Hyungseok Jang1, Michael Carl2, Yajun Ma1, Mei Wu1, Zhao Wei1, Saeed Jerban1, Eric Chang1,3, and Jiang Du1
1University of California, San Diego, San Diego, CA, United States, 2GE Healthcare, La Jolla, CA, United States, 3VA San Diego Healthcare System, San Diego, CA, United States
Synopsis
Double echo steady state (DESS) imaging allows
acquisition of two MR images with different contrasts from FID and echo images.
In this study, we explored the feasibility and efficacy of 3D UTE Cones-based
DESS (3D UTE-Cones-DESS) imaging of short T2 tissues in the knee joint. In ex
vivo study of four cadaveric knees and in vivo study of three healthy
volunteers, the UTE-Cones-DESS sequence provided high contrast imaging of the
osteochondral junction (OCJ), the menisci, and other short T2 tissues, as well
as T2 maps, under a total scan time of three minutes.
Introduction
Double echo steady state (DESS) sequence has
been utilized in knee imaging due to its excellent image contrast between
cartilage and synovial fluid1. DESS allows acquisition
of two MR images with different signal contrasts obtained from FID and echo
images. Furthermore, quantitative DESS imaging has been investigated to
estimate T2 and diffusivity2,3. More recently, it has
been shown that ultrashort echo time (UTE) DESS imaging is feasible4. In this study, we show
the feasibility and efficacy of 3D UTE-Cones-based DESS (3D UTE-Cones-DESS) in
imaging of short T2 tissues in the knee joint.Methods
In 3D UTE-Cones imaging, the center-out radial
spokes are twisted for more time-efficient encoding5. Figure 1-a shows the
pulse sequence diagram of 3D UTE-Cones-DESS. After the repetitive RF pulses (64
hard pulses in this study), steady state of the transverse magnetization is
achieved6. Then, 3D UTE-Cones-DESS
imaging is performed to encode k-spaces in two different compositions of MR signal:
S+ (FID from the current RF) and S- (echo from the previous RF). The S+ signal
is encoded with a center-out Cones read-out gradient placed after the RF pulse,
while S- is encoded with a fly-back Cones read-in gradient placed before the
next RF pulse. TE for the second echo (S-) can be calculated by: TE2=2TR-TE1,
where TE1 is the TE in UTE. T2 can be estimated using a simple equation based
on the signal ratio2: (TE2-TE1)/ln(S1/S2),
where S1 and S2 are the pixelwise signal intensities at TE1 and TE2,
respectively.
The 3D UTE-Cones-DESS
sequence was implemented on a 3T clinical MR system (MR750, GE Healthcare,
Waukesha, WI, USA), and tested in four cadaveric knees and three healthy volunteers in
accordance with IRB. The knee samples and two volunteers underwent knee joint imaging,
while one volunteer underwent tibia imaging. An 8-channel transmit/receive knee
coil (GE Healthcare) was used with the following imaging parameters: 1) 3D UTE-Cone-DESS
for knee joint imaging: sagittal plane, flip angle (FA) = 5, 10, or 20o
for ex vivo imaging and 10o for in vivo imaging, TR/TE1/TE2 = 5/0.2/9.8
ms, readout bandwidth=250 kHz, FOV=150x150x96 mm3,
matrix=256x256x48, and scan time=3 min; 2) 3D UTE-Cone-DESS for tibia imaging:
all parameters matched to the knee joint imaging except for axial plane, TR/TE1/TE2=6/0.2/11.8
ms, readout bandwidth=125 kHz, and scan time=3min 24sec; 3) CPMG (added in ex
vivo imaging): sagittal plan, FA=90o, TR=2000 ms, TE=6.2, 12.3,
18.5, 24.6, 30.8, 37.0, 43.1, 49.3, 55.4, 61.6, 67.8, 73.9 ms, readout
bandwidth=125 kHz, FOV=150x150 mm2, matrix=256x256, number of
slices=44, slice thickness=2 mm, and scan time=19min 30sec.
Results
For all ex vivo
and in vivo subjects, the 3D UTE-Cones-DESS sequence achieved high quality UTE
images (S+) and T2-weighted spin-echo images (S-). Figure 2 shows results from
a representative cadaveric knee joint (28-year-old female donor). S- images
(Figure 2-b) are more T2-weighted than S+ UTE images (Figure 2-a). Echo-subtracted
images (Figure 2-c) show short T2 contrast, where short T2 components exhibit
higher intensity. The weighted echo subtraction (Figure 2-d) further suppresses
fat and improves the short T2 contrast as indicated by arrows (red: tendon;
yellow: deep/calcified cartilage, blue: meniscus). Figure 3 shows the T2 maps estimated
with 3D UTE-Cones-DESS or CPMG imaging. The estimated T2 in the region of
interest (ROI) for quadriceps tendon indicated by dashed rectangles in Figure 3
is 5.7 ± 0.6 ms with an FA of 5o, 9.7 ± 1.1 ms with an FA of 10o,
and 19.8 ± 3.7ms with an FA of 20o in 3D UTE-Cones-DESS, and 19.0 ±
2.6ms in CPMG. 3D UTE-Cones-DESS with a higher flip angle shows T2 values more
similar to that in CPMG as a reference2. The spatial variation in T2 map is
presumably due to B1 inhomogeneity. Figure 4 shows results from a healthy
volunteer (29-year-old female), with improved contrast for short T2 tissues including
tendons (red arrows), the OCJ (yellow arrows), menisci (blue arrows), and ligaments
(green arrow). Figure 5 shows results from another healthy volunteer (32-year-old
male). The weighted echo subtraction provided high contrast imaging of short T2
tissues such as cortical bone (yellow arrows) and aponeurosis (red arrows). Discussion and conclusion
We successfully
implemented a 3D UTE-Cones-DESS sequence on a clinical 3T scanner and showed
the feasibility and efficacy of high contrast morphological and quantitative imaging
of short T2 tissues in the knee. It was shown that T2 estimation depended on
FA, where a higher FA yielded more accurate estimation, which was also noted in
the literature2. This is because a simple signal model was
used based on two images, which can be improved by incorporating more accurate
signal model with additional acquisitions with different FAs. Tissue
diffusivity can also be estimated by using different spoiling gradients3. Unlike the conventional DESS where S+
and S- signals are combined, we presented echo subtraction with the 3D UTE-Cones-DESS
to achieve high contrast imaging of short T2 tissues. The echo subtraction in
spin echo is less affected by chemical shift effect than in gradient echo-based
dual echo UTE imaging7. 3D UTE-Cones-DESS can be applied to various
musculoskeletal and neurological applications owing to the capability of fast high
resolution morphological and quantitative imaging of both short and long T2
tissues.Acknowledgements
The authors acknowledge grant support from NIH
(R01AR075825, 2R01AR062581, 1R01 AR068987), Veterans Affairs (Merit Awards 1I01RX002604),
and GE Healthcare.References
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