Yanjun Chen1,2, Zhenyu Cai2, Liang Li2, Carolyn Xie2, Michael Carl3, Eric Y Chang4, Jiang Du2, and Yajun Ma2
1The Third Affiliated Hospital of Southern Medical University, Guangzhou, China, 2UC San Diego, San Diego, CA, United States, 3GE healthcare, San Diego, CA, United States, 4VA health system, San Diego, CA, United States
Synopsis
Strong
fat signal contamination leads to significant errors in quantitative UTE (qUTE)
imaging of musculoskeletal tissue. In this study, we used a fat suppression technique
to investigate whether fat signals could be sufficiently suppressed in qUTE
imaging and whether the fat saturation preparation would affect the resultant
qUTE measures due to the induced water attenuation.
Introduction
Recently, several quantitative
ultrashort echo time (qUTE) imaging
techniques have been developed, including measures of T1, adiabatic
T1ρ, quantitative
magnetization transfer (qMT) modeling, magnetization transfer ratio (MTR), and
T2* (1-5). These qUTE biomarkers may provide useful information in early
disease diagnosis for diseases involving short T2 tissues such as calcified
cartilage, menisci, tendons, ligaments, and bones (6,7). However, fat tends to show
strong signal, consistently shifting into other tissue regions due to the
off-resonance effect in the non-Cartesian UTE imaging (8,9). This strong fat
signal contamination inevitably leads to significant errors in qUTE imaging of musculoskeletal
(MSK) tissues. In this study, a fat saturation (FS) technique was used in qUTE
imaging to investigate whether fat signals could be sufficiently suppressed and
whether the fat saturation preparation would affect the resultant qUTE measures
due to the induced water attenuation. qUTE without fat saturation preparation (non-FS)
was also used for comparison. Materials and Methods
Seven cartilage and
ten meniscus samples were harvested from five fresh cadaveric human knee joints.
Cartilage samples, including cartilage, subchondral bone, and spongey bone, were
cut into cuboid shapes with an approximate size of 26×21×5 mm3. Meniscus
samples were sectioned in the sagittal plane at a thickness of 4 mm. Peripheral
synovial tissue
samples containing fat were also reserved. High resolution scanning of the
whole knee joint was also carried out on six knee samples from six separate
donors.
qUTE-MR imaging (Figure
1) was performed on a 3T clinical MRI scanner (MR750, GE Healthcare
Technologies, Milwaukee, WI, USA). A high signal-to-noise ratio (SNR)
performance 30-ml birdcage T/R coil was used for scanning the cartilage and meniscus
samples, and an eight-channel
T/R knee
coil was used for scanning the whole knee joint.
qUTE imaging
protocol parameters were as follows: 1) T1 measurement
with 3D UTE-Cones actual flip angle (TR = 20/100 ms, flip angle (FA) = 45˚) and
variable flip angle (FA = 4˚, 8˚, 12˚, 16˚, 20˚, 25˚ and 30˚; TR = 20 ms) (UTE-Cones
AFI-VFA) method (1); 2) macromolecular
proton fraction f with qMT modeling and MTR measurement with a UTE-Cones MT
sequence (MT saturation power = 500°, 1000°, and 1500°; frequency offset = 2,
5, 10, 20, and 50 kHz; TR=100 ms; FA = 7˚; Nsp = 9) (2,3); 3) Adiabatic T1ρ measurement with adiabatic full passage
pulse train prepared UTE-Cones acquisitions (spin lock time = 0, 12, 24, 36,
48, 72, 96 ms; TR = 500, FA = 10˚, Nsp = 21) (4); 4) T2* measurement with a
multi-echo UTE-Cones sequence (TE = 0.032, 4.1, 8.1, 12.1, 16.1, and 32 ms (5).
Other sequence parameters were: 1) cartilage and meniscus samples: FOV = 5×5×2cm3,
matrix = 128×128×10; 2) whole knee joints: FOV = 15×15×10.8cm3, matrix = 256×256×36.
A commercially available fat saturation module (i.e., chemical shift selective saturation
technique) was placed before the excitation spoke train to suppress fat signal in
the qUTE imaging. Due to direct or
indirect saturation (i.e., MT effect) effects, it was possible for fat
saturation module to attenuate water signal, as well.
All analysis algorithms were written in Matlab (The MathWorks Inc.,
Natick, MA, USA) and were executed offline on the DICOM images obtained by the
acquisition protocols described above. The variations of the parameters between
FS-qUTE measures and non-FS-qUTE measures were also calculated in percentages (i.e.,
|PFS – Pnon-FS|/ Pnon-FS *100%). Results and Discussions
Compared with the non-FS-qUTE images, fat signals were
effectively suppressed for both cartilage (spongey bone region) and meniscus (synovial
tissue region) samples in the FS-qUTE images (Figure 2). Figure 3
demonstrates that the fat signals were uniformly suppressed in the whole knee
joint when using the FS technique. Compared with the images acquired by
non-FS-qUTE sequences, a much higher contrast of cartilage and meniscus was
found in the FS-qUTE images. Therefore, a more accurate qUTE imaging in knee is
expected because of the much decreased fat contamination in cartilage,
meniscus, ligament, tendon, and muscle in FS-qUTE images.
Table 1 summarizes qUTE measures for cartilage and meniscus samples with FS and without FS.
To investigate the effect of the FS module in qUTE imaging in regard to water attenuation,
the regions of interest (ROIs) were placed in regions without any fat. There was
significant T1 reduction in the measurements from FS-qUTE as compared to results
from the non-FS-qUTE. However, for adiabatic T1ρ, f with qMT modeling, MTR, and T2* measures, there were
very minor differences between FS-qUTE and non-FS-qUTE.
Table 2 summarizes
qUTE measurements for knee joint tissues with FS and without FS. Again, ROIs
were drawn in regions without any fat. It was found that adiabatic T1ρ, f with qMT modeling,
MTR, and T2* measures did not vary much between FS-qUTE and non-FS-qUTE imaging
of cartilage, meniscus, ligament, and muscle. Conclusion
Combined with the fat suppression technique,
high image contrast and decreased fat contamination could be obtained for qUTE
imaging. Accurate qUTE measures of adiabatic T1ρ, f with qMT modeling, MTR, and T2*
were achieved when fat suppression module is applied.Acknowledgements
The authors are thankful for support from R01AR075825, 1R01NS092650, 2R01AR062581, 1R01AR068987, I01CX001388, and I01RX002604.References
1. Ma YJ, Zhao W,
Wan L, Guo T, Searleman A, Jang H, Chang EY, Du J. Whole knee joint T1 values
measured in vivo at 3T by combined 3D ultrashort echo time cones actual flip
angle and variable flip angle methods. Magn Reson Med 2018; DOI:
10.1002/mrm.27510.
2. Ma YJ, Chang
EY, Carl M, Du J. Quantitative magnetization transfer ultrashort echo time
imaging using a time-efficient 3D multispoke Cones sequence. Magn Reson Med
2018; 79:692-700.
3. Ma YJ, Shao H,
Du J, Chang EY. Ultrashort Echo Time Magnetization Transfer (UTE-MT) Imaging
and Modeling: Magic Angle Independent Biomarkers of Tissue Properties. NMR
Biomed 2016; 29:1546-1552.
4. Ma YJ, Carl M,
Searleman A, Lu X, Chang EY. Du J. 3D adiabatic T1ρ prepared ultrashort echo
time cones sequence for whole knee imaging. Magn Reson Med 2018; 80:1429-1439.
5. Chang EY, Du J,
Iwasaki K, Biswas R, Statum S, He Q, Bae WC, Chung CB. Single- and bi-component
T2* analysis of tendon before and during tensile loading, using UTE sequences.
J Magnetic Resonance Imaging 2014; 42:114-120.
6. Chen B, Cheng
X, Dorthe EW, Zhao Y, D'Lima D, Bydder GM, Liu S, Du J, Ma YJ. Evaluation of
normal cadaveric Achilles tendon and enthesis with ultrashort echo time (UTE)
magnetic resonance imaging and indentation testing. NMR in Biomed 2018;
20:e4034.
7. Chang EY, Du J,
Chung CB. UTE imaging in the musculoskeletal system. J Magn Reson Imaging 2015
Apr;41(4):870-83.
8. Robson MD,
Gatehouse PD, Bydder M, Bydder GM. Magnetic resonance: an introduction to
Ultrashort TE (UTE) imaging. J Comput Assist Tomogr 2003;27:825–846.
9. Du J, Carl M,
Bydder M, Takahashi A, Chung CB, Bydder GM. Qualitative and quantitative
ultrashort echo time (UTE) imaging of cortical bone. J Magn Reson 2010 Dec
1;207(2):304-11.