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From PET detectors to PET scanners

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Abstract

This review describes the properties of available and emerging radiation detector and read-out technologies and discusses how they may affect PET scanner performance. After a general introduction, there is a section in which the physical properties of several different detector scintillators are compared. This is followed by a discussion of recent advances in read-out electronics. Finally, the physical performance of the several commercial PET scanners is summarized.

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Notes

  1. This result is lower than the experimental one [12, 13]. The differences are due to the formation of a particle with higher momentum, the positronium, a hydrogenoid atom where the positron is in a bound system with an electron. The positronium annihilates in 2γ either from the para-positronium (single state) or predominantly from the ortho-positronium (triplet state).

  2. For ultra-high-resolution PET scanner, the fluorescent photon should also be considered.

  3. Webpages of manufacturers of scintillation materials: 1, http://www.bicron.com; 2, http://www.rexon.com; 3, http://www.crystran.co.uk; 4, http://www.hilger-crystals.co.uk; 5, http://www.scionixusa.com/scintillation_detectors.html; 6, http://www.utari.com; 7, http://www.girmet.ru/~ramet/scintillator.htm; 8, an exceptionally rich source of up-to-date reference material on scintillators is the Web Page, University of California, Lawrence Berkeley National Laboratories, Center for Functional Imaging, http://cfi.lbl.gov/instrumentation/Publications.html.

  4. Thermionic noise is the spontaneous emission of electrons from the photocathode. For a bi-alkali photocathode at room temperature, approximately 100–1,000 electrons/cm2·s are produced, corresponding to dark currents of between 16 and 160 pA.

  5. To convert from kBq/cc in a patient into an administered activity, divide by 103 to convert to MBq/cc, multiply by the patient weight 70,000 g, divide by the fraction of the torso body activity within the field of view (approx one-fifth) and divide by 1.5 to account for physical decay and patient clearance between the injection time and the scan time.

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Acknowledgements

The authors would like to give special thanks to James Bland (CTI Knoxville, TN), Phil Vernon (General Electric, Toledo, OH), and Joel Karp (U.Penn, Philadephia, PA) for providing assistance in the preparation of Table 3, and to Bill Strauss (MSKCC, New York) for providing the impetus for this manuscript, for his excellent suggestions regarding content, and for his assistance in editing the final draft.

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Authors and Affiliations

  1. Department of Medical Physics, Memorial Sloan Kettering Cancer Center, 1275 York Avenue, New York, NY 10021, USA

    John L. Humm

  2. Physics Department, University of Wollongong, New South Wales, Australia

    Anatoly Rosenfeld

  3. Department of Physics “E. Fermi”, University of Pisa, Pisa, Italy

    Alberto Del Guerra

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Humm, J.L., Rosenfeld, A. & Del Guerra, A. From PET detectors to PET scanners. Eur J Nucl Med Mol Imaging 30, 1574–1597 (2003). https://doi.org/10.1007/s00259-003-1266-2

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