Kilian Stumpf1, Andreas Horneff1, Jan-Bernd Hövener2, and Volker Rasche1
1Department of Internal Medicine II, University Medical Center Ulm, Ulm, Germany, 2Department of Radiology and Neuroradiology, University Medical Center Kiel, Kiel, Germany
Synopsis
Artifacts due to the presence of metallic dental
materials often limit the application of MRI. These materials, such as dental
implants or fillings, often cause substantial artifacts e.g. in the oral cavity
impairing diagnostic accuracy. In this contribution, we present an approach for
conducting spin-echo based sequences with significantly reduced flip angles and
high excitation bandwidths of up to 17 kHz by using an inductively coupled local
coil, which in combination with single-point methods enables almost completely
artifact-free local imaging of e.g. dental titanium implants.
Introduction
Field inhomogeneities, e.g. induced by metallic implants,
cause strong off-resonances resulting in often severe image artifacts in its vicinity.
Spin-echo (SE) techniques are conventionally applied to cope with the resulting
rapid T2* decay1. The need for large flip angles (FA) results in a
limited excitation pulse bandwidth, leading to signal voids close to a metallic
object due to non-excited off-resonant spins. In order to remove these signal
voids, multispectral imaging (MSI) methods like MAVRIC-SL2 have been
suggested. However, MSI methods are prone to additional image artifacts, caused
by the combination of the separately acquired spectral images3. In
this contribution, we present a method that allows for local SE scans with
drastically reduced global FAs and high excitation bandwidths, thus enabling
excitation of spins even in close vicinity of metallic objects. In combination with
a single-point imaging (SPI) approach4, the feasibility of nearly artifact
free local imaging near metallic dental materials is demonstrated.Methods
All data were acquired with a 3T whole-body clinical
imaging system (Achieva, Philips Healthcare, The Netherlands) with a
four-element receive coil (Carotid Coil, Shanghai Medical Technologies). An
additionally used inductively coupled volume coil (ICC)5 lead to local
SNR enhancement within its local sensitivity range, thereby intrinsically
reducing the FOV. For the proposed approach, no decoupling of the ICC was
performed during excitation, resulting in a strong local B1 and hence FA
enhancement within the sensitivity region of the coil. With this approach, 90°
and 180° pulses can be achieved locally with low global RF excitation power, enabling
shorter pulse durations, higher excitation bandwidths and shorter acquisition
times.
The
vendor’s 3D Turbo Spin
Echo (3D-TSE) sequence was modified to allow the use of high-bandwidth Sinc-Gauss
pulses (3D-hBW-TSE). In order to completely avoid distortions and pile-up
artifacts a fully phase encoded 3D-TSE SPI sequence (3D-hBW-PESE) employing
non-selective block-shaped excitation and refocusing pulses was implemented. In
order to identify the load dependent B1 enhancement of the ICC, several FIDs,
each excited with a different FA (in the range of 1°-25°), were acquired before
each experiment. From the maximum and minimum signal intensities of the first
data points (k0), the local 90° and 180° FA
equivalents were identified. A B1 map of a phantom (agarose filled tube) was
acquired for validation. All data were reconstructed with an in-house build
reconstruction framework implemented in Matlab.
The suggested approach was evaluated for a titanium
dental implant screw (10x4.1mm) immersed in agarose and a porcine jaw
containing two dental implant screws. Relevant imaging
parameters are provided in Table 1.Results
Fig. 1A shows the FID signal intensities in dependence
on the global FA applied. A global FA of 6° was identified as the 90°
equivalent, indicating a 15-fold FA enhancement in the sensitivity range of the
ICC. The respective B1 map (Fig. 1B) acquired with global FA of 4° revealed
a local ICC FA of 60°, thus confirming the 15-fold FA enhancement.
FA
pairs of 6°-12° (agarose phantom) and
7.5°-15° (porcine jaw) yielded maximum excitation and refocusing bandwidths of
7.1 kHz (phantom and jaw) for the 3D-hBW-TSE
and 17.2 kHz (phantom) / 13.9 kHz (jaw) for the 3D-hBW-PESE sequences. In
comparison, for conventional 3D-TSE the maximum excitation bandwidth for a
90°-180° pulse pair resulted in 1.4 kHz.
Fig. 2 shows the 3D-TSE (A,B), 3D-hBW-TSE (C,D) and
3D-hBW-PESE (E) images of the implant screw for two different frequency
encoding directions. Signal loss and distortions are clearly visible in the
3D-TSE images, which can be clearly reduced in the 3D-hBW-TSE images. The
slightly increased pile-up artifacts as well as the remaining image distortions
can almost completely be removed with 3D-hBW-PESE. Quantitative
analysis of the apparent screw dimension yields 22.3x8.7 mm² (3D-TSE), 14.7x6.2
mm² (3D-hBW-TSE), and 10.4x4.5mm² (3D-hBW-PESE).
Images
of a porcine jaw containing two titanium dental bone-level implant screw (Fig. 3)
show similar outcome. The large areas with signal loss resulting in the FLASH
images (A,B) can be reduced with the 3D-hBW-TSE approach (C,D). 3D-hBW-PESE
(E,F) results to almost complete removal of all apparent susceptibility induced
artifacts.Discussion and Conclusions
Typical metal-induced artifacts as visible in conventional
3D-TSE and 3D-FLASH techniques can be distinctly reduced by higher excitation
bandwidth 3D-hBW-TSE, enabled by local B1 enhancement. However, the increase in
excitation bandwidth can lead to stronger pile-up artifacts in sequences using
frequency encoding, due to the larger amount of off-resonant excited spins. Almost
completely artifact free images can be achieved by combining local B1
enhancement with spin echo based SPI techniques as shown by the 3D-hBW-PESE
approach. Even though the combination of local B1 enhancement with conventional
3D-TSE methods yield distinct metal artifact reduction, in cases where the
direct vicinity of e.g. the implant is of interest the combination with SPI
methods appears promising. Further combination of 3D-hBW-PESE with advanced
undersampling techniques6 may further foster clinical application by
acquisition times in the minute range.Acknowledgements
JBH wishes to acknowledge funding by the DFG
(HO-4604/2-1)
The authors thank the Ulm University Center for Translational Imaging MoMAN for its support.
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