Hao Peng1, Liwen Wan1, Qian Wan1, Chuanli Cheng1, Xin Liu1, Hairong Zheng1, and Chao Zou1
1Shenzhen Institutes of Advanced Technology,Chinese Academy of Sciences, Shenzhen, China
Synopsis
T1 relaxation
time has been a valuable biomarker with emerging applications in cardiac
diseases and liver function. Traditional inversion-recovery T1 quantification
method is frequently applied as the reference for various T1 quantification
methods. When applied in targets where fat and water signals co-exists, the single
component fitting model would be in a dilemma. Combining the inversion-recovery T1 quantification
with existing fat-water quantification methods, this work presented a solution
for multi-component T1 quantification.
Proposed method has been tested on fat-water phantoms and showed good
consistency over a wide range of fat fractions.
Introduction
T1 relaxometry
has been an important quantitative tool for tumor detection[1] and fibrosis
stating[2]. However, when applied to the tissues with steatosis, the
unwanted fat signal would hinder the measurement of tissue T1. In this work, the conventional
inversion-recovery T1 measurement was combined with fat-water quantification
methods[4] to remove the bias from short T1 fat
signals and simultaneously evaluate the T1 relaxation time for fat and water components. Proposed
method was validated in fat-water phantoms and showed good consistency under
different fat-water ratios.Theory
$$$T_{1}$$$ relaxometry
based on inversion recovery method with multiple inversion time can be
formulated as:
$$$S_{n}=|M_{0}(1-\alpha \cdot e^{-\tau_{n}/T_{1}}+e^{-TR/T_{1}})| (1)$$$
where Sn is the signal
acquired at different inversion time τn; M0 is
the initial magnetization; α stands
for the actual inversion efficiency considering the imperfection of inversion pulse; T1 is
the unknown longitudinal relaxation time; TR is the repetition time. When
applied to organs such as liver or myocardium with fat infiltration, only an
apparent T1 relaxation
time could be derived through the original single component fitting model. To
simultaneously estimate the longitudinal relaxation time for both fat and water
component, the fitted model should be adjusted as follows:
$$$S_{n}=|M_{w}(1-\alpha_{w} \cdot e^{-\tau/T_{1,w}}+e^{-TR/T_{1,w}})+M_{f}(1-\alpha_{f} \cdot e^{-\tau/T_{1,f}}+e^{-TR/T_{1,f}})| (2)$$$
Mw and Mf was was
the signal intensities contributed from water and fat component respectively; T1,w and T1,f were
the longitudinal relaxation times for water and fat components; αw and αf was
the inversion efficiency considering the imperfections of the 180° RF
pulse for water and fat components respectively. Fat and water ratio could be evaluated
by the existing proton density fat fraction (FF) quantification method prior to
inversion-recovery scans, Eq.(2) can be converted to:
$$$S_{n}=M_{0}|(1-FF)\cdot(1-\alpha_{w} \cdot e^{-\tau/T_{1,w}}+e^{-TR/T_{1,w}})+FF\cdot(1-\alpha_{f} \cdot e^{-\tau/T_{1,f}}+e^{-TR/T_{1,f}})| (3)$$$Materials and methods
A
series of fat-water phantoms was constructed to investigate the accuracy of
proposed method. Fat-water phantoms #1-#7 was constructed according to ref.6
with FF ranged from 0 to 27.43%. A
concentration of 0.05mmol/L gadolinium was dropped to phantoms #8-#14 with FF
ranged from 0 to 25.68% to
shorten the phantom T1. To evaluate
the proton density fat fractions of these phantoms, a 2D multi-echo GRE
sequence was scanned beforehand with TE = 2.43/4.11/5.79/7.47/9.15/10.83ms,
flip angle = 2°, TR
= 19ms. For inversion recovery T1 measurement,
inversion time τ was
set to 100ms, 600ms, 1100ms, 2100ms, and 2600ms, repetition time was 3000ms
with fast spin echo sequence with TE = 8.62ms, and echo train length = 7.
The
first vial was constructed with no peanut oil and no gadolinium, so the conventional
inversion recovery method was applicable and could be used as the reference for
the T1 measurement of
the water component. All phantoms were placed into scanning room for two hours
before experiment so that the temperature could reach the room temperature. All
scans were conducted on 3.0T MR system (uMR 790, Shanghai United Imaging
Healthcare, Shanghai, China). The FF calculation was corrected to the
temperature. The fitting was implemented in MATLAB (Math Works, Natick, MA) on
a desktop computer.Results
The
proton density FF calculated for vial #1-#7 was 0.29%, 4.54%, 8.51%, 12.55%, 16.97%, 21.46%, 27.43%, respectively. T1 value
calculated by proposed method and traditional single component fitting method
for each vial was summarized in Tab.1. Compared to the #1 vial, the T1 values
of the water component was stable regardless of the fat fraction using the
multiple component method. Bland-Altman analyses for T1 calculated
by these two methods were shown in Fig.1. Proposed method (bias: 76.1ms, 95% CI
[-34.3ms, 186.6ms]) outperformed the single component methods (bias: -525.3ms,
95% CI [-1138.0ms, 87.75ms]).
The
proton density FF calculated for vial #8-#14 was 0.91%, 4.71%, 8.00%, 10.76%, 14.87%, 20.10%, 25.68%, respectively.
The calculated T1 values
were compared between the single component and multiple component methods, and
listed in Tab.2.Discussion and conclusions
In
this work, the conventional inversion-recovery T1 measurement
was combined with fat-water quantification method to overcome the confounding
factor from fat signal to T1 measurement
using a multiple component model. Proposed multiple component method showed
good consistency in measuring water T1 despite
the existence of fat signal and might be useful for T1 evaluation
in organs with fat infiltration.
The
limitation of the study is that we only used the phantom without fat as
reference. However, the fat content itself might have effect on the T1
relaxation time of the water component, which can be found in the both tables.
With the increase of fat content, the deviation of the T1 values to the phantom
without fat becomes larger. Thus, further validation should be considered using
the spectroscopic method[7] in the future.Acknowledgements
No acknowledgement found.References
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