1 23 Current Radiology Reports e-ISSN 2167-4825 Volume 4 Number 9 Curr Radiol Rep (2016) 4:1-14 DOI 10.1007/s40134-016-0176-6 CT and MRI of Aortic Valve Disease: Clinical Update Richard Hallett, Sina Moainie, James Hermiller & Dominik Fleischmann
1 23
Current Radiology Reports e-ISSN 2167-4825Volume 4Number 9 Curr Radiol Rep (2016) 4:1-14DOI 10.1007/s40134-016-0176-6
CT and MRI of Aortic Valve Disease:Clinical Update
Richard Hallett, Sina Moainie, JamesHermiller & Dominik Fleischmann
1 23
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CARDIOVASCULAR IMAGING (A BIERHALS, SECTION EDITOR)
CT and MRI of Aortic Valve Disease: Clinical Update
Richard Hallett1,2• Sina Moainie3
• James Hermiller4• Dominik Fleischmann5
Published online: 25 July 2016
� Springer Science+Business Media New York 2016
Abstract
Purpose of Review Imaging of the aortic valve and asso-
ciated aortic root pathology has historically been primarily
imaged by echocardiography. Recent advances in com-
puted tomography (CT) and magnetic resonance (MR)
imaging hardware and software have made routine, high-
resolution CT/MR assessment of morphology of the aortic
root and aortic valve practical and robust.
Recent Findings Improvements in ECG-synchronized CT
imaging have led to motion-free imaging of the aortic root
in most patients. MR techniques, including 4D flow MR
imaging, add additional information for assessment of the
aortic valve. These newer techniques are valuable for
classification and prognosis of the cardiovascular mani-
festations of bicuspid aortic valve (BAV) disease. CT
imaging has become integral to pre- and post-procedural
assessment of patients considered for transcatheter aortic
valve repair (TAVR). Post-processing techniques that
afford maximal information for surgical and interventional
management have developed in parallel to these
techniques.
Summary CT and MR imagings have developed into
robust techniques that yield diagnostic and prognostic
information in patients with a variety of aortic valve and
root pathology. This review includes review of recent
advances in available hardware and software. We also
discuss methods to maximize imaging value in assessment
of BAV, and in patients before and after TAVR.
Keywords Computed tomography � Magnetic resonance
imaging � Aortic valve � 4D Flow � Phase-contrast MRI �Transcatheter aortic valve replacement
Introduction
Imaging assessment of the aortic valve was long a domain
of echocardiography. In recent years, advances in imaging
and post-processing technology have allowed confident
imaging of aortic valve pathology by CT and MRI.
This article is part of the Topical Collection on Cardiovascular
Imaging.
Electronic supplementary material The online version of thisarticle (doi:10.1007/s40134-016-0176-6) contains supplementarymaterial, which is available to authorized users.
& Richard Hallett
Sina Moainie
James Hermiller
Dominik Fleischmann
1 Chief, Cardiovascular Imaging, Northwest Radiology
Network, Cardiovascular Imaging, St. Vincent Heart Center
of Indiana, Indianapolis, IN, USA
2 Adjunct Assistant Professor of Radiology, Department of
Radiology, Stanford University School of Medicine,
Stanford, CA, USA
3 Director of Aortic Surgery, St. Vincent Medical Group, St.
Vincent Heart Center of Indiana, Indianapolis, IN, USA
4 Director of Interventional Cardiology, St. Vincent Medical
Group, St. Vincent Heart Center of Indiana, Indianapolis, IN,
USA
5 Professor of Radiology, Chief of Cardiovascular Imaging,
Director, Computed Tomography, Department of Radiology,
Stanford University School of Medicine, Stanford, USA
123
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DOI 10.1007/s40134-016-0176-6
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Likewise, native aortic valve and aortic root disease,
including protean manifestations of bicuspid aortic valve
(BAV) disease, are well visualized and classified by CT/
MR imaging. Both CT and MRI are valuable, and often
complementary, for assessment of patients with BAV.
Novel techniques including 4D flow MRI have shown
promise for improving consistency and diagnostic yield for
aortic valve assessment. Evolving in tandem with refine-
ments in transcatheter aortic valve replacement (TAVR)
techniques, CT has become a critical tool for TAVR device
sizing, access route selection, detection of anatomic con-
traindications, and important extravascular findings. These
imaging techniques require thorough knowledge of aortic
root anatomy, and an understanding of the imaging tech-
nology utilized for data acquisition.
Anatomy of the Aortic Valve and Root
The aortic valve is an integral part of the aortic root, a
larger complex of structures that serves to separate the left
ventricle from the systemic circulation. As traversed by
blood from proximal to distal, these structures include the
aortic annulus (also called the ‘‘virtual basal ring’’), aortic
valve leaflets, commissures, and interleaflet triangles
[1, 2••, 3]. The leaflets are termed right (R), left (L), and
noncoronary (N). The junction of the sinuses of Valsalva
(SOV) and the ascending (tubular) aorta, representing the
highest point of leaflet attachment, is termed the sino-
tubular junction (STJ) (Fig. 1). The normal aortic valve has
three semilunar leaflets that create a triangular opening in
systole, and show complete central coaptation in diastole.
Variations in development can result in valves that are
unicuspid (single, deformed leaflet), bicuspid (two leaflets
in varying arrangements), or quadricuspid (four leaflets).
Owing to superior spatial resolution, ECG-synchronized
CT provides excellent depiction of aortic root anatomy. A
detailed discussion of aortic root anatomy is beyond the
scope of this article. Recent works are available that pro-
vide a thorough discussion of relevant aortic root anatomy,
structure, and function as well as radiologic-pathologic
correlation [2••, 3].
Technical Developments—CT
Synchronization of the electrocardiogram (ECG) to the
acquired CT dataset is essential to obtain motion-free
imaging of the aortic valve apparatus [4–6]. While ECG
synchronization techniques were conceived in the 1970s
[7] and have been available for clinical use since electron-
beam CT [8], the past decade has seen considerable
refinement in technical scanner specifications and syn-
chronization techniques [9, 10]. Current scanners deliver
rotation times as short as 250 ms and heart rate indepen-
dent temporal resolution of 66 ms. As a result, motion-free
imaging of the aortic root can be reliably obtained in most
patients.
The choice of ECG synchronization technique will
depend on the clinical question. If cine assessment of valve
motion is needed, or if measurements are needed in both
systole and diastole, retrospective ECG synchronization
(gating) is utilized. Retrospective ECG synchronization
results in greater radiation dose than prospective (‘‘step-
Fig. 1 Anatomy of the aortic root. a Blood-pool inversion volume-
rendered (BPI-VR) oblique coronal image. The aortic root consists of
structures from the annulus (virtual basal ring, black arrow) to the
sinotubular junction (pink arrows). The right and left sinuses of
Valsalva are depicted (dashed ovals). The left main coronary artery is
also visualized (arrowhead). b BPI-VR thick slab image looking into
the left sinus of Valsalva. Note the interleaflet triangles (I) the left
leaflet attachment near the sinotubular junction (arrowheads). The
central coaptation point of the commissures is seen in the middle of
the slab (arrow), with the left main coronary ostium visualized
cephalad to this point (Color figure online)
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and-shoot’’) and prospectively triggered, high-speed helical
(Flash mode) acquisitions [11–13]. However, use of ECG-
modulated mA (‘‘ECG pulsing’’) with retrospective tech-
nique allows full diagnostic dose to be administered only in
the segments of the R–R interval that are most important
for diagnosis [14]. This technique can result in dose sav-
ings of 40 % or more compared to standard retrospective
scanning [15••].
The use of automated tube potential selection [15••] and
iterative reconstruction (IR) techniques has also allowed
further reduction in patient radiation dose [16, 17]. IR
techniques utilize complex mathematical modeling (‘‘iter-
ations’’) and more precise modeling of scanner geometry
and noise statistics to more efficiently reconstruct image
data. The end result of IR technique is high-resolution
image quality with less noise, fewer blooming artifacts, and
improved contrast- and signal-to-noise ratios (CNR, SNR)
[18, 19]. IR techniques allow routine image acquisition at
100 kVp, which reduces estimated radiation dose 31 %
versus standard 120 kVp [20]. Recent refinement in IR
techniques, such as model-based IR (MBIR), further
improves image reconstruction quality and allows addi-
tional dose savings [21, 22].
Technical Developments—MRI
Imaging of the aortic valve by MRI is robust, and in many
ways offers complementary information to CT imaging.
Valvular anatomy can be classified; planimetry can be
performed; and the thoracic aorta can be well assessed by
current contrast-enhanced and noncontrast techniques
(Fig. 2). The ability to directly measure flow and calculate
transvalvular gradients by phase-contrast imaging is a clear
advantage for MR imaging. A recent best evidence sum-
mary concluded that MRI and echocardiography were
‘‘equally reliable’’ in assessment of the aortic valve,
although MRI was found to have better inter- and
intraobserver reliability and was better for assessment of
severe aortic stenosis [23].
4D Flow MRI
An emerging technique that directly impacts aortic valve
imaging has been the development of volumetric, time-
resolved three-dimensional phase-contrast (‘‘4D Flow’’)
MR imaging [24, 25••]. Originally described in 1991 by
Pelc et al. [26••], 4D flow has become increasingly clini-
cally useful.
Utilizing data acquisition over many heartbeats, with
respiratory-triggered or respiratory-compensated tech-
niques, PC data for an entire volume can be generated with
seven degrees of information (anatomy in x, y, z planes;
magnitude in x, y, and z planes; and time). Use of a blood-
pool MR contrast agent improves 4D flow data [27, 28]. A
recent consensus statement provides an excellent descrip-
tion of 4D flow technique, corrections, and results as well
as topics of ongoing research [25••]. 4D flow techniques are
valuable for numerous disease states including valvular
disease, aortopathies and aortic dissection, and congenital
heart disease [25••, 29–33].
Briefly, advantages of 4D Flow MRI over 2D-PC tech-
niques include free-breathing acquisition, lack of need for
precise plane placement to capture maximal flow/velocity
data, and the ability to interact with the data offline
(without the patient remaining on the table) on dedicated
processing software. Prescription of a single volume slab
acquires data that can be interrogated to yield flow data
across any plane within that volume (Fig. 3). This is par-
ticularly helpful when multiple 2D-PC acquisitions would
need to be acquired (e.g., congenital heart disease, aortic
Fig. 2 Standard aortic valve assessment by MRI. a 3-chamber
balanced SSFP cine frame shows dephasing jet at and above the aortic
valve (arrows) related to valvular aortic stenosis. LA left atrium, LV
left ventricle. b 3-chamber balanced SSFP cine frame from diastole
shows dephasing jet extending across the aortic valve into the LVOT,
consistent with aortic regurgitation (arrowheads). c Short-axis image
of the aortic valve in systole shows very poor excursion of the three
leaflets (arrows). Valve area tracing (planimetry) showed valve
orifice area of 0.8 cm2, consistent with severe AS
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coarctation), and can decrease time required to complete
the exam. Since 4D flow MRI acquisition is volumetric,
demonstration and quantification of eccentric valvular jets
and flow patterns are enhanced [34].
In patients with severe AS, stratification and manage-
ment decisions are currently based on three parameters:
transvalvular gradient, aortic valve area (AVA), and peak
velocity. While useful, these standard measurements fail to
account for pressure recovery, and do not perform well in
low-pressure/gradient states. These patient populations
include those with normal ejection fraction (EF) with low-
stroke volume and severe AS and low gradients, low EF/
low flow severe AS, and paradoxical AS (severe LVH with
low-stroke volume) [35, 36]. 4D flow MR can more fully
assess these physiologic states by estimating viscous and
turbulent kinetic energy (TKE) losses [29, 37].
Some drawbacks are inherent to 4D Flow techniques.
Acquisition time, initially quite lengthy ([60 min), was
associated with increased motion-related artifacts and
limited the technique to generally healthy (research)
patients [29]. Advances in acquisition techniques and other
technical improvements have decreased scan times to
\20 min, with some centers reporting acquisition times of
5 min or less [38, 39]. Additionally, the large amount of
data generated can produce long reconstruction and post-
processing times. Recent cloud-based service utilizing
massively parallel graphical processing unit (GPU) archi-
tecture has allowed client-based interaction with the 4D
flow data with less time penalty (Video1). 4D flow data are
also susceptible to motion-related artifacts and other arti-
facts inherent to 2D-PC techniques [25, 40]. Recent work
comparing 2D-PC MR with 4D Flow has suggested that
peak flow measurements determined by 4D flow are lower
in magnitude than 2D flow [41, 42]. More study is needed
to more fully understand the precise degree of compara-
bility between the two techniques.
Bicuspid Aortic Valve: Current Imaging with CT/MRI
Bicuspid Aortic Valve: Background
Bicuspid aortic valve (BAV) is a common (1–2 % of
general population) congenital disorder that manifests as a
variable fusion of the aortic cusps and commissures. BAV
is associated with aneurysms of the aortic root and several
patterns of aortopathy involving the thoracic aorta includ-
ing the transverse thoracic aorta [2, 43, 44]. The relative
contributions of the congenital connective tissue disorder
versus effects of altered hemodynamics in BAV aortopathy
remain controversial [45, 46]. Indeed, many now consider
management considerations in BAV patients to be similar
to those with Marfan syndrome; thus imaging considera-
tions may have utility for Marfan and related connective
tissue disease disorders. A recent thorough review provides
further information on diagnosis and surgical management
of these and other aortic root disorders [2].
Fig. 3 4D Flow MRI in a 25-year-old patient with complex
congenital heart disease (double outlet right ventricle, pulmonic
atresia, VSD; status post-Rastelli procedure, RV-PA conduit). Screen
capture from 4D Flow review and measurement software shows
volumetric slab dataset in three orthogonal planes. Measurement of
flow across the aortic valve is performed at the level of the dilated
aortic root, (circular gate, arrowheads), with cardiac output data noted
at right of the image (arrow), approximately 5 L/m. High velocity
flow, indicated by red color, is seen at the RV-PA conduit (**).
Gradient was calculated at 18 mmHg. Focal high velocity jet also
seen within the aortic valve, gradient calculated at 25 mmHg. Note
the eccentric stenotic jet across the aortic valve (red arrow, lower
right panel), which strikes the right lateral wall of the ascending aorta.
Similar types of abnormal flow patterns are implicated in differing
patterns of aortic aneurysm development in BAV patients (Color
figure online)
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Histopathologically, the aortopathy of BAV manifests as
decreased levels of fibrillin-1, increased levels of matrix
metalloproteinases, and cystic medial necrosis within
affected segments of the aortic wall [47–50]. BAV is also
associated with aortic coarctation and up to tenfold
increased risk of aortic dissection (AD) [51–53]. Inheri-
tance is likely autosomal dominant with incomplete pene-
trance; mutations in the NOTCH1 and ACTA2 genes have
been implicated [49, 54]. Interestingly, dilatation of the
aortic root and ascending aorta occurs in BAV patients
without significant valvular dysfunction [55, 56], as well as
family members of BAV patients who themselves are
without BAV [43, 50, 57], suggesting that long-term
familial screening is necessary.
Surgical management guidelines for aortic aneurysm in
BAV patients recommend surgery earlier than tricuspid
aortic valve patients. The Society of Thoracic Surgeons
Clinical Practice guidelines recommend surgery in BAV
patient when the root or ascending aorta exceeds 5.0 cm,
growth rate of[5 mm/yr occurs, or at 4.5 cm if there is a
family history of AD [58••]. Surgical decision-making also
supports an indexed measurement system for aortic
aneurysm measurement, where aneurysm size is indexed to
a patient-specific internal control such as body surface area
(aortic size index [2.75/m2) [59] or the diameter of the
descending aorta. Therefore, imaging specialists can play a
crucial role in BAV patient management by defining both
the presence and morphology of BAV as well as the tem-
poral evolution of thoracic aortic size.
Imaging of BAV
Transthoracic echocardiography (TTE) is generally the
first modality to assess BAV. However, secondary to
limited acoustic windows and adult body habitus, TTE
does not consistently evaluate the mid-distal ascending
and transverse thoracic aorta. Additionally, technical
issues related to heavy calcification and body habitus
may limit assessment; the number and arrangement of
cusps may be unclear in up to 25 % of patients [60]. 3D
TTE may provide significantly better visualization and
classification of BAV [61]. CT and MR imaging allows
determination of BAV morphology in nearly all patients
[62]. BAV morphology can be classified using the sys-
tem described by Sievers and Schmidtke, based on
analysis of 304 surgical BAV specimens [63]. The
number and arrangement of raphes (defined as the con-
joint or ‘‘fused’’ portions of two adjacent leaflets that
become a malformed commissure), the spatial positions
of cusps, and presence of valvular stenosis and/or
insufficiency are important for classification [63, 64]
(Fig. 4).
Fig. 4 Sievers classification of bicuspid aortic valve. Short-axis
diagrams of the aortic valve viewed from the left ventricle (as in CT).
Coronary ostia are noted by the double lines. R right, L left,
N noncoronary. Types are defined by the number of raphes: type 0 is a
‘‘true’’ bicuspid valve with no raphes (Lateral or AP subcategories).
Type 1 represents 1 raphe (red line), and represents three subcate-
gories, L-R, R-N, and N-L. Type 2 consists of valves with two raphes,
with only one subcategory, between L-R and R-N. Type 1, L-R is the
most common (71 %). Additional subcategory designations are
assigned for valvular stenosis (S), insufficiency (I), balanced stenosis
and insufficiency (B), and normal function (No). Adapted from
references ___ and ___. (Sievers and Blaye-Felice articles) (Color
figure online)
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CT is an accurate technique for assessment and classi-
fication of BAV. Classification is most reliable by review-
ing both diastolic and systolic datasets, with the latter aiding
in assessment of BAV raphes [65] (Fig. 5). Calcification is
easily depicted and can be scored in a similar manner to
coronary calcium; high scores correlate with significant
Fig. 5 CT Assessment of
bicuspid aortic valve. a Sievers
type 1, L-R BAV. Diastolic
phase image shows bicuspid
aortic valve. A raphe is
suggested but difficult to
visualize (arrow). The
remainder of the BAV is
vertically oriented and
symmetric (arrowheads).
b Systolic phase image shows
the raphe (arrow) between the
left and right cusps
(arrowheads) to better
advantage, indicating that the
valve is type 1, L-R rather than
type 0, vertical.
NC = noncoronary cusp.
c Sievers type 0 (lateral) BAV.
Diastolic phase short-axis CT
image. Note the symmetric
leaflets and vertical orientation
(arrows). d Systolic phase
short-axis CT image showing
classic ‘‘fishmouth’’ appearance
of symmetric BAV leaflets
(arrows)
Fig. 6 MR Planimetry of bicuspid aortic valve. a Short-axis systolic
image from cine SSFP series. There is a raphe between the right and
noncoronary sinus (arrowheads), consistent with type 1, R-N BAV. A
focus of valvular calcium is depicted as a focal signal void (arrow).
b Planimetry of the valve in systole (blue shaded area) shows an area
of 0.9 cm2, consistent with severe stenosis. c Curve (peak velocity on
y-axis, time on x-axis) from 2D-PC imaging shows peak velocity of
5.5 m/s (green line), consistent with severe stenosis and peak pressure
gradient estimation (modified Bernoulli equation) of [100 mmHg
(Color figure online)
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valvular gradients by echocardiography. Recent work sug-
gests an Agatston score of 1651 as an appropriate cut-off to
identify valves with significant gradient compared to
echocardiographic data [66]. Planimetry can be performed
to assess stenosis and insufficiency; aortic valve area
(AVA) results correlate well with echocardiographic pres-
sure gradients [3, 67, 68].
Routine MRI assessment of aortic valve morphology and
standard velocity/pressure information obtained by 2D-PC
MRI is now standard technology. BAV morphology can be
classified, planimetry performed (Fig. 6), and peak veloci-
ties/transvalvular gradients calculated by standard tech-
niques including balanced steady-state-free precession
(SSFP) cine imaging and 2D-PC assessment of flow.
However, BAV patients have higher incidences of aortic
dissection (AD) and mortality (even with normal-sized
aortas), and considerable variation exists in operative
decision-making in BAV patients with aneurysm [69].
Therefore, additional information may be valuable to tailor
management of BAV patients. 4D flow MRI can acquire
standard measurements, and can provide both qualitative
assessment of abnormal flow patterns and quantitative
information regarding the effect of the pathological flow
patterns [29], potentially becoming a more complete
assessment tool for BAV patients [70].
Aortic dilatation in BAV patients is likely related to a
combination of hemodynamic and tissue factors
[46, 71, 72]. Specific BAV morphology does correlate with
specific phenotypic manifestations in the thoracic aorta.
For example, L-R fusion is associated with larger SOV
Fig. 7 Patterns of aneurysmal disease in bicuspid aortic valve.
a Isolated root aneurysm (arrows), in a patient with Type 1, L-R
BAV. Isolated root dilatation is more commonly seen with this BAV
type. b Ascending thoracic aortic aneurysm without root dilatation, in
a patient with type 1, R-N BAV. MIP image from thoracic MRA
shows an aneurysm of the ascending thoracic aorta (ASC), with
normal-sized aortic root (arrows). Type 1, R-N BAV typically
presents at a younger age, have more valvular stenosis, and show
preferential dilatation of the ascending aorta. c Dilatation of the entire
root and ascending thoracic aorta. Patient with type 1, R-N BAV
exhibits 44 mm aneurysm of the aortic root (arrows), as well as
55 mm aneurysm of the ascending thoracic aorta (ASC). d Preferential
marked dilatation of the ascending aorta. Patient with a Type 0, lateral
BAV. Calcifications of the BAV can be seen (arrows). Note the
preferential dilatation of the ascending thoracic aorta (ASC), reaching
8 cm. There is no dilatation of the transverse thoracic aorta (Tr)
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dimensions, whereas R-N fusion is more commonly asso-
ciated with ascending aortic and arch dilatation [73–75].
Additionally, BAV patients with predominant valvular
stenosis (often L-R fusion phenotype) tend to have larger
SOV measurements, whereas dominant valvular insuffi-
ciency is associated with greater dilatation of the ascending
aorta [75] (Fig. 7). Pathologic flow states at the BAV, as
well as resultant abnormal flow-related changes in the aorta
can be well assessed by 4D flow MRI (Fig. 8).
MRI provides flow velocity information on BAV by
cine and 2D-PC imaging, and MRA provides characteri-
zation of areas of aortic dilatation. 4D flow MRI suggests
that various aneurysmal phenotypes are at least in part
related to the angle of the eccentric jet across the abnormal
valve and resultant regional wall shear stress (WSS) dif-
ferences [70, 74]. 4D Flow MRI also allows estimation of
viscous energy and turbulent kinetic energy (TKE) losses,
and other markers that may prove valuable for clinical
decision-making [37] (Fig. 8).
TAVR: Maximizing Preprocedural Information
Since the first report of placement in a human in 2002 [76],
TAVR has evolved from an experimental procedure into an
accepted tool in treatment of severe, symptomatic AS.
Recently, indications have expanded including valve-in-
valve placement, and clinical trials are now underway with
less severe operative risk populations. Additional access
routes and devices continue to be explored and refined.
Long-term follow-up and comparison to surgical aortic
valve replacement (SAVR) from the initial studies is now
available.
Data from the Placement of Aortic Transcatheter Valves
(PARTNER-1) have shown favorable results in high-risk
aortic stenosis patients undergoing TAVR with the Edwards
SAPIEN Valve, showing similar 5-year mortality rates ver-
sus SAVR [77]. Improved survival vs. SAVR at 2 years in
high-risk patients treated with Medtronic CoreValve was
recently reported [78]. Inoperable patients undergoing
TAVR also showed improved survival and functional status
versus standard treatment [79]. More recently, results of
TAVR in comparison to SAVR were reported for interme-
diate-risk patients in the PARTNER-IIA trial, utilizing the
second-generation Edwards XT valve. TAVR and SAVR
results were similar [80]. Furthermore, patients treated with
the third-generation SAPIEN-3 TAVRvalvewere compared
in a propensity-matched analysis to the SAVR patients from
PARTNER IIA, and TAVR was superior with half the
mortality and disabling stroke at one year [81]. Patient age
has also been shown to be less important, with little differ-
ence in major adverse events and one-year survival reported
in nonagenarians versus other patients [82]. A thorough
assessment of current results, complications, subgroup
analysis, and newer device designs can be found in recent
reviews [83, 84••].
Pre-TAVR imaging is critical—at our institutions CT is
an essential tool. Generation of submillimeter, isotropic
voxels with high spatial resolution, coverage of both the
heart and access vessels in one contrast injection, and
available offline review and interpretation position CT well
as a ‘‘one-stop shop’’ for pre-TAVR assessment. For dis-
cussion of other imaging modalities, the reader is directed
to an excellent review of available imaging modalities and
techniques by Caruso et al. [85].
Fig. 8 4D Flow of BAV. Panel
of images from assessment of
BAV. Note high velocity flow
across the symmetric BAV
(upper left panel, arrowheads).
Eccentric flow extending to
contact the right lateral aspect
of the ascending aorta is noted
(arrow, upper right panel).
Color-coded phase (flow) data
are displayed on the magnitude
data in orthogonal planes on the
lower panels
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The aortic annulus is an oval-shaped, 3D structure [86],
and is especially well suited for CT imaging assessment
(Fig. 9). Unlike standard echocardiography, CT allows full
3D assessment of annular morphology and dimensions,
valvular planimetry [68], and assessment of root geometry.
In the same scanning setting, CT can assess obstructive
coronary artery disease (such that invasive coronary
angiography may not be required) [87], determine access
routes [88], and identify significant extracardiac incidental
findings, some of which could represent contraindications
to TAVR. Up to 19 % of patients have iliofemoral access
vessel caliber unsuitable for access; necessitating
transapical or other access routes [89]. Up to two-thirds of
patients have incidental findings at TAVR CT, and up to
half of these require additional workup [89, 90].
Unsuspected malignancy has been detected in 4 % of
patients [89]. These findings reinforce the need for metic-
ulous review of extracardiac CT data.
CT imaging for TAVR planning can be performed with
a number of different protocols, including single or double
injections. Acquisition of the ECG-synchronized imaging
of the heart as well as nonsynchronized CTA of available
access vessels is necessary to determine the safest route for
accurate device delivery. The protocol for single injection
CT acquisition one institution is available in Table 1. Since
many TAVR candidates have underlying chronic kidney
disease, CT acquisition protocols are also adapted to
acquire diagnostic datasets at lower CM doses [91]. The
risk of exacerbating pre-existing renal dysfunction appears
to be low when the amount of CM given is no more than
Fig. 9 CT assessment of aortic root for TAVR planning. a Short-axis
volume-rendered CT image shows heavily calcified (arrows),
trileaflet aortic valve. The origin of the left main coronary artery is
noted (arrow). b Short-axis measurement of the annulus with
measurements of major and minor axis, area, and perimeter for
device sizing. Note the absence of annular calcification; annular
calcification can predispose to paravalvular aortic regurgitation after
device placement. c Long-axis image of aortic root (perpendicular to
image 9B) shows measurement of distance from annulus to left main
coronary artery (arrow). Distances of\10 mm may preclude current
TAVR device placement, secondary to potential for coronary
compromise. d Volume-rendered oblique coronal image through the
aortic root shows measurements for TAVR. The left main coronary
artery is shown (arrow). Distances from the annulus to LM origin
(15.9 mm) and from the annulus to the sinotubular junction (dotted
line, 20.1 mm) are listed. Calcifications at the aortic valve are
displayed in green (Color figure online)
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twice the estimated glomerular filtration rate (eGFR) [92].
Therefore, we limit CM volumes in patients with renal
disease that are no more than twice the eGFR, adjusted for
body weight: [CM (mL) = 2 9 eGFR9pt. weight (kg)/
75 kg].
Accurate measurement of the aortic annulus is impera-
tive, as undersizing of the annulus (and device) leads to
higher incidences of paravalvular aortic regurgitation
(PVR) [86, 93, 94]. Moderate to severe PVR, in turn, has
been shown to be an independent predictor of mortality.
Fig. 10 Paravalvular aortic regurgitation (PVR) after TAVR.
a Short-axis image at the aortic annulus in diastole shows a gap
between the TAVR device and the left lateral margin of the annulus
(arrow). L = device flow lumen. b Short-axis image through the
sinuses of Valsalva show eccentric positioning of the device,
restricted by heavily calcified leaflets (arrowheads). c Longitudinal
image (perpendicular to figure B) shows communication along the
margin of the device (arrowheads), allowing severe PVR
Fig. 11 Annular/subannular
calcification, planning for
TAVR. a Oblique sagittal MIP
image through the aortic root
shows a large, angulated
calcification (arrow) extending
from the annulus (arrowheads)
into the LVOT, eventually
becoming embedded in the
interventricular septum.
b Short-axis image of the LVOT
below the annulus shows the
calcification beneath the L/R
leaflets (arrows). c Volume-
rendered hollow image shows
extent of valvular, annular,
subannular, and LVOT
calcification. Note the heavy
calcification at the leaflet and
annular level (arrow)
49 Page 10 of 14 Curr Radiol Rep (2016) 4:49
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Mild–to-moderate oversizing (10–15 % annular area) [95]
has been recommended to decrease PVR without increas-
ing risks of annular rupture. CT-sizing protocols have been
shown to lead to a larger implanted valve (vs. TEE) in up to
one-third of TAVR patients [95]. Not all authors have
found this hypothesis to hold true; Freeman et al. reported
no consistent relationship between annular sizing by CT
and risk of patient-prosthesis mismatch (PPM), and pos-
tulate that PPM may be related to a native annulus that is
undersized relative to patient body size. [96].
The aortic annulus is a dynamic structure, and dimen-
sions are larger during systole, therefore systolic mea-
surements (25-35 % R–R interval, or absolute time of
200–250 ms after R-wave) are recommended to avoid
device undersizing [95, 97••]. The exact choice of systolic
reconstruction phase is controversial; in our practice, we
choose the systolic phase with maximal valve opening and
least motion-related artifact. Perimeter measurement is also
greatest in systole although may be less influenced by
changes in cardiac phase; this may be due to annular
reshaping. Depiction of the amount and location of
valvular, annular, and subannular LVOT calcium is a
predictor for post-TAVR PVR [98, 99], potentially inter-
fering with complete apposition of the device to the aortic
wall [98] (Fig. 10). Extensive calcification extending into
the LVOT may require higher positioning of the device to
decrease PVR risk (Fig. 11). CT can also determine the
line of perpendicularity and optimal C-arm angles for flu-
oroscopic monitoring during TAVR, eliminating the need
for contrast aortography while allowing optimal device
deployment visualization [100, 101].
Vascular access route determination is a critically
important part of the TAVR planning process. CT robustly
depicts vascular calcifications and centerline methods
provide accurate minimum luminal measurements, leading
to change in access direction in up to 43 % of patients
[102, 103].
CT can provide adequate access information for stan-
dard transfemoral (TF), transapical (TAp), and potential
direct/transaortic (Tao) and transsubclavian (TS) routes.
We utilize transsubclavian (TS) as an alternative access
when other access routes are unavailable, but avoid it in
patients with prior CABG or extensive vessel tortuosity.
Recently described TAo access [104] allows accurate
device delivery in patients with challenging access anat-
omy with potentially fewer complications. TAo access
requires only an upper ministernotomy or minithoracotomy
(right parasternal), which causes less respiratory compro-
mise than a complete ministernotomy for TA access. TAo
access also provides an easier path for sheath placement,
and may result in less direct myocardial injury. Access
must be obtained at least 5–7 cm (depending on device)
above the level of the valve; a ‘‘porcelain aorta’’ is a
contraindication to TAo access. We find preprocedural 3D
mapping images and/or video improves operator confi-
dence and understanding of nontraditional access routes
(video 3).
Conclusion
Recent advances in CT and MRI technology have allowed
introduction of techniques that provide robust functional
and anatomic information on aortic valve disease. 4D Flow
MR imaging is an emerging technique that allows volume
acquisition of phase-contrast MR data that can be interro-
gated offline (including cloud-based platforms) in any
plane. Current assessment of the spectrum of BAV disease
brings together complementary information from CT and
4D flow MR applications. Advances in CT imaging hard-
ware, protocols, and post-processing techniques have pro-
ven beneficial to the growing number of patients
considered for TAVR procedures. Continual refinement of
aortic valve imaging techniques and emerging new tech-
nologies can be expected to add additional benefits in the
future.
Funding James Hermiller reports personal fees from Edwards and
Medtronic.
Compliance with Ethical Guidelines
Conflict of Interest Richard Hallett, Sina Moainie, and Dominik
Fleischmann each declare no potential conflicts of interest.
Human and Animal Rights and Informed Consent This article
does not contain any studies with human or animal subjects per-
formed by any of the authors.
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