Xinya Zhao1, Xianshun Yuan1, Xiang Feng2, Mengxiao Liu3, Xiangtao Lin1, and Ximing Wang1
1Department of Radiology, Shandong Provincial Hospital, Jinan, China, 2MR Scientific Marketing, Siemens Healthcare, Beijing, China, 3MR Scientific Marketing, Siemens Healthcare, Shanghai, China
Synopsis
The
purpose of this study was to determine whether B1 inhomogeneity-corrected volumetric
T1 mapping of Gd-BOPTA enhanced liver MR imaging are able to evaluate the
degree of liver cirrhosis and to investigate their relationship with the
histological grading. Our study found that B1
inhomogeneity-corrected T1 mapping using Gd-BOPTA enhanced MR imaging could be
used in the quantitative evaluation of liver fibrosis.
Introduction
Liver fibrosis is a common progressive
chronic liver disease, which might be developed at increasing risk of cirrhosis
and hepatocellular carcinoma (HCC)1. Accurate assessment of liver fibrosis is crucial
in determining the treatment plan for patients and improving the prognosis.
Liver fibrosis could cause the changes of tissue properties, such as, iron overloading
and edema, and thus affected the T1 values. Gd-BOPTA, as a widely used
hepatobiliary-specific MR contrast agent, has advantages in diagnosing focal
liver lesions and may be a valuable assessment tool for the estimation of liver
function2,3. The purpose of this study was
to determine whether B1 inhomogeneity-corrected volumetric T1 mapping of
Gd-BOPTA enhanced liver MR imaging are able to evaluate the degree of liver cirrhosis
and to investigate their relationship with the histological grading. Methods
118 patients with hepatitis B virus
infection (47 female; mean
age 41.6±5.9 years) were enrolled in the present study. The inclusion
criteria were (i) liver surgery or biopsy was performed; (ii) Child-Pugh class
A based on Child-Pugh classification. Exclusion criteria included (i) hepatitis
C virus infection, nonalcoholic steatohepatitis or other chronic liver
diseases; (ii) Child-Pugh class B or higher.
All patients underwent MRI scan at
a 3T scanner (MAGNETOM Prisma, Siemens Healthcare, Erlangen, Germany) with an
18-channel body matrix coil. The axial T1-weighted VIBE sequence with dual flip
angles was acquired with the following parameters: repetition time (TR), 5.01
ms; echo time (TE), 2.3 ms; flip angles, 3o and 15o; slice
thickness, 3 mm; number of partitions, 48; FOV, 350 mm × 308 mm; bandwidth, 300
Hz/pixel; acquisition time, 17 s. Prior to T1-weighted VIBE acquisition, to
correct B1 heterogeneity, a B1 mapping pulse sequence was performed to cover
the entire liver using the saturated 2D Turbo FLASH method with the following
parameters:
Slice thickness, 8mm; number of
slices, 15; TR, 5050.0 ms; TE, 1.83 ms;
flip angle, 8o; FOV, 350 mm × 308 mm; bandwidth, 490 Hz/pixel,
acquisition time, 8 s.
Gd-BOPTA was used via vessel injection, with the injection rate of 1 ml/s and
the bolus of 0.2ml/kg. T1-weighted VIBE sequences were acquired with breath
holding both before and after contrast media injection in the hepatobiliary
phase (90 min). All the scans were performed with breath-holding. B1-corrected T1
maps were constructed inline using the vendor software MapIt (Siemens Healthcare).
Regions of interest (ROIs) were
manually drawn to cover the maximum of liver parenchyma at the same slices of
both pre- and post-contrast enhanced (CE) T1 maps, carefully avoiding focal
lesions and major branches of the vessels. The changes of T1 values after CE
was calculated and correlated with the degrees of liver fibrosis, indicated by
histological grades of biopsy or samples after surgery. Results
Figure 1 shows a demonstration that
the B1-corrected T1 maps could substantially improve the distribution of T1
values in the liver, compared to uncorrected T1 maps. Using histopathological
analysis, the stages of fibrosis in all patients were distributed with fibrosis
(F) from F0 to F4. Figure 2 shows five patients with different F stages, and their
corresponding T1 maps at pre-contrast and hepatobiliary phase. The mean native
T1 values and shorted T1 values at hepatobiliary phase at
F0 to F4 stage were extracted by manual ROIs, and then the T1 value changes
were calculated:
637.48 ms, 601.55 ms, 575.85 ms, 529.89
ms, 499.50 ms, respectively. The T1 value changes between F1 or lower and F2 or
higher were significantly different (P<0.05), while the T1 value changes
between F3 or lower and F4 were significantly different (P<0.05) (Figure 3). ROC
analysis were displayed in Figure 4. Discussion & Conclusion
There were no significant
differences in native T1 among different F stages. However, using Gd-BOPTA enhanced MR imaging, the T1
shortening effect is substantially different, especially between F1 and F2,
which could be used for early detection of fibrosis and in distinguishing
slight and moderate fribosis. , and between F3 or lower and F4, indicating
advancement into liver cirrhosis. In conclusion, B1 inhomogeneity-corrected T1
mapping using Gd-BOPTA enhanced MR imaging could be used in the quantitative
evaluation of liver fibrosis. Acknowledgements
NoneReferences
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