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Additional resources for Clinical PET: Principles and Applications
This method is computationally fast and less demanding on the quality of the raw image data. However, even this simplified method still requires the measurement of the tracer input function, the blood-time activity curve. Parametric imaging methods require the measurement of the tracer input function. The extrac- FOG IN PLASMA (Cp) k1 k2 FOG IN TISSUE (Ce) k3 k.. 4. The fluorodeoxyglucose (FDG) three-compartment system consisting of reaction in blood, tissue, and product in tissue. 1. Principles of PET Imaging tion of 30 blood samples over the imaging time and the effort to measure the blood activity information of these samples are rather demanding, especially for clinical studies.
These cameras also have the lowest detection sensitivity for positron imaging. There are two reasons for their low sensitivity. First, the use of lead collimation to define the direction of the detected gamma ray is very inefficient, because the collimator can absorb 95% or more of the incoming gamma rays. Second, the thin Nai(Tl) detector is optimized for stopping the 140-keV gamma ray for technetium 9mTc) imaging, and so most of the higher energy (511-keV) gamma rays from positron annihilation penetrate this thin detector without any interaction (about a 70% escape fraction).
09. When compared with a dedicated BGO PET camera, which uses detectors made of BGO scintilla- 1. Principles of PET Imaging tion material, the sensitivity of this modified SPECT camera is still 9 to 10 times lower for identical detection areas. However, the detection sensitivity of this class of camera is a substantial improvement (5 to 10 times) over dual-head cameras with lead collimators. 0 cm. 58,59 Hence, this camera type is a better choice than the lead collimator gamma camera for taking advantage of the more tumor-specific positron tracers with a relatively small additional investment.