Corina Kräuter1,2, Ursula Reiter1, Clemens Reiter1, Volha Nizhnikava1, Marc Masana3, Albrecht Schmidt4, Michael Fuchsjäger1, Rudolf Stollberger2, and Gert Reiter5
1Department of Radiology, Medical University of Graz, Graz, Austria, 2Institute of Medical Engineering, Graz University of Technology, Graz, Austria, 3Computer Vision Center, Universitat Autònoma de Barcelona, Barcelona, Spain, 4Department of Internal Medicine, Medical University of Graz, Graz, Austria, 5Research and Development, Siemens Healthcare Diagnostics GmbH, Graz, Austria
Synopsis
Automated mitral valve vortex ring evolution analysis
from magnetic resonance 4D flow data is feasible. However, time-consuming
manual segmentation of the left ventricular blood pool represents a bottleneck.
We simulated speed-up and variability of manual segmentation and analyzed the
impact on vortex ring parameters. Automated mitral valve vortex ring extraction
and analysis yielded robust results, even when applying the end-diastolic
segmentation mask to all cardiac phases. Error analysis of vortex ring
parameters showed that under-segmentation of the ventricular blood pool should be avoided.
Speeding up segmentation by using only the end-diastolic mask enables clinical
mitral valve vortex ring analysis studies.
Introduction
The
mitral valve (MV) vortex ring is a three-dimensional swirling blood flow
structure forming during diastole that is assumed to store kinetic energy1
and redirect blood entering the left ventricle (LV) towards the aorta.2,3
It was shown that the temporal evolution of the MV vortex ring can be extracted
from time-resolved three-directional cardiovascular
magnetic resonance phase-contrast imaging (4D flow).4,5 However, vortex ring
evolution analysis is limited by time-consuming manual segmentation of the LV cavity
throughout the cardiac cycle, which is either performed directly on 4D flow
magnitude images or on balanced steady-state free precession (b-SSFP) images of
a separate scan.6 Aim
of this study was to evaluate the sensitivity of automated MV vortex ring
extraction5 and vortex ring parameters to speeding up LV
segmentation by reducing the number of short-axis slices on the one hand and
using the end-diastolic segmentation mask for all phases on the other hand, as
well as to under- and over-segmentation of the LV blood pool.Methods
13
subjects (male/female 6/7; age 58.3±6.1 years) underwent 4D flow imaging at 3T
(Magnetom Skyra, Siemens Healthcare, Erlangen, Germany). A stack of slices
covering the LV was acquired using a two-dimensional retrospectively-ECG-gated
phase-contrast sequence with three-directional velocity encoding (temporal
resolution 41 ms interpolated to 30 cardiac phases, echo time 3.1 ms, flip
angle 12-20°, voxel size 1.8x2.5x4 mm3, velocity encoding 100 cm/s, two-fold
averaging). Prototype software (4DFlow, Siemens Healthcare, Erlangen, Germany)
was used for pre-processing of velocity vector fields (phase offset error
correction, phase unwrapping) and manual LV segmentation on reconstructed short-axis
magnitude images (slice distance d = 3.4 mm). Automated
extraction and analysis of MV vortex ring evolution were performed by in-house software5 implemented in Matlab
(MathWorks Inc., Natick, MA), which included detection of vortex ring
core and region (Figure 1) as well as calculation of vortex ring volume, mean vorticity, absolute kinetic energy and relative kinetic energy (normalized by vortex ring volume) for each phase. To assess the sensitivity of MV vortex ring analysis to
LV segmentation, three experiments using different segmentation masks were
performed (Figure 2). First, the slice distance of short-axis segmentation was
increased step-wise by taking each second (2d), third (3d), fourth (4d), fifth
(5d) and sixth slice (6d), respectively, leading to a maximum slice distance of
20.4 mm. Second, the segmentation mask at end-diastole (maskend-dia)
was applied to all cardiac phases. Third, the segmentation masks of all phases
were eroded (maskerode) and dilated (maskdilate) by one
voxel, respectively. Pair-wise comparisons of all
segmentation masks with the fully segmented control condition regarding vortex
ring existence at each phase were performed using kappa statistics. In vortex
ring phases common to both segmentation masks, overlap ratios of vortex core
and vortex region, respectively, were assessed using the dice coefficient. Early
and late diastolic MV vortex ring peak parameters determined under control
condition and with each segmentation mask were compared using paired t-test,
considering p < 0.05 as significant.Results
856±140 short-axis slices per subject were manually segmented in the control condition.
Early and late diastolic MV vortex rings were detected in each subject for all
segmentation approaches. Comparisons with the control condition regarding
vortex ring existence and overlap of vortex core and region, respectively, are
shown in Table 1. All segmentation masks yielded almost perfect agreement for
vortex ring existence and, apart from maskerode, very good to
excellent vortex ring core and region overlap ratios. Increasing slice distance
yielded a slight decrease in comparison scores. Figure 3 shows error plots for
early and late diastolic peak vortex ring volume, mean vorticity, and
absolute and relative kinetic energy for all segmentation masks. Most
significant differences to the control condition were observed for maskerode
and maskdilate, with higher absolute mean errors (up to 13%) for
maskerode. While the other segmentation masks also yielded sporadic
statistically significant differences, their absolute mean errors were small
(<6.8% for peak volume, <1.1% for peak mean vorticity, <3.2% for
peak absolute kinetic energy and <2.5% for peak relative kinetic energy).Discussion
Automated
MV vortex ring extraction is robust with respect to fast manual segmentation
approaches and is less sensitive to over- than to under-segmentation. Increasing
the segmentation slice distance not only showed that a speed-up of segmentation
on 4D flow magnitude images is feasible, it also indicated that using
registered LV contours from b-SSFP short-axis cine images, which are typically
acquired with approximately 10 mm slice distance, might work for automated MV
vortex ring extraction. If LV segmentation is performed only at one
end-diastolic phase, further substantial speed-up can be achieved. maskend-dia
yielded only a slightly lower vortex core overlap ratio than the ones of the
slice distance experiment while excellently agreeing with the control condition
regarding vortex ring existence and vortex region. Furthermore, vortex ring
parameters determined with maskend-dia showed low absolute mean errors. The finding that under-segmentation yields larger errors than
over-segmentation is reasonable as in the former case parts of vortex ring
core and region might be missed in the calculations.Conclusion
Reducing
LV segmentation to one end-diastolic phase enables clinical MV vortex ring
analysis studies with large patient cohorts. Under-segmentation of the LV blood
pool should be avoided.Acknowledgements
We thankfully acknowledge the support of the
OeNB Anniversary Fund (Grant No. 17934), the Generalitat de Catalunya (Grant
No. 2019FI_B1_000198) and the ESOR fellowship 2018/19.References
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