2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP
Towards Proton Computed Tomography
L. R. Johnson, B. Keeney, G. Ross, H. F.-W. Sadrozinski, A. Seiden, D.C. Williams, L. Zhang
Santa Cruz Institute for Particle Physics, UC Santa Cruz, CA 95064V. Bashkirov, R. W. M. Schulte, K. Shahnazi
Loma Linda University Medical Center, Loma Linda, CA 92354
• Proton Energy Loss in Matter
• Proton Tomography / Proton Transmission Radiography
• Proton Transmission Radiography Data
• Proton Transmission Radiography MC Study
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPPComputed Tomography (CT)
X-ray tube
Detector array
CT:• Based on X-ray absorption• Faithful reconstruction of patient’s
anatomy• Stacked 2D maps of linear X-ray
attenuation• Coupled linear equations• Invert matrices and reconstruct z-
dependent features
Proton CT: • replaces X-ray absorption with
proton energy loss • reconstruct mass density (ρ)ρ)ρ)ρ)
distribution instead of electron distribution
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP
0.01
1
100
104
1 10 100 1000
X-Ray Absorption Coefficient
BoneMuscleH2OFat
µ
X-Ray Energy [keV]
[1/cm]
1
10
100
10 100 1000
Stopping Power for Protons
Bone MuscleH2OFat
dE/dl[MeV/cm]
Proton Energy E [MeV]
Radiography: X-rays vs. Protons
Attenuation of Photons, ZN(x) = Noe- µµµµ x
Energy Loss of Protons, ρρρρ
NIST Data
dxdE
dldE ρ=
Low Contrast: ∆ρ∆ρ∆ρ∆ρ = 0.1 for tissue, 0.5 for bone
Measure statistical process of X-ray removal Measure energy loss on individual protons
∑∫ ∆≈=∆ ldxdEdx
dxdEE ρ
Bethe-Bloch
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPPNegative Slope in the Bethe-Bloch Formula
•Relatively low entrance dose
(plateau)
• Maximum dose at depth
(Bragg peak)
• Rapid distal dose fall-off
• RBE close to unity0
100
200
300
0
5
10
0 10 20 30 40 50
Proton Energy Loss in H2O
Proton Energy
[MeV]
Energy Deposit in 1mm
[MeV/mm]
Water Depth [cm]
E = 130 MeV E = 250 MeV
Imaging Treatment
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPPProtons vs. X-Rays in Therapy
Protons:
• Energy modulation
spreads the Bragg peak across the malignancy
X-rays:
• High entrance dose
• Reduced dose at depth
• Slow distal dose fall-off
leads to increased dose
in non-target tissue
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPPMilestones of Proton Computed Tomography
• R. R. Wilson (1946)Points out the Bragg peak, defined range of protons
• A. M. Cormack (1963)Tomography
• M. Goitein (1972)2-D to 3-D, Simulations
• A. M. Cormack & Koehler (1976) Tomography, ∆ρ∆ρ∆ρ∆ρ ≈≈≈≈ 0.5 %
• K. M.Hanson et al. (1982)Human tissue, Dose advantage
• U. Schneider et al. (1996)Calibration of CT values, Stoichiometric method
• T. J. Satogata et al. (Poster M10-204) Reduced Dose of Proton CT compared to X-Ray CT
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP What is new in pCT ?
• Increased # of Facilities with gantries etc.See the following talk by Stephen G. Peggs)
• 2 Ph.D. Theses at PSI and Harvard Cyclotron(U. Schneider & P. Zygmanski)
• Existence of high bandwidth detector systems for protons– semiconductors – high rate data acquisition ( > MHz)– large-scale (6”wafers)– fine-grained (100’s um pitch)
• Concerted simulation effort – Exploitation of angular and energy correlations– Support of data analysis– Optimization of pCT set-up (detector, energy, ..)– Dose calculation
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP Potential of Proton CT: Treatment Planning
Alderson Head Phantom
Range Uncertainties(measured with PTR)
> 5 mm> 10 mm> 15 mm
Schneider U. & Pedroni E. (1995), “Proton radiography as a tool for quality control in proton therapy,” Med Phys. 22, 353.
X-ray CT use in proton cancer therapy can lead to large uncertainties in range determination
Proton CT can measure the density distribution needed for range calculation.
There is an expectation (hope?) that with pCT the required dose can be reduced.
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP Low Contrast in Proton CT
ρρρρ
132537.2158.92.0131737.7161.51.5
131138.1163.61.1
130938.2164.11.0
TOF[ps]
Range [cm]
Energy[MeV]
ρ∗ρ∗ρ∗ρ∗ l[g/cm2]
150
200
250
0 5 10 15 20 25
Proton Energy
Proton Energy[MeV]
Depth in H2O [cm]
0
0.2
0.4
0.6
0.8
1Energy Loss in Water
dE (250)dE (250)+1.1dE (250)+1.5dE (250)+2
Energy Loss
[MeV/mm]ρρρρ
1.01.01.01.01.11.11.11.11.51.51.51.52.02.02.02.0
Sensitivity Study:Inclusion of 1cm thickness and density ρρρρat midpoint of 20cm H2O
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPPRequirements for pCT Measurements
Tracking of individual Protons requires Measurement of:
NE
Eσσ =><
%1≈Eσ
dxdE⋅=
AN D
• Proton angle to much better than a degreeMultiple Coulomb Scattering ΘΘΘΘMCS≈≈≈≈1o
• Proton location to few hundred um
• Average Proton Energy <E> to better than %
• In order to minimize the dose, the final system needs the best energy resolution! Energy straggling is 1- 2 %.
• Improve energy determination with statistics
• Issue: Dose D = Absorbed Energy / MassN/A = Fluence( for Voxel with diameter d = 1mm105 protons of 200 MeV = 7 [mGy])
0/6.13 Xlzp
MeVCMS ⋅
≈β
θ
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPPDose vs. Voxel Size for pCT Measurements
10-6
0.0001
0.01
1
10-6
0.0001
0.01
1
0.01 0.1 1 10
pCT: Contrast - Voxel Size - Dose 200 MeV Protons, 3Stdv.
d=5mm, Sid=2mm, 2%d=5mm, 2%d=1cm, 2%
Dose [mGy]
Density Difference [g/cm 3]
Voxel Diameter
Define voxel of volume d3
Dose in voxel = DvTake n =20cm/d settings Total dose D = n* Dv
52
2
~ Dd
E
⋅∆ ρσ
Trade-off between Voxel size and Contrast (∆ρ∆ρ∆ρ∆ρ) to minimize the Dose
Require 3σσσσ Significance
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP Studies in Proton Computed Tomography
• Exploratory Study in Proton Transmission Radiography– Silicon detector telescope– Simple phantom in front– Understand influence of multiple scattering and energy resolution on image
• Theoretical Study (GEANT4 MC simulation)– Evaluation of MCS, range straggling, and need for angular measurements– Optimization of energy
Collaboration Loma Linda University Medical Center – UC Santa Cruz
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPPExploratory Proton Radiography Set-up
Degraded down to 130 MeV by 10” wax block
27.3 cm30 cm
Beam from Synchrotron
Object
Wax block Air Air
250MeV 130MeV 50 + 130MeV
y x x ySi Modules
Proton Beam from Loma Linda University Medical Ctr @ 250 MeV
Object is aluminum annulus 5 cm long, 3 cm OD, 0.67 cm ID Very large effects expected, x = ρρρρ*l = 13.5 g/cm2
Traversing protons have 50 MeV, by-passing protons have 130 MeV
Silicon detector telescope with 2 x-y modules: measure energy and location of exiting protons
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPPSilicon Detector Telescope
• GLAST Readout
1.3 µs shaping time
Binary readout
Time-over-Threshold TOT
Large dynamic range
6.4 cm
6.4
cm
5 x 64 channels
Simple 2D Silicon Strip Detector (SSD) Telescope of 2 x-y modules
built for Nanodosimetry
• 2 single-sided SSD / module
measure x-y coordinates
• GLAST Space Mission developed SSD
194 µm pitch, 400 µm thickness
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP
PulseThreshold
Time-over-Threshold TOT TOT ∝∝∝∝ charge ∝∝∝∝ LET
Time-Over-Threshold ~ Energy Transfer
Digitization of position (hit channel) and energy deposit (TOT)
0
20
40
60
80
100
120
0 50 100 150 200
TOT Measurement vs Charge
TOT [us]
Input Charge [fC]
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPPCalibration of Proton Energy vs. TOT
Derive energy resolution from TOT vs. E plot
Good agreement between measurement and MC simulations
0
50
100
150
200
250
300
0 50 100 150
TOT Spectra for Low-energy Protons
250MeV40MeV24MeV17MeV
TOT [us]
10
100
10 100 1000 104
TOT vs Proton EnergyMeasurement and Expectation
ToT measuredTOT expected
TOT [us]
Proton Energy [MeV]
LLUMCSynchrotron P Beam
GLAST SLAC Test Beam
TOT Saturation
0
0.1
0.2
0.3
0.4
10 100 1000
Proton Energy Resolution
0
0.1
0.2
0.3
0.4
σσσσΕΕΕΕ/Ε/Ε/Ε/Ε
Proton Energy [MeV]
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPPImage of Al Annulus
Subdivide SSD area into pixels1. Strip x strip 194um x 194um2. 4 x 4 strips (0.8mm x 0.8mm)
Image corresponds to average energy in pixel
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP Energy Resolution => Position Resolution
Slice of average pixel energyin 4x4 pixels(need to apply off-line calibration!)
Clear profile of pipe,but interfaces are blurred
Hole “filled in”
“Fuzzy” Edges
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP Multiple Scattering: Migration
Protons scatter OUT OF target (not INTO).
Scatters have larger energy loss, larger angles, fill hole, dilute energy
Image Features:
Washed out image in 2nd plane (30cm downstream)
Energy diluted at interfaces
(Fuzzy edges, Large RMS, Hole filled in partially)
Migration of events
are explained by Multiple Coulomb Scattering MCS
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP GEANT4 MC: Use of Angular Information
Angular distributions well understood
Si Telescope allows reconstruction of beam divergence and scattering angles
Select 2 Areas in both MC and DataA = inside annulus : Wax + Al B = outside annulus : Wax only
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPPGEANT4 MC: Migration
Protons entering the object in front facebut leaving it before the rear face
Beam profile in slice
Energy of protons
entering front face
Migration out of object
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP
Energy Profile before (after ) Angle Cut
Energy RMS before (after ) Angle Cut
GEANT4 MC: Use of Angular Information
Less Migration
Angular Cut at ΘΘΘΘMCS of the Wax
Sharp Edges (Energy Average)
Sharp Edges (Energy RMS)
Angular cut improves the contrast at the interfaces
2002 IEEE NSS/MIC pCT: Hartmut F.-W. Sadrozinski , SCIPP
SCIPPSCIPP ConclusionsPresent status of pCT:
• Long tradition, increased interest with many new proton accelerators
(see next talk by Stephen G. Peggs)
• pCT will be useful for treatment planning
(reconstruction of true density distribution)
• Potential dose advantage wrt X-rays
( see Poster M10-204 by Satogata et al. )
• Use of GEANT4 simulation program aids in planning of experiments
(correlation of energy and angle, “migration”)
(see Poster M6-2, L. R. Johnson et al.)
Our future plans:• Optimization of beam energy
• Investigation of optimal energy measurement method
• Dose – contrast - resolution relationship on realistic phantoms