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A Least Squares Optimal Density Compensation Function for Gridding
Nicholas Dwork1, Corey Baron1, Ethan Johnson1, Adam B. Kerr1, Dwight G. Nishimura1, and John Pauly1

1Electrical Engineering, Stanford University, Stanford, CA, United States

Synopsis

Gridding is a relevant algorithm for both image reconstruction and pulse design. With Gridding, it is crucial to appropriately compensate for varying density of the sampling trajectory. In this paper, we present a technique to determine the weights by solving a least squares optimization problem.

Purpose

The Non-Uniform FFT (NuFFT) problem of type 1 is a relevant problem for image reconstruction [1] and RF Pulse design [2]. The Gridding algorithm is a computationally efficient direct method for solving these types of problems [3,4]. Importantly, if the trajectory $$$\boldsymbol{k}=(k_1,k_2,\ldots,k_N)$$$ does not cover k-space uniformly, then one must compensate for the varying density [1]. Density compensation is accomplished by pointwise multiplication of the Fourier values $$$\boldsymbol{F}\in\mathbb{C}^N$$$ by a vector of weights $$$w\in\mathbb{R}^N$$$. In this paper, we present a technique for determining density compensation weights by solving a least squares problem, which can be solved with known algorithms that are guaranteed to converge.

Theory

The Gridding algorithm is encapsulated in the following expression [4]:

\begin{equation} \hat{f}(n) = \frac{1}{c(n)}\text{DFT}^{-1}\left\{ \mathcal{T}\left[ (F\,S_w \circledast C) \text{III}_{\Delta k/\alpha} \right] \right\}[n], \end{equation}

where $$$F$$$ is the Fourier transform of the image $$$f$$$, $$$\hat{f}$$$ is a vector of estimates of $$$f$$$, $$$\text{III}$$$ is the comb function, $$$S_w(k)=\sum w_i\, \delta(k-k_i)$$$ (a distribution of weighted impulse functions), $$$\circledast$$$ represents a circular convolution, $$$C$$$ is the Gridding convolution kernel, $$$c$$$ is the deapodization function, $$$\alpha$$$ is the oversampling factor, and $$$\mathcal{T}$$$ is an isomorphism that maps the non-zero values of $$$F\,S_w$$$ to a vector in $$$\mathbb{C}^M$$$. In [5], Pipe et al. suggest determining the density compensation function with the following Fixed Point (FP) iteration:

\begin{equation*} diag(w_{i+1}) = diag(w_i) \, diag^{-1}\left( \mathcal{C} w_i \right)\end{equation*}

where $$$\mathcal{C}$$$ is the linear transformation that convolves the distribution of weighted impulse functions $$$S_w(k)=\sum\delta(k-k_i)$$$ with the Gridding kernel and evaluates the result on sample points. Intuitively, if $$$S_w^{(i)}\ast C\approx\boldsymbol{1}$$$ at all points in the support of $$$S_w$$$ then $$$S_w^{(i+1)}\approx S_w^{(i)}$$$. FP attempts to set the weights so that value before and after convolution with the Gridding kernel at all $$$k\in\boldsymbol{k}$$$ remains constant. However, this algorithm is not guaranteed to converge; the authors suggest running for 15 iterations, but figure 1 shows an example where the solutions after 1, 15, and 2000 iterations differ.

We propose to determine the weights by solving the following Least Squares problem:

\begin{equation*} \text{minimize} \hspace{8pt} \| \mathcal{C} \, w - \boldsymbol{1} \|_2. \label{eq:LSDC}\end{equation*}

Solving this problem also seeks to make $$$\mathcal{C}\,w\approx\boldsymbol{1}$$$. Importantly, though, this problem can be solved with efficient numerical algorithms (such as LSQR [7]). We call this algorithm Least Squares Density Compensation (LSDC); when compared to FP, it eliminates the requirement that a user specify the number of iterations (though a stopping criteria is required), and it is guaranteed to converge to an optimal solution (in a Least Squares sense).

Results

Figure 2 presents Gridding results of data collected with a phantom using a 2D radial trajectory with 418 radial lines, a field of view of 29 cm, and a resolution of 1.1 mm collected with a 1.5T scanner. There is an improvement in quality when LSDC is used instead of FP; the arrows point to regions where LSDC is able to reduce the amount of noise present in the imagery.

Figure 3 presents Gridding results of data collected with a phantom comprised of six bottles of varying substances using a propeller trajectory with 159 points per readout, 20 lines per angle, and 22 angles (each separated by the golden angle) collected with a 1.5T scanner. Again, there is an improvement in quality when LSDC is used. In addition to the area indicated by the arrow, there is a bright halo that is significantly reduced by LSDC.

Conclusion

We have presented a new algorithm for determining the density compensation function of the Gridding algorithm: LSDC. It is based on the FP algorithm presented by Pipe et al. [5]. LSDC can be solved with efficient numerical algorithms that are known to converge.

Acknowledgements

ND is supported by the National Institute of Health's Grant Number T32EB009653 “Predoctoral Training in Biomedical Imaging at Stanford University”, the National Institute of Health's Grant Number NIH T32 HL007846, The Rose Hills Foundation Graduate Engineering Fellowship, the Electrical Engineering Department New Projects Graduate Fellowship, and The Oswald G. Villard Jr. Engineering Fellowship.

References

[1] John I. Jackson, Craig H. Meyer, and Dwight G. Nishimura. Selection of a Convolution Function for Fourier Inversion Using Gridding. IEEE Transactions on Medical Imaging, 10(3), September 1991.

[2] Christopher J Hardy, Harvey E Cline, and Paul A Bottomley. Correcting for Nonuniform K-space Sampling in Two-dimensional NMR Selective Excitation. Journal of Magnetic Resonance (1969), 87(3):639–645, 1990.

[3] JD O’sullivan. A Fast Sinc Function Gridding Algorithm for Fourier Inversion in Computer Tomography. Medical Imaging, IEEE Transactions on, 4(4):200–207, 1985.

[4] Philip J Beatty, Dwight G Nishimura, and John M Pauly. Rapid Gridding Reconstruction with a Minimal Oversampling Ratio. Medical Imaging, IEEE Transactions on, 24(6):799–808, 2005.

[5] James G Pipe and Padmanabhan Menon. Sampling Density Compensation in MRI: Rationale and an Iterative Numerical Solution. Magnetic Resonance in Medicine, 41(1):179–186, 1999.

[6] Holden H Wu, Bob S Hu, Dwight G Nishimura, and Michael V McConnell. Multi-phase Coronary Magnetic Resonance Angiography Using a 3D Cones Trajectory. Journal of Cardiovascular Magnetic Resonance,13(1):1, 2011.

[7] Christopher C Paige and Michael A Saunders. LSQR: An Algorithm for Sparse Linear Equations and Sparse Least Squares. ACM Transactions on Mathematical Software, 8(1):43–71, 1982.

Figures

Gridding results of 2D cardiac image based navigators (iNAVs) from an undersampled spiral trajectory [6]. Density compensation weights were determined using FP with (left) 1 iteration, (center) 20 iterations, (right) 2000 iterations. The white arrow indicates a point in the image where the solution differs between all three.

(Top) gridding results of a phantom with bottles of oil on either side, (Bottom) scaled gridding results, (Left) Fixed Point results with 20 iterations, (Right) LSDC results. The white arrows point to areas where LSDC performs noticeably better than the FP method.

(Top) gridding results of a phantom with bottles of varying substances, (Bottom) scaled gridding results, (Left) Fixed Point results with 20 iterations, (Right) LSDC results. The arrow points to an area where LSDC performs better than the FP method.

Proc. Intl. Soc. Mag. Reson. Med. 25 (2017)
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