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The goal of iterative reconstruction is to find the best estimated slice that, when projected in multiple directions, is as close to acquired projections as possible.
Reconstruction of experimentally acquired projections from phantoms shows quantitative compensation for scatter and attenuation.
Note that the required computation time of FBP and iterative methods generally scales linearly with the number of acquired projections.
At the same time, the acquired projections are often limited in some way, for example having a low number of projections or a low signal-to-noise ratio.
Due to the limited number of counts in the acquired projections there are fluctuations inside the lung even for the simulated normal.
To enable direct feedback and optimization of experimental parameters, it is important that the acquired projections can be processed in a time comparable to data acquisition.
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The acquired projection images represent the two-dimensional spatial distribution of the energy absorbed in the detector and are formed at any geometry, taking into account energy spectrum, beam geometry and detector response.
We note that from the acquired projection data we can compute both Θ and t x.
Figure 3 presents an acquired projection and an axial slice reconstructed with the conventional protocol during the beamtime.
Very few details can be noticed in the acquired projection, thus confirming that the scanned sample is almost a pure phase object.
This novel sinogram binning approach when used with listmode acquisitions provides high temporal resolution by overlapping the image frames, where the image projection content is a fixed proportion from prior and newly acquired projection data (Fig. 1b).
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