quantitative meaures of novel pet tracers pet physics group ... - ncri pet · instrumentation...
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Quantitative measures of novel tracers
Will Hallett
Some controversial issues
Study design / Number of subjects / Radiation doseSubject / Production / ResourcesImage noiseWhat activity should we inject?Go/no go?Reconstruction parameters?
Study design
Typically we are not looking for potential lesions (not an observer problem)
Statistical test on an outcome measure from group(s) of subjects under more than one condition (e.g. on and off a drug)
If the states are the same (close) test-retest difference mean variance:
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- Ideally small compared to the size of the effect to detect
Reproducibility only useful if useful information retained (Reliability)
Study design
Typically a measured outcome will depend on
Calibration (scanner etc) Biology (underlying uptake – volume of distribution – SUV)Image noise (detection efficiency, dose)Other factors – subject motion, metabolite analysis etc
If these are all uncorrelated (not always)
Variance of the outcome mean will be the sum of the variances from these factors and decrease with the number of subjects
Image noise
Tomographic Image noise variance �����.
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Depends also on scanner efficiency, reconstruction
Voxel size dependence worse than ‘cut and count’
TOF partially recovers this – localisation of events
1170MBq injected, 2.8-1.5 kBq/ml
170MBq injected (F18)
Typical brain scan around 2kBq/ml
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NEMA NECR for different scanners
NEMA NECR for different scanners
Effect of filtering (‘smoothing’)
All pass
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1300 pixels in striatum VOI all pass mean
5mm mean
all pass sd
5mm sd
5mm Gaussian
Note effect of subject movement in last few frames
Effect of reducing the dose – simulation from real data
10101001000101001110101001010100111001101101011010100010101010010101010010101010101101010101000101010101101010100011010101010100
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10101001000101001110101001010100111001101101011010100010101010010101010010101010101101010101000101010101101010100011010101010100
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211 MBq scan
Sim. 106 MBq x 2 Sim. 52 MBq x 4 Sim. 26 MBq x 8 Sim. 13 MBq x 16
Subdivide list mode data into 2, 4, 8 and 16 ‘low dose’ data sets
Effect of reducing the dose
211MBq
13MBq
The Relationship Between Radioactive Dose and Precision of Outcome Parameters in Quantitative PET Imaging of the Human Brain Y.H. Nai, M.L. Cunneen, R.S. Dimber, W.A. Hallett, G.E. Searle BrainPET 2011 meeting
211MBq
13MBq
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Effect of reducing the dose on outcome measure – simulation from real data
211MBq
13MBq
13MBq
Effect of reducing the dose on outcome measure – simulation from real data
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Caudate
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Putamen
Injected activity (MBq)
BP
ND
CO
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Effect of reducing the dose on fitting error– simulation from real data
Effect of the dose – phantom studies
Instrumentation factors affecting variance and bias of quantifying tracer uptake with PET/CT R. K. Doot, J. S.
Scheuermann, P. E. Christian,J. S. Karp, P. E. Kinahan 6035 Med. Phys. 37, p 6035 2010
Purpose: …repeatability and reproducibility of serial PET measures of activity as a function of object size, acquisition,
reconstruction, and analysis method on one scanner and at three PET centers using a single protocol with long half-
life phantoms.
Methods: The authors assessed standard deviations SDs and mean biases of consecutive measures
of PET activity concentrations in a uniform phantom and a NEMA NU-2 image quality IQ
Phantom... Each experimental set consisted of 20 consecutive PET scans…
An equation was derived to estimate the SD of a new PET measure from a known SD based on the ratios of available
coincident counts between the two PET measures.
Results: For stationary uniform phantom scans, the SDs of maximum RCs were three to five times
less than predicted for uncorrelated pixels within circular regions of interest ROIs with diameters
ranging from 1 to 15 cm. For stationary IQ phantom scans from 1 cm diameter ROIs, the average
Reproducibility of GE DSTE, Philips Gemini TF, and Siemens Biograph Hi-REZ PET/CT scans of the same IQ phantom,
with similar acquisition, reconstruction, and repositioning among 20 scans, were, in general, similar mean and
maximum RC SD range 2.5% to 4.8%.
Conclusions: Short-term scanner variability is low compared to other sources of error. There are
tradeoffs in noise and bias depending on acquisition, processing, and analysis methods. The SD of
a new PET measure can be estimated from a known SD if the ratios of available coincident counts
between the two PET scanner acquisitions are known and both employ the same ROI definition.
Results suggest it is feasible to use PET/CTs from different vendors and sites in clinical trials if they
are properly cross-calibrated.
For same conditions Standard Error ~1/sqrt(counts)
Doot et al Med Phys 37 2010
Effect of dose - contribution to variance (SE) of BP
Data taken from BrainPET 2011 Dose and Precision of Outcome Parameters in Quantitative PET Imaging of the Human Brain Y.H. Nai, M.L. Cunneen, R.S. Dimber, W.A. Hallett, G.E. Searle
FBP PSF
FBP vs. PSF real data
FBP vs PSF phantom data
Images analysed according to NEMA NU (2007) Hot and cold sphere contrast values calculated
FBP Image PSF Image ROI Image
PSF reconstruction hot sphere images
FBP vs PSF hot sphere contrast – NEMA image quality phantom
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Hot Sphere Contrast
PSF 8i21s
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PSF 4i8s
FBP
Note: 2mm gauss filter was used for these and subsequent phantom comparisons
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Cold Sphere Contrast
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FBP vs PSF cold sphere contrast – NEMA image quality phantom
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Background Variability
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FBP vs PSF Background variability – NEMA image quality phantom
FBP vs. TrueX Contrast and acquisition times – NEMA image quality phantom
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Hot Sphere Contrast Versus Acquisition Time (PSF 6i,16s and FBP)
PSF 10minPSF 1minPSF 15sPSF 5sPSF 2sFBP 10 minFBP 1minFBP 15sFBP 5sFBP 2s
FBP vs. PSF Time Activity Curves
Reference Region - Cerebellum Putamen
PSF
FBP
FBP and PSF for
different ‘doses’
FBP vs. PSF Binding potential
Caudate - FBP Caudate - PSF