Correcting Geometric Distortion in B0 Mapping
Paul Chang1,2, Sahar Nassirpour1,2, Ariane Fillmer3,4, and Anke Henning1,3

1Max Planck Institute for Biological Cybernetics, Tuebingen, Germany, 2IMPRS for Cognitive and Systems Neuroscience, Eberhard Karls University of Tuebingen, Tuebingen, Germany, 3Institute for Biomedical Engineering, UZH and ETH Zurich, Zurich, Switzerland, 4Physikalisch-Technische Bundesanstalt, Berlin, Germany

Synopsis

The task of mapping B0 fields to characterise shim fields can be challenging since shim fields generate a highly inhomogeneous field that may be difficult to capture. Furthermore this results in geometric distortion of the B0 map which affects the characterisation of the shim field.

Geometric distortion correction was investigated using a gridded phantom and compared to the effect of using a high bandwidth on the read-out gradient. It was found that using a high bandwidth was more effective in reducing the distortion and that correcting the distortion using a phantom grid was not sufficient.

Introduction

One important application of B0 mapping is to characterise the shim fields as input for the calibration of B0 shim systems. To that end, B0 maps were acquired to assess the shim sensitivities and real shim fields for each shim coil. The problem with measuring strong B0 shim fields is that B0 inhomogeneity causes geometric distortion of the B0 map [1,2].

In this work, we investigate distinct acquisition and post-processing strategies to sufficiently reduce geometric distortions when characterising shim fields of MRI systems.

Method

A 9.4T Siemens Magnetom whole-body human MRI system equipped with an integrated 2nd order spherical harmonic B0 shim system and a 16-channel transceiver array coil [3] was used for all measurements. Two second order shim terms (ZY and XY) at 4mT/m2 were used for the investigation. A 3D gradient echo mapping (GRE) sequence was used based on the suggestions in [4]. The acquisition parameters were as follows: 192x192x192 resolution; 270x270x270mm FOV; TE = 4.00/4.76ms; TR = 10ms.

Two strategies were investigated; firstly, different bandwidths for the read-out gradient were used and secondly, a grid phantom was used for retrospective correction of geometric image distortions.

The read-out bandwidths used were 250Hz/pixel, 500Hz/pixel and 1300Hz/pixel. A 250mm diameter silicon oil cylindrical phantom with a plastic grid (with equidistant spacings of 15mm) was constructed (fig. 1).

For the retrospective distortion correction cross-points of the grid were marked automatically with a custom Matlab™ feature detection script. Cross-points in the cross-plane direction were then manually marked. The corrected positions of the crosspoints and their displacement were then calculated (based on the fact that the grid lines are parallel and spaced at 15mm). The mid-points of the marked cross-points were used to ensure that we took positions where the silicon oil was present (fig. 2).

The real fields were modelled by fitting a linear combination of spherical harmonic functions to the acquired B0 map for each shim term. This was done using either:

1) the entire B0 map of the phantom (without the grid being present during the acquisition to avoid additional distortions due to magnetic susceptibility differences between grid and oil) or

2) the B0 values at the mid-points with and

3) without position correction (with the grid inserted into the phantom during acquisition).

Maps of the modelled real field distributions were reconstructed on a 100x100x100mm FOV using the coefficients of the spherical harmonic functions.

The B0 map acquired with 3D GRE at 1500Hz/Px read-out bandwidth without the grid was used as the reference as it shows negligible geometric distortions (fig. 1 and 3). Fig. 4 shows a slice of the XY B0 map for using each of the three methods described above. Since it was difficult to see the differences, difference maps are shown for the same slice in fig. 5.

To evaluate the performance of the real field modelling and the impact of the retrospective geometric distortion correction difference maps between this reference and the modelled real fields were calculated for different acquisition bandwidths (as shown in fig. 6).

Results and Discussion

Fig. 3 shows the total displacement between the original and corrected mid-points for different bandwidths. The retrospective distortion correction can be seen to reduce the distance errors.

Using a retrospective distortion correction method can reduce the modelling error regardless of the read-out bandwidth (as shown in fig. 6). The improvement is more obvious when a lower bandwidth is used. However, modelling with the entire B0 map consistently gives better results than using the retrospective correction. This is due to the fact that the reduced spatial resolution (of the mid-points) is not sufficient to capture the field.

Therefore, although using a grid-based retrospective correction technique can improve the accuracy of the modelling such that it is comparable to using the entire B0 map, this method is more time-consuming. Furthermore, using the grid also introduces more susceptibility inhomogeneity in the B0 maps. Therefore, a grid-free, high read-out bandwidth B0 mapping sequence is recommended.

Conclusion

In conclusion, to reduce geometric distortion when measuring B0 maps, a high bandwith for the read-out gradient is sufficient. The use of a grid phantom for retrospective correction may increase the accuracy of the modelling. However, compared to using a grid-free B0 map acquired with a high bandwidth, the reduced sampling and higher susceptibility distortion of the grid phantom may make the modelling less accurate.

Note that this study was done assuming the reference field was an accurate estimation of the actual field. The study can be improved if a more reliable method of measuring the actual field was available.

Acknowledgements

No acknowledgement found.

References

[1] P. Jezzard and R. S. Balaban (1995) MRM

[2] P. Jezzard and S. Clare (1999) Human Brain Mapping

[3] G. Shajan et al. (2011) Proc. of ISMRM

[4] L. N. Baldwin et al. (2007) Medical Physics

Figures

Fig. 1 Section of a slice measured with a read-out gradient of (a) 250 Hz/Px, (b) 500 Hz/Px and (c) 1300 Hz/Px. Magnitude images in the top row shows clear distortions whereas the B0 maps on the bottom row do not.

Fig. 2 Mid-point (red) of the marked cross-points (blue) on the phantom grid. The mid-point is used as the B0 value and position since the silicon oil is between the phantom grid.

Fig. 3 The distance error between the corrected and uncorrected cross-points for the ZY term. As the read-out bandwidth increases, the distance between the corrected and corresponding uncorrected points decreases.

Fig. 4 Reconstructed B0 maps @ 0.1mT/m2 [Hz] of the XY term measured at 250Hz/Px using the mid-points (left), corrected mid-points (middle), and entire image (right).

Fig. 5 The difference between the reconstructed B0 map and the reference map @ 0.1mT/m2 [Hz]. Only one slice of the XY term is shown.

Fig. 6 Std. dev.(Hz) of the difference between the reference B0 map and modelled B0 fields @ 0.1mT/m2 on a 100x100x100mm FOV. The fields were reconstructed using spherical harmonic coefficients using only the mid-points, using corrected mid-points and using the entire B0 map.



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