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  • Meeting abstract
  • Open Access

2134 Validation of the spiral Fourier velocity encoding method

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Journal of Cardiovascular Magnetic Resonance200810 (Suppl 1) :A403

https://doi.org/10.1186/1532-429X-10-S1-A403

  • Published:

Keywords

  • Wall Shear Stress
  • Wall Shear Rate
  • Gold Standard Reference
  • Slice Profile
  • Visual Agreement

Introduction

Phase-contrast (PC) is the current "gold standard" for MR flow quantitation, despite suffering from partial volume effects. Fourier velocity encoding (FVE) resolves the distribution of velocities within each voxel, allowing larger voxels to be used. In 1995, Frayne et al. [1] proposed 2DFT FVE as a method for non-invasively measuring fluid shear rate and hence vascular wall shear stress, an important factor implicated in atherogenesis. Although the scan-time of this method was prohibitively long, the recently introduced spiral FVE method [2] shows promise as it is substantially faster. In this work, we provide an initial validation of spiral FVE in a carotid artery flow phantom, using high-resolution PC as the gold standard.

Theory

The spiral FVE method acquires a stack-of-spirals in k x , k y , k v space [2], where k v is the Fourier variable associated with the velocity distribution. Truncation in k-space follows a cylindrical shape, i.e. circular along k x , k y (with diameter 1/xy res ), and rectangular along k v (with width 1/v res ). The associated object-domain blurring can be modeled as convolution of m(x, y, v) with jinc(sqrt(x2+y2)/xy res ) and sinc(v/v res ).

Methods

Experiments were performed on a GE Signa Excite HD 3 T scanner with a pulsatile carotid flow phantom (Phantoms by Design, Inc.). A slice perpendicular to the carotid bifurcation was prescribed, and through-plane velocities were measured. A gradient-echo 2DFT phase-contrast sequence (0.33 mm resolution, 10 NEX) was used as a gold standard reference. Spiral FVE data with 3 mm resolution was obtained from the same scan plane. Both PC and FVE acquisitions were prospectively gated. The total scan time was 22 minutes for PC, and 24 seconds for FVE.

A simulated FVE dataset was derived from PC using the convolution model described above. For each temporal phase, the images m(x, y) and pc(x, y) (magnitude and phase difference, respectively) were used as follows:

fve(x, y, v) = [m(x, y).sinc (v-pc(x, y))/v res ] * jinc(sqrt(x2+y2)/xy res )

Spatial registration between PC-derived and measured FVE data was performed by visual inspection.

Results

For reference, magnitude and phase-difference images obtained from the first temporal phase of the phase-contrast data are shown in Figure 1. Simulated and measured time-velocity FVE distributions from representative voxels (circles in Figure 1) are shown in Figure 2.
Figure 1
Figure 1

Magnitude and phase-difference images obtained from the first temporal phase of the PC data.

Figure 2
Figure 2

PC-derived (top row) and spiral FVE (bottom row) time-velocity distributions from voxels at the indicated positions in Fig. 1.

Despite differences in temporal resolution, SNR, TR, flip angle and slice profile, good agreement was observed between simulated and measured FVE distributions. These results suggest that spiral FVE is capable of providing velocity histograms equivalent to those obtained with high-resolution 2DFT phase-contrast, in considerably shorter scan time.

Discussion

Spiral FVE is a time-efficient flow measurement method that provides spatially and temporally resolved velocity distributions in short acquisitions. It has been shown to work well in vivo [2], and has great potential for acceleration [3]. Velocity histograms obtained with spiral FVE showed good visual agreement with those obtained using high-resolution PC, even though acquired in a scan time 50 times shorter. We plan to repeat this study using identical TR, flip angle, and slice profile to quantify the level of agreement, and explore the use of spiral FVE for non-invasive measurement of wall shear rate with reasonable scan-times.

Authors’ Affiliations

(1)
University of Southern California, Los Angeles, CA, USA

References

  1. Frayne R, et al: MRM. 1995, 34: 378-View ArticlePubMedGoogle Scholar
  2. Carvalho JLA, et al: MRM. 2007, 57: 639-View ArticlePubMedGoogle Scholar
  3. Carvalho JLA, et al: Proc ISMRM. 2007, 15: 588-Google Scholar

Copyright

© Carvalho et al; licensee BioMed Central Ltd. 2008

This article is published under license to BioMed Central Ltd.

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