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Probing restricted diffusion and water exchange with free gradient waveforms: Addressing the need for a compartment model
Arthur Chakwizira1, Filip Szczepankiewicz2, Linda Knutsson1,3, and Markus Nilsson2
1Department of Medical Radiation Physics, Lund University, Lund, Sweden, 2Department of Diagnostic Radiology, Lund University, Lund, Sweden, 3Russell H. Morgan Department of Radiology and Radiological Science, Johns Hopkins University School of Medicine, Baltimore, MD, United States

Synopsis

Diffusion MRI can be used to probe restricted diffusion (compartment size) and water exchange (membrane permeability), but their effects on the signal are entangled. This problem can be addressed by the use of free gradient waveforms designed to disentangle the effects. However, a previously presented approach is invalid at high b-values and long diffusion encoding times. We develop a generalised restriction-exchange model that is valid for arbitrary gradient waveform and all relevant b-values and encoding times. The approach eliminates the shortcomings of the previous restriction-exchange framework.

Introduction

Diffusion time-dependence can be used to infer microstructural information from the diffusion-weighted signal.1,2 Measurement strategies that independently probe restricted diffusion and exchange yield estimates of cell size and permeability. 3–6 The restriction-exchange framework by Nilsson et al.7 uses free gradient waveforms described by two experiment parameters which capture restriction and exchange weighting. The framework is based on a second-order cumulant expansion which fails to capture signal decay at high b-values, and it relies on assumptions that only hold for short diffusion times and low frequencies in the diffusion spectrum.
Here, we propose a two-compartment restriction-exchange model that accommodates arbitrary gradient waveforms and is valid at all b-values, encoding times and frequencies in the diffusion spectrum. We validate the theory by using Monte-Carlo simulations of restricted diffusion and water exchange on a synthetic substrate.

Theory

We begin with the Kärger equations describing signal evolution between two spin ensembles (S1 and S2)
$$ \frac{\partial}{\partial t} \bigg ( \begin{matrix} S_1 \\ S_2 \end{matrix} \bigg) = [K - Dq(t)^2] \bigg ( \begin{matrix} S_1 \\ S_2 \end{matrix} \bigg) \hspace{24pt} (1)$$
where $$$K$$$ and $$$D$$$ are matrices of exchange rates and intrinsic diffusivities,

$$K = \begin{bmatrix}-k_{12} & k_{21} \\k_{12} & -k_{21} \\\end{bmatrix} \hspace{12pt}; \hspace{12pt} D = \begin{bmatrix}D_1 & 0 \\0& D_2\\\end{bmatrix}$$

and $$$q(t)$$$ is the dephasing vector as a function of time. When q is piecewise constant in time (e.g. SDE or DDE with short gradient pulses), Eq.1 has closed-form solutions. We derive a solution for any $$$q(t)$$$ by treating a gradient waveform as comprising a pair of impulses in every time-step $$$\Delta t$$$ (Fig.1).9 This results in a constant q-vector in every $$$\Delta t$$$, allowing us to solve Eq.1 and arrive at the generalized solution

$$ S(q, \Delta t, N) = \boldsymbol{1}\cdot \prod_{i=1}^{N} \exp([K - Dq_i^2]\Delta t )\cdot F \hspace{24pt} (2)$$

where $$$ \boldsymbol{1} = [1 \hspace{6pt} 1]$$$, $$$F = [f_1 \hspace{6pt} f_2]'$$$ is a vector of signal fractions and $$$N = T/\Delta t$$$ for a total diffusion encoding time $$$T$$$. This places no restriction on $$$q(t)$$$ and is thus applicable for arbitrary gradient waveforms. Eq.1 can be shown to adhere to previous theory 8 by taking its cumulant expansion to arrive at

$$S/S_0 \approx \exp(-\bar{D}b + \frac{1}{2}\text{Var}(D)\cdot (1 - k\cdot \Gamma)b^2) \hspace{24pt} (3)$$
where $$$\bar{D}$$$ and Var(D) are the mean and variance of diffusivities, and
$$\Gamma = \frac{Q_4}{3b^2}$$
where
$$ Q_4:= \sum_{i=1}^{N} (q_i^4 \Delta t^2)\Delta t + \sum_{j=1}^{N-1} \bigg( 6j\cdot \sum_{i=1}^{N-j}q_i^2q_{i+j}^2 \Delta t ^2 \bigg)\Delta t$$

Eqn.2 describes exchange in a two-component free diffusion setting, which does not address our goal of developing a two-compartment model. Following previous work 10, we account for restriction by introducing geometry-dependent apparent diffusivities given by
$$D(\cdot) = \frac{1}{2\pi b}\int_{-\infty}^{\infty} D(\omega)|Q(\omega)|^2d\omega \hspace{24pt} (4)$$
where $$$D(\omega)$$$ is the diffusion spectrum and $$$|Q(\omega)|^2$$$ is the encoding power spectrum. Here, $$$D(\omega)$$$ refers to the full spectrum, in contrast to its Taylor expansion used in previous work 10. Our final restriction-exchange model is then defined by
$$ S(q, \Delta t, N) = \boldsymbol{1}\cdot \prod_{i=1}^{N} \exp([K - \hat{D} q_i^2]\Delta t )\cdot F \hspace{24pt} (5)$$

where
$$\hat{D} = \begin{bmatrix}D(\cdot) & 0 \\0& D_2\\ \end{bmatrix}$$

Methods

Random walkers were simulated on a continuous 2D synthetic substrate consisting of regularly distributed circular permeable cells (Fig.2a). Exchange was implemented as described by Szafer 11. Simulation parameters were:

$$N_{particles} = 10^5, \Delta t = 10 \hspace{4pt} \mu\text{s}, f_1 = 0.7, D_1 = D_2 = 1.2 \hspace{4pt} \mu\text{m}^2/\text{ms}$$
$$k = [0, 2, 4, 6, 8, 10] \hspace{4pt} \text{ s}^{-1} \text{ at } d = 10 \hspace{4pt} \mu\text{m}, d = [4, 8, 12, 16, 20] \hspace{4pt}\mu\text{m at } k = 10 \text{ s}^{-1}, \hspace{4pt} T = 300 \text{ ms}.$$
Signals were generated using a protocol with different exchange- and restriction weightings as previously proposed by us (Figure 2b). The signals featured maximum b-values between 5 and 30 ms/µm$$$^ 2$$$ arrived at in 10 steps. Eq.5 was fitted by nonlinear-least-squared fitting to the signals to evaluate accuracy of estimates. Noise was added at $$$SNR = 100$$$ to investigate precision.

Results

Figure 3 shows the response of the developed theory to varying scenarios of restriction and exchange and demonstrates a good fit to simulated data. Estimates of exchange rate and compartment diameter are in harmony with ground truth. The figure also shows that our model correctly detects the fixed value of one parameter while the other is being varied. This is evidence of the ability to independently account for restriction and exchange. Model validity at high b-values and long encoding times is confirmed in Fig.4 which shows that our model fits the data well, at least up to b=30 ms/µm$$$^2$$$. Size and exchange estimates remain stable over all simulated b-values and encoding times. Precision in parameter estimates is depicted in Fig.5. The distributions are well-centered around the ground truth, with some slight skewing evident in the size estimates.

Discussion

We developed and validated a generalised exchange-restriction two-compartment model that is applicable to acquisitions with arbitrary gradient waveforms and any range of b-values and diffusion encoding times. The proposed representation can be used to obtain reliable parameter estimates in conditions where the cumulant expansion would fail. A possible shortcoming of the approach is the relatively large variance in size estimates. Future work will address this using protocol optimisation. 12

Acknowledgements

No acknowledgement found.

References

1. Stepišnik J. Time-dependent self-diffusion by NMR spin-echo. Physica B: Condensed Matter. 1993 May;183(4):343-350

2. Callaghan PT. A simple matrix formalism for spin echo analysis of restricted diffusion under generalized gradient waveforms. J Magn Reson. 1997;129(1):74-84

3. Kärger J. NMR self-diffusion studies in heterogeneous systems. Adv Colloid Interfac. 1985 Aug;23:129–148.

4. Yablonskiy D, Sukstanskii A. Theoretical models of the diffusion weighted MR signal. NMR Biomed. 2010 Aug;23(7):661-681.

5. Lasič S, Nilsson M, Lätt J, Ståhlberg F, Topgaard D. Apparent exchange rate mapping with diffusion MRI. Magn Reson Med. 2011;66(2):356-365

6. Reynaud O. Time-Dependent Diffusion MRI in Cancer: Tissue Modeling and Appli- cations. Front Phys. 2017 Nov;5

7. Nilsson M, Westin CF, Brabec J, Lasic S, Szczepankiewicz F. A unified framework for analysis of time-dependent diffusion: numerical validation of a restriction-exchange correlation experiment. Proceedings of ISMRM. Montreal, QC, Canada. 2019

8. Ning L, Nilsson M, Lasiˇc S, Westin C, Rathi Y. Cumulant expansions for measuring water exchange using diffusion MRI. J Chem Phys. 2018 Feb;148(7):074109.

9. Callaghan PT. A simple matrix formalism for spin echo analysis of restricted diffusion under generalized gradient waveforms. J Magn Reson. 1997;129(1):74-84. doi:10.1006/jmre.1997.1233

10. Nilsson M, Lasiˇc S, Drobnjak I, Topgaard D, Westin C. Resolution limit of cylin- der diameter estimation by diffusion MRI: The impact of gradient waveform and orientation dispersion. NMR Biomed. 2017 Jul;30(7):e3711

11. Szafer A, Zhong J, Gore J. Theoretical Model for Water Diffusion in Tissues. Magn Reson Med. 1995 May;33(5):697-712

12. Alexander DC. A general framework for experiment design in diffusion MRI and its application in measuring direct tissue-microstructure features. Magn Reson Med. 2008 Aug;60(2):439-48

Figures

Figure 1. Approach for deriving a generalized solution to the Kärger equations. A given point on an arbitrary gradient waveform (a) is treated as comprising a pair of infinitely short pulses (c) separated by the discretization step length (1 ms in this case). As the q-vector is now constant in every time-step a generalized discretised signal equation can be derived.

Figure 2: Components of validation. Panel (a) shows a 2D substrate modelling a cross-section through a cylindrical geometry. Panels (b), (c), (e), and (f) show waveforms used to generate signal. Panel (d) shows the restriction (y-axis) and exchange (x-axis) weightings of the waveforms, quantified by the parameters $$$\Gamma$$$ and $$$V_{\omega}$$$ defined in previous work.

Figure 3: Contrast and goodness of fit for different combinations of restriction and exchange. Panel (a) shows that the proposed model describes that data well in all simulated cases. (b) Exchange rate and cell size estimates are in good agreement with simulation. (c) Changes in exchange rate for a fixed size do not erroneously manifest in our model as a change in size. This demonstrates the independent contributions of restriction and exchange to the signal as captured by our model.

Figure 4: Demonstration of the robustness of the developed theory to ultrahigh b-values and long encoding times. Panel (a) shows a good agreement between model and simulation for all considered b-values. Panels (b) and (c) show that the theory produces stable estimates of size and exchange over the entire range of simulates b-values and encoding times.

Figure 5: Noise sensitivity of the estimated exchange rate and compartment diameter. Both distributions were centered around the ground truth, indicating good accuracy. Exchange estimates were more precise with a variation coefficient of 8%, compared with 24% for the diameter estimates.

Proc. Intl. Soc. Mag. Reson. Med. 29 (2021)
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