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The number of tables columns is arbitrary, except that at least one column must exist for the PET SRTM analysis; the first column is the length of each time frame in the PET reconstruction in units of seconds.
At the end of each time frame, each node samples its instantaneous queue length.
Radioactivity levels in arterial blood were measured via an automatic blood sampling system for the first 10 min (ABSS, Alogg Technologies, Mariefred, Sweden), followed by manual arterial sampling at the midpoint of each time frame.
Since FD-ISFA estimated the sound activity for each frequency bin independently, we calculated the number of active bins for each time frame and determined the source activity of each time frame by using threshold processing.
In order to optimize the bit distribution, a tailored evolutionary algorithm is proposed, considering that the number of bits associated to the transmission of the data of each time frame (i.e., the bit rate) is constrained.
At the beginning of each time frame, the BS executes an opportunistic beamforming algorithm for defining the random radiation pattern with weight vector w T, of dimensions (M T × 1).
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For the intestines, if specific high uptake was observed, individual ROIs were defined on each time frame of the PET images with about a 10% threshold.
For other low-uptake organs (adrenal gland, stomach contents, pancreas, ovary, uterus and testis), individual ROIs were drawn on each time frame of the PET images and referred to the co-registered MRI images.
Thereafter, a multi-frame SPECT acquisition consisting of six subsequent scans of identical bed position was initiated 5 min PI, with a scan time of 10 min for each time frame and a total acquisition time of 60 min. Frames were labeled with their mean acquisition time point, e.g., '10 min' for 5 to 15 min SPECT acquisition.
Given a GMM with G Gaussians, the posterior probability of each Gaussian is computed for each time frame, leading to a set of vectors of dimension G that represent the probability of each Gaussian at every time instant.
Using the WL mask and the three subdivisions mentioned above, four time activity curves (TACs) were generated by calculating the mean regional activity for each time frame of the dynamic PET.
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