Feasibility of Time-Resolved Subtractionless Contrast Enhanced Dixon MRA of the lower legs on 1.5T
Marc Kouwenhoven1, Silke Hey1, Christine Nabuurs1, Alan Huang1, Adri Duijndam1, Elwin de Weerdt1, Holger Eggers2, Niels Blanken3, and Tim Leiner3

1Philips, Best, Netherlands, 2Philips Research, Hamburg, Germany, 3Radiology Dept., University Medical Center, Utrecht, Netherlands

Synopsis

In this work, the feasibility is explored for subtractionless first-pass time-resolved contrast enhanced MRA of the lower legs on 1.5T using Dixon, viewsharing and parallel imaging with high acceleration factors. Results in seven consecutive patients are analyzed and compared with the conventional subtraction method. It is demonstrated that with the subtractionless method, bulk motion artifacts are eliminated, and SNR is significantly increased.

Introduction

Recently, a subtractionless Dixon method was proposed for first-pass stepping-table peripheral MRA, which relies on fat suppression instead of subtraction to reduce the background signal [1]. Advantages were shown to be higher SNR and CNR, robustness to motion, and a shorter scan time. Time resolved MRA of the lower legs has been shown to be beneficial as an add-on to multi-station peripheral MRA for patients with critical limb ischemia [2]. Time resolved MRA of the lower leg vessels using viewsharing techniques has been shown to be feasible [2,3] using subtraction of a mask to suppress background signal in all dynamic phases. Dixon has been applied on 3T with time resolved viewsharing techniques for dynamic contrast enhanced (DCE) MRI of the breast [4], and with time-resolved subtractionless CE-MRA using an interleaved variable density sampling pattern [5].

Purpose

The purpose of this work is to investigate the feasibility and show the potential benefits of time resolved subtractionless contrast enhanced MRA on 1.5T with viewsharing and a large FOV in the lower legs, using mDixon with flexible (shortest) echo times and parallel imaging with high acceleration factors. The novel approach was compared to conventional subtraction-based time-resolved MRA.

Methods

Seven patients with known or suspected peripheral vascular disease were examined on an Ingenia 1.5T scanner (Philips, Best, Netherlands) using the standard Anterior Body Coil and the built-in posterior coil. A single dose of Gadobutrol (Bayer Healthcare, Berlin, Germany) was used, with an injection speed of 1 mL/sec. 3D volumetric images were acquired with a FOV of 430 x 430 mm2 and a volume thickness of 150 mm, using a T1-weighted spoiled dual-gradient-echo sequence with a bandwidth of 610 Hz/pixel and a TE1/TE2/TR of 1.8/3.6/5.6 ms. Acquired spatial resolution was 1.1 x 1.1 x 2.0 mm3; data was reconstructed to 1 x 1 x 1 mm3. An eightfold acceleration by parallel imaging (SENSE) was used, with a partial Fourier factor of 0.65, which together with the use of an elliptical k-space shutter resulted in a net acceleration of 15.5x. Viewsharing was applied with a keyhole percentage of 15% and a peripheral sampling density of 25% [3,4,6], resulting in an additional 2.76 fold increase in temporal resolution. Compared to fully sampled conventional scanning, this resulted in a total net acceleration factor of 43. The temporal resolution per dynamic phase was 5.5 sec, with a temporal footprint of 19.5 sec. To enable comparison with conventional subtraction, a mask was acquired at the beginning of the acquisition. 12-19 dynamic phases were acquired. Total scan time was 1:25-2:00 minutes. Water images were reconstructed using mDixon reconstruction capable of handling flexible echo times, using a multi-peak spectral fat model [7]. Source modulus images were obtained from the first echo. The comparison between water and subtracted modulus images could thus be made from the same acquisition.

Results

In 1/7 patients (14%) significant motion was observed, corrupting the subtraction images; in a further 2/7 patients (28%) only mild motion was observed. Compared to the subtracted modulus images, the SNR in the unsubtracted Dixon water images was increased by a factor of 1.89 (SD 0.19) on average. Coronal MIPs obtained in two patients with disease in the tibial and peroneal arteries are shown in Fig. 1, 2 and 3. The effect of bulk motion is shown in Fig. 4, where misregistration artifacts in the subtracted modulus images significantly increases the background signal. As can be seen from the water images in Fig. 4, the subtractionless mDixon method effectively eliminates these motion artifacts.

Discussion

Compared to the subtracted modulus images, the increase in SNR for the unsubtracted Dixon water images was a factor of 1.89 on average, which is in line with theoretical predictions [8]. No significant water-fat swap artifacts were observed, despite the echo spacing of 1.8 ms, which is relatively short for Dixon on 1.5T. The viewsharing and high acceleration factor allowed a sufficiently high temporal resolution with a relatively thick 3D volume, which facilitates easy planning.

Conclusion

The feasibility of time-resolved subtractionless MRA with viewsharing, Dixon and parallel imaging with a high acceleration factor has been demonstrated in this work on patients at 1.5T. The main advantages of the subtractionless method are nearly doubled SNR and the elimination of misregistration artifacts due to bulk patient motion. Both advantages can contribute to better clinical imaging, since the main indication for time-resolved MRA of the lower legs is for patients with critical limb ischemia, which often find it difficult to lay still for a longer period, and in which it can be important to visualize small (collateral) vessels.

Acknowledgements

References

1. Leiner T, Habets J, Versluis B, Geerts L, Alberts E, Blanken N, Hendrikse J, Vonken EJ, Eggers H. Subtractionless first-pass single contrast medium dose peripheral MR angiography using two-point Dixon fat suppression. Eur Radiol 2013;23(8):2228-2235.

2. Andreisek G, Pfammatter T, Goepfert K, Nanz D, Hervo P, Koppensteiner R, Weishaupt D. Peripheral arteries in diabetic patients: standard bolus-chase and time-resolved MR angiography. Radiology 2007;242(2):610-620.

3. Voth M, Haneder S, Huck K, Gutfleisch A, Schonberg SO, Michaely HJ. Peripheral magnetic resonance angiography with continuous table movement in combination with high spatial and temporal resolution time-resolved MRA With a total single dose (0.1 mmol/kg) of gadobutrol at 3.0 T. Invest Radiol 2009;44(9):627-633.

4. Le Y, Kroeker R, Kipfer HD, Lin C. Development and evaluation of TWIST Dixon for dynamic contrast-enhanced (DCE) MRI with improved acquisition efficiency and fat suppression. J Magn Reson Imaging 2012;36(2):483-491.

5. Morrison CK, Rahimi MS, Wang K, Holmes JH, Bannas P, Motosugi U, Korosec FR. Time-resolved Dixon MR angiography of patients with peripheral vascular disease at 3.0 T, Abstract 0241, Proceedings of the joint ISMRM-ESMRMB meeting, 2014, Milan, Italy.

6. Lim RP, Shapiro M, Wang EY, Law M, Babb JS, Rueff LE, Jacob JS, Kim S, Carson RH, Mulholland TP, Laub G, Hecht EM. 3D time-resolved MR angiography (MRA) of the carotid arteries with time-resolved imaging with stochastic trajectories: comparison with 3D contrast-enhanced Bolus-Chase MRA and 3D time-of-flight MRA. AJNR Am J Neuroradiol 2008;29(10):1847-1854.

7. Eggers H, Brendel B, Duijndam A, Herigault G. Dual-echo Dixon imaging with flexible choice of echo times. Magn Reson Med 2011;65(1):96-107.

8. Stinson EG, Trzasko JD, Weavers PT, Riederer SJ. Dixon-type and subtraction-type contrast-enhanced magnetic resonance angiography: A theoretical and experimental comparison of SNR and CNR. Magn Reson Med 2015; 74:81-92

Figures

Fig. 1. Coronal MIP projections of 10 selected consecutive dynamic phases of the unsubtracted Dixon water images. Temporal resolution is 5.5 seconds, with a temporal footprint of 19.5 seconds.

Fig. 2. Coronal MIPs of subtracted modulus images (left) and of unsubtracted Dixon water images (right).

Fig. 3. Coronal MIPs of subtracted modulus images (left) and of unsubtracted Dixon water images (right).

Fig. 4. Coronal MIPs of subtracted modulus images (top row) and of unsubtracted Dixon water images (bottom row) from a patient with significant motion especially towards the end of the acquisition. 3 selected dynamic phases are shown; 20 seconds (left column), 58 seconds (middle column) and 1:46 (right column).



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