Simon Stephan1, Simon Reiss1, Thomas Lottner1, Ali Caglar Özen1, and Michael Bock1
1Dept. of Radiology, Medical Physics, Medical Center University of Freiburg, Faculty of Medicine, University of Freiburg, Freiburg, Germany, Freiburg, Germany
Synopsis
For quantitative
myocardial perfusion measurements with intra-arterial contrast agent (CA)
injection precise knowledge of the arterial input function (AIF) is needed. Not
necessarily absolute values of the AIF are needed if blood flow measurements
are used to normalize the perfusion maps. In this work it is shown for a
constant-flow phantom that this method works and probable issues for
transferring the method to in-vivo measurements are discussed.
Introduction
In
MR-guided coronary catheterizations contrast agent (CA) is directly
injected through a catheter, and the dynamic signal change in the
myocardium is mapped to assess myocardial perfusion defects and
vascular supply territories1,2,3.
Recently it was shown that it is also possible to use the tracking
coil of an active catheter to determine the arterial input function
(AIF) for quantitative myocardial perfusion measurements4.
In this work a deconvolution analysis5
was performed to create quantitative perfusion maps. Systematic
differences in the AIF determination were seen between AIFs from
active tracking coils and input functions that are measured in large
blood vessels4.
To overcome this limitation, in this work we developed a
normalization method which is using the measured blood flow around
the catheter coil to normalize the perfusion values.Materials and Methods
To
mimic arterial blood flow into myocardial tissue a perfusion phantom
was constructed from a plastic tube which was connected in series to
a dialysis filter. An active catheter (8F,
see fig. 1) was inserted into the upstream section of the tube to
inject CA and measure the AIF. MR imaging experiments were performed
at a clinical 3T MRI system (Prisma, Siemens) using a FLASH sequence
with saturation recovery preparation. The dynamic signal change was
imaged before, during and after CA injection (10ml-bolus, 0.5%
Gd-DTPA) via the catheter. The following imaging parameters were
used: TE=1.6ms, TR=4.0ms, α=8°,
(Δx)3=0.8×0.8×8.0
mm3.
The image plane was oriented such that it encompassed both the
dialysis filter and the supplying tube to be able to determine a
reference AIF from the images. The catheter AIF was measured by
sampling data in an additional acquisition block without spatial
encoding only from the catheter coil.
Before
and after the perfusion measurement the volume flow rate of the
supplying tube was determined using a phase contrast flow measurement
(VENC=60cm/s). The measured volume flow rate was used for the flow
correction of the measured AIF using the relation4,6: $$$[Gd]_\mathrm{Blood}=\frac{1}{1+q}[Gd]_\mathrm{inj}$$$
with the volume flow rate ratio $$$q=\frac{Q_\mathrm{Blood}}{Q_\mathrm{inj}}$$$.
A
deconvolution analysis5
was implemented to extract quantitative perfusion maps from the AIF.
For every voxel the measured concentration-time curve of the
myocardium was fitted by a convolution of the AIF and a Fermi
function. The perfusion map was normalized by spatial integration and
normalization to the flow measured in the supplying tube, because the
absolute concentration of the CA in the AIF was not known.Results
The
perfusion maps shown in fig. 2 show that the perfusion map of the
dialysis filter is almost identical for the image-based and the
catheter-based method. A quantitative comparison between the two
methods shows an excellent linear correlation (r²
= 1.0) and no systematic flow-dependent deviations (Bland-Altman
plots, fig. 3).Discussion & Conclusion
The
results show the possibility of measuring quantitative perfusion in
the perfusion phantom without the knowledge of the absolute AIF.
Since the perfusion phantom represents an ideal situation, not all
relevant features of the myocardium are represented, and the results
cannot be transferred exactly to in-vivo measurements. Firstly, the
perfusion phantom provides a constant flow, whereas the myocardial
blood flow is pulsatile. This limitation might be overcome using
time-resolved flow measurements and averaging over the cardiac cycle,
which can easily be achieved using fast projection measurements from
the tip tracking coil7.
In
conclusion this work shows that the precision of perfusion
measurements with AIFs from catheter coils might be substantially
increased by adding flow information around the catheter coil. The
technique has shown excellent results in a phantom setup and will be
further tested in in-vivo measurements.Acknowledgements
This
work was partially supported by an institutional cooperation with Siemens. Support from A. Hengerer, F. Maier and A. Krafft (Siemens) is gratefully acknowledgedReferences
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