Uten Yarach1,2, Matthew Bernstein1, John Huston III1, Myung-Ho In1, Yi Sui1, Daehun Kang1, Yunhong Shu1, Erin Gray1, Nolan Meyer1, and Joshua Trzasko1
1Radiology, Mayo Clinic, Rochester, MN, United States, 2Department of Radiologic Technology, Faculty of Associated Medical Sciences, Chiang Mai University, Chiang Mai, Thailand
Synopsis
Single-polarity
reference scan-based paradigms are routinely used to combat Nyquist ghosting
artifacts, they often fail to the fully suppress them because of statistical
biases in estimated correction coefficients that result from noise and
off-resonance effects. Prior work has shown that use of dual-polarity
reference scans can mitigate the latter. In this work, we propose that this
concept can be generalized to enable robust Nyquist ghost correction (NGC)
directly from two reversed-readout EPI acquisitions – without explicit
reference scanning. In-vivo results show the similar trends as in phantom
examples, with the proposed-NGC mitigating aliasing artifacts
representing up to 20% intensity errors.
Background and Purpose
Nyquist ghosting is a common artifact in echo planar
imaging (EPI)1-3 caused by: 1) readout gradient-induced low-order
eddy currents; and 2) receive chain imperfections (e.g., group delay). These
effects impose phase modulations of which polarity alternates with readout
direction (i.e., even or odd), which causes ghost artifacts to appear at half
field-of-view (FOV) intervals. Ghost artifacts degrade image interpretability and
compromise quantitative measurement validity4,5. The Nyquist ghost
related to low order concomitant fields may be compensated in realtime6,7.
In practice, although single-polarity reference scan-based paradigms are routinely
used to combat Nyquist ghosting, they often fail to the fully suppress them because
of statistical biases in estimated correction coefficients that result from
noise and off-resonance effects. Prior work3,8-10 has shown that use
of dual polarity reference scans can mitigate the latter. In this work, we propose
that this concept can be generalized to enable robust Nyquist ghost correction
(NGC) directly from two reversed readout EPI acquisitions – without explicit
reference scanning. We derive a model-based process for directly estimating
statistically optimal NGC coefficients from multi-channel k-space data, present
robust and efficient numerical procedures for performing this task, and
experimentally demonstrate its corrective advantages.Methods
I. Reverse Readout EPI Acquisition: A reverse readout polarity EPI acquisition
comprises performing two phase-encoded EPI acquisitions, whose readout gradient
polarities have opposite sign at onset (see Fig. 1). After temporally Fourier
transforming the raw EPI dataset (before ramp resampling, if needed) along the
readout direction, the mth sample of the nth readout line of an EPI acquisition can be
modeled as:
$$g_{n,\pm}[m,c]=H_{n,\pm}(\alpha,\beta)[m]f_n[m,c]+\epsilon_{n\pm}[m,c]---(1)$$
where c
is
the coil index, "$$$\pm$$$"
denotes readout gradient polarity, $$$H_{n,\pm}[m]=e^{\pm(-1)^nj(\alpha{m}+\beta)}$$$
is
the system response function,
$$$\alpha$$$ and
$$$\beta$$$
are
the unknown system coefficients9,
is
the actual k-space signal, and $$$ε_{\pm}$$$
is
zero-mean Gaussian noise with
(CxC) coil
covariance $$$\Psi$$$ . The reversed readout data set can be written
in ensemble (2MxC)
as:
$$g_n=\begin{bmatrix}g_{n,+}\\g_{n,-}\end{bmatrix}=\left(I\otimes\begin{bmatrix}H_{n,+}(\alpha,\beta)\\H_{n,-}(\alpha,\beta)\end{bmatrix}\right)f_n+\begin{bmatrix}\epsilon_{n,+}\\\epsilon_{n,-}\end{bmatrix}---(2)$$
where $$$\xi=[\alpha\quad\beta]^T$$$
and $$$\otimes$$$
is
Kronecker’s product.
II.
Proposed System Delay Estimation: The system coefficient
vector $$$\xi$$$
and unmodulated
k-space signal $$$f$$$
can be determined from (2) via maximum
likelihood (ML) estimation, which comprises solving:
$$\mathop{\min}_{f\in\mathbb{C},\xi\in\mathbb{R}}\left\{J(f,\xi)\triangleq\sum_{n=1}^{N}\sum_{c=1}^{C}\left\Vert\Phi_n(\xi)f_{n,c}-g_{n,c}\right\Vert^2_{\psi^{-1}}\right\}---(3)$$
The optimizing k-space signal
estimate is $$$f_n=\frac{1}{2}\Phi^*_n(\xi)g_n$$$
, where “*” denotes the
Hermitian transpose. Variable Projection11
(VARPRO) of $$$f$$$
into
$$$J(\cdot)$$$
reduces the dimensionality of (3) to:
$$\mathop{\min}_{\xi\in\mathbb{R}}\left\{J(\xi)\triangleq\sum_{n=1}^{N}\sum_{c=1}^{C}\left\Vert(\frac{1}{2}\Phi_n(\xi)f_{n,c}-I)g_n\right\Vert^2_{\psi^{-1}}\right\}\equiv\sum_{m=1}^{M}|u[m]|cos\Big(2\delta^T _m B \xi-\angle u[m]\Big)---(4)$$
where
$$$\delta_m$$$ denotes
Kronecker’s delta, B is
an Mx2
Vandermonde submatrix, $$$K_n=g_{n,+}\Psi^{-1}g_{n,-}$$$
, and the sufficient statistic $$$u[m]=\sum_{n,even}K_n[m,m]+\sum_{n,odd}\overline{K_n[m,m]}$$$
. Minimizers
of this non-convex cost can be found by preconditioned gradient
descent:
$$\xi_{t+1}=\xi_t-P^{-1}\triangledown{J(\xi)}---(5)$$
with dense preconditioner $$$P=4B^T(\sum_m|u[m]|\delta_m\delta^T_m)B$$$
, using the magnitude
weighted least squares (MWLS) approximation of (4) applied to $$$\angle{u}$$$
following 1D phase unwrapping
(PUN) as an initial estimate. Following estimation of $$$\xi$$$
, $$$f$$$
is
readily determined using the above expression.
III. Data Acquisition
and Image Reconstruction: Two healthy volunteers
were imaged under an IRB-approved protocol on a compact 3T-MRI system12:
(Gmax=80mT/m, SR=700T/m/s), with C=32 receive-only brain coil. Both
standard (forward-only; NEX=2) and reverse readout gradient polarity (forward+reverse)
EPI acquisitions were performed for the comparison. The standard raw datasets
were averaged before NGC using the vendor pipeline13. For the
reverse readout acquisition, the unmodulated raw dataset was estimated via the
above described approach. Images from both result sets were then reconstructed
via root-sum-of-squares (RSS) or SENSE for acceleration factors R=1 and R={2, 3},
respectively.Results
Figures 2a,b depict two example non-convex cost
function spaces ($$$J(\xi)$$$)
, which contain many local and global extrema.
The pre-PUN sufficient statistic $$$\angle{u[m]}$$$
are shown
in the subfigures. Overlaid convergence plots (color) demonstrate the
impact of initial guess selection on convergence rate and attraction. Utilizing
the MWLS result for the unwrapped sufficient statistic (PUN+MWLS) provides
rapid convergence to (non-unique) global minima, as compared to the
non-unwrapped MWLS and fixed-value initializations $$$(0,\pi)$$$. Figure
3 shows strong residual Nyquist ghost artifacts the phantom images generated
with the standard acquisition and vendor NGC. For R=1, these artifacts are
dominant in the background region whereas for R=2 they are dominantly in the
foreground, the latter being due to error propagation through SENSE unfolding. In
contrast, the proposed reverse readout acquisition and NGC method largely
mitigates these artifacts at both acceleration rates. In Figure 4, in-vivo
results (R=3) show the similar trends as in phantom examples, with the proposed
NGC paradigm mitigating aliasing artifacts representing up to 20% intensity errors.Discussions
The proposed NGC acquisition and reconstruction
paradigm provides superior artifact mitigation relative to the standard method in
both phantom and in-vivo brain experiments, and across acceleration rates. This is directly attributable to the improved
noise management and prospective avoidance of off-resonance biases in the
proposed approach. Although this paradigm requires a two-pass acquisition, we
anticipate that it can be combined with higher acceleration factors or
incorporated into multi-pass EPI sequences (e.g., diffusion weighted imaging
(DWI)) to minimize or eliminate additional overhead above conventional setups. With
appropriate generalization, this robust physics-driven paradigm could potentially
serve as a platform for managing complex ghosting artifacts due to anisotropic
gradient delays, cross-term and higher-order readout eddy currents, as well as
encoding gradient eddy currents (e.g., diffusion lobes). The performance of the
proposed setup may also be further improved through use of target-dependent
regularization or constraints, such as minimum entropy regularization14
or linear predictability15.Acknowledgements
This work was supported by NIH
U01 EB024450.
References
1.
Mansfield P. Multi-planar image formation using NMR spin-echoes. J Phys C.
1977; 10:L55–L58.
2.
Bernstein M.A., King K.F., and Zhou X.J, Handbook of MRI Pulse Sequences 2004;
Burlington, MA, USA: Elsevier.
3.
Hu X. Le TH. Artifact reduction in EPI with phase-encoded
reference scan. Magn Reson Med 1996; 36, 166-171.
4.
Van der Zwaag W., Marques J.P., Lei H., Just N., Kober T., and Gruetter R.
Minimization of Nyquist ghosting for echo-planar imaging at ultra-high fields
based on a "negative readout gradient" strategy. Magn Reson Med 2009;
30(5):1171-1178.
5.
Porter D.A., Calamante F., Gadian D.G., and Connelly A. The effect of residual Nyquist
ghost in quantitative echo-planar diffusion imaging. Magn Reson Med 1999;
42(2): 385-392.
6. Tao S, Weavers PT, Trzasko JD, Shu Y, Huston J 3rd, Lee SK, Frigo LM, Bernstein MA. Gradient pre-emphasis to counteract
first-order concomitant fields on asymmetric MRI gradient systems. Magn Reson Med. 2017; 77(6):2250-2262.
7. Weavers PT, Tao S, Trzasko
JD, Frigo LM, Shu Y,
Frick MA, Lee SK, Foo TKF, Bernstein MA. B0 concomitant field compensation for MRI systems
employing asymmetric transverse gradient coils. Magn Reson in Med 2017; 79: 1538– 1544.
8.
Hoge WS, Polimeni JR. Dual‐polarity GRAPPA for simultaneous reconstruction and
ghost correction of echo planar imaging data. Magn Reson Med. 2016; 76: 32–
44.
9.
Reeder S.B., Faranesh A.Z., Atalar E., and McVeigh E.R. A novel
object-independent balanced reference scan for echo-planar imaging. J Magn
Reson Imaging 1999; 9(6): 847-852.
10.
Mock BJ. Method and apparatus for reducing artifacts in echo
planar imaging. 6,259,250. US Patent. 2001 Jul 10.
11.
Golub GH, Pereyra V. Differentiation of
pseudo-inverses and nonlinear least-squares problems whose variables separate.
SIAM J Numer Anal 1973; 10:413–432.
12.
Foo TKF, Laskaris E, Vermilyea M, et al. Lightweight, compact, and
high-performance 3T MR system for imaging the brain and extremities. Magn Reson
Med 2018; 80(5): 2232-2245.
13.
Hinks RS, Mock BJ, Collick BD, Frigo FJ, Shubhachint T.
Method and system for image artifact reduction using nearest-neighbor phase
correction for echo planar imaging. 7,102,352. US Patent. 2006 Sep 5.
14.
Skare S., Newbould r., Clayton D.,
Bammer R., and Moseley M. A fast and robust minimum entropy based
non-interactive nyquist ghost correction algorithm. in Proc. Int. Soc. Magn
Reson Med 2006; pp. 2349.
15.
Jin K.H., Lee D, and Ye J.C. A general framework for compressed sensing and
parallel mri using annihilating filter based low-rank hankel matrix. IEEE Trans. Comput. Imag. 2016; 2(4):
480–495.