Motion Imaging in RT - AAPM HQamos3.aapm.org/abstracts/pdf/127-37431-418554-126119.pdf · Motion...
Transcript of Motion Imaging in RT - AAPM HQamos3.aapm.org/abstracts/pdf/127-37431-418554-126119.pdf · Motion...
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Advances in MRI-based Motion Management for
Radiation Therapy
Jing Cai, PhD, DABR
2017 AAPM 59th Annual Meeting, Denver, CO
► Review of current MRI techniques for motion management
► Advances in MRI technique for simulation
4D-MRI using 2D acquisition
4D-MRI using 3D acquisition
► Advances in MRI technique for treatment delivery
4D-MRI with highlighted vessels
On-board 4D-MRI
► Other advances
Hyperpolarized gas tagging MRI
Outline
Motion Imaging in RT
▪ 4D-CT is the current clinical standard for motion imaging
▪ Excellent contrast in the lung to reveal lung tumor motion
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Limitations of 4D-CT in Imaging Abdominal Cancers
▪ 4D-CT suffer insufficient contrast in the abdomen to reveal tumor motion, leading to potential errors
Imaging Motion Using MRI
4D-MRI for RT
▪ Compared to 4D-CT, 4D-MRI improves tumor contrast and tumor motion measurement for abdominal cancers.
4D
-CT
4D
-MR
I
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▪ 4D-MRI leads to smaller target volume (54.0 cc in 4D-MRI, 104.8 cc in 4D-CT) with reduced safety margin
Target Volume: 4D-MRI vs 4D-CT
Cord
Liver
Right kidney
ITV4D-CT
ITV4D-MRI
4D-CT Plan
4D-MRI Plan
▪ 4D-MRI plan spared more healthy liver tissue than 4D-CT plan.▪ Mean dose to liver: 20.7 Gy ~ 34.2 Gy for 4D-MRI and 4D-CT.
Treatment Plan: 4D-MRI vs 4D-CT
Size Matters
Be SMART
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4D-MRI Strategies
Based on 2D Acqusition
• fast 2D MR sequence + breathing signal
• image processing, relatively easy to implement
• limited selections of usable MR sequences
Based on 3D Acqusition
• fast 3D MR sequence + breathing signal
• more challenging, MR sequence development
• hardware and software demanding
2D Acquisition 3D Acquisition
Retrospective I II
Prospective III IV
4D-MRI Using Cine 2D Acquisition
4D-MRI
True fast imaging with steady-state free precession
(TrueFISP, FIESTA)
• T2/T1-w
• 3-10 frames/sec
• Phase sorting
Single-Shot Fast Spin-Echo
(SSFSE, HASTE)
• T2-w
• ~ 2 frame/sec
Sequential / Interleave Acquisition
Repeat Volume Measurement
To obtain different phases at each slice
Determine Minimal # of Repetitions (NR)
To satisfy data sufficient condition
4D-MRI Using Sequential 2D Acquisition
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4D-MRI Using Sequential 2D Acquisition
4D-MRI Image Quality: Cine ~ Sequential
2D Acquisition with K-space Sorting
iFFT
Respiratory signal
iFFT
iFFT
Sli
ce
1S
lice
1S
lice
1
Re
pe
titi
on
1R
ep
eti
tio
n 2
Re
pe
titi
on
3
Raw k-space data
Sorted k-space data
Reconstructed 4D images
Sli
ce
2-N
Sli
ce
2-N
Sli
ce
2-N
phase1
phase2
phase3
phase2
phase1
phase3
phase3
phase2
phase1
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Simulated 4D-MRI
Original 4D-XCATImages
Healthy Volunteer4D-MRI
2D Acquisition with K-space Sorting
Diffusion-weighted 4D-MRI: 4D-DWI
b-value=0
X Y Z
b-value=500 s/mm2
DWI Image Acquisition
Healthy Volunteer
Collaboration with Siemens
Diffusion-weighted 4D-MRI: 4D-DWI
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Challenges for 4D-MRI Development
▪ suboptimal or inconsistent tumor contrast ▪ long image acquisition times▪ insufficient temporal and spatial resolution
▪ inaccurate breathing signals▪ poor handling of breathing variation▪ lack of patient validation and applications
Motion Probability Density Function (PDF)
PDF-driven Sorting Multi-cycle Recon
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Probability-based Multi-cycleCycle 1 Cycle 2 Cycle 3
Average Intensity Projection (AIP)
Reference Conv. Prob.
Difference Map
Conv. Prob.
ConventionalSingle-cycle
PDF-driven Sorting Multi-cycle Recon: 2D
tissue discontinuity
2D acquisition
PDF-driven Sorting Multi-cycle Recon: 3D
3D acquisition
blurring, noise
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Cycle 2Cycle 1
Probability-driven Multi-cycle Sorting
Cycle 3
Phase Sorting
Single Cycle
T=3.60 s
PDF-driven Sorting Multi-cycle Recon: 3D
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30.4 30.128.6
17.3
0
5
10
15
20
25
30
35Tumor SNR
Cycle 3
Probability-driven Sorting
Cycle 1 Cycle 2 Single Cycle
Improved Tumor SNR
Phase Sorting
0.0270.033
0.072
0.042
0
0.01
0.02
0.03
0.04
0.05
0.06
0.07
0.08
STD of inter-phase tumor volumes
Reduced Tumor Volume Variation
Cycle 3
Probability-driven Sorting
Cycle 1 Cycle 2 Single Cycle
Phase Sorting
T2/T1-w4D-MRI
Reference Phase
Other Phases
DIR
DVFs
Cine-MRI
Motion Trajectory
Parameters
Remodeled DVFs
3D T2-w MRI
DIR
Deformed T2-w MRI
‘Synthetic’4D-MRI
ParametersImproved Synthetic4D-MRI
Correction
Improve 4D-MRI via Motion Modeling
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0 20 40 60 80 1000
2
4
6
8
10
Phase (%)
Dis
plac
emen
t (m
m)
SI
AP
ML
0 20 40 60 80 100 120 140 160 180-8
-4
0
4
8
12
Image Index
Dis
pla
ce
me
nt (m
m)
SI
AP
ML
▪ Normalized cross correlation (NCC) based tracking technique
0 20 40 60 80 1000
2
4
6
8
10
Phase (%)
Dis
plac
emen
t (m
m)
SI
AP
ML
0 20 40 60 80 1000
1
2
3
4
5
6
7
8
9
Phase (%)
Dis
plac
emen
t (m
m)
SI~original
AP~original
ML~original
SI~fitted
AP~fitted
ML~fitted
▪ A quartic polynomial formula was used to fit the motion trajectories
Improve 4D-MRI via Motion Modeling
▪ DVF temporal fitting
To correct the motion estimated from 4D-MRI DVFs by incorporating motion information extracted from cine-MRI.
▪ DVF spatial fitting
Using a quartic polynomial fitting formula to fit DVFs in three spatial dimensions.
𝒑𝒊𝒛(𝒙,𝒚,𝒛)
(𝒙, 𝒚, 𝒛)(𝒙𝟎, 𝒚𝟎, 𝒛𝟎)
Cine-MRI
𝒂𝒊𝒛𝟎(𝒙𝟎,𝒚𝟎,𝒛𝟎)
𝒑𝒊𝒛𝟎(𝒙𝟎,𝒚𝟎,𝒛𝟎)
4D-MRI
Voxel position
Pa
ram
ete
r
Improve 4D-MRI via Motion Modeling
Before optimization After optimization
95.5
96
96.5
127
128
12922
24
26
28
30
AP (cm)ML (cm)
SI (c
m)
0%10%
30%40%
50% 60%20%
70%
80%
90%
95.596
96.597
127
128
12922
24
26
28
30
AP (cm)ML (cm)
SI (c
m)
0%
90%
10%20%
30%
40%50% 60%70%
80%
▪ Voxel-wise motion modeling and optimization
Improve 4D-MRI via Motion Modeling
Temporal fitting
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Anterior->Posterior
Infe
rior-
>S
uperior
DVF between frame 1 and frame 6 in sagittal slice #93
50 100 150 200 250
5
10
15
20
25
30
35
40
Original DVF After temporal fitting After spatial fitting
Spatial fitting
Improve 4D-MRI via Motion Modeling
Synthetic 4D-MRI
Original 4D-MRI
Coronal Sagittal Axial
Improve 4D-MRI via Motion ModelingPatient Example
Super Resolution 4D-MRI
Collaboration with Dr. DG Shen, UNC Chapel Hill
Groupwise registration for
motion estimation and spatiotemporal resolution
enhancement
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Before SR
After SR
Super Resolution 4D-MRI
Collaboration with Dr. DG Shen, UNC Chapel Hill
Before SR
After SR
Super Resolution 4D-MRI
Collaboration with Dr. DG Shen, UNC Chapel Hill
Super Resolution 4D-MRI
Before SR
After SR
Collaboration with Dr. DG Shen, UNC Chapel Hill
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Fast 4D-MRI with View Sharing
Reference No VS VS w. Equal Freq Cutoff
VS w. Vari. Freq Cutoff
4D-XCAT
Fast 4D-MRI with View SharingDigital Phantom
‘4D-MRI’
• 7T Small animal scanner • Custom built breathing motion phantom• Motion range 5 mm• 2 minutes acquisition Time • 10 Phases T1w 4D-MRI
Fast 4D-MRI with View SharingPhysical Phantom
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i-thphase
For each k-data point (kxyz, t): Amp.
Time
Ai
Pi
Ai : Amplitude difference to phase bin center
Pi : Phase (percentage) difference to phase bin center
Fast Robust 4D-MRI through Spatiotemperal Constrained Sorting and Compressed Sensing Reconstruction
𝑆𝑇𝐼𝑖 𝑘𝑥𝑦𝑧 , 𝑡 =𝐴𝑖(𝑘𝑥𝑦𝑧 , 𝑡)
𝐴𝑡 𝑘𝑥𝑦𝑧
2
+𝑃𝑖(𝑘𝑥𝑦𝑧, 𝑡)
𝑃𝑡
2
,
𝑖 = 1,2, . . 10
Original MR
ROI
50%, w/o TGV
50%, w. TGV
25%, w/o TGV
25%, w. TGV
▪ Total generalized variation (TGV) reconstruction algorithm to maximally recover the missing information, to determine optimal k-space under-sampling pattern for various MR sequences
Fast Robust 4D-MRI through Spatiotemperal Constrained Sorting and Compressed Sensing Reconstruction
Ground-TruthSTI-sorted
(New)
Phase-sorted(Conventional)
Stitching artifacts
Less blurring
Fast Robust 4D-MRI through Spatiotemperal Constrained Sorting and Compressed Sensing Reconstruction
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12-min9-min
STI-Sorted
Phase-Sorted
6-min
Better image quality
Fast Robust 4D-MRI through Spatiotemperal Constrained Sorting and Compressed Sensing Reconstruction
FREEZEit MRI• TWIST-VIBE/StarVIBE/GRASP, Fat-suppressed T1-w 3D GRE
• Radial version of VIBE, Stacks of star k-space sampling
• Compressed sensing & parallel imaging
• High robustness to motion artifacts
• Thorax, abdomen, pelvis, DCE, 4D, cardiac
Siemens, NYU Langone Medical Center
3D VIBE GRE Pulse Sequence
• A 3D stack-of-stars gradient echo sequence (3D VIBE GRE) with golden angle sampling of the radial views
• kx-ky: radial read out; kz: Cartesian encoding
• Golden-angle trajectory
• n = n 111.25 (180/1.618)
• radial spokes never repeat
• fill the largest gap by previous spokes
• relative uniform k-space coverage
• uncorrelated in temporal dimension
Restricted © Siemens Medical Solutions USA, Inc., 2017
KxKy
Kz
KxKy
top view
front view
stack-of-stars
Slides courtesy: Li Pan, Siemens HealthineersJames Balter, University of Michigan
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► A self-gating respiratory signal is derived from the k-space centers (kx = ky = 0, kz~= 0), similar to the signal of a respiratory bellow
► Retrospectively binning of the radial spokes into multiple breathing states
► Uniform binning - evenly splits the data into a user-defined number of bins with equal number of radial spokes in each bin
► Ungated and binned images were reconstructed online
respiratory signal
Slides courtesy: Li Pan, Siemens HealthineersJames Balter, University of Michigan
3D VIBE GRE Pulse Sequence
Restricted © Siemens Medical Solutions USA, Inc., 2017
► Patient with Intrahepatic tumor
► 4D MRI provides much better soft tissue contrast and delineation of intrahepatic tumor compared to 4D CT
4D CT
4D MRI
Slides courtesy: Li Pan, Siemens HealthineersJames Balter, University of Michigan
Restricted © Siemens Medical Solutions USA, Inc., 2017
3D VIBE GRE: Patient Example
4D CT
4D MRI
4D CT
4D MRI
3D VIBE GRE: Patient Example
Slides courtesy: Li Pan, Siemens HealthineersJames Balter, University of Michigan
Restricted © Siemens Medical Solutions USA, Inc., 2017
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ROCK sampling pattern
Fa
t-S
at
T2
-pre
p bSSFPQuasi-spiral interleave
(n=30) Fa
t-S
at
T2
-pre
p
TR=180ms
4D-MRI sequence using ROCK sampling pattern
ROCK 4D-MRI: Methods
Courtesy of P. Hu, PhD, UCLA
Respiratory motion-resolved, self-gated 4D-MRI using rotating Cartesian k-space (ROCK)
ROCK 4D-MRI: Methods
Data binning based on Respiratory Amplitude
▪ 8 respiratory bins
▪ Soft-gating approach
Courtesy of P. Hu, PhD, UCLA
Arduino Step Motor 3D printed parts
ROCK 4D-MRI: Phantom
Courtesy of P. Hu, PhD, UCLA
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ROCK 4D-MRI: Methods
Courtesy of P. Hu, PhD, UCLA
ROCK 4D-MRI: 1.5T Siemens
Courtesy of P. Hu, PhD, UCLA
Courtesy of P. Hu, PhD, UCLA
ROCK 4D-MRI: 0.35T ViewRay
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Deng Z et. al Magn Reson Med. 2015 May 14. PMID: 25981762
• Current sequence uses a Koosh-ball like sampling trajectory.
• Self-gating lines were inserted to guide data binning and reconstruction.
• A large axial slab (~40cm in SI direction) is excited.
4D-MRI for Vessel Highlight
Courtesy of Wensha Yang, PhD
4D-MRI for Vessel Highlight
Courtesy of Wensha Yang, PhD
Coronal Sagittal
Axial
4D-MRI for Vessel Highlight
Courtesy of Wensha Yang, PhD
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nonSS 4D-MRISS-4D-MRI
4D-MRI for Vessel Highlight
Courtesy of Wensha Yang, PhD
a. b.
c.
SS-4D-MRI nonSS 4D-MRI
4D-CT
0.6
1.1
1.6
0 5 10 15 20
4D-CT
nonSS 4D-MRI
SS 4D-MRI
Rela
tive in
tensity
Distance (mm)
d.
4D-MRI for Vessel Highlight
Courtesy of Wensha Yang, PhD
Volumetric cine (VC) MR images are estimated from prior 4D MRI and 2D cine MRI
Prior 4D MRI On-board 2D CINE
MRIprior
VCMRI
Deformation Field, D
MRIprior is end-expiration phase of prior 4D MRI
Data fidelity
constraint
S*VCMRI
2DCineslice
?
Volumetric Cine (VC) MRI
Harris et al, Int. Journal Rad Onc Bio Phy, 2016
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VC-MRI: Patient
VCMRI
Axial Coronal Sagittal
• VC-MRI generated based on patient motion modeling, and
sparsely sampled 2D MR cine images.
• Real time volumetric MRI imaging
• Temporal resolution: up to 30 frames/s.
• Spatial resolution: 1.875 x1.875 x5mm
Harris et al, Int. Journal Rad Onc Bio Phy, 2016
0.0s 0.7s 1.4s 2.1s
Hyperpolarized Gas Tagging MRIUntagged HP MRIProton MRI 2D HP Tagging 2D DVF 3D HP Tagging
DIR of Proton MRI
Before After
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40 60 80 100 120 140
40
60
80
100
120
140
160
Proton MRI Tagging DVFTagging MRI
DIR-based DVFs
DVF Comparison: Tagging vs DIR
Contour PropagationDose Warping
Contour PropagationDose Warping
EOI
EOE
EOI
EOE
DIR
Tracking
Comparison Comparison
Tagging MRI for DVF Assessment
Hybrid Proton MRI and HP 3He Tagging MRI Acquisition
End of Inhalation End of Exhalation
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Spatial Distribution of DVF Error
DIR 1 DIR 2
DIR 3 DIR 4 DIR 5
Tagging DVF Optimized DIR DVF
Tagging DVF Original DIR DVF
Physiological-based DVF Optimization
Original DVF
1st Optimization based on Tagging DVF
2nd Optimizationbased on
Tagging Ventilation
Optimized DVF
Summary
• MRI provides unique advantages over CT for motion management of abdominal cancers in RT.
• Current challenges in 4D-MRI include motion artifacts, limited spatial resolution, lack of internal features, etc.
• Fast MR imaging together with sophisticated sorting and reconstructions techniques hold great promises in improving 4D-MRI image quality.
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AcknowledgementsDuke Radiation Oncology
Fang-Fang Yin, PhD
Mark Oldham, PhD
Jim Chang, PhD
Lei Ren, PhD
Brian Czito, MD
Manisha Palta, MD
Chris Kelsey, MD
Rachel Blitzblau, MD
UCLA
Yingli Yang, PhD
Duke Radiology
Nan-kuei Chen, PhD
Paul Segars, PhD
Mustafa Bashir, MD
Michael Zalutsky, PhD
MDACC
Jihong Wang, PhD
Siemens
Xiaodong Zhong, PhD
Brian Dale, PhD
UNC-CH Radiology
Dinggang Shen, PhD
Guorong Wu, PhD
Duke Department of Radiation Oncology
http://www.golfersagainstcancer.org/homehttp://www.philips.com/global/index.page