Dual Energy Radiography
Dual Energy Imaging with Dual Source CT Systems Rainer Raupach, PhD Siemens Healthcare
[email protected] Radiograph
Bone image 2 energies
Tissue image
2 materials
Armato SG III. Experimental Lung Research. 2004;30 (suppl 1):72-77.
kV Switching with SOMATOM DRH – in the 80s Calculation of material selective images: Calcium and soft tissue
Principle of Dual Energy CT Data acquisition with different X-ray spectra: 80 kV / 140 kV
Standard image
Rapid kVp switching
Mean Energy: Calcium image
56 kV
76 kV
Basis material decomposition
Low kVp
Tube 1 Soft tissue image
Tube 2
High kVp
Attenuation profiles
Different mean energies of the X-ray quanta
W. Kalender: Vertebral Bone Mineral Analysis, Radiology 164:419-423 (1987)
1
SOMATOM Definition The World’s First Dual Source CT
Principle of Dual Energy CT Many materials show different attenuation at different mean energies
Faster than Every Beating Heart 1.0E+02
gated mode / same kV high temporal resolution (80ms) Cardiac imaging
Iodine Bone
Attenuation
56 kV 76 kV 1.0E+01 Large increase
One-Stop Diagnosis in Acute Care non gated mode / same kV low temporal resolution Obese patients, low kV scanning
1.0E+00 Small increase 1.0E-01 10
30
50
70 90 Energy / keV
110
130
Beyond Visualization with Dual Energy
150
different kV (gated and non-gated)
Reason: different attenuation mechanisms (Compton vs photo effect)
“Contrast Enhanced Viewing” using Dual Energy Information in Addition to Simple Image Mixing
Spectra of Dual Energy Applications
Basic application: Enhanced viewing, contrast optimization Contrast enhanced studies: Iodine has much higher contrast at 80 kV Non-linear, attenuation-dependent blending of the images combines benefits of 80 kV (high contrast) and mixed data (low noise) Direct Angio
Lung PBV
Virtual Unenhanced
Lung Vessels
140 kV
Hardplaque Display
Heart PBV
Musculoskeletal
Gout
Calculi Characterization
Lung Nodules* *510(k) approved
80 kV
Blending
Brain Hemorrhage
Xenon* Courtesy of CIC Mayo Clinic Rochester, MN, USA
2
syngo Dual Energy Direct subtraction of bone
syngo Dual Energy Direct subtraction of bone Modified 2-material decomposition: Separation of two materials Assume mixture of blood + iodine (unknown density) and bone marrow + bone (unknown density) Separation line 600
Iodine pixels
Bone 550 HU
HU at 80 kV
500 400
Automatic bone removal without user interaction Clinical benefits in complicated anatomical situations: Base of the skull Carotid arteries Vertebral arteries Peripheral runoffs
Bone pixels
Blood+iodine
80kV
Marrow+bone
300
Iodine 425 HU
Modified 2-material decomposition: Separation of bone and Iodine
200 100
Soft tissue
0 -100 -100
Bone 400 HU
Blood Marrow
Iodine 250 HU
140kV 0
100
200 300 HU at 140 kV
400
500
600
syngoDualEnergy Differentiation between hard plaques and contrast agent
Courtesy of Prof. Pasovic, University Hospital of Krakow, Poland
Image Based Methods Modified 2-material decomposition: Characterization of kidney stones Urine + calcified stones / uric acid stones
HU at 80 kV
high Z
low Z
HU at 140 kV
Courtesy of CCM Monaco, Monaco
3
syngo Dual Energy Musculoskeletal Visualization of tendons
syngo Dual Energy Visualization of Tendons: Tibialis posterior tendon rupture SOMATOM Definition World’s first DSCT Spatial Res. 0.33 mm Rotation 0.5 sec Scan time: 4 s Scan length: 133 mm 140/80 kV Eff mAs 80/150 Spiral Dual Energy
Courtesy of University Medical Center Grosshadern / Munich, Germany
Courtesy of University Medical Center Grosshadern / Munich, Germany
Applications of Dual Energy CT
Gout: Application
Three material decomposition: quantification of iodine – iodine image
HU at 80 kV
Iodine
Iodine content
65
Tissue
0
-100
Fat -90
0
60
HU at 140 kV
Vancouver General Hospital, Canada
Removal of iodine from the image: virtual non-contrast image
4
Image Based Methods
Applications of Dual Energy CT
Most promising application: 3-material decomposition Calculation of a virtual non-contrast image, Iodine quantification
Virtual non-contrast image and iodine image: Characterization of liver / kidney / lung tumors Solve ambiguity: low fat content or iodine-uptake Quantify iodine-uptake in the tumor and at the tumor surface Differentiation benign - malignant Monitoring of therapy response Mixed image
Mixed image 80kV+140kV
Virtual unenhanced image
VNC image
Iodine image
Iodine overlay image
+
Courtesy of University Hospital of Munich - Grosshadern / Munich, Germany
SOMATOM Definition Flash Latest Generation of Dual Energy CT
Applications of Dual Energy CT Quantification of iodine to visualize perfusion defects in the lung Avoids registration problems of non-dual energy subtraction methods 80/140kV Mixed Image
Iodine Image
Mixed image + iodine overlay
System Design Two X-ray tubes at 95°, each with 100 kW
33 cm
Two 128-slice detectors, each with 64x0.6mm collimation and z-flying focal spot Embolus
SFOV A/B-detector: 50/33 cm 0.28 s gantry rotation time 75 ms temporal resolution
Courtesy of Prof. J and M Remy, Hopital Calmette, Lille, France
5
Dual Energy Imaging with Tin Filtration ‘Definition’ vs. ‘Definition Flash’: Improved DE Signal
SOMATOM Definition Flash Single dose Dual Energy
Mixed Images
80 kV 140 kV overlap
VNC
Iodine
DE Images
Definition
Conventional DE
DSCT Dual Energy DE with Selective Photon Shield
80 kV 140 kV with SPS overlap
Tissue characterization Improved DE contrast Dose-neutral compared to a single 120 kV scan
Definition Flash
DE with Selective Photon Shield
SD and dose: equal
SD: -25%
Images acquired and processed in collaboration with CIC Mayo Clinic Rochester, USA
SOMATOM Definition Flash Impact of the Selective Photon Shield
SOMATOM Definition Flash Image Dual Energy Whole Body CTA: 100/140Sn kV @ 0.6mm
Dose neutral DE: comparison of 120 kV and 100 kV/140 kV+0.4 mm Sn Single DE CT Scan
120kV, 500mA
100/140Sn kV, 500mA
noise: 14.1 HU
noise: 13.9 HU
iodine: 329.0 HU
iodine: 330.0 HU
bone: 334.8 HU
bone: 335.3 HU
Courtesy of Friedrich-Alexander University Erlangen-Nuremberg - Institute of Medical Physics / Erlangen, Germany
6
Dual Energy CT
New Application Classes
Are there alternative approaches? 40 keV
Sequential acquisition at 80 kV and 140 kV with single source CT Registration problems (heart/lung motion, varying contrast density) Fast kVp-switching during the scan with single source CT Inadequate power at low kV Unequal noise for low and high kV data Measurement of Lung Nodule enhancement courtesy of ASAN Medical Center, Seoul, Korea
Measurement of Xenon Concentration
190 keV
Spectral sensitive „sandwich“ detectors Inferior spectral separation
courtesy of ASAN Medical Center, Seoul, Korea
Mono-energetic imaging courtesy of Klinikum Großhadern, Munich, Germany
Dual Energy CT Evaluation of alternative approaches
Quantum counting Paralysis at high flux rate Spectral overlap by fluorescence and pile-up
Dual Energy CT Evaluation of alternative approaches
dual−source (tin filter) dual−source (std. filter) sequential kVp dual−layer (GOS) dual−layer (CsI) dual−layer (ZnSe) quantum counting (CZT)
1.6 1.4
DE Performance @ equal dose
relative DEC²
1.2 1 0.8 0.6 0.4
Dose
0.2 0 15
20
25 30 35 phantom diameter [cm]
40
45
S. Kappler et al., Dual-energy performance of dual-kVp in comparison to dual-layer and quantum-counting CT system concepts, Proceedings of the SPIE Medical Imaging Conference, Volume 7258, pp. 725842 (2009)
7
Thank you!
8