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  • Workshop presentation
  • Open Access

Accelerated and KWIC-filtered cardiac T2 mapping for improved precision: proof of principle

  • 1, 2,
  • 1, 2,
  • 1, 2,
  • 1, 2,
  • 1, 2 and
  • 1, 2
Journal of Cardiovascular Magnetic Resonance201517 (Suppl 1) :W30

https://doi.org/10.1186/1532-429X-17-S1-W30

  • Published:

Keywords

  • Phantom Study
  • Radial Image
  • Radial Line
  • Motion Sensitivity
  • Matrix 256x256

Background

In recent years, several successful variations of T2-prepared cardiac T2 mapping techniques have been described for the quantification of cardiac edema [1,2,3]. Radial imaging for high-resolution T2 mapping [3] has the advantage of reduced motion sensitivity, but suffers from a lower signal-to-noise ratio (SNR) due to the undersampling of the periphery of k-space and the density compensation function (DCF) that increases the weight of the relatively noisy and less densely sampled k-space periphery (Fig.1a). Since the contrast of an image is defined by the center of k-space, a KWIC (k-space weighted image contrast [4]) filter can be used to share only the periphery among radial images that have the same geometry and different contrast, such as those used to generate a T2 map (Fig.1b). Furthermore, when undersampling is used to acquire more images per T2 map (resulting in more k-space peripheries that can be shared), KWIC filtering further reduces the noise-like undersampling artifacts (Fig.1c). The goal of this study was therefore to test whether the use of the KWIC filter leads to a higher precision in radial T2 maps for a given acquisition time.
Figure 1
Figure 1

Schematic overview of radial k-spaces and their DCF. a) A normal radial k-space sampling pattern with above it the DCF along one radial line, which will be used to weigh the k-space points when regridding before the Fourier transform. Because of their high density, data from the center of k-space have a much lower weight than data from the outside. b) Three similar k-spaces that share their periphery through the KWIC filter, thus increasing the local sampling density and decreasing the local DCF (which in turn prevents noise amplification). The circles (determined with the Nyquist criterion) indicate the radii outside of which an extra k-space is added. c) An undersampled KWIC-filtered k-space. While the number of lines has decreased, the periphery of k-space still has a higher sampling density.

Methods

Standard navigator-gated radial T2 maps at 3T (Siemens Skyra) were acquired with 3 T2Prep durations, 308 radial lines with golden-angle increment per image, matrix 256x256, and spatial resolution (1.17mm)2 [3] in an agar-NiCl2 phantom with relaxation times that approximated myocardium and blood. Subsequently, T2 maps at the same location were acquired with 6 T2Prep durations, with 308 and 110 lines per image. T2 maps were reconstructed both with and without the KWIC filter. The T2 standard deviations (σT2) of the myocardial compartment in the resulting T2 maps were then compared. Finally, the same protocol was applied for the myocardium in 3 healthy volunteers.

Results

All phantom T2 maps could be successfully reconstructed (Fig.2a). The KWIC-filtered and undersampled T2 map was acquired in 72% of the standard acquisition time, and resulted in a σT2 decrease from 2.1 to 1.2ms (Fig.2b). The acquisitions in the volunteers were similarly successfully reconstructed, and the resulting T2 values and σT2 for the KWIC-filtered T2 maps (38.7±3.3ms) did not differ from the standard T2 maps (37.6±3.1ms, Fig. 2c&d).
Figure 2
Figure 2

Radial T2 mapping with the KWIC filter. a) Example of a T2 map of the phantom, with a homogeneous T2 in blue-green circular compartment that has relaxation times similar to those of the myocardium. b) Results of the different T2 mapping techniques in the phantoms. The KWIC-filtered image that uses ~36% of the radial lines (and thus 72% of the acquisition time) has a significantly lower T2 standard deviation. c and d) Short-axis cardiac T2 maps in volunteers demonstrate equivalency of the undersampled images.

Conclusions

The phantom study demonstrated that the application of the KWIC filter to radial T2 mapping allows for a shortening of the acquisition time together with an increase in precision. The equivalency of the KWIC-filtered protocol in vivo might be caused by the lower overall SNR that is exacerbated by the undersampling, although this needs to be investigated in a larger cohort.

Funding

Emma Muschamp Foundation (RBvH).

Authors’ Affiliations

(1)
Radiology, University Hospital (CHUV) and University (UNIL) of Lausanne, Lausanne, Switzerland
(2)
Center for BioMedical Imaging (CIBM), Lausanne, Switzerland

References

  1. Foltz : MRM. 2003Google Scholar
  2. Giri : JCMR. 2009Google Scholar
  3. van Heeswijk : JACCImaging. 2012Google Scholar
  4. Song : MRM. 2000Google Scholar

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