1
Seite 1
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 1Master‘s Program in Medical Physics
Chair in Computer Assisted Clinical MedicineFaculty of Medicine Mannheim University of HeidelbergTheodor-Kutzer-Ufer 1-3D-68167 Mannheim, GermanyLothar.Schad@MedMa.Uni-Heidelberg.dewww.ma.uni-heidelberg.de/inst/cbtm/ckm/
Physics of Imaging Systems
Basic Principles of X-Ray Diagnostic II
Prof. Dr. Lothar Schad
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 2
source: Morneburg. “Bildgebende Systeme für die medizinische Diagnostik” 1995
Anode MaterialFixed Anode Turning Anode Ele-
ment
Atomic
number Z
Max. Temperature Tmax
at 1,33×10-2 Pa
°C
Thermal
Conductivity λ
W/(cm K)
Q-Factor
Order
c: Specific Heat
Q-Factor
Order
Cu 29 1032 3,98 119113 8 3,68 110135 10
Mo 42 2167 1,38 125599 7 1,88 171106 8
Ag 47 832 4,18 163450 4 3,18 124350 9
Ta 73 2587 0,55 103868 9 1,13 213402 6
W 74 2757 1,3 265223 1 1,81 369273 1
Re 75 2557 0,71 136160 6 1,38 264650 4
Os 76 2280 0,87 150754 5 1,77 306706 3
Ir 77 2220 1,46 249572 3 2,06 352136 2
Pt 78 1742 0,71 96472 10 1,41 191585 7
Au 79 (1063) 3,14 263687 2 2,81 235975 5
U 92 (1132) 0,25 26036 11 0,75 78108 11
cTZ ⋅⋅⋅⋅ ρλmaxλ⋅⋅ maxTZ c⋅⋅ρλ
2
Seite 2
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 3
construction of turning anode
double angle anode
sliding-contact bearing(lubrication solvent: fluid metal In-Ga-Sn)
source: Dössel. “Bildgebende Verfahren in der Medizin” 2000
Anode Constructiontungsten-rhenium molybdenum graphite
- molybdenum: √λρc = 1.88 > 1.81 (tungsten)- graphite: cgr = 10 cW- material combination allows 106 Ws = 10 s at 100 kW !
high powerlow power
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 4
source: Morneburg. “Bildgebende Systeme für die medizinische Diagnostik” 1995
t time for one rotation (= 1/f)A focus area (2δl)f rotating frequencyλ thermal conductivityρ densityc specific heat
Turning Anode: Geometry
focal spot
3
Seite 3
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 5
source: H. Morneburg. “Bildgebende Systeme für die medizinische Diagnostik”, 1995
Turning Anode: Temperature Increase
basic temperature
ring temperature
focus spot temperature
number of rotations
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 6
source: Morneburg. “Bildgebende Systeme für die medizinische Diagnostik” 1995
Turning Anode: One Rotation Temperature
anode temperature ϑ
depth coordinate z
focal spot
maximum temperature ϑm (z)
4
Seite 4
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 7
source: Morneburg. “Bildgebende Systeme für die medizinische Diagnostik” 1995
High-Frequency Generator
- constant voltage over time (< 10 - 20%, for CT < 2%)- control of voltage by triodes (ideal: < 0.1% variation → expensive
band pass filterU1/U2 = - N2/N1
data transferto other
componentsof X-ray system
inverter
heating
turning anodestarter
X-ray tube
voltageregulation
datalink
mAsswitch
datacontrol
controlconsole
service exposureunit
electricitynetwork
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 8
source: Morneburg. “Bildgebende Systeme für die medizinische Diagnostik” 1995
Generator Variation of Applied Dose: ΔD
10-20% for film/foil-combination3-7 % for Kino2-4 % for DSA
∫ ⋅=At
dttIQ0
)(
thyristor timing
imaging time tiexposure time te(IEC/DIN 0750)
single exposure time ts
“on” “off”shoot
chosenQref
Uref
5
Seite 5
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 9
source: Morneburg. “Bildgebende Systeme für die medizinische Diagnostik” 1995
focus spot 0.6 mm40 kW150 Hz
IA as a function of loading time tfor different UA
(for preheated anode with 300 W)
Turning Anode: Maximum Loading
- typical loading curve for turninganode
- max. mAs-product for given UA- switch-off at max. mAs to avoidoverheating !
anode current IA
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 10
source: Dössel. “Bildgebende Verfahren in der Medizin” 2000
- “generator with fixed current” creates a constantcurrent and switch-off after reaching the requested dose or the loading limit(max. mAs-product)
- “generator with falling load”starts with large current whichdecreases during exposureleading to minimized exposuretime and wrong exposed films
Generator with “Falling Load”
generator with falling load
generator with fixed load
loading limit
6
Seite 6
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 11
- components:
• X-ray tube• high-voltage generator• patient couch• dose measuring unit• scatter grid• film/foil cassette• operator console• film developing system• accumulator foilswhen using digital X-ray imagingwith laser readout unit
Complete X-Ray GeneratorX-ray tube
collimator system
radiation protection box
X-ray film cassette
bodyobject
used radiation cone
mirror forlight field
bulb forlight field
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 12Examples
7
Seite 7
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 13
1 X-ray tube2 X-ray collimator3 lead shielding to protect
patient’s non exposed body4 patient couch with low Z5 monitor6 electronic image intensifier7 TV tube8 lead glasses with lateral
protection9 lead thyroid protection10 lead whole body protection11 lead-lamellae to protect
examiners
1
2
3
4
5
6
7
8
9
10
11
source: BfS 2003
Urological X-Ray Examination
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 14
X-Ray Imaging
X-Ray Imaging
8
Seite 8
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 15
- double-sided X-ray film (cross section)
emulsion: suspension of silver/bromine crystals in gelatinesupporting layer: flexible polyester or cellulose acetate
source: Laubenberger and Laubenberger. „Technik der medizinischen Radiologie“, Deutscher Ärzte-Verlag 1999
X-Ray Film: Schema
polyester foil
cover
emulsion
undercoating
emulsion
cover
undercoating
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 16X-Ray Film: Chemistry
film emulsion of AgBr:
- light:AgBr reduction to Ag and Br
- development:Ag atoms grow to small μm grains
- fixation:remove AgBr by appropriate solution
Br + hυ → Br + e-
Ag+ + e- → Ag
problem:- low absorption of emulsion !- emulsion on both sides of film → crossover: unsharp image on second side of film
9
Seite 9
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 17
source: Biehl and Zier. „Röntgenstrahlen - ihre Anwendung in Medizin und Technik“, Leipzig 1980
- optical dense S = grade of film darkening
- gradient of density curve= γ-valueγ large: large contrast at
low dose γ small: modest contrast but
large dose range
- at linearity:μ >> film bright (bones)μ << film dark (air)
X-Ray Film: Density Curve
optical dense
object coverage
dark
enin
g co
vera
ge
shoulder
solarization
fog linea
r par
t of c
urve
(opt
imal
exp
osur
e)
log (light intensity)or dose ~ μd
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 18
only about 1% of the intrinsic X-ray photons are absorbed by the film emulsion !
problem
darkening at position of a developed film depends on the number of free silver atoms and therefore depends on the number of X-ray
photons which have been absorbed at this position
X-ray film alone is not practical for medical applications !
X-Ray Film: Problem
10
Seite 10
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 19
source: Dössel. “Bildgebende Verfahren in der Medizin” 2000
excitation and light emission in accumulator foils (energy level schema)
Accumulator Foils
- store X-ray information in foil- electrons are excited from valence to conduction band creating e-/hole-pairs- recombination of e-/hole-pairs by laser → stimulated luminescence- readout foil and directly convert digitally- foil handling like X-ray film (no new mechanical construction necessary)
light emission
valence band
conduction band
excitationX-ray
centers of light
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 20
solid state material: energy band representation
Solid State Material I
- electrons can be in energy levels of an atomdiscrete: single atom; continuous: solid state material
- valence band: filled with electrons; conduction band: emptyoften: energy state between both bands forbidden → isolator
- impurities in the solid state material can produce energy levels in the forbidden area
11
Seite 11
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 21Solid State Material II
- by activation (energy larger than the difference between valence and conductingband) electrons can be moved from valence band to the conducting band
- when the electron is removed, a hole (positive) is appearing at electron´s position- holes behave like electrons but with positive charge- hole filled by neighboring electron, hole moves to that position- efficiency: 20 – 50%- 97% efficiency of absorption of generated light- reduction of radiation by factor of 10 – 20- shorter radiation time with less motion artifacts- smaller focus spot → higher resolution- material choice: high X-ray absorption, high conversion efficiency into visible light- total efficiency: product of absorption and conversion efficiency
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 22
X-ray film cassette with accumulator foil
conversion of X-ray radiation into visible light and subsequent detection using film → luminescence
luminescent substances: calcium / tungsten (CaWO4)lanthanum / bromide endowed with terbium (LaOBr:Tb)gadolinium / sulfur endowed with terbium (Gd2O2S:Tb)
source: Laubenberger and Laubenberger. „Technik der medizinischen Radiologie“, Deutscher Ärzte-Verlag 1999
Accumulator Foils: Material
cassette front
front foilfilmback foilfoamcassette backwith lead
12
Seite 12
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 23
• luminescence layer can have a much larger X-ray attenuation factor than the emulsion layer; luminescence layer can contain elements with large atomic number Z and large density ρ
• luminescence layer can be much thicker than emulsion layer because luminescence layer will not be developed or fixed
• luminescence layer can create from one X-ray quantum many visible photons
example: 100 keV-quantum is absorbed by 100 % and converted by 100 % intovisible light at 550 nm (2.26 eV) → 44.000 visible photons !
Accumulator Foils: Advantages
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 24
- quality criteria for accumulator foils:- high absorption for X-rays- high light efficiency and quantum yield- good adaptation of light emission spectrum
to film sensibility for dose reduction
- result: low radiation exposure, short exposure times, minimization ofmovement artifacts, small focus spot of the tube, large image contrast
Accumulator Foils: Quality
(for same film darkening)
- amplifying factor V of accumulator foil:
V =
typical values: V = 10 - 20
dose with accumulator foildose without accumulator foil
13
Seite 13
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 25
accumulator foils X-ray absorption in a 100 µm foil at:
40 keV 60 keV 80 keV
efficiency of light emission
% % % %
CaWO4 33 13 27 4
LaOBr:Tb 73 33 17 13
Gd2O2S:Tb 37 51 28 19
source: Morneburg. “Bildgebende Systeme für die medizinische Diagnostik” 1995
important for dose !
Accumulator Foils: Absorption Conversion
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 26
- mass absorption coefficient μ/ρ of different light emission materials as a function of X-ray energy
- Gd2O2S:Tb best material withcharacteristic K-line at 50 keV fits wellto the spectral distribution of diagnostic X-ray radiation
source: Morneburg. “Bildgebende Systeme für die medizinische Diagnostik” 1995
Mass Absorption Coefficient
energy of X-ray quants
relative spectraldistributionof X-ray radiation
14
Seite 14
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 27
source: Dössel. “Bildgebende Verfahren in der Medizin” 2000
Spectral Light Emission
wavelength
intensity of light emission
X-ray film blue-sensitive
X-ray filmgreen-sensitive
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 28
source: Dössel. “Bildgebende Verfahren in der Medizin” 2000
- scattered light:radiation of fluorescence lightin all directions
- “cross over” effect:fluorescence light penetratesfilm base layer and developsthe foil at backside emulsionof the film
Image Blurring and Foil Thickness
thin foil
filmbaselayer
emulsion
foil
thick foil
foil
emulsion
reflection effect
“cross over” effect
15
Seite 15
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 29
X-ray imaging using accumulator foils(semi-conductor foil using “heavy metal halogenide phosphor” compound)
→ was the first step to “digital radiology”
conversion from light centers to ground state is “optically forbidden”
light centers stay excited
source: Dössel. “Bildgebende Verfahren in der Medizin” 2000
Accumulator / Storage Foils: Readout
accumulator foil is transported in a light-proofed cassette from the X-ray unitto the readout system
1. exposure
4. delete and regenerate
3. readout
2. storage
conducting band
valence band
light centers
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 30
scanning of the stored image by a laser with very small focus
wavelength of the laser is adapted to the stimulation of the light centers
detection of emitted light using a photomultiplier
photomultiplier signal is digitized line-by-line and stored in a digital image
→ digital luminescence
source: Dössel. “Bildgebende Verfahren in der Medizin” 2000
Accumulator / Storage Foils: Laser Scanner
accumulator foil
photomultiplier
color filter
deflection mirrorlaser
16
Seite 16
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 31
source: Laubenberger and Laubenberger. „Technik der medizinischen Radiologie“, Deutscher Ärzte-Verlag 1999
Digital Luminescence Radiography (DLR)
cassette
image data
foil depot
semi-conductor
foil
image readout delete station
light sources
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 32
linear characteristic curve over 5 to 8 order of magnitudes !
source: Dössel. “Bildgebende Verfahren in der Medizin” 2000
Signal / Dose Relation
filmdarkening
luminescent material
film / accumulator foil
17
Seite 17
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 33
• digital image, i.e. data processing with computer possible
• not sensitive to wrong film development because of the large dynamic range
• linear characteristic line
DLR Advantage
RUPRECHT-KARLS-UNIVERSITY HEIDELBERG
Computer Assisted Clinical MedicineProf. Dr. Lothar Schad
12/9/2008 | Page 34
X-ray beam
readout ICsline driver ICs
detector area:43 cm x 43 cm
pixel size:143 µm
resolution:3.5 LP/mm
Direct Digital Solid State Detector: CsI, aSiX-ray radiation
photocathode
- future: CCD (charge coupled devices)