Ralph Sinkus1, Simon Auguste Lambert1, Lucas Hadjilucas1, Shaihan Malik2, Anirban Biswas1, Francesco Padormo2, Jack Lee1, and Joseph V Hajnal2
1Imaging Sciences & Biomedical Engineering Division Kings College, King's College London, London, United Kingdom, 2Centre for the Developing Brain & Department Biomedical Engineering, King's College London, London, United Kingdom
Synopsis
Classical DWI methods extract information about
microstructural tissue complexity from the signal decrease of the MR-magnitude
as a function of b-value. Utilization of linear gradients for motion encoding
prevents theoretically the use of the MR-phase. Rather, the diffusion
information is encoded in the MR-magnitude via global spin dephasing due to
Brownian motion with zero net phase shift. This dogma is overturned when
considering quadratic gradient fields in space. We demonstrate in theory,
experiment, and simulation that the diffusion process leads to a net phase
shift with minimal loss in signal magnitude when imaging at the minimum of the
quadratic gradient.Purpose
To develop a novel method for DWI which enables utilization
of the MRI-phase for encoding the diffusion of water molecules.
Introduction
Diffusion Weighted Imaging (DWI) in MRI uses the loss of phase coherence
within the imaging voxel – induced by the random walk of the spins under the
influence of a linear gradient – to deduce micro-structural information. Since
diffusion is typically dyadic (i.e. equal # of spins moving in opposed
directions), the entire spin ensemble within the imaging voxel does not
experience a net phase accrual, but only a loss in total signal magnitude due
to dephasing. Hence, classical DWI cannot utilize the MRI-phase information per
se.
DWI2 is based upon the idea that a diffusing spin in a 2nd
order magnetic field (i.e. B(z)=β*z2) will experience only positive
phase accrual independent of the direction of motion. Thus, DWI2 can
explore the MRI-phase information. Furthermore, the absence of a linear
component (i.e. B(z)=α*z) in the proximity around z=0 leads to minimal loss in signal
magnitude. Thus, in DWI2 the SNR remains minimally altered when
imaging at this preferred position. This opens the gateway to entirely new
concepts for diffusion weighted imaging, in particular to elevated sensitivity
to micro-architectural complexity currently hidden due to limited SNR [1].
Material & Methods
Experiments used a classical spin-echo sequence with TE=50ms
and TR=500ms at 3T (Philips Medical Systems). As shown in the figure, a water
sample (a) was placed along the z-symmetry axis of two Helmholtz coils (inner ∅=10mm,
# 150 windings for each coil, length of each coil=10mm, separation of 8.6mm
between coils, ∅0.3mm for copper wire) which could be operated in
linear or quadratic mode. Imaging was done at z=0 with transverse image
orientation to explore the effect of the linear or quadratic field on the
diffusion of the water molecules. One single sinusoidal gradient pulse was
applied after the π/2-pulse and before the π-pulse at ν=100Hz with a current of
1A. Pre-emphasis of the gradient pulse was adjusted to ensure a net pulse area
of zero. A magnetostatic field simulation (FEMM 4.2) of the quadratic coil configuration
yields β=5300T/m
2 at z=0. Analytic calculus predicts a net
phase-change φ=γDβ/(2ν
2) = (-)0.16 [rad] (with D the water
diffusion coefficient and γ the gyromagnetic ratio). Monte Carlo simulations (Camino
software [2], #100000 particles, pure water, β=7560T/m
2, ν=30Hz) were performed to
investigate the correctness of the analytic calculus.
Results
The resulting images of the MR-magnitude and MR-phase for
both coil configurations (linear, quadratic) are shown in (b) without (0A) and
with application of a current (1A). The linear coil configuration leads – as
expected – to a significant reduction in magnitude (c) without any statistically
significant phase change (d). This is corroborated by analytic calculus. On the
contrary, the quadratic coil configuration leads to no statistically significant loss in
magnitude (as expected), while a statistically significant negative phase drift
is measured. The measure phase shift of (-)0.24±0.11rad agrees within errors
with the theoretically expected of (-)0.16rad. Monte Carlo simulations
(e) confirmed the net phase shift for the quadratic field configuration (φ
AVG=-1.44rad) with
excellent agreement to the analytic expression (φ
theory=-1.45rad).
Discussion & Conclusions
Classical
DWI is a powerful method for gaining insight into tissue microstructure. Its
diagnostic value is currently explored for various applications, from diagnosis
over response to therapy to prediction of outcome. Intrinsically, DWI uses the
decrease of the MR-magnitude signal as a function of b-value for extracting the
mono-exponential or bi-exponential ADC value(s). More complex diffusion
information are obtained via stretched exponentials [3], or ADC-values at
shorter diffusion time scales via oscillating gradients [4]. Still, all those
methods utilize the MR-magnitude information. The inevitable loss in signal
often limits DWI to low b-values and hence restricts the potential of the
method for characterizing microstructure. DWI
2 overcomes this
limitation by using 2
nd order spatial field changes for encoding the diffusion
information. As expected from theory – and experimentally demonstrated – a
quadratic field gradient leads to a minimal loss in signal magnitude in
combination with a net shift in phase when operating in close proximity of z=0
for B(z)=βz
2. Monte Carlo simulations of freely diffusing water
molecules show excellent agreement between theory and simulation results, further
demonstrating the validity of the proposed method. The essential conservation
of signal for DWI
2 leads therefore to a paradigm shift for DWI as
currently inaccessible domains can now be explored.
Acknowledgements
This research was funded/supported by the French National Cancer Institute (INCa, TRANSLA1212-065). This research was funded/supported by
the National Institute for Health Research (NIHR) Biomedical Research Centre
based at Guy’s and St
Thomas’ NHS Foundation Trust and King’s College London. The views
expressed are those of the author(s)
and not necessarily those of the NHS,
the NIHR or the Department of Health. This research was funded/supported by
the MRC strategic gran (MR/K006355/1).
References
[1] Magnetic Resonance in Medicine 59:447–455 (2008)
[2] 14th ISMRM, Seattle, WA, USA, p. 2759, May 2006.
[3] Magn Reson Med. 2010 Nov; 64(5): 1499–1509.
[4] Cancer Res 2008; 68: (14). July 15, 2008