© 2013 laureate international universities ... - ccp pet-mr€¦ · motion signal (0.1 sec) motion...
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© 2013 Laureate International Universities® | Confidential & Proprietary
2 © 2013 Laureate International Universities® | Confidential & Proprietary
Datasets for research
Data
Acquisition
Data
Reconstruction
Data
processing
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Limitations in medical imaging research
When you do research in medical imaging you face problems:
• Limited clinical data (you also need ethical approval)
• Limited or no access to the reconstruction tools
• Physicians always have limited time to help you with the diagnosis
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What is the solution?
Επεξεργασία
δεδομένων
Data simulation Development of
algorithms
Data
Acquisition
Data
Reconstruction
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Dynamic MR image acquisition
(high resolution)
• 1.5 T Philips AchievaTM
• T1 weighted turbo field echo (TFE) sequence
• Repetition time = 3.3 ms
• Echo time = 0.9 ms
• Flip angle = 10
• MRI dataset reconstruction = image resolution 1.5×5×1.5 mm3
• (feet-head, right-left, anterior-posterior)
• temporal resolution 0.7s/time frame.
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MRI-derived motion model
Diaphragm displacement (mm)
-50 -40 -30 -20 -10 0 10 20
45
40
35
30
25
20
15
10
5
0
- 5Hea
d-fo
ot z
-dis
plac
emen
t (m
m)
InspirationExpiration
Inspiration polynomial fit
Expiration polynomial fit
Motion model
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…
MR navigator
& images
Motion
estimation
Dis
pla
ce
ment
Navigator position
Motion model gives the displacement of
each voxel in the image according to the
navigator position for the x, y, z axis.
Use of real time MR data with motion and navigator
signal from the diaphragm in order to create a motion
model that give us motion that has longer duration.
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…
MR navigator
& images
Motion
estimation
Dis
pla
ce
ment
Navigator position
Motion model gives the displacement of
each voxel in the image according to the
navigator position for the x, y, z axis.
1. Each of the 105 MRI images was registered to the reference breath
hold image using a hierarchical registration algorithm
2. To measure the respiratory signal, the feet-head position of the
diaphragm was used as an external surrogate
3. For each control point in each image the displacements were
calculated as functions of the surrogate signal
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How the MRI-derived motion model was
used for simulations
Motion model Motion signal (0.1 sec) MR motion fields
×
9
For any respiratory signal, the motion model is used to calculate motion fields
necessary to transform the reference distribution (i.e. the 3D tracer uptake distribution)
to the relevant respiratory positions and generate a moving phantom.
No tracer kinetics within the body or radioactivity physical decay was simulated in
this investigation.
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10
Motion-model solution
…
MR navigator
& images
Motion
estimation
Motion
model
MR
navigator
Motion
estimates
Model formation (calibration) Model application
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How we simulated the 3D PET distribution…
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3D PET distribution 3D MR segmentation
L1 L2 L3
L4 L5 L6
L7 L8 L9
L1
L2
L5 L8
L3
L6 L9
Simulate 3D PET distribution
F18-FDG
• 3D MRI reference image was manually segmented into different tissue types
• Uniform SUVs were assigned to each type according to the tracer.
• Emission and attenuation images were simulated
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4D PET distribution
3D PET distribution
4D MR motion fields
Analytic
simulations
Attenuated,
scattered, noisy
sinograms
Simulate 3D PET distribution
F18-FDG
STIR software:
• Software for image reconstruction and data manipulation in medical
imaging (http://stir.sourceforge.net)
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Motion model Motion signal (0.1 sec)
3D PET phantom Analytic simulations
PET raw data
4D PET datasets Transformation
MR motion fields
×
14
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15
× Amplitude: 6-20 mm
×
[5] Schleyer et al Phys Med Biol 2011 [6] Liu et al Phys Med Biol 2009
• Motion signals from PET images [5]
for 3 breathing types [6] : Type A : Long quiescent
motion periods
Type C: Random
baseline shifts
Type B: Regular quiescent
motion periods
Fre
qu
ency
Am
pli
tud
e
Am
pli
tude
Am
pli
tude
Fre
qu
ency
Fre
qu
ency
Time (sec) Time (sec) Time (sec)
Amplitude Amplitude Amplitude
• Lesions: 6-12 mm , contrast: 3:1-7:1
• Simulated PET resolution: 6mm & 3mm
Motion model Motion signal (0.1 sec)
3D PET phantom Analytic simulations
PET raw data
4D PET datasets Transformation
MR motion fields
×
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Example of reconstructed images 18F-FDG
0
10 Reference position Breathing type 1
Breathing type 3Breathing type 2
0
10 Reference position Breathing type 1
Breathing type 3Breathing type 2
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What about new radiotracers?
Apply the method for radiotracer : 68Ga
The effect of positron range was included in the 68Ga-PSMA simulations as the
kinetic energy of 68Ga is much higher than 18F.
A) B)
0
18
0
18
Simulated radioactivity distribution for the 68Ga-PSMA A) without
blurring and B) with blurring for 68Ga at 3 T.
Kernels relative to 68Ga in the
A) cortical bone, B) water and
C) lung tissue at 3 T.
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What blurring for 68Ga can cause
Table 2: Lesion characteristics before and after applying blurring for GA68-PSMA.
Lesion 1
⌀ 16 mm
Liver
Lesion 2
⌀ 16 mm
Lung
Lesion 3
⌀ 16 mm
Lung
Lesion 4
⌀ 16 mm
Liver
Lesion 5
⌀ 16 mm
Lung
Lesion 6
⌀ 16 mm
Lung
Lesion 7
⌀ 10 mm
Liver
Lesion 8
⌀ 10 mm
Lung
Lesion 9
⌀ 10 mm
Lung
Ideal SUVmax 20 6 6 20 6 6 20 6 6
Blurred
SUVmax 19.99 4.83 4.83 19.99 4.98 4.83 19.77 4.14 4.12
Mean/std SUV 16.34/2.88 3.30/0.94 3.3/0.94 16.23/2.85 3.32/0.93 3.3//0.93 15.07/2.81 2.72/0.80 2.61/0.80
Theoretical
Volume (mm3) 2144 2144 2144 2144 2144 2144 523 523 523
Measured
Volume with
34% SUVmax
threshold
(mm3)
2240 2470 2470 2048 2512 2472 896 1168 1016
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Example of simulated data: 68Ga-PSMA
0
18 Reference position Breathing type 1
Breathing type 3Breathing type 2
0
18 Reference position Breathing type 1
Breathing type 3Breathing type 2
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Example of reconstructed images: 18F-FDG
Static Type A (No-MC) Type B (No-MC) Type C (No-MC)
Reso
luti
on ≈
3m
m
Reso
luti
on ≈
6m
m
8mm , 3:1 lesion/back.
8mm , 6:1 lesion/back.
8mm , 6:1 lesion/back.
8mm , 3:1 lesion/back.
Static Type A (No-MC) Type B (No-MC) Type C (No-MC)
Reso
luti
on ≈
3m
m
Reso
luti
on ≈
6m
m
8mm , 3:1 lesion/back.
8mm , 6:1 lesion/back.
8mm , 6:1 lesion/back.
8mm , 3:1 lesion/back. No-motion correction After motion
correction
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Conclusion
1. A scheme to simulate realistic synthetic (i.e. 100 ms) PET data of
two different and widely used radiotracers using a combination of
dynamic and static MRI acquisitions of healthy volunteers.
2. This approach allows incorporation of models of respiratory motion
to generate temporally and spatially correlated MRI and PET
datasets, as expected in simultaneous PET-MRI acquisitions.
3. Simulations with realistic anatomy and motion trajectories as those
observed in real subjects can help investigate the performance of
different reconstruction and motion correction methods.
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Acknowledgments
Prof Paul Marsden
Mr Christian Buerger
Dr Andy King
Dr Kris Thielemans (main
STIR developer)
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