore BL, Dasi LP. 2015. Coronary ow impacts aortic leaet
mechanics and aortic sinus hemodynamics. Ann Biomed
Eng. 43:2231–2241.
Sucosky P, Balachandran K, Elhammali A, Jo H, Yoganathan
AP. 2009. Altered shear stress stimulates upregulation of
endothelial VCAM-1 and ICAM-1 in a BMP-4- and TGF-
beta1-dependent pathway. Arterioscler romb Vasc Biol.
29:254–260.
Sun L, Sucosky P. 2015. Bone morphogenetic protein-4 and
transforming growth factor-beta1 mechanisms in acute
valvular response to supra-physiologic hemodynamic
stresses. World J Cardiol. 7:331–343.
Sun L, Chandra S, Sucosky P. 2012. Ex vivo evidence for the
contribution of hemodynamic shear stress abnormalities
to the early pathogenesis of calcic bicuspid aortic valve
disease. PLoS One. 7:e48843.
Sun L, Rajamannan N, Sucosky P. 2013. Dening the role of
uid shear stress in the expression of early signaling markers
for calcic aortic valve disease. PLoS One. 8:e84433.
Waller BF, Orr CM, Slack JD, Pinkerton CA, Van Tassel
J, Peters T. 1992. Anatomy, histology, and pathology of
coronary arteries: a review relevant to new interventional
and imaging techniques-Part I. Clin Cardiol. 15:451–457.
Westerhof N, Lankhaar J-W, Westerhof BE. 2009. e arterial
Windkessel. Med Biol Eng Comput. 47:131–141.