Abstract
Objective
In most half-Fourier imaging methods, explicit phase replacement is used. In combination with parallel imaging, or compressed sensing, half-Fourier reconstruction is usually performed in a separate step. The purpose of this paper is to report that integration of half-Fourier reconstruction into iterative reconstruction minimizes reconstruction errors.
Materials and methods
The L1-norm phase constraint for half-Fourier imaging proposed in this work is compared with the L2-norm variant of the same algorithm, with several typical half-Fourier reconstruction methods. Half-Fourier imaging with the proposed phase constraint can be seamlessly combined with parallel imaging and compressed sensing to achieve high acceleration factors.
Results
In simulations and in in-vivo experiments half-Fourier imaging with the proposed L1-norm phase constraint enables superior performance both reconstruction of image details and with regard to robustness against phase estimation errors.
Conclusion
The performance and feasibility of half-Fourier imaging with the proposed L1-norm phase constraint is reported. Its seamless combination with parallel imaging and compressed sensing enables use of greater acceleration in 3D MR imaging.
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Notes
\(\angle x - P = 0\) denotes a group of linear equations because it can be rewritten as \(x_{\text{i}} - x_{\text{r}} \cdot \tan \left( P \right) = 0\), where \(x_{\text{i}}\) repsents the imaginary part of x, and \(x_{\text{r}}\) represents the real part of x.
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Acknowledgments
The authors thank the journal referees for their helpful comments. This work was partly supported by Siemens Healthcare, Erlangen, Germany.
Conflict of interest
The authors declare that they have no conflict of interest.
Ethical standards
All volunteer studies in this work were approved by the ethics committee in the university medical center and have therefore been performed in accordance with the ethical standards laid down in the 1964 Declaration of Helsinki and its later amendments. The manuscript does not contain clinical studies or patient data.
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Appendices
Appendix 1
Proof of the Convexity of L1PC: set \(z = \alpha x + \beta y, \;0 \le \alpha \le 1.0, \;0 \le \beta \le 1.0, \;\alpha + \beta = 1.0\), W is an arbitrary constant matrix.
Note that the real part of \(z_{i} - \left| {z_{i} } \right|\) is a negative value, so
Therefore, \(\left\| {\left( {x - \left| x \right|} \right) \circ W} \right\|_{1}\) is convex.
Proof of the Convexity of L2PC: set \(z = \alpha x + \beta y,\; 0 \le \alpha \le 1.0, \;0 \le \beta \le 1.0, \;\alpha + \beta = 1.0\), W is an arbitrary constant matrix.
It has been proved that \(\left| { < U,V > } \right| \le \left| U \right|\left| V \right|, \in R^{n}\). We have
Therefore, \(\left\| {\left( {x - \left| x \right|} \right) \circ W} \right\|_{2}\) is convex.
Appendix 2
For L1PC, given \(f_{1} = \left\| {\left( {x - \left| x \right|} \right) \circ W} \right\|_{1} = \left\| g \right\|_{1}\), where x and W are \(n \times 1\) vectors. W is constant during the iterative optimization procedure.
The gradient operator of \(f_{1}\) is
Here \(\left( X \right)^{*}\) represents the conjugate transpose of matrix X. \(\overline{X}\) represents the complex conjugate of X.
Here,
Here, \(\varepsilon\) is a small scalar value to avoid “division by zero”.
and
For L2PC, given \(f_{2} = \left\| { \left( {x - \left| x \right|} \right) \circ W} \right\|_{2} = g_{2}\), where x and W are \(n \times 1\) vectors. W is constant during the iterative optimization procedure.
The gradient operator of \(f_{2}\) is
Here \(\left( X \right)^{*}\) represents the conjugate transpose of matrix X. \(\overline{X}\) represents the complex conjugate of \(X\).
Its entry
and
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Li, G., Hennig, J., Raithel, E. et al. An L1-norm phase constraint for half-Fourier compressed sensing in 3D MR imaging. Magn Reson Mater Phy 28, 459–472 (2015). https://doi.org/10.1007/s10334-015-0482-7
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DOI: https://doi.org/10.1007/s10334-015-0482-7