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Computed Tomography(Part 2)
Jonathan Mamou and Yao WangPolytechnic School of Engineering
New York University, Brooklyn, NY 11201
Based on Prince and Links, Medical Imaging Signals and Systems and Lecture Notes by Prince. Figures are from the book.
EL-GY 6813 / BE-GY 6203 / G16.4426Medical Imaging
F16 Yao Wang @ NYU 2
Last Lecture• Instrumentation
– CT Generations– X-ray source and collimation– CT detectors
• Image Formation– Line integrals– Parallel Ray Reconstruction
• Radon transform• Back projection• Filtered backprojection• Convolution backprojection• Implementation issues
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This Lecture• Review of Parallel Ray Projection and Reconstruction• Practical implementation with samples• Fan Beam Reconstruction• Signal to Noise in CT
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Review: Projection Slice Theorem• Projection Slice theorem
– The 1D Fourier Transform of a projection at angle θ is a line in the 2D Fourier transform of the image at the same angle.
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Reconstruction Algorithm for Parallel Projections
• Backprojection Sum:– Backprojection of each projection– Sum
• Filtered backprojection:– 1D FT of each projection– Filter each projection in frequency domain– Inverse 1D FT– Backprojection– Sum
• Convolution backprojection– Convolve each projection with the ramp filter– Backprojection– Sum
• Which one gives more accurate results? Which one takes less computation?
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Practical Implementation• Projections g(l, θ) are only measured at finite intervals
– l=nτ; – τ chosen based on maximum frequency in G(ρ,θ), W
• 1/τ >=2W or τ <=1/2W (Nyquist Sampling Theorem)• W can be estimated by the number of cycles/cm in the projection direction in the most detailed
area in the slice to be scanned• For filtered backprojection:
– Fourier transform G(ρ,θ) is obtained via FFT using samples g(nτ, θ)– If N sample are taken, ideally 2N point FFT should be taken by zero padding
g(nτ, θ)• Recall convolving two signals of length N leads to a single signal of length 2N-1
• For convolution backprojection– The ramp-filter is sampled at l=nτ– Sampled Ram-Lak Filter - limiting the rho-filter to within (-1/2τ , -1/2τ )
( )
==−
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evennoddnn
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See paper at http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3708767/
Practical Implementation of Filtered Backprojection
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From paper at http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3708767/pdf/1475-925X-12-50.pdfNote this implementation perform L point DFT assuming the projection data has L points. L is odd. The reconstructed values near the boundary may have ringing artifacts.
Note that backprojection is implemented within the evaluation of inverse FT.
Practical Implementation of Convolution Backprojection
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Here again: Back projection is implemented within convolution!
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The Ram-Lak Filter (from [Kak&Slaney])
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1st Generation CT: Parallel Projections
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3G: Fan Beam
Much faster than 2G
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Fan Beam: Equiangular Ray
We will focus on the equiangular detector setting on the right in this lecture.
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Equiangular Ray Projection
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Equiangular Ray Reconstruction
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Derivation not required for this class. Detail can be found at [Kak&Slaney].Note typos in [Prince&Links], 1st ed.
β−φ Convolution weighted backprojection
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Typos in [Prince&Links, 1st Ed]• P. 207, Eq. (6.38), change to
• Eq. (6.39) change to
• Eq. (6.40),(6.41)
)(sin'
)sin'(2
γγ
γγ cD
Dc
=
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Practical Implementation• Projections p(γ,β) are only
measured at finite intervals– γ=nα; – α chosen based on maximum
frequency in γ direction, W• 1/α>=2W or α<=1/2W
• For convolution backprojection– The filter cf(γ) is sampled at γ=nα– Sampled Filter g(nα)– q(nα,β) = p’ (nα,β) *g(nα)
• For backprojection– For given (r,φ), for a given β,
determine (D’,γ)– Use interpolation to determine
q(γ,β) from known values at γ=nα– Modify the projection based on D’
(weighted backprojection)Back projection and sum
( ) ( )( )
( ))sin()cos(),(tan
)cos()sin(),(' 222
φβφβφγ
φβφβφ
−+−=
−+−+=
rDrr
rrDrD
-1/2
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Matlab Functions for Fan Beam CT• Relevant functions:
– fanbeam(), ifanbeam()
Fan Beam Reconstruction Through Rebinning [Smith&Webb]
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Constrained Optimization Formulation (Algebraic Reconstruction Techniques or ART)
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CT Quality Evaluation• Blurring Effect• SNR
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Effect of Area Detector• Practical detector integrates the detected photons over
an area• Mathematically, the detector can be characterized by an
indicator function s(l) (aka impulse response)• The measured projection g’(l,θ) is related to the “real”
projection g(l,θ) by– g’(l,θ)= g(l,θ) * s(l)– G’(ρ,θ)= G(ρ,θ) S(ρ)
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Windowing Function• Recall that the ideal filter c(ρ) is typically modified by a window
function W(ρ)
• Overall Effect
)(*)(*),(),(ˆ)()(),(),(ˆ is ansformFourier tr whose),,(ˆ projection
thefrom image tedreconstruc theas of thought becan ),(ˆ
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=⇔=
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Blurred Projection
h(x,y): PSF of the blurring
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Circular Symmetry of Blurring
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PSF given by Hankel Transform
222 yxr +=
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Circularly Symmetric Functions and Hankel Transform
• Circularly symmetric:– f(x,y) = f(r), only depends on the distance to the origin, not angle
• Fourier transform of circularly symmetric function is also circularly symmetric– F(u,v)=F(ρ)
( )
{ }
∫∫
∫∫ ∫
∫∫
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=
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∞
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00
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)sincos(1)(;)2()(2)(
Transform Hankel
)()2()(2)()}cos(2exp{),(
)(),( If
)}cos(2exp{),(
}sinsincoscos2exp{),(),(
sin,cos;sin,cosLet
drrJrdrrJrfF
FrdrrJrfrdrrfdrjF
rfyxf
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rdrdrrjrfF
vuryrx
Bessel function of the first kind and 0
thorder
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Common Transform pairs• See Table 2.3
• Scaling property
• Duality: If h(r) <-> H(ρ), then H(r)<->h(ρ)
{ } )/(1f(ar)Hankel 2 aqFa
=
{ }{ }
{ }2
)()(
41)(2)(sinHankel
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F22
2222
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−=
==>
=−−
+−+−
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Derivation of Hankel transform pairs are not required. But you should be able to use given transform pairs, to determine the blur function.
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Example • Example 6.5 in [Prince&Links]
– Detector: rectangular detector with width d
• S(l)=rect(l/d)– Rectangular window function
• W(ρ)=rect(ρ/2ρo); ρo>>1/d
– What is the PSF ?
• Solution– S(l)=rect(l/d) <-> S(ρ)=d sinc(dρ)– ρo >>1/d -> – H(ρ)=S(ρ) W(ρ)~= S(ρ) =dsinc(dρ)
(Hankel transform of h(r))
{ }
{ }
{ }
22
2
2
4
)/(2)(
propertyduality Using
)/(1f(ar)Hankel
41
)(2)(sincHankel
)(Hankel inverse)(
rd
drrectrh
aFa
rectr
Hrh
−=
=
−=
=
π
ρ
ρπ
ρρ
Illustrate and explain h(r)
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Noise in CT Measurement
akNVarakNE
kekakN
ij
ij
ak
ij
==
==
=== −
}{
}{
,...1,0;!
}Pr{
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What about the measured projection
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CBP Approximation
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Definitions and Assumptions
gij are independent because Nij are independentDeriving mean and variance of µ(x,y) based on the independence assumptionSee [Prince&Links] for derivation
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• Variance increases with ρo (cut-off freq. of filter), and T (detector spacing), decreases with M (number of angles), N bar (or N0) (x-ray intensity)
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SNR of the Reconstructed Image
C: fractional change of µ from \bar µ
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SNR in a good design
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SNR in Fan Beam
N=Nf/Dw=L/D
SNR decreases as D increases. Reason: Convolution of the projection reading with the ramp filter couples the noise between detectors, and effectively increases the noise as the number of detector increasesBut larger D is desired to obtain a good resolution.
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Rule of Thumb
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Aliasing Artifacts• Nyquist Sampling theorem:
– If the maximum freq of a signal is fmax, it should be sampled with a freq fs>=2max, or sampling interval T<=1/2fmax
– If sampled at a lower freq. without pre-filtering, aliasing will occur• High freq. content fold over to low freq
– Prefilter to lower fmax, and then sample
• If the number of samples in each projection (D) or the number of projection angles (M) are not sufficiently dense, the reconstructed image will have streak artifacts– Caused by aliasing– Practical detectors are area detectors and perform pre-filtering
implicitly
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From [Kak&Slaney] Fig. 5.1
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Summary• Parallel projection reconstruction
– Backprojection summation– Fourier method (projection slice theorem)– Filtered backprojection– Convolution backprojection– Practical implementation: using finite samples
• Fan beam projection and reconstruction– Weighted backprojection
• Blurring due to non-ideal filters and detectors– Approximate the overall effect by a filter:
• h(l)=w(l)*s(l); H(ρ)=W(ρ) S(ρ)– Circularly symmetric functions and Hankel transform
• Equivalent spatial domain filter h(r)=inverse Hankel {H(q)}• Noise in measurement and reconstructed image
– Factors influencing the SNR of reconstructed image• Average X-ray intensity, Number of angles (M), number of samples per angle (D), filter
cut-off ρo
• Impact of number of projection angles and samples on reconstruction image quality
– Nyquist sampling theorem– Streak artifacts
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Reference• Prince and Links, Medical Imaging Signals and Systems, Chap 6.• A. C. Kak and M. Slaney, Principles of Computerized Tomographic Imaging.
Originally published by IEEE, 1998. E-copy available at http://www.slaney.org/pct/
– Chap 3 Contain detailed derivation of reconstruction algorithms both for parallel and fan beam projections. Have discussions both in continuous domain and implementation with sampled discrete signals.
– Chap 5 discusses noise in measurement and reconstructed image.– Chap 5 also covers aliasing effect with more mathematical interpretations
• A useful lecture note from Prof. Fessler– http://web.eecs.umich.edu/~fessler/course/516/l/c-tomo.pdf
• Lecture note by Prof. Parra– http://bme.ccny.cuny.edu/faculty/parra/teaching/med-imaging/lecture4.pdf– http://bme.ccny.cuny.edu/faculty/parra/teaching/med-imaging/lecture5.pdf
• For more discussion on aliasing due to under sampling– https://engineering.purdue.edu/~malcolm/pct/CTI_Ch05.pdf
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Homework Due: 9:50 am on Friday October 12
• Reading: – Prince and Links, Medical Imaging Signals and Systems, Chap 6,
Sec.6.3.4-6.5• Note down all the corrections for Ch. 6 on your copy of the textbook
based on the provided errata.• Problems for Chap 6 of the text book:
– P.6.9– P.6.10 (part e is not required)– P.6.13.
• Hint: solution for part (a) should be
– P.6.19– P.6.20
( )( )
≤≤−≤≤−+
=otherwise
allalala
lg0
2/02/302/2/3
)60,( µµ
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Computer AssignmentDue: 9:50 am on Friday October 12
Will send assignment via NYU Classes today.