Alexey Samsonov1, Aaron Field1, Vasily Yarnykh2, and Julia Velikina3
1Radiology, University of Wisconsin, Madison, WI, United States, 2Radiology, University of Washington, Seattle, WA, United States, 3Medical Physics, University of Wisconsin, Madison, WI, United States
Synopsis
Macromolecular proton fraction (MPF), the key two-pool MT model parameter, was established as a robust myelin-sensitive index, with clinical
relevance in demyelinating diseases. However, as MPF assesses macromolecules relative
to tissue water, its specificity to myelin is limited. i.e., MPF changes
may occur independent of myelin, e.g., in the setting of inflammation and edema. Further, relating MPF to macromolecules may be
ambiguous due to unequal concentrations of protons in macromolecular and
water compartments. We demonstrate
implications of these effects for MPF
interpretation using phantom and ex-vivo experiments and propose a
new macromolecular measure that explicitly accounts for tissue water
effects.
INTRODUCTION
Two-pool
modeling of magnetization transfer (MT) effect in biological tissue yields several parameters uniquely characterizing its macromolecular and water compartments1. The key parameter of
interest, macromolecular proton fraction (MPF),
was established as a robust myelin-sensitive index2-4, with demonstrated clinical
relevance in demyelinating diseases,
including multiple sclerosis (MS)5-7. However, as MPF only assesses macromolecules relative
to tissue water, its specificity to myelin is necessarily limited, i.e., changes
in MPF may occur independent of myelin
status, e.g., in the setting of inflammation and edema8, which alter tissue water
content and vary with disease course and therapy9. Further, relating MPF to macromolecular content may be
ambiguous due to unequal molar concentrations of protons in macromolecular and
water compartments10. In this work, we demonstrate
implications of these effects for MPF
interpretation using controllable phantom and ex-vivo experiments and propose a
new measure of macromolecular content that explicitly accounts for tissue water
effects.THEORY
$$$MPF$$$ is defined as a ratio of macromolecular
($$$M_b$$$) to total ($$$M_0$$$) (i.e., macromolecular+free water ($$$M_w$$$)) proton magnetizations:$$MPF=M_b/M_0\\ M_0=M_b+M_w.$$Equivalently, in terms of compartment-specific molar proton
concentrations $$$C_b,C_w$$$ and volumes $$$V_b,V_w$$$10,$$MPF=C_bV_b/(C_bV_b+C_wV_w).$$The sought
proportionality of $$$MPF$$$ to $$$V_b$$$ is confounded by its dependence
on $$$V_w$$$ and ratio of $$$C_b$$$ to $$$C_w$$$. To circumvent these limitations, we propose to measure macromolecular
protons with respect to a standard reference, e.g., magnetization of pure water
($$$M_{ref}$$$). The new parameter, macromolecular proton content ($$$MPC$$$),$$MPC=M_b/M_{ref},$$can be calculated as$$MPC=PD_T\cdot{MPF}.$$Here, $$$PD_T=M_0/M_{ref}$$$ and reflects
the total (macromolecules + water) proton density. Using standard $$$PD$$$ map from variable flip angle (VFA), spoiled
gradient echo (SPGR) single-pool $$$PD/T_1$$$ mapping11 as an estimate of $$$PD_T$$$ may not be accurate,
because it does not account for macromolecular protons. Instead, we utilize modified
cross-relaxation imaging (mCRI) method12, which estimates $$$MPF$$$ and other two-pool MT parameters
accounting for total magnetization in its equation, given in general form as:$$I=S_0\cdot{F}_{ST}(MPF,k,R_{1w},T_{2b}),$$where $$$S_0$$$ is
total magnetization weighted by instrumental scaling $$$\beta$$$,
receiver sensitivity $$$C$$$, and $$$R_2^*$$$ decay:$$S_0=\beta{C}e^{-R_2^*T_E}M_0.$$It follows that $$$PD_T$$$ can be obtained by demodulating
by pre-measured $$$C$$$ and $$$R_2^*$$$ maps,$$S_{0,D}=\frac{S_0}{Ce^{-R_2^*T_E}},$$and normalizing
result by its average in pure water (e.g., in water vial):$$PD_T=S_{0,D}/<S_{0,D}>.$$METHODS
The
experiments were performed in gelatin phantoms and ex-vivo tissue. One phantom
set was created by dissolving gelatin in H2O at 20,30,40,50% concentrations (by weight). The second set of 30% gelatin
phantoms was created using mixtures of H2O and MRI-invisible D2O of varying
proportions (D2O=0,25,50,75%).
One hemisphere of fixed canine brain slab was soaked in 40%/60% D2O/H2O mix until reaching diffusion equilibrium with
tissue water (controlled by monitoring MRI signal until its stabilization, ~1h)
to modulate tissue water compartment. The other hemisphere was placed into
water and served as the control. Experiments were performed on 3.0T GE MR750
(Waukesha, WI). The objects were scanned along with water vial as a reference
using 8ch coil. mCRI acquisition protocol included B1 mapping with AFI13 and four VFA SPGR and eight MT-SPGR
scans with different combinations of off-resonance frequency and MT saturation powers
as described before12. A reference scan from each set
was repeated with body coil. The receiver
sensitivity $$$C$$$ was obtained using body
coil normalization14 with correction of residual sensitivity
by 2nd order polynomial15. $$$R_2^*$$$ effects were ignored due to short $$$T_E$$$=1.7ms. The fit was performed with
full mCRI model12. Ten WM and
ten GM structures were manually labelled in D2O-treated hemisphere of the
ex-vivo sample; ROIs placed in the contralateral structures of non-treated
hemisphere served as paired controls. The differences were evaluated using
paired t-test, with statistical significance set at p=0.05.RESULTS
Figure
1 illustrates correction in H2O+D2O+30%
gelatin phantoms. MPF increases
dramatically with increasing D2O
proportion (decreasing water content) demonstrating its limitation for tissue
water-independent assessment of macromolecules. Low sensitivity of MPC to H2O+D2O proportions indicates its higher
specificity to macromolecular content. Both MPF
and MPC vary linearly with gelatin concentration
in H2O phantoms (Fig. 2).
Yet, the analysis of intercepts indicates a weaker agreement with absolute macromolecular
content for MPF as compared to MPC, potentially due to different proton
molar fractions in gelatin and water. Figure 3 shows results of ex-vivo
experiments. MPF values in WM/GM were
significantly different (p<1e-5) between control and D2O-treated hemispheres (percent errors relative to the
control 31.20%/25.98% for WM/GM, respectively). At the same time, MPC differences (1.34%/2.44%) were not
statistically significant (p=0.38/0.11). Correction by standard PD map from VFA SPGR fit11 led to more
pronounced and statistically significant differences in MPC (5.29%/4.71%, p<0.003), indicating improved accuracy of
mCRI-based mapping for tissue
water correction.CONCLUSIONS
Our
results confirm theoretical sensitivity of MPF
to water compartment properties. As such, its interpretation
may be ambiguous in settings of inflammation and edema and other pathological
substrates modulating tissue composition (e.g., gliosis and cellular
infiltrations). The proposed MPC
compensates the tissue water effects using mCRI-based estimate of proton
density and external water standard for normalization. For in-vivo applications, the normalization may be based on the cerebrospinal
fluid signal, which provides internal, temperature-consistent reference in
standard PD mapping16.
MPC may be useful as a measure of brain
remyelination in trials of anti-inflammatory MS therapies and stroke studies,
in which normalization of water content due to resolution of edema is known to
affect other tissue water-sensitive outcome measures of brain repair9,17. Acknowledgements
The
work was supported by NIH (R01EB027087, R21NS109727) and GE Healthcare.
We thank Dr. Ian Duncan (UW-Madison) for providing the fixed brain
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