Positron Emission Tomography
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1 Positron Emission Tomography Presenter: Difei Wang June,2018 Universität Bonn
2 Contents 2 / Positron emission Detected events Detectors and configuration Data acquisition
3 Positron emission Positron emission = β + decay p n + e + + ν On atomic level A Z X A Z 1 Y + e + + ν kev Collinearity no physical collimation needed Positron range Source: D.L. Bailey, D.W. Townsend, P.E. Valk, and M.N. Maisey. Positron Emission Tomography: Basic Sciences. Springer London, / 24
4 Positron emitting nuclide 4 / 24 Nuclide Maximum positron energy (MeV) Range in water (mm) Deduced RMS Half lifetime 11 C min 13 N min 15 O min 18 F min 82 Rb min
5 Positron emission D : distance between two coincidence detectors Source: Pat Zanzonico. Positron emission tomography: a review of basic principles, scanner design and performance, and current systems. Sem Nucl Med 34:87-111, / 24
6 Spatial resolution Spatial resolution = physical + instrumentation factors Physical factors 1. Positron range degrades spatial resolution. The range-related blurring is reduced by the tortuous path and the spectral distribution of positron energies. 2. Non-collinearity related blurring depends on the distance between two coincidence detectors. Δθ D whole body scan: ~2 mm small animal scan: ~ 0.3 mm 6 / 24
7 Coincidence event True coincidence event energy range : 250 ~ 650 kev Source: Pat Zanzonico. Positron emission tomography: a review of basic principles, scanner design and performance, and current systems. Sem Nucl Med 34:87-111, / 24
8 Timing window 1. The position of the annihilation 2. Signal processing 3. Scintillation decay time 8 / 24
9 Detected Events in PET 1. True True count rate is linearly proportional to the activity. 2. Random Random count rate increases more rapidly than the true count rate. Source: D.L. Bailey, D.W. Townsend, P.E. Valk, and M.N. Maisey. Positron Emission Tomography: Basic Sciences. Springer London, / 24
10 Detected Events in PET 10 / Scatter Scatter count rate is linearly proportional to the activity. The scatter-to-true ratio is independent of timing window. Source: D.L. Bailey, D.W. Townsend, P.E. Valk, and M.N. Maisey. Positron Emission Tomography: Basic Sciences. Springer London, 2004.
11 Detector materials 11 / 24 Source: D.L. Bailey, D.W. Townsend, P.E. Valk, and M.N. Maisey. Positron Emission Tomography: Basic Sciences. Springer London, 2004.
12 Detector materials 12 / 24 Material NaI (Tl) BGO LSO GSO Density (g/cm 3 ) Effective atomic number Z eff Attenuation coefficient μ (/cm) Light output (photons/ kev) ,000 9,000 30,000 8,000 Scintillation decay time (ns) Energy resolution (% FWHM)
13 Spatial resolution 13 / 24 instrumentation factors Depth of interaction effect (DOI effect): The relatively thick detector elements lead to a loss of resolution. Center : resolution: R det = d/2 Away from the center : d = d cos θ + x sin θ resolution: R det R det [cos θ + x d sin θ] x : 2 3 cm d : cm Source: S.R. Cherry, J.A. Sorenson, and M.E. Phelps. Physics in Nuclear Medicine. (4th ed). Philadelphia, PA, Saunders, 2012
14 Block detectors X = (PMT A+ PMT B ) (PMT C + PMT D ) PMT A + PMT B + PMT C + PMT D Y = (PMT A+ PMT C ) (PMT B + PMT D ) PMT A + PMT B + PMT C + PMT D Source: S.R. Cherry, J.A. Sorenson, and M.E. Phelps. Physics in Nuclear Medicine. (4th ed). Philadelphia, PA, Saunders, 2012 (left) D.L. Bailey, D.W. Townsend, P.E. Valk, and M.N. Maisey. Positron Emission Tomography: Basic Sciences. Springer London, 2004 (right) 14 / 24
15 15 / 24 Modified block detectors 1.Quadrant sharing block design Each PMT monitors corners of four different blocks. + : reduce the number of PMTs : need more time to process the signal Source: S.R. Cherry, J.A. Sorenson, and M.E. Phelps. Physics in Nuclear Medicine. (4th ed). Philadelphia, PA, Saunders, 2012
16 Modified block detectors 16 / Phoswich LSO GSO This approach makes use of the difference in decay times of two scintillators. The event can be localized into upper or lower layer. + : reduce the DOI effect : worse performance Source: S.R. Cherry, J.A. Sorenson, and M.E. Phelps. Physics in Nuclear Medicine. (4th ed). Philadelphia, PA, Saunders, 2012
17 Detector configurations 17 / 24 Source: S.R. Cherry, J.A. Sorenson, and M.E. Phelps. Physics in Nuclear Medicine. (4th ed). Philadelphia, PA, Saunders, 2012
18 Detector configurations 18 / 24 Multi-coincidence fan beam detection: Each detector element is operated in coincidence with multiple opposed detector elements. 2D: Fan beam 3D: Cone beam Useful field-of-view Source: S.R. Cherry, J.A. Sorenson, and M.E. Phelps. Physics in Nuclear Medicine. (4th ed). Philadelphia, PA, Saunders, 2012
19 Data acquisition θ: polar angle φ: azimuthal angle Source: D.L. Bailey, D.W. Townsend, P.E. Valk, and M.N. Maisey. Positron Emission Tomography: Basic Sciences. Springer London, / 24
20 Data acquisition 20 / 24 p ( s, φ) Source: D.L. Bailey, D.W. Townsend, P.E. Valk, and M.N. Maisey. Positron Emission Tomography: Basic Sciences. Springer London, 2004 (left) S.R. Cherry, J.A. Sorenson, and M.E. Phelps. Physics in Nuclear Medicine. (4th ed). Philadelphia, PA, Saunders, 2012 (right)
21 Data acquisition Direct plane: Crystal ring collects data from a single slice. Cross plane: Crystal ring collects data from adjacent rings Source: S.R. Cherry, J.A. Sorenson, and M.E. Phelps. Physics in Nuclear Medicine. (4th ed). Philadelphia, PA, Saunders, / 24
22 Data acquisition 22 / 24 The axial sensitivity profile for 3-D acquisition reaches its maximum at the center of the field-of-view. Source: S.R. Cherry, J.A. Sorenson, and M.E. Phelps. Physics in Nuclear Medicine. (4th ed). Philadelphia, PA, Saunders, 2012
23 Attenuation correction PET only system: simultaneous emission/transmission scan Blank scan: without the patient, once a day Transmission scan: with the patient; all events Emission scan: with patient, coincidence events 23 / 24
24 Conclusion 24 / 24 Positron emission Detectors Data acquisition Possible events
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