Kai Ruppert1, Faraz Amzajerdian1, Yi Xin1, Hooman Hamedani1, Luis Loza1, Tahmina S. Achekzai1, Ryan J. Baron1, Ian F. Duncan1, Harrilla Profka1, Yiwen Qian1, Mehrdad Pourfathi1, Federico Sertic1, Stephen Kadlecek1, and Rahim R. Rizi1
1Radiology, University of Pennsylvania, Philadelhia, PA, United States
Synopsis
Septal
wall thickness (SWT) measurements with hyperpolarized xenon-129 (HXe) MRI are
typically conducted as spectroscopic acquisitions that lack spatial
information. Recently, efforts have been made to obtain spatial maps of SWT.
Here, we investigated differences in apparent lung physiology between
peripheral and central lung regions and found an
implausible change in observed capillary transit time and SWT from the
periphery to the center of the lungs. This effect is likely caused by the
transport of xenon-saturated blood towards the heart, and is not based on
physiological differences, thus requiring a fundamental revision of analytical
gas uptake models.
Purpose
Apparent
alveolar septal wall thickness (SWT) measurements obtained with hyperpolarized
xenon-129 (HXe) MRI are sensitive to inflammatory or fibrotic pathologies in
the lung parenchyma1-7. Such measurements are typically conducted in
the form of global spectroscopy acquisitions that lack spatial information. In
recent years, efforts have been made to obtain regional maps of SWT8,9.
However, the analytical models used to extract this metric from the acquired
xenon gas uptake measures are all based on the assumption of unidirectional gas
transfer from the alveoli to the lung parenchyma, with subsequent xenon
accumulation in the downstream blood pool. While such assumptions are a
reasonably accurate description for the lung as a whole when assessed with
global spectroscopy, these prerequisites break down at the regional level,
where the xenon signal in more central lung volumes might also be affected by
inflowing blood from the periphery. In this work, we investigated whether there
is a regional difference in the observed apparent gas uptake between peripheral
and central lung regions.Methods
Imaging
experiments were performed in sedated New Zealand rabbits (approx. 4 kg).
Animals were ventilated with room air until imaging began, at which point the
gas mix was switched to 20% oxygen and 80% HXe for 5 breaths (6 ml/kg tidal volume),
followed by an 8-s breath-hold at either end inspiration (EI) or end expiration
(EE). All studies were approved by the Institutional Animal Care and Use
Committee.
MR imaging was
conducted using
a 1D-projection gradient-echo sequence with left-to-right frequency encoding that
employed a non-selective 700-μs Gaussian RF excitation pulse centered at
the dissolved phase (DP) resonance 3,530 Hz downfield from the gas-phase
resonance. Taking advantage of the large frequency difference between the two
phases combined with a sufficiently small acquisition bandwidth, HXe in the
pulmonary air spaces and dissolved in the lung tissue were imaged
simultaneously, side-by-side10-12. The following sequence parameters
were used: matrix size 1920×80; TE 2.6 ms; FOV 220 mm; receiver bandwidth 120
Hz/pixel; flip angle 7°, TR 10 ms (TR90°,equiv 1.3 s10).
During the breath hold, the dissolved-phase magnetization was saturated 6 times
every 500 ms with 3 consecutive 3-ms frequency-selective Gaussian RF pulses
centered at 200 ppm and separated by 1.2 ms spoiler gradients. Septal wall
thickness and capillary transit time were calculated using the analytical
uptake model of Patz et al.13, based on the recovery of the averaged
dissolved-phase signal following each saturation pulse. All MR studies were performed at 1.5T (Avanto; Siemens) using a custom
xenon-129 transmit/receive birdcage coil (Stark Contrast, Erlangen, Germany).
Enriched xenon gas (87% xenon-129) was polarized using a prototype commercial
system (XeBox-E10, Xemed LLC, Durham, NH).Results and Discussion
Figure 1a shows the normalized 1D DP signal in
the rabbit lung as a function of time following saturation of the DP
magnetization. The signal within the cardiac cavity was set to zero due to its
low signal-to-noise ratio. For clarification, the DP signals of just the edges
of the lung are plotted in Fig. 1b. While the xenon accumulation in the
periphery of the lung levels off following the initial filling phase, the xenon
signal at the center of the lung keeps increasing, indicating a continued
inflow of DP magnetization from the blood flow towards the heart. These
discrepancies in gas accumulation dynamics are reflected in an apparent drop of
the extracted capillary transit time (Fig. 1c) and an apparent increase in
alveolar SWT (Fig. 1d), respectively, from the periphery towards the center. Since
in a healthy lung no such outside-in asymmetry of transit time and SWT is
plausible, it most likely can be attributed to regional differences in gas
transport dynamics.Conclusion
We demonstrated an implausible change in
observed capillary transit time and SWT from the periphery to the center of the
lungs. This effect is likely caused by the transport of xenon-saturated blood
towards the heart, giving rise to an unaccounted signal increase that biases
the model-based parameter extraction and is not based on physiological
differences. Our measurements indicate that the assumptions underlying the existing
analytical gas-transport models are violated in the case of spatially resolved
SWT measurements. We therefore conclude that the extraction of consistent SWT
maps from regional xenon gas uptake images necessitates a fundamental revision
of these models.Acknowledgements
Supported by NIH grants
R01 EB015767, R01 HL129805, S10 OD018203 and R01 CA193050. References
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