The term transconvolution designates a numerical method used in medical imaging, in particular emission computed tomography. Transconvolution enables a subsequent manipulation of the Point spread function (PSF) in already recorded images. Properties of an image such as the spatial resolution or the appearance of small objects are determined by the PSF of the imaging system used for image acquisition. Different imaging systems with different PSFs therefore provide slightly different images of one and the same object. Starting from known PSFs of different tomographic systems, the transconvolution method allows an image recorded on a particular tomograph to be converted as if it had been acquired by another tomograph. The method can thus ensure the comparability of images that were originally recorded on different systems.
Definition Given two different tomographs with different point spread functions p s f 1 {\displaystyle psf_{1}} and p s f 2 {\displaystyle psf_{2}} the imaging process can be defined in terms of convolution as
o b j ∗ p s f 1 = i m g 1 {\displaystyle obj*psf_{1}=img_{1}}
o b j ∗ p s f 2 = i m g 2 {\displaystyle obj*psf_{2}=img_{2}}
with " ∗ {\displaystyle *} " representing the convolution operator and i m g 1 {\displaystyle img_{1}} and i m g 2 {\displaystyle img_{2}} representing the two slightly different images of the same object o b j {\displaystyle obj} as seen by the respective tomographs. The two equations yield the relationship
i m g 1 ∗ p s f 1 − 1 ∗ p s f 2 = i m g 2 {\displaystyle img_{1}*psf_{1}^{-1}*psf_{2}=img_{2}}
with p s f 1 − 1 {\displaystyle psf_{1}^{-1}} representing the inverse function of the according point spread function p s f 1 {\displaystyle psf_{1}} . The inverse point spreading function p s f 1 − 1 {\displaystyle psf_{1}^{-1}} diverges and can not be determined or handled numerically. But, within certain boundary conditions, the complete term p s f 1 − 1 ∗ p s f 2 {\displaystyle psf_{1}^{-1}*psf_{2}} is approximately computable by numerical methods. The transconvolution function t f {\displaystyle tf} is defined as
t f = p s f 1 − 1 ∗ p s f 2 {\displaystyle tf=psf_{1}^{-1}*psf_{2}}
which results in the formula
i m g 1 ∗ t f = i m g 2 {\displaystyle img_{1}*tf=img_{2}}
With the PSFs of the respective tomographs known, it is thus possible to convert an image i m g 1 {\displaystyle img_{1}} recorded by the first tomograph into an i m g 2 {\displaystyle img_{2}} emulating an image as recorded by the second tomograph. Of course, the method is subject to certain limits, in particular the computed i m g 2 {\displaystyle img_{2}} can not represent spatial frequencies not captured to at least some degree by p s f 1 {\displaystyle psf_{1}} . Consequently, the spatial resolution of an image can not be increased arbitrarily.
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