The relationship between image noise and spatial resolution of CT scanners

Transcription

1 The relationship between image noise and spatial resolution of CT scanners Sue Edyvean, Nicholas Keat, Maria Lewis, Julia Barrett, Salem Sassi, David Platten ImPACT*, St George s Hospital, London *An MDA device evaluation group,

2 Image noise and spatial resolution Aims Describe the origins of the ImPACT Q factor Explore the proportionality relationships in particular; noise against resolution From the findings, look at some implications 2

3 The ImPACT Q factor Describes a relationship of image quality with respect to dose Q α 2 3 f σ z D f = spatial resolution σ = image noise z = slice width D = dose High Q factor good image quality with low dose high spatial resolution, low noise, narrow slice 3

4 The ImPACT Q factor Drawn from the proportional relationship σ 2 α z f 3 D f = spatial resolution expressed as a frequency (c/cm) σ = image noise z = slice width D = dose 4

5 Theoretical derivation Rodney Brookes and Giovanni di-chiro (1976) Statistical limitations in x-ray reconstructive tomography Medical Physics Vol 3, No 4 July 1976 Riederer S.J., Pelc N.J. and Chesler D.A. (1978) The Noise Power Spectrum in Computed Tomography Physics in Medicine and Biology (3), σ 2 ( µ ) π = 2 β γ ( E) e α ω z µ D en E 5

6 Other publications, reports and books Bassano D.A. (1980, AAPM Summer School) Specification and Quality Assurance for CT Scanners IPEM TGR 32 iii (1st Edition, 1981) Measurement of Performance Characteristics of CT Scanners Farr RF and Allisy-Roberts PJ (1997) Physics for Medical Imaging Seeram E., 2000 Computed Tomography, Physical Principles, Clinical Applications and Quality Control (2nd Edition) σ 2 α z f 3 D 6

7 Unpacking the relationship noise relationship with number of photons established number of photons σ 2 α proportional to slice thickness and mas (dose) 1 N σ 2 α z 1 D 7

8 Unpacking the relationship noise relationship with spatial resolution? σ 2 α f 3? σ 2 α z f 3 D 8

9 Empirical approach measure image noise and spatial resolution range of convolution constant dose and slice width σ 2 α z f 3 D 9

10 Image noise scan projection radiograph water filled phantom image scan noise = standard deviation (σ) of CT values in region of interest 10

11 Spatial resolution high contrast edge ESF MTF sharp image CT PTFE MTF (%) smooth image CT w 10 Position Along Edge spatial frequency (cm -1 ) 11

12 12

13 Modulation transfer function resolution descriptors frequency at MTF 50 sharp image frequency at MTF 10 Q uses average of MTF 50, MTF 10 more recently MTF (%) smooth image MTF 80 MTF 2 cut-off spatial frequency (cm -1 ) integral (area under curve) 13

14 Scanners and algorithms used IGE Lightspeed h: soft, standard, lung, detail, bone, edge b: soft, standard, lung, detail, bone, edge Siemens Volume Zoom h: AH..10,20,30,40,50,60,70 b: AB...10,20,30,40,50,60 Toshiba Aquilion h: FC 20,21,22,23,24,25,26,27,28,30,80 b: FC.10,11,12,13,14,30 Marconi (Philips) MX8000 h: A,EB,EC,B,C,D b: A,EC,B,C,D 14

15 Siemens VZ, all algorithms, head scans log % noise for 40 mgy log % noise (σ) different algorithms power 5.7 R 2 = σ 2 α f σ 2 α f 3 power ( f ) Average of MTF 50 and MTF 10

16 Empirical view of noise versus resolution early papers only considered simple algorithms ramp filter and Hanning weighted some filter frequencies boosted very differently Amplification Frequency (lp/cm) 16

17 Siemens VZ, low res. algorithms, head scans 10.0 log % noise for 40 mgy log % noise (σ) 1.0 power 4.6 R 2 = power ( f ) Average of MTF 50 and MTF 10

18 All scanners, all algorithms, body scans 10.0 log % noise for 40 mgy 1.0 power 5.1 power 4.8 R 2 = R 2 = R 2 = power 4.3 power 5.7 R 2 = LightSpeed Mx8000 Aquilion VolumeZoom 0.1 ( f ) Average of MTF 50 and MTF 10

19 All scanners, low res. algs, body scans 10.0 power 4.9 power 3.6 % noise for 40 mgy 1.0 R 2 = R 2 = power 3.9 power 3.8 R 2 = R 2 = LightSpeed Mx8000 Aquilion VolumeZoom 0.1 ( f ) Average of MTF 50 and MTF 10

20 Empirical view of noise versus resolution early papers derivations focussed on limiting resolution characteristics eg detector aperture Amplification Frequency (lp/cm) 20

21 Mean of all scanners, all MTF, all algorithms Body scans parameter resolution power for sigma^2 mean range +/- mtf mtf mtf mtf mtf integral avg MTF50,

22 Empirical view of noise versus resolution power factor for MTF 50 and MTF 10 is greater than 3; ~ between 4 and 5 2 σ α f z 4 5 D 22

23 Empirical view of noise versus resolution how does this affect the calculation of Q? minimise the influence of the power relationship specify resolution eg. body resolution values of MTF 50 = 3.4 c/cm, MTF 10 = 6 c/cm find algorithm giving resolution data closest to that value calculate Q Q α 2 3 f σ z D 23

24 All scanners, body scans, lower resolution algorithms 2.1 % noise for 40 mgy use a specific average MTF 50 and MTF 10 value LightSpeed Mx8000 Aquilion VolumeZoom Average of MTF 50 and MTF 10

25 All scanners, body scans, lower resolution algorithms 2.1 % noise for 40 mgy σ 2 α Average of MTF 50 and MTF 10 f 3 LightSpeed Mx8000 Aquilion VolumeZoom

26 All scanners, body scans, lower resolution algorithms % noise for 40 mgy LightSpeed Mx8000 Aquilion VolumeZoom Average of MTF 50 and MTF 10

27 Conclusion The ImPACT Q factor relies on an established relationship σ 2 α f 3 z using average resolution parameters from the MTF, the noise squared relationship to resolution is shown to be to a power greater than 3 2 σ by choosing algorithms close to a fixed spatial resolution the algorithm dependence is minimised α f z D 4 5 D 27

28 The relationship between image noise and spatial resolution of CT scanners Sue Edyvean, Nicholas Keat, Maria Lewis, Julia Barrett, Salem Sassi, David Platten ImPACT*, St George s Hospital, London *An MDA device evaluation group,

29 Theoretical Relationships Rodney Brookes and Giovanni di-chiro Statistical error in reconstructed image i.e. image noise energy absorption co-efficient Logarithmic attenuation average depth dose factor photon energy σ 2 ( µ ) = π 2 ( E) β γ e ω h α µ D en E beam spreading factor (non parallel rays) dose detector aperture slice width 29

30 Theoretical Relationships σ 2 ( µ ) = π 2 β γ 1200 ( E) ω e 3 α z µ D en E 30

31 Microtomography - Basics Time SNR ρµ r 2 4 exp µ d 2 SNR = signal-to-noise resolution ρ = density µ = linear attenuation coefficient r = voxel dimension d = object diameter Courtesy of Dr. E.J. Morton, Department of 31 Physics, University of Surrey

32 Mean of all scanners, average MTF 50,10 all algorithms low res. agorithms mean range +/- mean range +/- body head MTF 50,10 lower by 20% with lower res. algs. Head ~ 10% higher than body Power factor between 4 and 5 32

33 The ImPACT Q factor Describes image quality with respect to dose High Q (quality) factor good image quality at low dose image quality in terms of high spatial resolution, low noise, narrow slice Q α 2 3 f σ z D f = spatial resolution σ = image noise z = slice width D = dose 33

34 Unpacking the relationship σ 2 α z f 3 D noise relationship with number of photons established number of photons σ 2 α proportional to slice thickness and mas (dose) 1 N σ 2 α z 1 D 34

35 Empirical view of noise versus resolution power factor is greater than 3; ~ between 4 and 5 early papers only considered simple algorithms ramp filter and Hanning weighted some filter frequencies boosted very differently theory looked at limiting resolution Amplification Frequency (lp/cm) 35

36 Theoretical derivation Rodney Brookes and Giovanni di-chiro (1976) Statistical limitations in x-ray reconstructive tomography Medical Physics Vol 3, No 4 July 1976 Riederer S.J., Pelc N.J. and Chesler D.A. (1978) The Noise Power Spectrum in Computed Tomography Physics in Medicine and Biology (3), σ 2 ( µ ) π = 2 β γ ( E) e α ω z µ D en E 36

37 Theoretical derivation Rodney Brookes and Giovanni di-chiro (1976) Statistical limitations in x-ray reconstructive tomography Medical Physics Vol 3, No 4 July 1976 Riederer S.J., Pelc N.J. and Chesler D.A. (1978) The Noise Power Spectrum in Computed Tomography Physics in Medicine and Biology (3),