Timothy J. Tredwell, John Yorkston Greg Heiler, Jeff Chang ...ridl.cfd.rit.edu/products/talks/QLID...
Transcript of Timothy J. Tredwell, John Yorkston Greg Heiler, Jeff Chang ...ridl.cfd.rit.edu/products/talks/QLID...
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Imaging Arrays for Medical Applications
Timothy J. Tredwell, John YorkstonGreg Heiler, Jeff Chang, Jackson Lai
Carestream Health
RIT Quantum Limited Detector WorkshopMarch 2009
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Outline
• Introduction to medical imaging modalities• MEV
– PET, SPECT• KEV
– CT, X-Ray• EV
– Molecular Imaging, Endoscopy, NIRS• mEV
– Ultrasound, MRI
• Radiography
• Molecular Imaging
• Applications for Quantum Limited Detectors
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Medical Imaging Modalities
X-ray systems CT MRI SPECT/PET
Ultrasound
Endoscope
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Imaging Sources
X-ray
PET
CTSPECT
functional NIRS
MRI
MEG
Ultrasound
Endoscope
(add THz imaging)
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Morphology ⇔ Physiology ⇔ Metabolism ⇔ MoleculeRadiography
CT
Ultrasound
MRI
PET/SPECT
Optical
TF. Massoud et al. GENES & DEVELOPMENT 2003
10-3-10-5mol/L
10-11-10-12mol/L10-9-10-12mol/L (fluorescence)10-15-10-17mol/L (bioluminescence)
Imaging Targets
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CoincidenceCircuit
Nuclei
+
Positron
ー Electron
+
ー
ー
+
511keV Gamma-ray
511keV Gamma-ray
Imaging MEV PhotonsPET (Positron Emission Tomography)
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Imaging MEV Photons PET (Positron Emission Tomography)
Detector Module
PMT
ScintillatorBismuth GermanateOxide (BGO)
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Imaging MEV Photons SPECT (Single Photon Emission Tomography)
PHA
Digitizer
PC
Pulse Arithmetic Circuit
Gamma ray detector module
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Imaging MEV Photons SPECT (Single Photon Emission Tomography)
Shielding
Light guide
Scintillation crystal
Photomultiplier tube
Optical grease
Al Casing
Collimator
• SPECT identifies regions of abnormal uptake or deficit of a radiotracer
• Often combined with CT for attenuation correction and registration
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Imaging KEV Photons CT (Computer Tomography)
X-ray tube
multi-slice detector• 0.5 – 2 mm detector• ~ 32-256 detectors
First dual-energy systems coming to market
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Imaging KEV Photons CT (Computer Tomography)
Collimator
Scintillator
Photo Diode
X-ray
• Future CT systems may move to flat-panel detectors if the noise can be sufficiently reduced
• Higher resolution (100 µm vs. 500 µm)• Larger area coverage• Allows area detection of entire organs without helical scan• Allows dynamic imaging of organs – such as dynamic
angiography• Being explored by GE and Siemens
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Imaging KEV Photons Radiography
Generator(10 – 100 KEV)
X-Ray Filter(Al)
ScintillatorGRID
Flat panel detector
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(Image courtesy Dr. B. Polischuk, Anrad Corp.)
Imaging KEV Photons: Radiographya-Si:H Flat-Panel Array: Very Large Area
17 inch
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Imaging EV (vis-IR) Photons Endoscope Imaging
objective lens
light guide
forceps hole
nozzle
connectionpart
operationpart
insert part
LCD monitor
videoscope
videoprocessorlight source
camera
printer 26 mm
11 mm
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Imaging EV (vis-IR) Photons Endoscope Imaging
Color Image Sensors for Endoscopic Imaging• Small area• Low power• Highly integrated – few leads• High resolution• Withstand autoclave temperatures• Future - stereoscopic
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Imaging EV (vis-IR) Photons : Molecular ImagingBiomedical Field
R&DPredictionDiagnosisTherapy
Human
DNA Life Science Fields
Medical Fields
Genome
Proteome
Metabolome
Drug DiscoveryProtein
CellCellome
Gene Diagnosis/ Therapy
IntegrationMolecular Imaging
Phisiome
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“MI techniques directly or indirectly monitor and record the spatiotemporal distribution of molecular or cellular processes for biochemical, biologic, diagnostic, or therapeutic applications.”
“Report of a Summit on Molecular Imaging” Radiology 2005
in vivocellular or molecular levelimaging
in vivocellular or molecular levelimaging
CellCell
Molecular ProbeReporterLigand
Molecular Target( Biomarker)
DNA Protein Cell Organ
Molecular Imaging
Imaging EV (vis-IR) Photons Molecular Imaging
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Fluorescence light Filter
Cooled CCD
Mouse
Excitation Wavelength Filter
Excitation light Fiber
White light Source
Excitation light
Fluorescencelight
Fluorescent Probe
PC
Imaging EV (vis-IR) Photons Fluorescence Imaging
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Wavelength (nm)
WaterHb
Opticalwindow
absorption characteristics of hemoglobin and water in human
Imaging EV (vis-IR) Photons: NIRS Optical Absorption Characteristics
Abs
orpt
ion
Rat
e in
Hum
an (
a.u.
)
0
20
40
60
80
100
400 500 600 700 800 900 1000 1100 1200 1300 1400
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Wavelength(nm)
Absorption(cm-1)
Scattering(cm-1)
L1/10(mm)
400 47.00 18.00 0.46
450 36.00 16.00 0.55
500 12.00 13.00 1.06
550 23.00 11.00 0.84
600 9.60 8.90 1.44
650 2.70 7.60 2.93
700 1.50 6.80 4.16
750 1.30 6.50 4.57
810 0.72 5.60 6.62
1 mm↓
1/10
6 mm↓
1/10
Imaging EV (vis-IR) Photons: NIRSOptical Constants and Transparency of Living Subject
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Imaging mEV Photons Magnetic Resonance Imaging (MRI)
X Coil
Y Coil
Z Coil
BB00
SS
NN
zz
xx
yy
SS
NN
Electromagnetic induction current
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Ultrasound Imaging
transducer
packingmaterial acoustic
matchinglayer
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Image FusionPET and CT
PET Only
CT Only
• Anatomy
• Construct density map for absorption correction
Fused Images
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Outline
• Introduction to medical imaging modalities• X-ray, CT, MRI, SPECT, PET, Ultrasound, Endoscope,
NIRS
• Radiography• Introduction to digital radiography• Clinical challenges• Amorphous silicon imaging arrays• LTPS silicon imaging arrays• Silicon imaging arrays
• Molecular Imaging
• Applications for Quantum Limited Detectors
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DR: “Digital” Radiography
DR: 1 step acquisition with electrical “scanning”
“Flat panel” and CCD based technology (introduced ~1995)
(Courtesy Imaging Dynamics Corp.)
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2 Dimensional Projection Radiography
Procedural Volume Trends
-
500
1,000
1,500
2,000
2,500
2001 2002 2003 2004 2005 2006 2007 2008
Proc
edur
es (M
s)
Nuc Med
ULtrasound
MR
CT
Digital X-ray
Analog x-ray
§ Still most common exam
§ >1.5x109 exams per year
§ Chest imaging most common
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CCD Based Systems Fundamental issue with size of CCD
3-4cm
30-40cm
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Multiple CCD Configuration
• SwissRay and Apelem• Reduces de-mag.
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Multiple CMOS Configuration
• CaresBuilt & Star V-Ray• CMOS…. cheap• Stitching an issue !
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Detector Cross-sectionFlat-Panel Detector Construction
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Image courtesy Mr. K. Schwarz, Direct Radiography Corp.
Flat-panel Detector Construction
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System Configuration
X-ray GeneratorSynchronization
Control(enables “Advanced Applications”)
Control PC and PACS
Detector housingGrid and AEC
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Flat-Panel Detector Advantages
§Highest image quality due to high collection effic.
§Inherently digital information§ Allows quantitative analysis of image information§ Allows easy distribution to remote destinations
§One step acquisition of images§ Fast delivery of image§ Improves efficiency of workflow
§Significantly reduced profile & weight
§No geometric/magnetic distortion
§Computer controlled & integrated with x-ray delivery§ Enables advanced applications
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Current Clinical Situation
Flat-Panel Detectors
Megavoltage
MammographyGeneral Rad.
DSA/Fluoro.CardiacReal Time Imaging
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Anatomical Noise
• 3 dim. structure projected into 2 dim.• Overlapping structures obscure clinical details• Anatomical structure noise > x10 detector noise
3-Dim 2-Dim
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Anatomical Noise in Projection Radiography
MammographyChest Radiograph
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wb
IL
IH
Low-Energy Image
High-Energy Image
Bone Image
( ) ( ) ( )Lb
HBone IwII lnlnln +−=
IBone
60-90 kVp
120-150 kVp
Tissue Discrimination: Dual-Energy Imaging
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Tissue Discrimination: Dual-Energy Imaging
IL
IH
wsLow-Energy Image
High-Energy Image
60-90 kVp
120-150 kVp Soft-Tissue Image
( ) ( ) ( )Ls
HSoft IwII lnlnln −=
ISoft
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Dual-Energy Increases Conspicuity of Subtle lesions
(Courtesy: JM Sabol, GE Healthcare and RC Gilkeson, Dept. Radiology Case Western Univ.)
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Spatial Discrimination: Tomosynthesis
Utilizes parallax relative motions between shots
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15 mm nodule
16-degree tube angle, 61 projection images, 5 mm slice spacingTotal tomo exposure ≈ Lateral image exposure (screen film)
(Courtesy: James Dobbins, PhD, Duke University Medical Center)
Chest Tomosynthesis Clinical Example15 mm hilar nodule not visible in projection image
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Flat-panel “Cone Beam” CT
2
2
1 1
3
3
4
4
5
5
6
6
7
7
8
8
Detector
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CBCT Spatial Discrimination
• Isotropic resolution• Patient dose << CT• Some soft tissue vis.
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Pre-Op.
( D. A. Jaffray and J. H. Siewerdsen, Princess Margaret Hospital , University of Toronto )
Intra-Post Op.Evaluation
Needle
PMMA
CBCT Image Guidance
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Advanced Imaging Modality Requirements
Dual Energy Tomo-Synthesis Cone-beam CT
Number of images
2
Total dose 1XDose per image 50%Frame rate ~5 fps
Number of images
~20 -100
Total dose 1X-5XDose per image 10%Frame rate ~5-30fps
Number of images
100’s
Total dose 1X - 10X+Dose per image 1 % – 5 %
Frame rate ~30 fps
2
2
1 1
3
3
4
4
5
5
6
6
7
7
8
8
Detector
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Key Vectors for Radiographic Detector Development
§ 2-D Projection Radiography§ Cost (on-glass electronics, digital lith. & fab-less design)§ Robustness & weight (robust plastic/metal substrates)
§ Advanced Applications (Dual energy and 3D modalities)§ Improved sensitivity (SNR) at low exposure (“smart” pixels)§ Improved spatial resolution (improved x-ray converters)§ High frame-rate readout (on-glass electronics)
Flexible Substrate
(Courtesy Dr. T.Jackson PennState)
On-glass Shift Register
1 mm
Active Pixel Design
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Outline
• Introduction to medical imaging modalities• X-ray, CT, MRI, SPECT, PET, Ultrasound, Endoscope,
NIRS
• Radiography• Introduction to digital radiography• Clinical challenges• Amorphous silicon imaging arrays• LTPS silicon imaging arrays• Silicon Imaging arrays
• Molecular Imaging
• Applications for Quantum Limited Detectors
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DR X-ray detection
Indirect SystemX-ray
Light
Flat-panel Imaging
Array
Direct System
X-ray
+- ++++-
--- α-Se
Photoconductor
Scintillator
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• Structured phosphor improves quantum efficiency
X-Ray Converter
Powdered Phosphor Structured Phosphor (CsI)
• Structured phosphor maintains spatial resolution• Photoconductor internal field functions similarly
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Signal and Noise: Chest Radiograph140 µm pixel dimension
GridScintillator &Detector
Patient
X-ray exposure X-rays to scintillator
Photons from scintillator
Electrons collected
Quantum Noise
Per pixel Per pixel Per pixel Per pixel Per pixel
Outside Chest 142,000 142,000 88,750,000 31,808,000 84,410Ribs 142,000 426 266,250 95,424 4,623Ribs 142,000 426 266,250 95,424 4,623Lungs 142,000 ~ 1,420 887,500 318,080 8,441Mediastinum 142,000 142 88,750 31,808 2,669Heart 142,000 < 142 < 88,750 < 31,808 2,669
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Signal and Noise vs. ExposureProjection radiography: chest
1.E+02
1.E+03
1.E+04
1.E+05
1.E+06
1.E+07
1.E+08
0.001 0.01 0.1 1 10 100Exposure (mR)
Sign
al (e
lec)
& N
oise
(rm
s el
ec) Signal
(electrons)
Quantum Noise
Electronic NoiseMaximumExposure
30 mR
Typ. EntranceExposure
7.2 mRLungs
0.29 mRHeart
0.12 mR
Qua
ntum
Lim
ited
to 0
.02
mR
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Photosensors for Indirect Radiographic DetectorsPIN Photodiodes
ITO
Al bias line
30 nm P+ α-Si
500 nm i α-Si
50 nm N+ α-SiMo electrode
nitride
Advantages• High quantum efficiency• Low dark current• Operated steady-state (no transient)Disadvantages• P+ not widely available – requires
special process capability
Quantum Efficiency• 85% quantum efficiency in green
• QE drops in blue due to absorption in P+
• QE in red decreases due to band edge
+-
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07/10/2008 Carestream Health Restricted Information 54
PIN Photodiode in DR ArraySpectral Quantum Efficiency
350 400 450 500 550 600 650 7000
0.1
0.2
0.3
0.4
0.5
0.6
0.7
0.8
Wavelength (nm)
Qua
ntum
Effi
cien
cy
Primary Array Spectral Quantum Efficiency
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Reducing the interference, reflection lossesOptimization of layer thicknesses
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a-Si Detector ArraysPassive Pixel Design
139 µm pixel
Gateline (M1)
Dataline
(M2)
Bias Line (M
5)
Gateline
Dataline
Bia
s Li
ne
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07/10/2008 Carestream Health Restricted Information 57
Cross-section of Vertically Integrated DR Array
400 nm Nitride
M2 : Data electrode (MoW)
M3 : Mushroom electrode (MoW)
M4 : Top electrode (IZO)
2nd passi : SiNx
p-i-n
1st passivation
M1 : Gate electrode (MoW)
Gate insulator : SiNx
145 nm
388 nm
158 nm
487 nm
130 nm
125 nm
316 nm
395 nm
M5 : Bias electrode
130 nm
Active : a-Si:H
Glass
500 nitride
Gateline: 145 nm MoWDataline: 158 nm MoW
PIN: 500 nm a-Si
Bias Line: 50nm MoW, 200nm AlTop Electrode: 125 nm IZOMushroom electrode: 130 nm MoW
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07/10/2008 Carestream Health Restricted Information 58
ARIA 1 Performance VerificationLinearity (uncorrected)
103 104 105 106 107 108 109103
104
105
106
107
108
Photons per pixel
Ele
ctro
ns p
er P
ixel
Linearity Response, versus Exposure (-3.0V photodiode bias)
Linear over 5 decades of illuminationCharge Capacity = 60M electrons
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Noise in Amorphous silicon passive pixel arrayDataline thermal noise dominates
• Dataline is in Metal 2, gateline in metal 1 with 500 nm inter-layer dielectric
• Dataline thermal noise ~ C*R1/2 is the largest contributor with 9,000 electrons noise
• Next largest noise source is < 2,000 electrons
Baseline
0 2000 4000 6000 8000 10000
Reset
TFT Transient
TFT Shot
PD Shot
Data Line Thermal
Total Noise
e-rms
Dataline thermal noise at 9,000 el dominates
~ C*R1/2
• High M2 dataline resistance• High M1-M2 overlap capacitance
(500 nm nitride)
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Experimental a-Si Passive PixelReduced dataline thermal noise
• 2 µm thick BCB layer or thick nitride dielectric between TFT plane and photosensorplane
• Planarization of topography• Reduced overlap capacitance
• Dataline in metal 5• 500 nm Al for low resistance• 2,000 nm BCB + 400 nm nitride dielectric for reduced overlap capacitance
Dielectric
0.6 µm PIN diode
TFT
2 µm BCB between TFT & photosensor
Dataline in low-resistance Metal
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Experimental a-Si Passive Pixel3X Noise Reduction in Passive a-Si Arrays
0 2000 4000 6000 8000 10000
Reset
TFT Shot
PD Shot
Data Line Thermal
Total Noise
e - r ms
New Design 2 um BCB
New Design500 nm Si02
Baseline
• ~40% Reduction in CDL
• ~90% Reduction in RDL
• 4X reduction in data line thermal noise
4X DL noise reduction
3X overall noise reduction
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Advanced a-Si arraysActive pixel designs
• Advantages• Noise Reduction: Dataline thermal noise reduced by charge gain of pixel amplifier (>10X)• Speed Increase: 10X or more reduction in dataline setting time due to active amplifier
• Disadvantages• Yield: 9X increase in transistor area and ~ 3 additional bias and clock lines• Linearity: Smaller linear range of output vs. exposure• Stability: TFT threshold voltage shift with aging – TFT is amplifier, not a switch
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Amorphous Silicon Shift Register for Active Pixel Array120 um pitch a-Si:H shift register
Time (ms)0.0 0.5 1.0 1.5 2.0
Out
put V
olta
ge (V
)
-5
0
5
10
15
20
25
30Input
1st output2nd output
3rd output
4th output
13th output
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Advanced a-Si arraysActive pixel designs
• Dataline thermal noise reduced 5X by charge gain of pixel amplifier
• External amplifier noise reduced 5X by charge gain of pixel amplifier
• Largest remaining noise source is reset noise of the photodiode – can be further reduced by thicker intrinsic amorphous silicon
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07/10/2008 Carestream Health Restricted Information 65
Fabrication of DR Array on Metal Foil
Laminate to Glass
BeforePlanarization
After BCBPlanarization
Planarize
Fabricate ArrayRelease
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PIN photodiodes on stainless steel substratesComparison of 280 C PIN diodes on glass and on free-standing Stainless foil
JD(-1V) = 36 pA/cm2 JD(-1V) = 47 pA/cm2
280 C PIN on Glass 280 C PIN on StainlessPIN Diodes on Stainless
125 µm stainless foil3 µm BCB planarization
8 nm rms roughness
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Outline
• Introduction to medical imaging modalities• X-ray, CT, MRI, SPECT, PET, Ultrasound, Endoscope,
NIRS
• Radiography• Introduction to digital radiography• Clinical challenges• Amorphous silicon imaging arrays• LTPS silicon imaging arrays• Silicon imaging arrays
• Molecular Imaging
• Applications for Quantum Limited Detectors
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LTPS imaging array with peripheral circuits
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LTPS imaging array with peripheral circuitsPMOS LTPS Shift Register
Start (n) CLK 3 CLK 1
Output (n+1)
4 / 4 +4 um
4 / 4+4 um
4 / 4 +4 um
4/ 4 +4 um
0.09 pF
4 / 4 um
4 / 4 um
16 / 4 um
4 / 4 um
NextInput
VDD
T1
T2
T3
T4
T5
T6
T7
T8
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Pixel of LTPS Imaging Array with a-Si PIN photodiode
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Key Challenges for LTPS Imaging ArraysReset TFT leakage current: siphons off photo-charge
Photocurrent
TFT LeakageCurrent
IDS(VDS, T)
Net ChargeVDS
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Sources of Leakage in LTPS TFT’s
• Surface topography at grain boundary edges causes gate oxide leakage
• Variable from TFT to TFT
• Generation current at grain boundaries results in TFT leakage
• Gate-to-drain field enhances leakage current, resulting in exponential increase in leakage with gate voltage, even band-band tunneling
• Variable from TFT to TFT
TFT Channel Leakage At Grain Boundaries
Gate Oxide Leakage at Grain Boundaries
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Key Challenges for LTPS Imaging ArraysThreshold voltage variability
Current Mirror Column Amplifier TFT
Pixel Amplifier TFT
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Noise in LTPS Imaging Arrays
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SummaryDirections for radiographic detector development
• 2-D Projection Radiography
• Robustness, weight Detector arrays on metal foil & plastic
• Cost Fabless model (utilize display fabs)
• Advanced Applications (Dual energy and 3D)
• Improved sensitivity Improved passive pixel designsActive pixel a-Si arraysActive pixel LTPS
• Improved resolution Structured phosphorsDirect detectionActive pixel LTPS with peripheral circuits
• High frame rate Active pixel a-Si arraysActive pixel LTPS
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Outline
• Introduction to medical imaging modalities• X-ray, CT, MRI, SPECT, PET, Ultrasound, Endoscope,
NIRS
• Radiography• Introduction to digital radiography• Clinical challenges• Amorphous silicon imaging arrays• LTPS silicon imaging arrays• Silicon Imaging arrays
• Molecular Imaging
• Applications for Quantum Limited Detectors
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Carestream Dental Array
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Typical characteristics of CMOS Imagers for Dental
5,000:1Dynamic range50 - 100 rms electronsNoise~ 500K electronsSaturation charge40%Fill factor~ 50% at 550 nmQuantum Efficiency1,440 x 1,920Pixels~ 27mm x 36mmArray size18 µmPixel dimension
Typical valuesParameter
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Noise in CMOS Image Sensors
Barbato Pain, ISSCC 2007 Imager Forum
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Photodiodes for CMOS image sensorsP-N junction and Pinned Photodiode
P-N Junction Photodiode Pinned Photodiode
Barbato Pain, ISSCC 2007 Imager Forum
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Noise in small-pixel CMOS image sensors
Barbato Pain, ISSCC 2007 Imager Forum
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Photon Counting Arrays for Medical ImagingMedipix Project
• Collaborative European program
• Goal is to develop a photon-counting CMOS-Si backplane modules
• Interconnect to a variety of sensor chips• Bump-bonded to CdTe and CdZnTe• GaAs• Si
• 4-side tiling for large-area detector arrays
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Photon Counting Arrays for Medical ImagingMedipix 2 and Medipix 3 chip
• Medipix 2• 55 µm square pixels can accept positive
or negative charge• 256x256 array for a 14mm x 14mm
image area• 3-side buttable• Adjustable upper and lower detection
thresholds• 13-bit counter in each pixel• Up to 100 kHz count rates
• Medipix 3• 4-side buttable with 55 µm pixels • 2 counters per pixel (for simultaneous
read-write)• Dual-energy mode with two threshold
levels• Can operate either in photon counting or
in integration mode
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Comparison of Medical Imaging Array Technologies
Flat PanelSilicon
Radiography
Molecular Imaging?
Dental
Molecular Imaging
Endoscopy
Molecular ImagingMedical Applications
1,000-5,000 el100-500 el5-100 el1 elNoise
70% with a-Si PIN70% 70% * gainQuantum Efficiency
40-400 µm40-400 µm2-40 µm200 µmPixel dimension
$ 0.50/in2$ 1.00/in2$ 40.00/in2> $ 200.00/in2Cost/area
14” - > 25”4” – 14”< 1” typical
~ 4” max
0.5”Imager Area
A-SiLTPSIntegratingPhoton counting
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Outline
• Introduction to medical imaging modalities• X-ray, CT, MRI, SPECT, PET, Ultrasound, Endoscope,
NIRS
• Radiography• Introduction to digital radiography• Clinical challenges• Amorphous silicon imaging arrays• LTPS silicon imaging arrays• Silicon Imaging Arrays
• Molecular Imaging
• Applications for Quantum Limited Detectors
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“MI techniques directly or indirectly monitor and record the spatiotemporal distribution of molecular or cellular processes for biochemical, biologic, diagnostic, or therapeutic applications.”
“Report of a Summit on Molecular Imaging” Radiology 2005
in vivocellular or molecular levelimaging
in vivocellular or molecular levelimaging
CellCell
Molecular ProbeReporterLigand
Molecular Target( Biomarker)
DNA Protein Cell Organ
Molecular Imaging
Molecular Imaging
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Fluorescence light Filter
Cooled CCD
Excitation Wavelength Filter
Excitation light Fiber
White light Source
Excitation light
Fluorescencelight PC
Fluorescence Imaging
Microwell Plate
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89
Typical photon flux in the range of 10³–10⁶ph/mm²/sec
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Detection with cooled CCD cameras
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Light Collection Efficiency ~ NA/(m2+1) is < 1%NA = Numerical Aperturem = demagnification
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Sample amorphous silicon molecular imaging array
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PD FF > 70%
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Comparison Between Optical and Contact Type Sensors
Cooled CCD a–Si:H Contact Sensors
Throughput• Multiple shots may be required per sample plate.
• Slower sensor, but can whole plate is imaged at once.
Cost
• Higher cost per unit area for sensor.• More complex mechanical assembly.• May require cooling equipment depending on application.
• Lower sensor cost with volume.• May be viable as disposables.• Low dark current at room temperature.• No optical lens assembly.
Efficiency
• High loss through optical assembly (over 99% loss)
• Higher optical coupling efficiency (over 80%) and lower cross talk.• Higher QE for common dye wavelength.• Charge loss through trapping in defects.
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Fluorescence light Filter
Cooled CCD
Mouse
Excitation Wavelength Filter
Excitation light Fiber
White light Source
Excitation light
Fluorescencelight
Fluorescent Probe
PC
In-Vivo Fluorescence Imaging
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Fluorescence Imaging of Tumor-bearing Mouse
A
B
C
E
D
A B C D E
ICG-labeled Nano-particle
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Avalanche photodiode array for fluorescence imaging
F. Borghetti et. Al., A CMOS Single-Photon Avalanche Diode Sensor for Fluorescence Lifetime Imaging2007 International Image Sensor Workshop
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Avalanche photodiode array for fluorescence imaging
150 ps time resolution
F. Borghetti et. Al., A CMOS Single-Photon Avalanche Diode Sensor for Fluorescence Lifetime Imaging2007 International Image Sensor Workshop
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Avalanche photodiode array for fluorescence imagingPhoton detection probability and sensitivity
F. Borghetti et. Al., A CMOS Single-Photon Avalanche Diode Sensor for Fluorescence Lifetime Imaging2007 International Image Sensor Workshop
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Outline
• Introduction to medical imaging modalities• X-ray, CT, MRI, SPECT, PET, Ultrasound, Endoscope,
NIRS
• Radiography• Introduction to digital radiography• Clinical challenges• Amorphous silicon imaging arrays• LTPS silicon imaging arrays• Silicon imaging arrays
• Molecular Imaging
• Applications for Quantum Limited Detectors
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Accelerating Basic Research/Drug Development
PET CT Optical
Small Animal Imaging System for Preclinical Research
in vivo test using molecular imaging
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Outline
• Introduction to medical imaging modalities• X-ray, CT, MRI, SPECT, PET, Ultrasound, Endoscope,
NIRS
• Radiography• Introduction to digital radiography• Clinical challenges• Amorphous silicon imaging arrays• LTPS silicon imaging arrays• Silicon imaging arrays
• Molecular Imaging
• Applications for Quantum Limited Detectors
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Light Sources Description Advantages Disadvantages
Gas Laser
■ Electric current is discharged through gas to produce light
■ Helium-Neon, 635nm
■ Commonly available■ Available in specific
wavelengths
■ Large, hot, and fragile
Solid-state and Semiconductor
Laser
■ A laser that uses a solid crystal as the gain medium
■ Fixed wavelength■ Yttrium Aluminium
Garnet (YAG), 532nm
■ Small, efficient, and controllable
■ Long life
■ Wavelength choices are restricted to a limited set
White Light Source
■ Xenon arc light source■ Range of wavelengths
from 350nm to 750nm or more
■ Single source is adequate for multiple excitations
■ Large, hot and fragile
■ Needs filters to isolate wavelengths
■ Lower intensity than laser source
Excitation Sources
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Excitation Strategies
Excitation Strategy Description Advantages Disadvantages
Simultaneous Excitation
■ Light sources excite multiple dyes in the same pixel at the same time
■ Increased scanning speed
■ Increased crosstalk■ Reduced SNR
Pixel Shifting
■ Light sources excite multiple dyes at different pixels at the same time
■ Reduced crosstalk■ Increased SNR
■ Misalignment■ Require image
registration
Fiber Optics
■ Fiber optic cables direct light from external light source to scanning optics
■ Allow large lasers and alternative light sources
■ Reduced optical power delivery
■ Reduced resolution
Gated Laser
■ Light sources are toggled■ One light source excite
one pixel at a given time
■ Laser lifetime extended
■ Eliminated crosstalk
■ Reduced scanning speed