1) CT dose index (CTDI) measures radiation output of CT scanners. Modern measures include CTDI100, CTDIvol, and dose length product (DLP).
2) Automatic exposure control (AEC) modulates tube current based on patient attenuation to maintain consistent image quality while reducing dose.
3) Dose reduction techniques in CT include AEC, bowtie filters, iterative reconstruction, prospective gating, and dynamic collimation.
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2. Introduction to presentation
CT Dose Index
CTDI100
CTDIvol
DLP
Effective dose
CT dose reduction techniques
AEC
Filter
Reconstruction
3. CT Dose Index
CT dose index (CTDI) is the standardized
measure of the radiation output of a CT system,
Currently used measures are the CTDI100 and
CTDIw, modified to CTDIvol for modern helical
scanners.
6. Measurement of CTDI
• Ionisation pencil chamber
– Air-filled chamber
– X-rays cause ionisations in
chamber, causing current to
flow, proportional to exposure
– Instant readings, good
accuracy, easy to use
100 mm
7. Measurement of CTDI
• Single slice measurement
(z-axis)
Dose
T
Nominal
beam width
( )dzzD
T
1
CTDI
-
∫
+∞
∞
=
( )dzzD
T
1
CTDI
50
50-
100
∫
+
=
-50 +50
∫
+
−
=
50
50
D(z)dz
n.T
1
CTDI100
n = no. slices imaged simultaneously
T = nominal imaged width
Davge
T
100Davge
CTDI100
×
=
8. CTDI100
• CTDI100 is a measure of radiation dose on a 100mm
long pencil ionization chamber.
• Centre
• Periphery - 1 cm depth
(mean of 4 positions)
C
P1
P2
P3
P4
320 mm
‘Body’
‘Head’
160 mm
140
mm
9. Measurement of MSAD(Multiple Scan
Average Dose)
CTDI ≈ ‘Series’ dose
Multi-scan
‘Series’ dose
CTDI×
×
=
I
TN
MSAD
T
T is the nominal scan width (mm)
I is the distance between scans (mm)
I
N is the number of scans
N × T is the total nominal scan width
10. CTDI100
• Typical CTDI100 values (mGy)
40
Head
Body
40
4040
40
20
2020
20
10
Periphery : centre ≅ 1:1 Periphery : centre ≅ 2:1
11. Derivatives of CTDI100
• CTDIW
• Weighted average CTDI: represents the average
dose for contiguous irradiation
• CTDIw = 1/3 CTDI100,C + 2/3 CTDI100,P
CTDIC CTDIP
12. Derivatives of CTDI100
• CTDI100 & CTDIw refer to a pitch of 1
• Average absorbed dose dependent on pitch
Contiguous Extended Overlapping
14. Radiation risk: DLP
• CTDIvol is a measure of absorbed dose, energy
absorbed per unit mass
• To measure radiation risk from stochastic effects
the total energy absorbed must be considered
• In CT this can be estimated using the Dose Length
Product, DLP
15. DLP = CTDIvol . L (mGy.cm)
DLP1 ≅ DLP2
where L = scan length
Dose length product
L1
T
Pitch 1
8 rotations
Pitch 2
8 rotations
L2
T
as CTDIvol2 = CTDIvol1
2
16. Estimates of effective dose (E)
• Can be obtained from DLP
• Effective dose = DLP. CF (mSv)
•
•
•
•
•
•
Conversion factors not scanner specific or location
specific
Region of body Conversion factor,EDLP
(mSv mGy-1
cm-1
)
Head & neck 0.0031
Head 0.0021
Neck 0.0059
Chest 0.014
Abdomen& pelvis 0.015
Trunk 0.015
17. CT dose reduction techniques
AEC systems have a number of
potential advantages, including better
control of patient radiation dose,
avoidance of photon starvation
artifacts, reduced load on the x-ray
tube, and the maintenance of image
quality in spite of different attenuation
values on CT scans
18. Types of AEC
Patient-Size AEC
Z-axis AEC
Rotational or Angular AEC
Operation of AEC Systems on
Different Multidetector CT Scanners
Exposure 3D
CARE Dose 4D
19. Patient-Size AECPatient size AEC: the tube current is adjusted
based on the overall size of the patient to reduce the
variation in image quality between small patients and
large patients. For a given patient size, the
appropriate milliamperage is selected and is used for
the entire examination or scan series
Hi-mA
Lo-mA
20. Z-axis AEC: tube current is modulated
according to patient attenuation along the z-
axis.The goal is to reduce the variation in image
quality of images from the same series.
attenuation
21. Patient-Size AECRotational AEC: The tube current is decreased
and increased rapidly (modulated) during the course
of each rotation to compensate for differences in
attenuation between lateral (left-right) and A-P
(anterior-posterior) projections .
highattenuationlow attenuation
22. Combination of AEC functions
• Tube current is adjusted during scanning to compensate for
attenuation differences – dose applied to patient only where
needed, avoiding dose where it isn’t
mA
position
23. On line’ modulation–uses attenuation data from previous rotation–
adapts tube current to patient attenuation ‘on the fly’
24.
25. Scan projection radiographs (SPRs, known as scout,
scanogram or topogram views) are the main way that
AEC systems assess the attenuation of the patient in
order to set the tube current
26. To obtain correct attenuation data from SPR
always centre the patient carefully
Patient is positioned in the
isocenter –
optimal dose and image quality
Patient is positioned too high -
increased mAsPatient is positioned too low -
reduced mAs and increased noise
28. Benefits of CT scanner
AEC
Consistent image quality
Potential for dose reduction
through
exposure optimisation
Reduced tube loading
Extended scan runs(OLP)
Reduction in photon starvation
artifact
29.
30. 30
• Images along length of phantom (no AEC)
•
•
•
•
•
•
•
•
Constant mA
Testing the AEC
31. 31
Testing the AEC
• Measure noise with AEC off and on
• Monitor mA, CTDIvol
0
4
8
12
16
20
24
28
-150 -100 -50 0 50 100 150
Z-position (mm)
Noise(%)
automA off
Noise Index 12
Increased
mA
Decreased
mA
Constant mA
Same
mA
Increased
mA
Decreased
mA
32. 32
Coronal view Sagittal view
z-axis
AEC off
z-axis
AEC on
Noise
increases
Constant
noise
Testing the AEC – Viewing with MPR
39. Image obtained in middiastole
(75% of R-R interval)
reconstructed using 1.5-mm slice
thickness at high tube current
shows low-noise
Image obtained in midsystole
(30% of R-R interval)
reconstructed using 1.5-mm slice
thickness shows higher-noise
image obtained at low radiation
dose
41. Scan range
Conventional technology
without Dose Shield
SOMATOM Definition AS+ with
Adaptive Dose Shield
Scan range
Dynamic Collimation
• In helical scanning extra rotations are needed at end of imaged
volume
– Significant extra dose: wide beam widths and short scans
• Dynamic collimation - collimator blades open and close
asymetrically at start and end of scan
42. (a) conventional and (b) adaptive section collimation CT scanning protocols. For
adaptive section collimation, shape of x-ray cone beam at beginning and end of spiral
acquisition is controlled by two collimators made of absorbent material.