DWI^2: exploring the MRI-phase for imaging diffusion
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/m2 at z=0. Analytic calculus predicts a net phase-change φ=γDβ/(2ν2) = (-)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/m2, 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 (φAVG=-1.44rad) with excellent agreement to the analytic expression (φtheory=-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. DWI2 overcomes this limitation by using 2nd 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)=βz2. 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 DWI2 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

Figures

(a) Concept of DWI2, (b,c,d) experimental results in a water phantom, and (e) phase distribution from MC simulations for linear and quadratic coil configuration.



Proc. Intl. Soc. Mag. Reson. Med. 24 (2016)
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