Lixing Ren1,2, Xiaowei He2, Dandan Zheng3, and Enhua Wu2,4
1University of Chinese Academy of Sciences, Beijing, China, 2The State Key Lab. of CS, Institute of Software, Chinese Academy of Sciences, Beijing, China, 3Clinical Science, Philips Healthcare, Beijing, China, 4University of Macau, Macau, China
Synopsis
Understanding the nature of the pressure changes
is crucial for diagnosis and therapy strategy optimization for aortic aneurysm.
4D flow MRI had offered the opportunity to assess 3D blood flow
characteristics. However, the pressure quantification is still a challenge due
to the low signal-to-noise ratio and the partial volume effects near the wall.
The focus of this work is to address this deficiency by proposing a novel
workflow of direct pressure estimation based on simulated noisy 4D flow MRI data.
Introduction
In aortic
aneurysm, which is a common cause of morbidity and mortality1, the
spatial distribution and temporal changes of pressure in aortic are critical in
initiating complications such as dissection and rupture. Understanding the
nature of these pressure changes is crucial for diagnosis and therapy strategy
optimization. 4D flow MRI had offered the opportunity to assess 3D blood flow
characteristics. However, the pressure quantification is still a challenge
because of the low signal-to-noise ratio and the partial volume effects near
the wall2. The focus of this work is to address this deficiency by
proposing a novel workflow to study direct pressure estimation based on simulated noisy
4D Flow MRI data.Methods
To evaluate the accuracy of pressure estimation
for 4D Flow MRI data tainted by noise, blood is modeled as an incompressible
inviscid fluid governed by the following Navier-Stokes equations$$\frac{\partial \mathbf{u}}{\partial t}=-\mathbf{u}\cdot \triangledown \mathbf{u}-\frac{1}{\rho}\triangledown p, subject\;to\;\triangledown \cdot \mathbf{u}=0$$where $$$\mathbf{u}$$$ is
blood velocity, $$$p$$$ is blood pressure and blood density $$$\rho$$$ is set to $$$1060kg/m^{3}$$$. Figure
1 demonstrates an overview of our estimation-simulation scheme.
Synthetic
data. A segmented aortic arch is selected as the vessel
wall for blood simulation. Velocity profiles extracted from the in vivo
measurements and zero pressure were used as inlet and outlet boundary conditions
(BCs), respectively. A standard finite volume method (FVM) was used to generate
velocity and pressure sequences over one cardiac cycle. To mimic the
acquisition of 4D Flow MRI data, both the 3D velocity and pressure fields were
extracted from the sequence every 40ms. During the extraction, white noises with
different intensities were added to mimic experimental data with uncertainty.
Pressure computation.
To estimate the pressure field based on two successive
velocity fields, a variational energy formulation is proposed as follows $$E^{n+1}=(\mathbf{u}_s^{n}-\frac{\delta t}{\rho}\triangledown p)^{T} \mathbf{W}(\mathbf{u}_s^{n}-\frac{\delta t}{\rho}\triangledown p)+\lambda (\mathbf{u}_s^{n}-\frac{\delta t}{\rho}\triangledown p-\mathbf{u}_s^{n+1})^{T}\mathbf{W}(\mathbf{u}_s^{n}-\frac{\delta t}{\rho}\triangledown p-\mathbf{u}_s^{n+1})$$where $$$\mathbf{u}_s^{n}$$$ and $$$\mathbf{u}_s^{n+1}$$$ denote the extracted velocity field at time n
and n+1, $$$\delta t$$$ denotes the time interval (which is 40ms in
our current setting), $$$\mathbf{W}$$$ is
a diagonal matrix with each entry representing the fraction of blood occupying each
voxel. Minimizing the first term of $$$E^{n+1}$$$ with respect to pressure $$$p$$$ is equivalent to enforcing $$$\mathbf{u}_s^{n}$$$ to be divergence-free3. Minimizing
the second term of $$$E^{n+1}$$$ guarantees the final velocity should not
deviate too far from the exacted velocity $$$\mathbf{u}_s^{n+1}$$$. $$$\lambda$$$ is a positive control parameter to balance the
effects of above two terms.Results
Figure 2 shows a comparison of pressure estimation
error compared to the CFD-generated pressure field, where 10% white noise were
added to CFD-generated velocity fields during the velocity extraction. To
compare the effectiveness of our direct pressure estimation method, an
alternative solution involving divergence-free smoothing (DFS)4 for $$$\mathbf{u}_s^{n}$$$ and $$$\mathbf{u}_s^{n+1}$$$ is also implemented, it can be noted that the
pressure field is sensitive to velocity smoothing. Instead, our direct
variational pressure estimation method is able to decrease the pressure estimation
error up to 95%. Additionally, the pressure estimation accuracy with different
intensities of white noise were examined in Figure 3, corresponding to white
noise intensities of: 0%(i.e., no noise), 5%, 10%, 15% and 20%.Discussion
Computational results for pressure show that
the accuracy of pressure estimation could be largely affected by noise. Velocity
smoothing helps to reduce the divergence error in velocity fields,
nevertheless, it does not help improve the accuracy in computing the pressure
field according to our experiments. Our direct variational pressure computing method
shows improved accuracy in resisting noise during acquisition. Concerning
limitations, this study did not asses the accuracy of our method on actual 4D
Flow MRI imaging data yet. Further evaluation is required to confirm the
accuracy compared to other boundary conditions5, numerical solvers6
as well as pressure measured by intravascular catheterization.Conclusion
A direct variational
approach applicable to wall-bounded flow has been developed for computing
pressure field from velocity data generated from CFD simulation. The results
indicate that it has a good anti-noise capability. It is expected to improve
the estimation accuracy of pressure required for the reliable diagnosis of
cardiovascular diseases with 4D flow MRI. Acknowledgements
This work was supported by the the National Key
R&D Program of China (No. 2017YFB1002700), the National Natural Science
Foundation of China (No.6187070657) and Youth Innovation Promotion Association,
CAS (No.2019109).References
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