Renee Miller1, Arunark Kolipaka2, Vicky Wang3, Martyn Nash3, and Alistair Young1
1Anatomy with Radiology, University of Auckland, Auckland, New Zealand, 2Radiology, Biomedical Engineering and Internal Medicine, The Ohio State University Wexner Medical Center, Columbus, OH, United States, 3Auckland Bioengineering Institute, University of Auckland, Auckland, New Zealand
Synopsis
In this study, we examined the determinability of
anisotropic stiffness parameters using finite element analysis simulations of
harmonic steady-state wave behaviour. Two
simulation experiments, of cylindrical phantom and left ventricular geometries,
and one phantom experiment using magnetic resonance elastography (MRE) were
carried out. The transversely isotropic material properties were determined
using a least-squares optimisation algorithm by matching a modelled
displacement field to the reference, or MRE, displacement field. The results
showed that the parameters were uniquely identifiable even in the presence of
noise.Purpose
The purpose of the study was to investigate the identifiability
of homogeneous, transversely isotropic, linear elastic material properties from
a displacement field obtained using magnetic resonance elastography (MRE). In
addition, the study investigated using finite element modelling (FEM) as an
inversion method which takes into account a subject-specific geometry and
realistic boundary conditions in order to solve for homogeneous and anisotropic
material properties.
Methods
FEM Simulations: Harmonic displacement was simulated in two
models, a cylinder and LV geometry with a histological muscle fibre field (Figure
1a
and Figure
2b).
Abaqus 6.13 (Dassault Systèmes Simulia Corp., Providence, USA) was used to
simulate the steady-state harmonic motion; Gaussian noise was added to the
displacement field; and a least squares objective function was used to
determine the optimal transversely isotropic material properties by minimizing
the difference between modelled and reference displacement fields. A
Monte-Carlo simulation (n=30) was run, randomly generating the Gaussian noise
distribution for each simulation. Four parameters were optimised: structural
damping coefficient (s), transverse Young’s
modulus (E1), fibre Young’s
modulus (E3) and Poisson’s
ratio (v). In the reference model,
these parameters were set to: s =
0.25, E1 = 18.0 kPa, E3 = 60.0 kPa and v = 0.495. A parameter sweep was run and
the determinability of the four parameters was further evaluated based on three
identifiability criteria obtained from the Hessian at the minimum of the
objective function. The three criteria were: 1) the D-optimiality criterion
related to the volume of the indifference region, 2) the eccentricity criterion
related to the ratio of the most identifiable to least identifiable parameter,
and 3) the M-optimality criterion related to the parameter interaction.
MRE Experiment: A cyclindrical phantom (r = 76.2 mm and h = 127 mm) was vibrated at 60 Hz using a pneumatic driver and imaged using a GRE MRE sequence to collect wave images at four phase offsets relative to the harmonic displacement in a 3T MRI scanner (Tim Trio, Siemens Healthcare, Germany). In the FE model, displacements from the MRE images were applied on all sides of the phantom. A transversely isotropic material law was used and the fibre direction was arbitrarily set to run longitudinally through the phantom. A least squares objective function was used to minimize the difference between modelled and MRE displacements, at the internal nodes, in order to determine the optimal material properties.
Results
Results from the two Monte-Carlo simulation experiments and
the phantom material parameter optimisation are listed in Table
1.
The D-optimality criterion for each experiment was large
which showed that the volume of the indifference region, or minimum, was small,
and hence identifiable. The parameters were largely independent of one another,
based on the M-optimality criterion values of 0.84 and 0.94, for the cylinder
and LV experiments, respectively. When parameters are completely independent, the
M-optimality value is one. The eccentricity criteria were greater than one for
each case indicating that the parameters are not equally identifiable.
The average shear stiffness of the phantom has previously been
measured to be 5.6 kPa using local frequency estimation (LFE), a common
inversion algorithm used to calculate isotropic shear stiffness from MRE displacement
maps1. Since the material is
isotropic, the shear modulus can be equated to a Young’s modulus of 16.8
kPa. The Young’s modulus determined from the FE method differed from the LFE
method by 5%.
Discussion
The
Monte-Carlo simulations with added Gaussian noise resulted in values which were
extremely close to the true parameters for both the cylinder and LV geometries.
The parameter sweeps also revealed one clear global minimum within the
parameter space (Figure 1b and Figure
2b). Since the parameters are largely independent
of one another, each eigenvector is primarily associated with one parameter
direction. The size of each eigenvalue gives relative information on the
determinability of the corresponding parameter. In both the cylindrical and LV
simulations, the Poisson’s ratio was the least identifiable parameter when
compared with the damping coefficient and Young’s moduli. In the phantom
experiment, between
v = 0.4995 and
v = 0.4998 (the optimal value), the
objective function only changed by %0.3. Above 0.4995, Poisson’s ratio had
little effect on the objective function. In subsequent experiments, the
Poisson’s ratio will be fixed to save valuable computational time without
sacrificing accuracy of the other parameters.
Conclusion
Overall, this initial work shows that using displacement data
from MRE to identify anisotropic material properties is a well-posed problem
even in the presence of noise.
Acknowledgements
This research was supported by an award from the National
Heart Foundation of New Zealand and by the NeSI high performance computing
facilities; American Heart Association# 13SDG14690027 and NIH#R01HL124096. References
1. Manduca, a., et al., Spatio-temporal directional filtering for
improved inversion of MR elastography images. Medical image analysis, 2003.
7: p. 465-73.