what is in-room image-guidance? why in-room image … a. jaffray, kamal chawla, cedric yu, john w....
TRANSCRIPT
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The Use of In-room kV Imaging for IGRT
John W. Wong, Johns Hopkins University
David Jaffray, Princess Margaret Hospital
Fang-fang Yin, Duke University
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Disclosure
• The presenter has
– research agreement funded by Elekta
– financial interest in cone-beam CT technology
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Why In-Room Image-Guidance?
• To improve the targeting precision and accuracy so that treatment margin from CTV to PTV could be reduced
• Challenges:– uncertain about the target location– uncertain about the target shape– uncertain about the target motion– limitations of tools used for image-guidance
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What is In-room Image-Guidance?Use of imaging method in the treatment room while patient
stay at the treatment position
• To localize, monitor, and track surrogates which are associated to the patient and are of interest to radiation treatment
• To generate a list of choices for decision-making and intervention for positioning and modification
• To direct how the treatment couch or radiation beam should be modified
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TG 104: The role of In-room KV imaging for patient setup and target localization
Fang-Fang Yin, Co-Chair, Duke University Medical CenterJohn Wong, Co-Chair, John Hopkins UniversityJames Balter, University of Michigan Medical CenterStanley Benedict, Virginia Commonwealth UniversityJean-Pierre Bissonnette, Princess Margaret HospitalTimothy Craig, Princess Margaret HospitalLei Dong, M.D. Anderson Cancer CenterDavid Jaffray, Princess Margaret HospitalSteve Jiang, Massachusetts General HospitalSiyong Kim, Mayo Clinic, JacksonvilleCharlie Ma, Fox Chase Cancer CenterMartin Murphy, Virginia Commonwealth UniversityPeter Munro, Varian Medical SystemsTimothy Solberg, University of Nebraska Medical CenterQ. Jackie Wu, Duke University Medical Center
* Gigas Mageras, Ellen YorkACMP 2011_jww
Objectives
1. Understand the challenges of treatment verification; leading to in-room kV imaging
2. Understand the configurations and operation principles of different in room kV x-ray imaging systems
3. Understand the requirements for effective implementation and quality assurance for IGRT
4. Understand the clinical applications and the associated limitations
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Evolution of in-room x-ray imaging in RT
In the 50’s – 60’s:
• A separate kV x-ray system and Cobalt-60 unit linked through a mobile couch (Karolinska University Hospital);
• A kV x-ray source attached to the beam stopper of a Cobalt-60 unit (Holloway 1958)
• A customized Cobalt-60 unit (Johns and Cunningham 1959) linear accelerator (Weissbluth,Karzmark et al. 1959)
• A Cobalt-60 unit and a kV x-ray tube mounted at 90o from each other on a circular ring (Netherlands Cancer Inst.)
• A Cobalt-60 unit with an x-ray tube mounted to the collimator at an offset angle (Shorvon, Robson et al. 1966)
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Ontario Cancer Institute's X-otron Cobalt-60 unit
kV x-ray source
kV Imaging on-board a cobalt-60 unit
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• 70’s – 80’s --- The age of MV port film
– “Ready-pack” and film system for radiation therapy (Haus, Marks, Griem, 1973)
• 80’s ---- 45o
off-set kV x-ray source
– 10 MV medical accelerator at MGH (Biggs, et al. 1985)
– same screen/film system with MV beam (Shiu, 1987)
– RADII product by HRL Inc
• 80’s ---- The advent of electronic portal imaging (EPI)
– Renewed recognition of deficient MV image quality
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Evolution of in-room x-ray imaging in RT Challenges of Portal Imaging
• Quality difference between prescription kV images and treatment MV images
– May affect accuracy in error detection
• Deriving appropriate correction from EPID images
– Large residual error of correction using single projection, 20% > 5 mm
• Need for more projection and more repeat imaging
– Concerns of imaging dose (4-6 MU per film image)
• Lack of soft-tissue contrast
– uncertainty in the actual delivered dose
• kV in place of MV imaging offers a reasonable solution
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Absorption Unsharpness: kV vs MV
50kVp 6 MV100 kVp
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Absorption Unsharpness: kV vs MV
X Position (mm)
-15 -10 -5 0 5 10 15
Transm
ission (
scaled
to full r
ange)
0.0
0.2
0.4
0.6
0.8
1.0
Al
20mm
Detector (M=1.05)
6MV
100 kVp
50 kVp2 MeV
50 keV
30 keV
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The era of in-room kV x-ray imaging in RT
90’s – present: Gantry mounted kV imaging
• Low-Z target to generate low energy MV x-rays for imaging (Galbraith 1989; Ostapiak, O'Brien et al. 1998)
• Integrated kV-MV x-ray target (Cho and Munro 2002)
• Gantry mounted 37o
offset kV/MV imaging system with image intensifier(Sephton and Hagekyriakou 1995)
• Gantry mounted kV/MV imaging system with EPID
– 45o offset (Jaffray, Chawla et al. 1995)
– 90o offset with CBCT capability (Jaffray et al. 1999).
– Precursor to modern commercial systems
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A little story – Dual Beam Imaging, 1995
DAVID A. JAFFRAY, KAMAL CHAWLA, CEDRIC YU, JOHN W. WONG.DUAL-BEAM IMAGING FOR ONLINE VERIFICATION OF RADIOTHERAPY FIELD PLACEMENT. Int. I. Radiation Oncology Biol. Phys., Vol. 33. No. 5. pp. 1273-1280, 1995
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A little story: MV conebeam CT in 1995
• Paul Cho introduced CBCT algorithm (U Washington, 1993)
• Chang Pan manually acquired 90 projection images (6 MV)
– in room, rotate phantom, out of room, shoot and acquire
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Dual Beam Imaging on
Philips SL: 1996
Practicing on Bare Drum: Spring 1997
SL Mechanicals -under load
D. Jaffray R. CookeD. DrakeM.
Moreau
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• April – May 1997, Two weekends, one month apart
• Wk 1: Drill holes, move electronics; Wk 2: Mount x-ray source and imager
Wood Cover
CCD EPID
The era of in-room kV x-ray imaging in RT
90’s – present: Room-mounted systems
• An in-room CT scanner with the medical accelerator (Akanuma, Aoki et al. 1984; Uematsu, Fukui et al. 1996)
• Wall/ceiling/floor - mounted multi-kV fluoroscopy systems
– Murphy and Cox 1996 -- Prototype CyberKnife)
– Schewe, Lam et al. 1998 -- Portable CCD-based imager
– Shirato, Shimizu et al. 2000 - 4 systems for gating RT
– Yin, Ryu et al. 2002 – BrainLab kV image guidance
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The “Omni” in-room CT system
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In-room Conventional CT for IGRT
Memorial Sloan Kettering Cancer Center, 2003
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ACMP 2011_jww Curtsey of Lei Dong, Ph.D., MD Anderson Cancer Center, TX
Varian-GE ExaCTTM-on-Rails
Side rail to
provide
balance
Magnetic
encoder
strip
Central
guide rail
Fig. IIA.-3 There are three rails in this moving-gantry CT scanner. The central rail contains positional sensor and drive mechanism; and the two side rails provide level and balance during movement.
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helical scan:3 cm/s; scout scan: 7.5 cm/s
From C Ma
Curtsey of Lisa Grimm, Ph.D., Morristown Memorial Hospital, NJ.
Siemens Primatom system
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Siemens CT-on-Rails Ceiling/Floor-Mounted System
SDD: 3.62 mSID: 2.34 mPixel: 0.4 mmMatrix: 512x512
DigitalDetector
kV x-ray tube
F-F Yin Med Phy 2002
Novalissystem
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Ceiling/Floor-Mounted System
Detector
X-ray tube X-ray tube
Recessed Detector
Curtsey of Accuray, Inc.
Detectors above the floor
Detectors under the floor
Cyberknife system
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Gantry-Mounted Systems
Elekta Synergy
Varian OBI
Siemens Artiste
kV Fluoroscopic, Radiographic, and CT Functionality
Radiographic Tomographic
Fluoroscopic
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The “Omni” Gantry System at Duke
Recessed ExactTract KV tube
KV DetectorVideo/IR Camera
OBI KV Detector
OBI KV tube
MV Detector
NovalisTx SystemDuke University Medical Center
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Acceptance Testing: Imaging System
• The primary goal for acceptance testing is to verify the components, the configurations, the functionality, the safety, and the performance of the system relative to the specifications described in the purchasing agreement and/or installation documentation from the vendors
• Data generated in the acceptance testing could be used as the baseline for routine QA
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127.5
128.0
128.5
129.0
129.5
130.0
130.5
127.0 128.0 129.0 130.0
T-G
Dir
ection, Y
Axi
s,
mm
X Axis in A-B Direction, mm
Exp CW
Exp CCW
Adjusted points
Adjusted circle
Couch shift
126.5
127.0
127.5
128.0
128.5
129.0
129.5
127.0 128.0 129.0 130.0
T-G
Dir
ection, Y
Axi
s,
mm
X Axis in A-B Direction, mm
Exp CW
Exp CCW
Adjusted points
Adjusted circle
Couch shift
Dia = 0.6 mmDia = 2.5 mm
Before After
Acceptance: Synergy Table Axis “Tuning”TG142 : +/- 1mm
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Integrated CT/Linac: Mechanical precision and alignment uncertainty
(Court, et al, MDACC)
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Fiducial Transfer Method
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Acceptance Testing: Gantry Imaging System
• Room design and shielding consideration
• Verification of Imaging System Installation
• Safety and Mechanical Configurations
– System interlocks
– kV imaging arm movement
• Geometric Calibration
• Localization Accuracy
• Image Quality
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Elekta XVI system
• 2D Imaging system checks
– 2D low contrast visibility (0.9%)
– 2D spatial resolution (1.8 lp/mm)
• 2D geometric accuracy
– kV localization of MV isocenter from different gantry
– specification < 4 pixel, 1.04 mm
• ave. 1.5 pixels, max 3 pixel
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Leeds TOR 18FG
Elekta XVI Acceptance (Baseline)
• 3D imaging system checks
– Uniformity
– Low Contrast visibility
– Spatial Resolution
– Transverse vertical/horizontal scale
– Sagittal geometric
• 3D registration accuracy
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Elekta/Varian: 3D spatial resolution
TrueBeam image courtesy of Peter Munro
9
11
1315
9
11
1315
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Elekta XVI Acceptance (Baseline)
• 3D imaging system checks
– Uniformity: 1.1%
– Low contrast visibility (polystyrene – LDPE, 1.26%)
– Spatial resolution (12 lpcm)
– Transverse vertical/horizontal scale (as expected)
– Sagittal geometric (as expected)
• 3D kV-MV registration accuracy
– < 1 mm as specified
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Quality Assurance Programs
• Safety and functionality
• Geometric accuracy
• Dosimetric information
• Software and hardware
• Imaging system with delivery system alignment/coincidence
• Image quality
• TG 142 sets the frequencies and criteria
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ACMP 2011_jww * Recommendations for Imaging System QA
Procedure non-SRS/SBRT SRS/SBRT
Daily
ACMP 2011_jww * Recommendations for Imaging System QA
Procedure non-SRS/SBRT SRS/SBRT
Monthly
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Annual
Procedure non-SRS/SBRT SRS/SBRT Dose/Exposure vs Imaging Modality
Murphy et al Med Phys 2007 TG 76 Report
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Calibration for Ceiling/floor-Mounted System (ExacTrac System)
Isocenter calibration phantom x-ray calibration phantom
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QA for OBI/CBCT
• Safety and functionality
– Interlocks, lights, network-flow.
– All test items are verified during tube warm-up (< 5 min)
• Geometric accuracy
– OBI isocenter accuracy
– Accuracy of performance for 2D-2D match and couch shift
– Mechanical accuracy (arm positioning of KVS and KVD)
– Isocenter accuracy over gantry rotation
• OBI Image quality
– Radiography: contrast resolution and spatial resolution
– CBCT: HU reproducibility, contrast resolution, spatial
resolution, HU uniformity, spatial linearity, and slice thickness.
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1. MV Localization (0o) of BB;
collimator at 0 and 90o
qg-180 +180
u
v
qg
Reconstruction
qg
2. Repeat MV localization of BB for
gantry angles of 90o, 180o, and 270o
3. Adjustment of BB to treatment
isocenter
4. Measurement of BB location in kV
radiographic coordinates (u,v) vs. qg.5. Analysis of ‘Flex Map’ and
storage for future use
6. Use ‘Flex Map’ during routine
clinical imaging
+1mm
-1mm
MV-kV calibration --- Elekta
XVI1
XVI2
XVI3
XVI4
XVI5
26 cm CW
26 cm CCW
40 cm CW
40 cm CCW
50cm CW
50 cm CCW
FOV:Rot. Dir:
Flex Maps: Synergy (XVI) Units
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-150 -100 -50 0 50 100 150-0.1
-0.05
0
0.05
0.1
U [
cm]
mean
+/- 2
-150 -100 -50 0 50 100 150-0.1
-0.05
0
0.05
0.1
Gantry angle [o]
V [
cm]
Long term stability for one unit (NKI)
u
v
6 calibrations
over 15
month period
Weekly QA of MV/kV isocenter calibrationACMP 2011_jww
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All Flex Maps: Synergy (XVI) Units
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OBI1 Approach – “Residual”
Accept if within specified tolerance.
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Daily Geometry QA
• Align phantom with lasers
• Acquire portal images (AP & Lat) & assess central axis
• Acquire CBCT
• Difference between predicted couch displacements (MV & kV) should be < 2 mm
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Daily Geometry QA
• Align phantom with lasers
• Acquire portal images (AP & Lat) & assess central axis
• Acquire CBCT
• Difference between predicted couch displacements (MV & kV) should be < 2 mm
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Full kV/MV Calibration - Monthly
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Compare Portal Image & DRR
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Iso _kV
Iso _OD I = Q /A P h an to m = L asers /OD I
Iso _M V
M V R ad iatio n
Iso cen ter
M V M ech an ica l
Iso cen ter
M V N o m im al
Iso cen ter
x
z
y
E 1 (EP ID’s)
E 2 (CBCT )
E 3
Current* Action Level on E3: 2 mm (in any one direction)
* Due to large observer variability in MV alignment
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2006 XVI Daily QA Results (E3 Error)
XVI1 XVI2 XVI3 XVI4 XVI5
[mm] L/R S/I A/P
M (-0.04, -0.72, 0.52)
Ave(σ) (0.96, 0.82, 1.04)
~ 6 Months of Daily QA Testing ACMP 2011_jww
2007 OBI Daily QA Results (E3 Error)
OBI1 OBI2 OBI3 OBI4
[mm] L/R S/I A/P
M = (-0.08, -0.19, 0.27)
Ave(σ) = (0.51, 1.02, 0.71)
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CBCT: Geometric Accuracy and Precision
CBCT vs Orthogonal Portal Images
Phantom - Unambiguous Object
40 measurements over several months
Elekta Synergy RP
Sharpe et al. - Med Phys. 2006 Jan;33(1):136-44. ACMP 2011_jww
IG Performance:Connectivity,Orientation/Scale Checks
CT
Simulation
Treatment Planning System
XVI
Acquisition
OBI
Acquisition
Off-line Image
Review/Archive
On-line Images
Planning CT‟s
DIC
OM
/RT
Volumetri
c
Refere
nce
Images
DICO
M/R
T
Image Source: GE and Philips CT Planning: Philips Pinnacle v7.4
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• Anthropomorphic phantom• 4 Orientations• Target bony anatomy • Arbitrary initial shifts• Plot residual error• 5 XVI units
Residual Error
IG Performance:Connectivity,Orientation/Scale Checks
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0.00
0.02
0.04
0.06
0.08
0.10
0.12
0.14
0.16
0.18
1
Re
sid
ua
l A
bso
lute
Err
or
[cm
]
.
.
L/R
S/I
A/P
All XVI‟s
IG Performance:Connectivity,Orientation/Scale Checks
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Baseline CBCT Imaging
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Affects
•How often can you scan
•Resolution
•Contrast/dose – thick patients
•Image homogeneity
•Noise
•Size
•Resolution
•Angular sampling
•Image homogeneity / noise
•Speed
•Resolution
X-ray source:
•Heat capacity
•Focal spot size
•Energy range
•Bow-tie filter
Flat-panel detector
•Quantum efficiency
•Size
•Resolution
•Speed
•Scatter grid
Gantry
•Speed
•Accuracy (constancy)
Bow-Tie Filter
• Reduce Scatter
• Lower Skin Dose
• Reduce Saturation
30 mm
2 mm
Aluminum
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Application of a Bow-Tie FilterBow-TieNo Bow-Tie
Central dose 3 cGy, skin 4 cGy Central dose 3 cGy, skin 3 cGy
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Effect of size (scan length) on image quality
1 mm2 voxels, 1 mm slice
thickness, 32 mA, 40
ms, 120 kV, 1.5 cGy
2 cm 12 cm
20 cm
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Speed matters
• Number of projection images affects streak artifacts
• Given the IEC limit of 1 RPM
– Varian: 360 images for fast scan
– Elekta: 180 images for fast scan
• How much do you need?
– This depends on the task
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Which dose to use?
0.25 cGy 0.5 cGy
1 cGy 2 cGy
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Dose Projections Translation (mm) Rotation (dg)
L-R C-C A-P L-R C-C A-P
3.0 cGy 640 -0.4 -2.3 -2.4 -1.0 0.1 0.3
0.3 cGy 64 -0.4 -2.4 -2.5 -1.0 0.0 0.3
0.1 22 -0.4 -2.4 -2.4 -0.9 0.1 0.3
0.1 cGy3.0 cGy 0.3 cGy
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Scatter grid
• Scatter grid attenuates
– + Scatter
– - Primary beam
• Software correction may be equally effective
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Scatter correction algorithms
Elekta: scatter uniform and proportional to average image
intensity where there is patient in the beam
Boellaard et al. Two-dimensional exit dosimetry using a liquid-
filled electronic portal imaging device and a convolution model
Radiother. Oncol. 44 149-157, 1997
Without correction With correction
Varian TrueBeam: iterative kernel based scatter estimation
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Reconstruction settings
• Slice thickness
• Pixel size
• Pre-filtration
• Interpolation
• Reconstruction filtration
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1 mm slice thickness
Slice Thickness: 1 mm2 voxels, 20 mA, 20 ms, 120 kV, 1 cGy
3 mm slice thickness
5 mm slice thickness
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1 mm slice
thickness
5 mm slice
thickness,averaged
in all directions
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PIXEL SIZE: 32 mA, 40 ms, 120 kV, bowtie, 3 cGy
2 mm2 voxels, 2 mm slice thickness 1 mm2 voxels, 1 mm slice thickness
0.5 mm2 voxels, 0.5 mm slice thickness 0.5 mm2 voxels, 2.5 mm slice thickness ACMP 2011_jww
Elekta setting: smoothed
1 mm2 voxels, 1 mm slice thickness, 32 mA, 40 ms, 120 kV, bowtie, 3 cGy
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Un-smoothed
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Patient Dose Estimation: kV-CBCT
• Beam Quality: HVL (kVp, filtration)
• Tube output: Reference (mR/ mAs)
• Scanning Geometry: SAD, FOV, No. of projections
• Technique settings: mAs
• Patient Size (Body , Head…)
Dose depends on
AAPM’10
Bench top CBCT System
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CBCT: Radial Dose
0 2 4 6 8
0.6
0.8
1.0
1.2
1.4
1.6
1.8
2.0
2.2
2.4
Dos
e (
cGy)
Depth (cm)
FOV: 5 cm x 26cm
FOV: 10 cm x 26cm
FOV: 15 cm x 26cm
FOV: 26 cm x 26cm
Phantom: 16 cm dia.
Imaging Technique:
100 kVp
100 mA
20 ms
330 Projection
660 mAsDepth
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CBCT: Radial Dose
0 2 4 6 8 10 12 14
0.6
0.8
1.0
1.2
1.4
1.6
1.8
2.0
2.2
2.4
Dos
e (c
Gy)
Depth (cm)
FOV: 5 cm x 26cm
FOV: 10 cm x 26cm
FOV: 15 cm x 26cm
FOV: 26 cm x 26cm
Phantom: 30 cm dia.
Imaging Technique:
120 kVp
100 mA
20 ms
330 Projection
660 mAsDepth
Clinical Imaging Dose Measurements
A simple and clinical feasible method to estimated the CBCT imaging dose
Detectors Detectors
Kim et al,
Radiat Prot Dosi. 2008
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0
0.5
1
1.5
2
0 10 20 30
Tota
l Do
se (
cGy)
Field Size (z) (cm)
Dcenter
D2cm
CBCT Imaging Dose: Offset Geometry (FOV 40 cm)
Experimental Setup Dose vs. Field Size
Nuclear Enterprises Free-Air Chamber (0.6 cc)
32 cm “Body” Phantom330 projections at 2 mAs / proj
Islam et al., Med. Phys. 2006
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mA
s/ P
roje
ctio
n
Number of Projections
2
1
0.5
80 160 320
Variation of image quality with lens dose (cGy)
4.02.01.0
0.5 1.0 2.0
0.25 0.5 1.0
Deciding the Necessary Image Quality for the Application
16x Reduction
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Low Dose (1.5 mGy) Pediatric Imaging for Routine On-line IGRT
Artifacts in kV CBCT
• Cupping and streaks due to hardening and scatter (A&B)
• Gas motion streak (C)
• Rings in reconstructed images due to dead or intermittent pixels (D)
• Streak and comets due to lag in the flat panel detector (E)
• Distortions (clip external contours and streaks) due to fewer than 180 degrees + fan angle projection angles (F)
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IGRT is Clinical Quality Assurance
• Provides measurement of patient position in treatment position.
– Quantitative, accurate, repetitive
– Minimally invasive
– Large field-of-view
– Markers, bone, soft-tissue, skin-line
• Verify consistency of planned and actual geometry
– Provides a critical data source for rational margin design
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MV vs kV Fallacy
• Daily orthogonal open-field MV/kV projection imaging; 14 patients
• Alternate week kV- vs MV-based correction
• Verify correction with kV orthogonal pair
• MV and kV correction similar with adequate anatomic information
• Appreciable rotation uncertainty
• Main kV advantage: reduced imaging dose
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H&N LungH&N Lung Pelvic
Off-Line In-Room Image-Guidance
Reference images
Patient setup
Correction?
Treatment
Ynth treatment
On-board images
Patient planning information/Patient information system
N
StatisticalAnalysis (m,)
In-room imaging
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On-Line In-room Image-Guidance
Reference imagesPatient setup
Correction? TreatmentN
Correct position
Y
Feedback
In-room imaging III In-room imaging II
In-room imaging I
Patient planning information/Patient information system
On-board images
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Data: 1
Generic Margin
~ 2.5S + 0.7
Conventional RT
Data: n < N
Corrects for
systematic error
Off-line Adaptive RT
Data: daily
Corrects for all
setup/motion errors
On-line correction
Clinical IGRT Strategies:Margin --- from population to individual margin
• Key technologies for
quantifying treatment
uncertainties:
• Organ motion:
Computed
Tomography
• Daily setup:
Electronic Portal
Imaging
SI
Lat
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Adaptive Gating
ExacTrac IGRT
6D RoboticsFrameless Radiosurgery
Image-Guidance with ExacTrac
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Workflow Using Snap Verification
Initial 6D setup
Treat field 1 Treat field 2 Treat field 3
Snap verification for field 2
Snap verification for field 3
Snap verification for field 4
Treat field 4
....
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Use Case: Intra-Fraction Imaging
Example of dual x-ray imaging
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Image-Guidance with CT-on-Rails
Treatment
Room
Treatment Planning
Intranet
LINAC console
LINAC
Control Room
Alignment
Protocol
In-room
kV CT/CBCT
Images
Couch
Shifts
Gating
Signal
Planning and R&V System
Room
Reference CT
Reference
CT datasetImage
Storage
Imaging console
Correction?
R&V
System
Patient couch
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Use Case – SBRT Pancreatic Cancer
• Collaborative randomized trial – Hopkins, Stanford, MSKCC
• 2-3 mm PTV expansion
• Implanted markers for visualization
• Hopkins: Breath-hold (ABC) planning CT to immobilize motion
• Setup: Compare free breathing planning CT with CBCT
• Treatment
– free breathing fluoroscopy of markers to verify motion
– kV projection to verify ABC-moderate deep inspiration- setup
– breath-hold kV projection imaging to verify markers’ positions during treatment
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ABC-kV AP setup
ABC-kV lateral setup kV intra-fx monitor at one beam angle
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Planning CT with target contours
Use Case: 3-D Free-Breath ITV with CBCT
CBCT images prior to correctionCBCT images after correctionPost-treatment CBCTWang et al Ref J 2007
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Au markers validation: MV vs. kV shift difference
MV with Markers CBCT with Markers
• Independent Alignment Methods
• 16 patients (~250 fx)
• Duration: 6 months
• Unambiguous Surrogate (3 Au markers)
vs
Moseley et al. Int. J. Rad. Onc. Biol. Phys., 63, 2007ACMP 2011_jww
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Upper GI
21%
Lung
41%
Head and Neck
26%
Lymphoma
3%
Sarcoma
9%
Background
• The XVI system is linked to the Remote
Automatic Table Movement (RATM).
• The patient is shifted per the image-guidance
system via the remote couch interface.
• The stability of the system and residual error is
measured through verification scans acquired
following a table shift.
Methodology
• Collection Period Oct 19th „06 – Nov 17th „06
• Patients with repeat (verification) scans were
measured and matched using an Automatic
Algorithm
• 34 patients with 135 scans
Clinical “end-to-end” assessment of IGRT
W Li et al. J Appl Clin Med Phys. 2009 Oct 7;10(4):3056
Summary
The introduction of in-room kV imaging provides new opportunities to further improve treatment accuracy and precision. At the same time, it presents new challenges for its efficient and effective implementation.
Each in-room kV imaging method has its strengths and limitations. The user is well advised to match the clinical objective with the appropriate technology; or at least to apply the image guidance information to within the bounds of its validity:
imaging dose, field of view, sharpness vs contrast
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Summary
• Guidance documents are available to assist in the establishment of QA programs for IGRT technologies
• Published literature demonstrate that these systems can be accurate, precise, and reliable.
– Compare your results to others.
– Adapt upgrades --- high resolution panels
• Maintenance of IGRT performance is central to confidence in appropriate PTV margin.
• An integrated daily check for IG system consistency has been implemented into routine clinical use with a 15 minute time penalty.
Future considerations for in-room x-ray IGRT
• Need to analyze institutional data (4.5 TB in 4 machine-years)
– Margin specification, revised action level, frequency
• On-board CT/CBCT is a snap shot
– Soft tissue target localization remains challenging
– Dose concerns with intra-fraction x-ray monitoring
– Alternative solutions are needed
• EM transponders
• MRI-Linac
• Integrated on-board ultrasound imaging
• Motion artifacts are problematic
– 4D CBCT, Breath-hold CBCT
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1a
CBCT system
US system
(a)_ (b)_ (c)_
Contrast Enhanced CBCT – OBI 1.4 with no breathing motion
Courtesy of Michael Lovelock and Josh Yamada MD; MSKCC
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Summary
• Radiotherapy x-ray imaging systems have a wealth of tunable parameters – users can change these!
• Imaging dose and field of view should be set given the clinical requirements
• Image resolution and sharpness can be set according to preference, but increasing sharpness also increases noise
• For image guidance, a high resolution is not required -‘soft’ reconstructions offer slightly better soft tissue contrast
ACMP 2011_jww
Varian - Elekta
Parameter Varian Truebeam ElektaXVI4.5
Energy range 40-140 kV 70-150 kV
Bow-tie filter yes yes
Detector QE 60% (CsI) 60% (CsI)
Detector size 30 x 40 cm 40 x 40 cm
Pixel 197 mm 400mm
Frame rate used 11 fps 5.5 fps
Scatter grid yes no
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