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