By Augusto Giussani, Christoph Hoeschen
This quantity addresses a variety of matters within the box of nuclear drugs imaging, with an emphasis at the most up-to-date learn findings. preliminary chapters set the scene through contemplating the function of imaging in nuclear drugs from the scientific viewpoint and discussing the results of novel brokers and functions for imaging. The physics on the foundation of the main sleek imaging platforms is defined, and the reader is brought to the newest advances in photo reconstruction and noise correction. a number of novel suggestions are then mentioned, together with these constructed in the framework of the EURATOM FP7 MADEIRA study undertaking at the optimization of imaging tactics with the intention to allow a discount within the radiation dose to fit tissues. Advances in qc and caliber coverage are lined, and the e-book concludes by means of directory ideas of thumb for imaging that would be of use to either rookies and skilled researchers.
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Additional info for Imaging in Nuclear Medicine
The relative energy resolution pﬃﬃﬃ is 2:35= S % 10 % FWHM, resulting in a typical admissible energy window of pﬃﬃﬃ 14 %. A better yield Y gives Y times better resolution, and a correspondingly narrower energy window can be used to reject scatter and background radiation. 3 Physics of Imaging in Nuclear Medicine Fig. 6 Illustration of different types of events in photon detection 33 object tracer detector 1 2 3 Fig. 1. The detectors are placed in a stationary ring around the object with a typical ring diameter of D ¼ 80 cm and thickness h % 20 cm.
4 Planar Imaging and SPECT The most popular radiotracer, 99mTc, emits a single photon with energy of 140 keV per decay. To detect the origin of the registered photon, Anger  developed a mechanically collimated camera shown in Fig. 4. The present detectors are improved versions of the same principle, with multiple pinholes instead of a single one, and better scintillators and light detectors. 5 m2 and has a thickness of 1–2 cm, corresponding to approximately ten half-lengths for 99mTc radiation.
For each of the two photons, its detection probability η will be determined by the half-value thickness d1/2 of the sensitive 36 A. 2). Typical scintillator detectors have u/d1/2 % 3 and η of 90 % or more is common. This efficiency is further restricted by the criterion that only photons with energy falling in a selected window are accepted, in order to reject photons scattered in the object. This implicates that also photons undergoing Compton scattering in the detector are rejected. 2), and consequently, probability of a valid interaction of each of the photons, ε, is equal to η reduced by a factor between 2 (BGO) and 3 (LYSO).
Imaging in Nuclear Medicine by Augusto Giussani, Christoph Hoeschen