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Combined Update Using Grouped Isochromats for Fast Bloch Simulation
Hidenori Takeshima1
1Imaging Modality Group, Advanced Technology Research Department, Research and Development Center, Canon Medical Systems Corporation, Kanagawa, Japan

Synopsis

Keywords: Software Tools, Simulations, Bloch equations

Motivation: Computational cost of the Bloch simulation was high.

Goal(s): This research aims to reduce the computational cost.

Approach: A new computation method using grouped isochromats is proposed. The proposed method shared computation of the isochromats whose parameters were same for each part of gradients. The processing time of two sequences were evaluated using a phantom (consisting of approximately 4 million isochromats) with and without the proposed method.

Results: The proposed method accelerated the simulation up to 7.7 times.

Impact: The proposed method accelerated up to 7.7 times for simulating the Bloch equations. The proposed method shared computation of the isochromats whose parameters were same for each part of gradients.

Introduction

There are many implementations for simulating the Bloch equations and their extensions1-9. The high computational cost of the simulation was a common problem to be overcome. Several algorithms such as utilization of combined transitions3-5 and no temporal changes6 were effective for reducing the computational cost. Special hardware such as general-purpose graphics processing unit (GPGPU)6-8, and cloud computing9 was also effective. Nevertheless, the simulation with several million isochromats was still time-consuming. The goal of this research is further reduction of its computational cost.

Methods

The author proposes a new computation method using grouped isochromats for further acceleration of the simulation. Before simulations, isochromats of a phantom were grouped for processing 4 different gradient types of sequences efficiently. The criteria used for grouping the isochromats are shown in Figure 1.
As shown in Figure 2, a pulse sequence to be processed was split into three parts: (a) with an RF pulse (with-RF), (b) with ADC sampling (with-ADC), and (c) other. The proposed method used a piecewise constant approximation (during $$$\Delta t=1$$$ microsecond) for processing a pulse sequence.
In processing with-RF and with-ADC parts, the proposed method tried to classify the part into one of the above-mentioned gradient types. If the classification was succeeded, grouped isochromats were combined for computing the processing part with the accelerated mode (explained later). Otherwise, the following conventional mode was used.
Conventional Mode
The with-RF part was processed by updating each magnetization $$$N_{RF}$$$ times. In an update step, the simulator multiplied a $$$4 \times 4$$$ transition matrix5 $$$\boldsymbol{U}(t,\Delta t,k)$$$ depending on RF pulse $$$B_{xy}(t)$$$, gradients $$$G_x(t)$$$, $$$G_y(t)$$$, and $$$G_z(t)$$$ of the with-RF part; and $$$T_1(k)$$$, $$$T_2(k)$$$, and $$$\Delta B_0(k)$$$ of the $$$k$$$-th isochromat. To compare with a state-of-the-art algorithm, the per-isochromat caching algorithm using combined transitions5 given as
$$U_{combined}(t_0,t_{N_{RF}},k)=\boldsymbol{U}(t_{N_{RF}-1},\Delta t,k)\cdots \boldsymbol{U}(t_0,\Delta t,k)$$
was also included in both conventional and acceleration modes.
In the with-ADC and other parts, magnetizations were updated from $$$t_0$$$ to $$$t$$$ by computing the analytic solution
$$M_{xy}(t,k)=M_{xy}(t_0,k)\exp \Big(-\frac{t-t_0}{T_2(k)}\Big)\exp \Big(\int_{t_0}^t -\gamma B_z(t,k) dt \Big),$$ and
$$M_z(t,k)=M_0(k) +(M_z(t_0,k)-M_0(k))\exp \Big(-\frac{t-t_0}{T_1(k)}\Big)$$
where $$$B_z(t,k)=G_x(t) x + G_y(t) y + G_z(t) z + \Delta B_0(k)$$$. In the with-ADC part, an ADC sample was given as $$$A(t)=\sum_k M_{xy}(t,k)$$$ when receiver coil sensitivities were not considered. When positions $$$(x,y,z)$$$ were not changed, these update required $$$N_{ADC}$$$ and 1 times for with-ADC and other parts, respectively.
For processing a phantom, the magnetizations of $$$K$$$ isochromats were updated for all three parts. The orders of the computation are $$$O(N_{RF}K)$$$, $$$O(N_{ADC}K)$$$, and $$$O(K)$$$ for with-RF, with-ADC and other parts, respectively.
Accelerated Mode
In the case of the with-RF part, isochromats in an isochromat group were designed for sharing properties for computing the above-mentioned transition matrix. Unlike the existing per-isochromat methods3-5, the proposed method computed the above-mentioned combined transitions once, and multiplied $$$U_{combined}(t_0,t_{N_{RF}},k)$$$ to all isochromats for each isochromat group.
In the case of the with-ADC part, it was sufficient to compute the sum of magnetizations $$$\sum_k M_{xy}(t,k)$$$ for each isochromat group, and to compute $$$A(t)$$$ using the sums of magnetizations for all isochromat groups instead of magnetizations for all isochromats.
When number of isochromat groups $$$K_{group}$$$ is much less than $$$K$$$, the computational cost is reduced to $$$O(N_{RF}K_{group})$$$ and $$$O(N_{ADC}K_{group})$$$ for with-RF and with-ADC parts, respectively.
Evaluations
For running the proposed method efficiently, isochromats of a brain phantom (matrix size: $$$480 \times 480 \times 40$$$, FOV: $$$240 \times 240 \times 240$$$ mm3) were placed in grid points. The variations of isochromat parameters $$$T_1$$$, $$$T_2$$$ and $$$\Delta B_0$$$ were also limited to certain numbers using a k-means clustering method (with 16, 32, 64 and 128 clusters) for the accelerated mode, as shown in Figure 3.
The processing time of single-slice spin-echo and EPI sequences (Figure 4 (a)) were evaluated with and without the accelerated mode of the proposed method.

Results

Individual processing time are shown in Figure 4 (b). Reconstructed images using a gridding algorithm for all cases are shown in Figure 5. The proposed method accelerated the simulation 2.4 and 6.2-7.7 times for spin-echo and EPI sequences, respectively.

Discussion

Processing grouped isochromats for individual parts of sequences reduced the computational cost of the simulation. Since there were no significant differences between the reconstructed images with and without clustering, using static isochromats pre-processed with a clustering algorithm was an efficient way for accelerating the simulation without losing reality of phantoms.

Conclusion

A new method using grouped isochromats was proposed for simulating the Bloch equations. The proposed method significantly reduced the computational cost without using special hardware for accelerating simulations.

Acknowledgements

The acquisitions of data used for generating the brain phantom were approved by our institutional review board and informed consent was obtained from the volunteer.

References

1. Stöcker T, Vahedipour K, Pflugfelder D, Shah NJ. High-performance computing MRI simulations. Magn Reson Med. 2010; 64:186-193.

2. Liu F, Velikina JV, Block WF, Kijowski R, Samsonov AA. Fast realistic MRI simulations based on generalized multi-pool exchange tissue model. IEEE Transactions on Medical Imaging. 2017; 36:527-537.

3. Taniguchi Y, Nakaya C, Bito Y, Yamamoto E. MRI high-speed simulator using transition matrix method and periodicity of magnetization. Systems and Computers in Japan. 1995; 26:54-62. doi: 10.1002/scj.4690260206.

4. Scholand N, Graf C, Uecker M. Efficient Bloch simulation based on precomputed state-transition matrices. In Proceedings of the Joint Annual Meeting ISMRM-ESMRMB, London, United Kingdom, 2022. p. 748.

5. Takeshima, H. A fast and practical computation method for magnetic resonance simulators. Magn Reson Med. 2023; 90: 752-760.

6. Xanthis CG, Venetis IE, Chalkias AV, Aletras AH. MRISIMUL: A GPU-Based Parallel Approach to MRI Simulations. IEEE Transaction on Medical Imaging. 2014; 33:607-617.

7. Kose R, Kose K. BlochSolver: A GPU-optimized Fast 3D MRI Simulator for Experimentally Compatible Pulse Sequences. Journal of Magnetic Resonance. 2017; 281:51-65.

8. Castillo-Passi, C, Coronado, R, Varela-Mattatall, G, Alberola-López, C, Botnar, R, Irarrazaval, P. KomaMRI.jl: An open-source framework for general MRI simulations with GPU acceleration. Magn Reson Med. 2023; 90: 329-342.

9. Xanthis CG, Aletras AH (2019) coreMRI: A high-performance, publicly available MR simulation platform on the cloud. PLoS ONE 14(5): e0216594.

Figures

Figure 1. The criteria used for grouping isochromats. The parameters $$$T_1$$$, $$$T_2$$$ and $$$\Delta B_0$$$ must be shared in all isochromats of each group. In addition, the $$$x$$$, $$$y$$$ and $$$z$$$ coordinates must be shared in all isochromats of each group in the cases of Gx-only, Gy-only and Gz-only, respectively. These conditions can be satisfied by applying a clustering algorithm to isochromats of a phantom before running simulations.

Figure 2. A pulse sequence and the gradient types of its parts. The pulse sequence to be processed were split into three parts: (a) with an RF pulse (with-RF), (b) with ADC sampling (with-ADC), and (c) other. The proposed method tried to classify the with-RF and with-ADC parts into the gradient types for using the accelerating mode.

Figure 3. Generation process of a phantom with limited variations of isochromat parameters. At first, parameter maps were generated using an arbitrary parameter mapping method. The parameter maps were adjusted by applying a clustering algorithm (K-means in the evaluations). The $$$M_0$$$ map was adjusted again by using the adjusted T2 map and (an) available image(s). After all maps were generated, the isochromats whose $$$M_0$$$ values were small were truncated. Since the $$$\Delta B_0$$$ map was not acquired, $$$\Delta B_0$$$’s were filled with zeros in the evaluations.

Figure 4. (a) Sequence parameters used in the evaluations. All RF pulses consisted of 4000 sampling points. (b) Processing times measured on a 3.70 GHz CPU (10 cores and 20 hardware threads) using the proposed method (16 – 128 clusters in the columns of num. clusters) and the conventional mode only (no accel. in the column of num. clusters). Numbers of isochromats were varied because of the final truncation step of the phantom generation.

Figure 5. Reconstructed images using a gridding algorithm for all cases. There were no significant differences between the reconstructed images with and without clustering when at least 64 clusters were used.

Proc. Intl. Soc. Mag. Reson. Med. 32 (2024)
4681
DOI: https://doi.org/10.58530/2024/4681