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2.1. Jagiellonian PET: J-PET
Due to the growing demand for Positron Emission Tomography scanners, which in
Poland and other countries is still insufficient, an innovative method for the construction of
these devices was developed [7] [8] [9] [10] [11]. Expensive inorganic
scintillators were
replaced by low-cost plastic scintillators. 1 cm
3
of plastic scintillator costs approximately
$1. Usage of plastic scintillators instead of inorganic ones decreases price of the whole
scanner significantly.
So far plastic scintillators have not been investigated as detectors of gamma quanta
in PET scanners because of much lower detection efficiency
comparing to inorganic
crystals and negligible probability of photoelectric effect. Gamma quanta interact with low
atomic number elements, which plastic
scintillators are made of, predominantly via
Compton effect. That leads to continuous charge spectra. In addition, efficiency of gamma
quanta detection is much lower than in inorganic crystals.
This disadvantage can be
compensated by very good timing properties of plastic scinitillators and by the large size of
the diagnostic chamber.
In Table 2 selected parameters describing properties of BC (Saint Gobain) and
EJ (Eljen Technology) plastic scintillators and four inorganic crystals (BGO, GSO, LSO
and LYSO) that are used in traditional PET scanner are given.
Light outputs of LSO or
LYSO crystals are much higher in comparison to plastic scintillators. However, attenuation
length in plastic scintillator is longer than in crystals. Because plastic scintillators can be
produced in any shapes and sizes, longer attenuation length makes possibility to design and
manufacture long scintillator strips in which the light will be transferred effectively even at
large distances. This in turn enables to construct PET scanner
basing on long scintillator
strips with large field of view. In such scanner imaging of whole patient body or its large
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