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Part I
Physicists do it in Hospital
Tong Xu
Dept. of PhysicsCarleton University
Why there are physicists in the hospital?
Medical Physicists
Where in the hospital can you find them? Diagnosis imaging departments:
• Radiology and Nuclear Medicine (CT, MRI, PET…) Cancer centre
• Medical Physics department (Radiotherapy)
What is their job? Make sure the equipments are working
according to their physics specifications Perform radiotherapy treatment planning
Why we need physicists to perform these tasks?
Let’s to go back to the history of some of the medical technologies.
Related Medical Technologies
X-ray CT
Magnetic Resonance Imaging
Radiation Therapy
Three examples …
Discovery of X-ray
First discovered by German Physicist Wilhelm C. Röntgen in 1895
On a New Kind of Rays Nature 53, 274-276 (23 January 1896)
Discovery of X-ray Independently
discovered by Nikola Tesla in 1896
Discovery of x-ray 1. Crookes Tube
Invented by Sir William Crookes, chemist and physicist, around 1860s.
A demonstration of the cathode ray – accelerated electron beam.
Discovery of x-ray2. Cathode ray
Cathode ray is a beam of electrons
Discovery of x-ray3. Rontgen’s experiment
A mystery radiation was coming out from the tube
Röntgen called it
X-ray
In fact, x-ray is just a ray of light photons with much higher energy than
ordinary light
Typical x-ray spectrum
Medical Application of x-ray
Röntgen received the First Physics Nobel price in 1901
X-ray radiograph
It’s a shadow image of human
What do we need to see through a human?
X-ray
X-ray Computer tomography
X-ray projections of heart
CT Image reconstruction
Projections at different angle 3D structure
http://rpop.iaea.org/
Inventers
Theory proposed by a physicist Allan MacLeod Cormack in1956 two papers in the Journal of Applied Physics
in 1963 and 1964
First Prototype by electrical engineer Godfrey Hounsfield in 1969
The first CT prototype
First Prototype by Godfrey Hounsfield in 1969
Cormack and Hounsfield shared the Medical Nobel prize in 1979
Magnet Resonance Imaging1. Stern molecule beam (1922)
Individual gas molecules fly through a pair of magnets
developed by German Physicist Otto Stern and Walther Gerlach in 1922
Magnet Resonance Imaging2. Some nucleus are like tiny
magnets
S
N
S
N
Detector
Magnet Resonance Imaging2. Some nucleus are like tiny
magnets
N
S
S
N
Detector
S
N
S
N
Otto Stern received Physics Nobel prize in 1943
Magnet Resonance Imaging3. Precession of magnetic dipoles
Some nuclear has magnetic momentum
They are like magnetic dipoles
They precess around the external magnetic field Just like a Gyroscope
Check out this animationhttp://www.simplyphysics.com/MRI_shockwave.html
B
Magnet Resonance Imaging3. Precession of magnetic dipoles
The precession frequency
ω is in the radio frequency range is the Gyromagnetic ratio
BB
Magnet Resonance Imaging3. Precession of Magnetic dipoles
BAligned against the external
Magnetic field B
Higher energy state
Aligned with the external Magnetic field B
Lower energy state
The nucleus feel more comfortable to stay in lower energy state
N
S
Magnet Resonance Imaging4. Nuclear Magnetic Resonance
What if I send nucleurs a Radio wave that has the same frequency as the
precession?
American physicist Isador I. Rabi had an great idea!
Magnet Resonance Imaging4. Nuclear Magnetic Resonance
Detector
S
N
S
N
Radio frequency signal ~
Magnet Resonance Imaging4. Nuclear Magnetic Resonance
The nucleus will resonance with the RF wave
They absorb RF energy
And flip to higher energy state
Can measure the nuclear magnetic montemtum precisely
Isador I. Rabi received Physics Nobel prize in 1944
Magnet Resonance Imaging5. NMR with solids and liquids
In 1946, two other Americans, Edward M. Purcell and the Swiss-born Felix Bloch, separately apply this nuclear magnetic resonance (NMR) method to solids and liquids.
Purcell and Bloch received Physics Nobel prize in 1952
Principle of NMR
Since the gyromagnetic ratio γ is unique for nucleus of each elementsNuclear Magnetic Resonance is a powerful tool for chemical analysis
B
Resonance frequency
Until 1970s….
Magnet Resonance Imaging5. Apply NMR to imaging
Paul Lauterbur & Peter Mansfield applied NMR to image body in 1970s
Introduced gradients to the magnetic field
Thus, frequency the radio wave emitted by the nucleus tell us where they are.
Magnetic Resonance Imaging
MRI scanner
Source: sfu.ca
MRI
A technique for imaging soft tissues
source: lecture slides from Prof. I. Cameron
Lauterbur and Mansfield received Medical Nobel prize in 2003
Cancer diagnosis
http://www.dcmsonline.org/
Ch
est
X-
ray
x-ra
y C
T
Nu
cle
ar
Med
icin
e
Physics in Cancer treatment
Radiation Therapy
Uses ionizing radiation
Kills tumour by damaging tumour cells
Radiation therapy
External beam radiation therapy
Use x-ray generated from linear accelerator.
Max energy: 4~20 (MeV, 106 eV)
Mega-Electron-Volt Compare to visible light: 2-3 eV Compare to UV light: 3-5 eV 1000,000 times higher than UV light
Linear accelerator (Linac)
Source:www.cerebromente.org.br
Accelerated high energy electron beam hit aTungsten target
Produce high energy x-ray beam
Treatment planning
It’s also a job for physicists !
X-ray , electrons, photons, scatter radiation dose …
Only a medical physicist were trained to deal with them !
Summary
Many medical technologies are originated from physics discovery.
Then, developed by physicists.
Medical physicists are The “customer service” team Improve the techniques Develop new techniques
Ionizing radiation damages the cell
Ionizing radiation
DNA
x-ray photons
Electron
Ionizing radiation
DNA
X-ray photon
Excited by physics discoveries
Passionate about People’s well being
Positron Emission Tomography (PET)
http://www.mni.mcgill.ca/cog/paus/techniques.htm
PET image
How is x-ray been generated?1. Bremsstrahlung radiation
How is x-ray been generated2. Characteristic x-ray radiation
Part II
Positron Emission Tracking (PeTrack): the prototype and its evaluations
Tong Xu, Marc Chamberland, Benjamin Spencer, Simon Massad
Carleton University, Ottawa, Canada
Outline
Introduction
Concept of PeTrack
Simulation study and results
The prototype the evaluation
Conclusion
External beam Radiation therapy
http//www.stfranciscare.org
Radiation delivery requirement
Deliver high radiation dose to tumour
Minimize radiation to healthy tissue around the tumour
Accurate delivery of x-ray beam
3 Tricks...
Trick #1:Focusing multiple beams
Trick #2:Collimate the beam to the shape of tumour
This method is called3D-conformal radiation therapy (3D-CRT)
3D conformal Radiation therapy (3D-CRT)
Shape the field following the outline of tumor
Trick #3:Intensity modulation inside the field
This is one step forward of 3D-CRT, with the addition of intensity modulation inside the field.Intensity modulated radiation therapy (IMRT)
Tumour
Spinal cord3D
-CRT
Intensity is uniform inside the field
IMRT
Intensity is not uniform inside the field
Accuracy of radiation therapy Significant development has been
done in diagnose and delivery techniques (PET, SPECT, IMRT…)
The tumor motion remains a limiting factor.
The moving target
Tumour moves due to:RespirationCardiac beatingOther visceral motions
The tumor can move by more than 3 cm !
Three level of motion management
None Breath holding orRespiratory gating
Real-timetumor tracking
Radiation field
Motion management
Breath holding
Respiratory gating
Breath holding
Methods:– Self breath holding – Active breathing control device
Limitations– Reproducibility (up to 6 mm residual
motion)– Difficult for Lung cancer patient to
tolerate
Respiratory gating
Breath normally!
Uses: External markers Implanted internal markers Others
– Spirometry– Temperature sensor– Strain gauge…
Respiratory gating
LinacBeam
On
Off
Gating Thresholds
Berbeco et al. 2005
External markersTang et al. 2004
Correlation between external and internal motion Koch et al 2004
Unstable breathing Ozhasoglu et al. 2002
Phase shift Ozhasoglu et al. 2002
Internal markers
Implanted in or close to tumor
Invasive
Provide exact location of tumor
Internal marker tracked by x-ray Shirato et al. 2000
X-ray tube
Image detector
Radiation dose from the x-ray fluoroscopy Shirato et al. 2004
Up to 1.2 Gy skin dose per hour of treatment time
Not feasible for intensity modulated radiation therapy – 20 – 30 minutes /fraction– large volume of normal tissue 25-30% of
tumor dose!
Calypso® 4D LocalizationSystem (EM marker)
MRI artifacts of EM transponders X Zhu et al, 2009
RealEye tracking system Shchor et al 2010
RealEye tracking system Can only track one marker
Can not be used for 10MV beam or higher due to induced radioactivity
Tracking with Positron emission marker
Miniature markers ( 0.8 mm)
Labeled with positron emission isotopes (0.1 mCi)
Track markers by detecting annihilation gamma
PeTrack
PeTrack is NOT PET
(Clinical Whole body PET)
Can PET system locates an object with <1 mm accuracy?
Over-all image resolution of PET : 4 - 8 mm
Yes, if the geometry of the source is known
Find a point in 3D with the minimum summed distance to the coincident lines
It is NOT image reconstruction !
Localize PeTrack marker
Patient
Detector Detector
PeTrack system for tumor tracking
Linac
PeTrack detectors
PositronemissionMarker
PeTrack Detector modules
Detector module
PeTrack marker and isotopes
I-124 As-74 Rb-84
T1/2
(days)
4.2 18 32
β+
Fraction23% 29% 23%
Can be implanted with biopsy needle of size 18 Gauge (1.27 mm)
The challenge
The algorithm
Classify the coincident lines using Mixture-of-Gaussians clustering technique
Determine the position of each markers from its coincident line cluster
Find the true location with iteration
Initial estimation
Computer simulation results
Based on a Monte Carlo simulation package: GEANT4.Four markers were simulated
Localization precision
0 50 100 150 200 2500.0
0.5
1.0
1.5
Loca
lizat
ion
erro
r (m
m)
Coincidient Lines per marker
Dynamic Thorax Phantom
Phantom rod
MarkerDirection of motion
RMSE (mm)
3D RMSE (mm)
R2
1
AP 0.30
0.39
0.844
LR 0.20 0.954
IS 0.14 0.997
2
AP 0.42
0.53
0.636
LR 0.26 0.812
IS 0.17 0.997
3
AP 0.29
0.40
0.969
LR 0.25 0.986
IS 0.13 0.998
Average 0.24 0.44 -
The PeTrack Prototype
BGO crystal and Position Sensitive PMT
Single Marker
Adj. R2
Measured amplitude
(mm)
Expected value(mm)
Error(mm)
x 0.99 9.63 ± 0.05 10.00 -0.37
y 0.99 5.16 ± 0.04 5.34 -0.18
z 0.81 0.65 ± 0.02 0.67 -0.02
3D track of two markers
-5
0
5
10
15
-20
-15
-10
-50
510
-15
-10
-5
0
5
10
15
Positions of one of the marker
0 10 20 30 40 50 60
-5
0
5
10
15
positio
n (
mm
)
Time(s)
X Y Z
Two markers precision
Standard deviation of the distance between the two marks during the motion tracking: 0.73 mm
Estimated precision: 0.52mm
Conclusion
PeTrack can perform tracking of multiple fiducial markers with sub-mm precision
It is a potential technique for achieve hyperfractionation treatment for moving tumors.
Acknowledgement
Dr. Richard Wassenaar Nathan Churchill, University of
Toronto
Supported by Natural Sciences and Engineering Research Council of Canada
Thank you!
Tracking of a single Line marker
Life time dose (0.1 mCi marker)
Isotope 124I 74As 84Rb
Half life (days) 4.2 18 32
dose (Gy) @ 5 mm (volume: 0.5cc) 2.6 9.0 18.6
dose (Gy) @ 10mm (volume: 4.2cc) 0.7 2.46 4.96
dose (Gy) @ 15mm (volume: 14 cc) 0.32 1.09 2.24
As compared with x-ray fluoroscopy dose Higher maximum dose
Very small volume effected (~ 10 cc vs 1000 cc
Can be implanted inside the tumor
Precision
5.0 mm PET spatial resolution provides 0.5 mm localization precision
With only about 100 events!
lines coincident ofNumber
resolution spatial PETPrecision
Motion trace of marker #3 and
predicted motion trace
Distribution of the1D prediction error
95th percentile (100 ms) = 2.3 mm
95th percentile (200 ms) = 2.7 mm
Distribution of the3D prediction error
Latency(s)
1D pred. error(mm)
3D pred. error(mm)
0.1 0.0 ± 0.8 1.3 ± 0.6
0.2 0.0 ± 0.9 1.4 ± 0.7
Life time doseActivity = 0.1 mCi
Sensitivity within the Field of view
Frame based stereotactic neurosurgery
http://www.elekta.com/healthcare_international_stereotactic_neurosurgery.php
Fiducial-less trackingSchweikard et. al. 2004
Synthetic a serial of CT at different time points by deforming two CT scans : Inhale and exhale
Registration of real-time x-ray projections with digitally reconstructed images from Synthetic CT scans
Registration computing time: 5 -10 sec Accuracy depends on the deforming
model of lung
Physical Requirement of tumor tracked radiation therapy
Track the tumor in real-time Predict the tumor position to
account for the lag of delivery system
Fast reaction of delivery system
Current internal tracking techniques
X-ray marker EM marker
Sampling rate 30 sec-1 10 sec-1
Precision 0.5 mm 0.2 mm
Marker size Φ0.8~1.6mm
Φ1.8mm x 8. mm cylinder
Radiation dose Upto 1.2 G/h Zero
Correlation between external and internal motionOzhasoglu et al. 2002
Complex tumor trajectory Ozhasoglu et al. 2002
Correlation coefficient (R)Koch et al. 2004
SpirometryHoisak et al. 2004
Higher correlation (R= 0.51 - 0.99) than that of skin marker (R= 0.39 – 0.98)
Difficult to tolerate
Radiation dose from the x-ray fluoroscopy Shirato et al. 2004
External markers -1
Passive or active infrared skin markers
Marker position tracked by camera in real time
Linac gated by the position of external markers
Linear accelerator generate pulsed x-ray
Pulse frequency– 100 – 400 Hz
Pulse width – 1 – 10 μs
Blanking of PeTrack detector
Expected data acquisition duty cycle > 80%
PMT HV gating
Expectation-Maximization -1 Expectation step. Compute the
probabilities for all trajectories, n=1,…N, belonging to each cluster, k=1,…K
K
j
ij
ijn
ij
ik
ikn
iki
kn
mTdGa
mTdGap
1
)()()(
)()()(
)(,
,),(
,),(
Expectation-Maximization -2 Maximization step. Update
parameters
N
pa
N
n
ikn
ik
1
)(,
)1(k
ik
ik Vmm
)()1(
N
n
ikn
N
n
ikn
ikn
ik
p
mTdp
1
)(,
1
2)()(
,)1(
),(
Previous worksGundogdu, 2005
Intended for industrial application Two particle was tracked Resolution 20 -30 mm
The challenge
Simultaneously tracking of three or more markers
Distance between markers: a couple centimeters
The existing algorithm for single particle tracking dose not apply
Scatter rejection
R=2σ
Patient
Expectation-Maximization iterations
1. Initial estimation
2. Expectation Clustering by the probability of each trajectory
3. Maximization Update the position of markers
4. Repeat step 2 and 3 until converge.
Speed of the algorithm
Four markers 400 coincident events 2.8GHz P4
20 ms/run Tumor position can be updated at
a rate > 10 Hz
Lift time dose for different treatment duration
Required activity at the time of implanting
Breath holding
Methods:– Self breath holding – Active breathing control device
Limitations– Reproducibility (up to 6 mm residual
motion)– Difficult for Lung cancer patient to
tolerate
Respiratory gating
Breath normally!
Uses: External markers Implanted internal markers Others
– Spirometry– Temperature sensor– Strain gauge…
Respiratory gating
LinacBeam
On
Off
Gating Thresholds
Berbeco et al. 2005
External markersTang et al. 2004
Correlation between external and internal motion Koch et al 2004
Unstable breathing Ozhasoglu et al. 2002
Phase shift Ozhasoglu et al. 2002
Identify failed markers
A failed marker should be identified automatically from the output of the algorithm
ka
k
Relative activity of marker # kRoot mean square distance form marker # k to its trajectories
Identify failed markers
> 3 mm
< 0.02ka
k
Identify failed markers with criteria
The source of tumor motion Respiration
Cardiac beating
Other visceral motions
Lung tumor motions trajectoriesSeppenwoolde et al. 2002
Internal marker tracked by x-ray Shirato et al. 2000
X-ray tube
Image detector
Internal marker tracked by x-ray Shirato et al. 2000
Positron emission and annihilation
Positron Emission Tomography (PET)
http://www.mni.mcgill.ca/cog/paus/techniques.htm
PET image
Physical limits on PET resolution
Humm et al, 2003
Over-all resolution: 4 - 8 mm(Whole body PET)
http://www.raytest.de/pet/clearPET/clearPET.html
Three 22Na Markers
Activity of 22Na: ~425 kBq/marker
PET Image reconstruction
http://depts.washington.edu/nucmed/IRL/pet_intro/intro_src/section4.html
Yes! A single point source can be tracked with < 1 mm accuracy
Park et al. 1993, Park et al. 2002
The algorithm
Assuming the distance from a marker to its annihilation coincident lines follows a Gaussian distribution
k Standard deviation ~ system spatial resolution
Methods
PeTrack simulation model Based on a Monte Carlo simulation
package: GEANT4 Patient: Φ 30cm x 60 cm water
phantom Distance from isocenter to detectors:
50 cm Detector: 40x40 array of 4x4x30 mm3
BGO crystals Energy resolution: 25% Spatial resolution ~ 4 mm
PeTrack simulation model Marker: active 0.4 mm spherical
core with a 0.2 mm thick gold shell
Single marker simulation:– Sensitivity, scatter fraction, dose
Four markers with I-124 were placed around isocenter: (0,0,0), (15,0,0), (0, 20,0), (0,0,20) (in mm)– Evaluate the algorithm
Definition of a valid event (trajectory)
Detected energies fall in the energy window (420-600 keV)
Coincidence has to be between detector A1 and A2, or between B1 and B2
Simulate the initial estimation error Error on the initial estimation
– patient setup– respiration– marker migration
Initial estimation is generated randomly around the true position– ± 5, ± 10 , ± 15 mm
1000 runs of the algorithm
Definition of success marker and run Localized by the algorithm within 1.5
mm from its true position
A successful run:– All four markers was allocated successfully
Precision:– Mean error among 1000 runs from the true
positions
Run success rate
0 200 400 600 800 1000
20
30
40
50
60
70
80
90
100R
un s
ucce
ss r
ate
(%)
Coincident lines per marker
± 5 mm initial error ±10mm initial error ±15mm initial error
Total coincident lines per run
Marker success rate
0 50 100 150 200 25065
70
75
80
85
90
95
100M
arek
er s
ucce
ss r
ate
(%)
Coincident lines per marker
± 5 mm initial error ±10mm initial error ±15mm initial error
Number of runs with different number of Successful markers
Initial error range (mm)
± 5 ± 10 ± 15
All 4 markers are successful 997 985 777
3 markers are successful 3 15 144
2 markers are successful 0 0 75
1 marker is successful 0 0 4
All 4 markers failed 0 0 0
Cardiac BeatingShirato et al. 2004
Yes! A single point source can be tracked with < 1 mm accuracy
Park et al. 1993, Park et al. 2002, Sarah E. Palmer et al, 2006