Chuanli Cheng1,2, Chao Zou1, Hairong Zheng1, and Xin Liu1
1Shenzhen Institutes of Advanced Technology, Chinese Academy of Sciences, Shenzhen, China, People's Republic of, 2University of Chinese Academy of Sciences, Beijing, China, People's Republic of
Synopsis
A novel two-point fat water separation
method using safest path region growing with self-feeding phasor estimation
algorithm is proposed. The phasor map is estimated by multiresolution region
growing scheme where the seed pixels identification and region growing scheme
is performed independently between coarser resolutions, avoiding the erroneous
propagation between resolutions. The “self-feeding” mechanism when merging the
phasor maps ensures the reliability of seed pixels selection at the finest
resolution. The algorithm was tested on c-spine and abdomen data and shown to
be robust in fast varying field and disjoint areas.Introduction
Two-point fat water separation methods are preferred in some fast applications
such as dynamic imaging and abdominal imaging where fat needs to be suppressed
homogeneously. The original two-point method proposed by Dixon
1
acquired two images at echo times (TEs) with fat and water in and out of phase.
The two-point methods are then generalized to flexible TEs
2,3. Although
these methods have been applied successfully to many cases, there still exist
challenges with multiple disjoint regions or drastic change of B
0. In
this paper, a novel two-point method using safest path region growing with self-feeding
phasor estimation algorithm is introduced for robust fat water separation.
Theory
Our method has three
main features: multiresolution scheme, safest path region growing scheme and self-feeding
mechanism. Firstly, the seed pixels identification for region growing is
performed independently at different resolutions. The lower resolution source images
are obtained by spatially filtering the original images with low pass filters
and down-sampling at a certain rate [M
j,N
j],
j=
1,
2,
3, …,
J. Then, the candidate phasor solutions
for each pixel are calculated using the method proposed by Eggers et al
2.
Seed pixels are identified according to two criteria: (1) adequate SNR; (2)
uniqueness of the true solution. The advantage of multiresolution scheme is
that more seed pixels can be found in lower resolution in assumption of field
smoothness, as indicated in Figure 1 using simulation data. Second, for the
region growing scheme, the safest path is maintained based on the SNR of the
pixels, the number of neighboring seed pixels, and threshold for phasor
differences between neighboring pixels, which makes the region growing path
more robust in low SNR areas. Starting from the seed pixels, the region growing
scheme is executed to obtain the phasor map in each resolution. The low
resolution phasor maps are then propagated to the finest resolution directly.
For each pixel at the finest resolution, the phasor closest to the phasor
solution of the corresponding pixel at lower resolution is chosen. Since a
group of phasor maps at different resolutions are obtained, the propagation
step is also implemented independently between different resolutions, and a
group of phasor maps at the finest resolution is consequently derived. Third, a
self-feeding mechanism is introduced to merge the phasor maps into one phasor
map. The pixels with the consistent phasor solution from all the resolutions
are identified as seed pixels at the finest resolution, whereas the left pixels
with inconsistent phasor solution are reset to underdetermined, as shown in
Figure 2. The region growing scheme is applied again to obtain the final
phasor map followed by smoothing. The “self-feeding” mechanism ensures the
reliability of seed pixels selection at the finest resolution. Figure 3 shows the flowchart of the proposed
method.
Materials and Methods
The
proposed method was tested on c-spine and abdomen data. Two volunteers with
informed consent (IRB approved) were recruited. The MRI scan in c-spine/abdomen
was implemented on a 3T system (Siemens, TIM TRIO, Erlangen, Germany) with a
FLASH sequence. The basic protocols for the study were (c-spine/abdomen): TR = 200/50ms,
matrix = 320×240/256×152, slice thickness = 3/6mm, flip angle = 30°/25°,
TE = 4.64/5.51ms.
The algorithm
was implemented in MATLAB (Mathworks, NATICK, USA). Four resolutions with
down-sampling rates [4 4], [6 6], [8 8] and [10 10] were used to obtain the
coarser resolution images.
Results
In all slices,
fat/water images and phasor maps were successfully derived from two-point images.
Figure 4 shows the separated fat/water images and the phasor maps of a sagittal
slice of c-spine and a transversal slice of abdomen. The results show that the
algorithm works well with the disjoint area (such as chin, liver and arm) and
fast varying field area in the neck.
Discussion
Although
the SNR of the reconstructed water/fat images by the proposed two-point method tends
to be lower in comparison with three-point methods, the scan time is decreased as
the proposed method is a flexible two-point method with no constraint on TEs. Different
from traditional two-point methods, the phasor map in this paper is estimated
by multiresolution region growing scheme where the seed pixels identification
and region growing scheme is performed independently between coarser
resolutions, avoiding the erroneous propagation between resolutions. Besides, the
“self-feeding” mechanism when merging the phasor maps ensures the reliability
of seed pixels selection at the finest resolution.
Conclusions
A
novel two-point fat water separation method using safest path region growing
with self-feeding phasor estimation algorithm is proposed. It is shown that the
algorithm is robust when applied to regions with fast varying field and
disjoint areas.
Acknowledgements
This work was supported by the National Natural Science Foundation of China (No. Y320241001, Y320331001, Y320221001 and 11504401) and the Shenzhen Fundamental Research Project (No. JCYJ20150521094519487)References
1. Dixon WT.
Simple proton spectroscopic imaging. Radiology 1984;153(1):189-194.
2. Eggers H,
Brendel B, Duijndam A, Herigault G. Dual-echo Dixon imaging with flexible
choice of echo times. Magnetic resonance in medicine 2011;65(1):96-107.
3. Berglund J,
Ahlstrom H, Johansson L, Kullberg J. Two-point dixon method with flexible echo
times. Magnetic resonance in medicine 2011;65(4):994-1004.