WO2016112135A1 - Détecteur pet trapézoïdal compact avec partage de lumière - Google Patents

Détecteur pet trapézoïdal compact avec partage de lumière Download PDF

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Publication number
WO2016112135A1
WO2016112135A1 PCT/US2016/012386 US2016012386W WO2016112135A1 WO 2016112135 A1 WO2016112135 A1 WO 2016112135A1 US 2016012386 W US2016012386 W US 2016012386W WO 2016112135 A1 WO2016112135 A1 WO 2016112135A1
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WIPO (PCT)
Prior art keywords
crystals
scintillation crystals
face
sensor module
adjacent
Prior art date
Application number
PCT/US2016/012386
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English (en)
Inventor
Robert S. Miyaoka
William C. J. HUNTER
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University Of Washington
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Publication of WO2016112135A1 publication Critical patent/WO2016112135A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/037—Emission tomography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/20—Measuring radiation intensity with scintillation detectors
    • G01T1/2018—Scintillation-photodiode combinations
    • G01T1/20182—Modular detectors, e.g. tiled scintillators or tiled photodiodes
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/20—Measuring radiation intensity with scintillation detectors
    • G01T1/2018—Scintillation-photodiode combinations
    • G01T1/20183—Arrangements for preventing or correcting crosstalk, e.g. optical or electrical arrangements for correcting crosstalk
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
    • G01T1/2914—Measurement of spatial distribution of radiation
    • G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)

Definitions

  • PET Positron Emission Tomography
  • Small animal imaging has emerged as an important research field.
  • positron emission tomography PET
  • MRI magnetic resonance imaging
  • Desirable characteristics in a small animal imaging PET system include (1) high image resolution; (2) high absolute sensitivity; (3) the ability to work in a strong magnetic field; and (4) a compact size.
  • the present inventors have created a novel high resolution, monolithic crystal small animal PET detector that provides a number of advantages over discrete crystal detector designs.
  • Relatively large scintillation crystals are preferred for a monolithic crystal detector because of the challenges associated with positioning events near the edges of a crystal, which makes two-dimensional monolithic crystal geometry less than ideal for a compact PET detector.
  • the PET detector may use elongate trapezoidal slat crystals (TSC) to produce a compact annular detector.
  • TSC trapezoidal slat crystals
  • a PET detector suitable for use in a PET/MRI imaging system is disclosed in Xiaoli Li, et al., "Design of a trapezoidal slat crystal (TSC) PET detector for small animal PET/MR imaging," Nuclear Science Symposium Conference Record (NSS/MIC), 2010 IEEE (hereinafter, Li), which is hereby incorporated by reference in its entirety.
  • TSC trapezoidal slat crystal
  • FIGURE 1 A front view of a prior art PET detector 50 is shown schematically in FIGURE 1.
  • the PET detector 50 includes a plurality of detector modules 52 assembled in an annular arrangement. During imaging, the subject is positioned generally along the center axis of the annular assembly.
  • a detector module 52 is shown in a detail view in FIGURE 1.
  • the detector module 52 includes a scintillator body 51 that is shaped as an isosceles trapezoid.
  • An optional optical window or light guide 57 is fixed to an outer end of the scintillator body 51, and two rows of coplanar photodetectors 60, for example, silicon photomultipliers (SiPM), are positioned to detect light released from scintillation events in the scintillator body 51.
  • a 2 X 12 array of photodetectors 60 may be provided on each scintillator body 51.
  • the scintillator body 51 comprises a plurality of elongate slat crystals 54 (8 shown) that are trapezoidal in cross section, and tapers in the radially inward direction.
  • Light-blocking/reflecting elements 56 between each of the slat crystals 54 prevent (full length) or limit (less than full length) light sharing between adjacent slat crystals 54.
  • Full length light-blocking/reflecting elements 56 cover both radial sides of the scintillator body 51.
  • Light-blocking/reflecting elements 56 that extend only partially along the radial length of the adjacent slat crystals 54 permit some light from a scintillation event in one slat crystal 54 to be shared with an adjacent slat crystal 54.
  • an outer portion of some of the interior slat crystal 54 faces are joined with transparent glue 108 (indicated by dashed lines), that allow light sharing internally within the module 52.
  • This light sharing feature provides information that can be used to estimate the crystal of interaction of the scintillation event occurring in the detector module 52.
  • this PET detector provides for light sharing only internally within a module 50, and requires two or more coplanar rows of photodetectors 60.
  • the detector modules 50 are therefore relatively wide, to accommodate the two co-planar photodetectors 60, which limits the practical compactness of the scanner.
  • the detector modules 50 do not incorporate light sharing between adjacent modules 52. It would be beneficial to have narrower detector elements to improve the resolution of the PET imager 50.
  • a positron emission tomography (PET) scanner includes a plurality of sensor modules arranged adjacently to form an annular detector ring.
  • the sensor modules include (i) plural scintillation crystals with oppositely disposed converging faces, and plural light blocking elements interleaved with the scintillation crystals to form a scintillator assembly having a trapezoidal cross section; (ii) an end-face light blocking element fixed to an end face of the scintillator assembly, and blocking a radially inner portion of the end face, leaving a radially outer portion unblocked; and (iii) a row of photodetectors fixed to a radially inner or outer face of the scintillator assembly.
  • the sensor modules are configured to share light across the radially outer portion of the end- face with an adjacent sensor module. Light may also be shared between adjacent crystals within a crystal module.
  • the PET scanner includes a computing system operatively connected to the plurality of sensor modules to receive signals from the rows of photodetectors during operation of the PET scanner.
  • the sensor modules share light with adjacent sensor modules such that the shared light is detected by respective rows of photodetectors that are not coplanar.
  • the scintillation crystals are slat crystals having a wedge shape with parallel outer and inner faces connected by converging faces.
  • the scintillation crystals have an inner face with a width of 1.0 mm or less, and in some embodiments the inner face width is 0.5 mm or less. In some embodiments the scintillation crystals are at least 40 mm in length. In an embodiment the sensor modules each comprise six or fewer scintillation crystals. In an embodiment the light block elements are reflective.
  • At least some of the light blocking elements extend radially from a radially inner end of adjacent scintillation crystals only part way to a radially outer end, such that the radially outer portion is not blocked and light can be shared between the adjacent scintillation crystals
  • the plurality of scintillation crystals are fixed to each other with a transparent glue.
  • the sensor modules include a light guide disposed between the scintillator assembly and the row of photodetectors.
  • a sensor module for a PET scanner includes (i) a plurality of scintillation crystals with oppositely disposed converging faces and a plurality of light blocking elements interleaved with the plurality of scintillation crystals to form a scintillator assembly having a trapezoidal cross section; (ii) an end-face light blocking element fixed to an end face of the scintillator assembly, configured to block only a radially inner portion of the end face of the scintillator assembly such that a radially outer portion of the end face is not blocked; and (iii) a row of photodetectors fixed to an inner or outer face of the scintillator assembly operable to detect scintillation photons generated in the scintillator assembly.
  • the plurality of scintillation crystals are elongate slat crystals having a wedge shape with parallel outer and inner faces connected by converging faces.
  • the plurality of scintillation crystals have an inner face with a width of 0.5 mm or less, and a length of at least 40 mm.
  • the sensor module has six or fewer scintillation crystals. In an embodiment the light blocking elements are reflective.
  • At least some of the plurality of light blocking elements disposed between adjacent pairs of scintillation crystals in each sensor module extend from a radially inner end of adjacent scintillation crystals only part way to a radially outer end of the adjacent scintillation crystals, such that a radially outer portion of the adjacent crystals is not blocked by the light blocking element such that light can be shared between the adjacent scintillation crystals through the radially outer portion of the adjacent crystals.
  • the sensor module includes a light guide disposed between the scintillator assembly and the row of photodetectors.
  • FIGURE 1 is a schematic front view of a prior art PET detector, with a detail view of a detector module;
  • FIGURE 2 is a partially exploded view of a PET detector in accordance with the present invention.
  • FIGURE 3 is a front view of the scanner ring for the PET detector shown in FIGURE 2;
  • FIGURE 4 is an exploded view of one detector module of the PET detector shown in FIGURE 2;
  • FIGURE 5 is a front view of two detector modules of the PET detector shown in FIGURE 2.
  • FIGURE 2 illustrates an ultra-compact positron emission tomography scanner 100 in accordance with the present invention.
  • PET Positron emission tomography
  • a PET imaging system comprises three main components, a radioactive tracer that is administered to the subject to be scanned, a scanner that is operable to detect the location of the radioactive tracer (indirectly, as discussed below), and a tomographic image processing system.
  • the radioactive tracer includes a radioactive isotope and a metabolically active molecule.
  • the tracer is injected into the body to be scanned, wherein the metabolically active molecule allows the tracer to be metabolized in active cells.
  • the body After allowing time for the tracer to concentrate in certain tissues, the body (or a portion of the body) is positioned in the center channel of the annular PET scanner 100.
  • the radioactive decay event for tracers used in PET studies is positron emission. An emitted positron travels a short distance in the body tissue until it interacts with an electron. The positron and electron interact in an annihilation event that produces two 511 KeV anti-parallel photons.
  • the PET scanner 100 detects pairs of photons from annihilation events from detector modules on opposite sides of the annihilation event, essentially simultaneously.
  • a 511 KeV photon has a high energy and will pass through many materials, including body tissue. While the high energy allows the photon to travel through and exit the body, the high-energy photons are difficult to detect directly. Therefore, PET detectors are configured to detect the high-energy photons indirectly. Photon detection is the task of scintillator crystals 103 in the PET scanner 100. To detect a high-energy photon, sometimes referred to herein as a gamma photon, the scintillator crystal 103 absorbs or scatters (e.g., via Compton scattering) the gamma photon and emits a large number of low-energy photons (scintillation photons), which may be visible light photons.
  • gamma photon the scintillator crystal 103 absorbs or scatters (e.g., via Compton scattering) the gamma photon and emits a large number of low-energy photons (scintillation photons), which may be
  • the incident gamma photons typically produce lantthousands of scintillation photons in a very short flash or scintillation event.
  • the number of scintillation photons produced in the slat crystal 103 is proportional to the energy deposited by the gamma photon.
  • "slat crystal” is expressly defined to mean a scintillation crystal having a wedge shape with parallel inner and outer faces connected by converging faces.
  • the scintillation photons are readily detected with photodetectors 104 that may be placed on the radially outer or inner surface of the scintillator crystals, or on both the inner and outer surfaces.
  • Exemplary photodetectors 104 include photomultiplier tubes (PMT), avalanche photodiodes (APDs), Si-PIN photodiodes, silicon drift photodiodes, and silicon photomultipliers (SiPM).
  • the signals from the photodetectors 104 are analyzed to identify the relevant scintillation crystal 103 and determine the location of the scintillation event within the scintillation crystal 103 (preferably, in three spatial dimensions). The time of the scintillation event and the total energy of the event are also obtained.
  • Exemplary scintillation crystals include Nal(TI) (thallium-doped sodium iodide),
  • BGO bismuth germinate
  • LSO lutetium oxyorthosilicate
  • GSO gadolinium orthosilicate
  • LYSO cerium-doped lutetium yttrium orthosilicate
  • LuAP lutetium aluminum perovskite
  • LGSO LG Q 4Gdi gSiC ⁇ : 22.0 mol% Ce
  • LaBr 3 lanthanum bromide
  • lutetium fine silicate and the like.
  • Additional suitable scintillation crystals are disclosed in U.S. Pat. 7,132,060 to Zagumennyi et al., which is hereby incorporated by reference.
  • BGO when BGO interacts with high-energy radiation, such as gamma- rays or x-rays, it emits a green fluorescent light with a peak wavelength of 480 nm.
  • BGO is used for a wide range of applications in high-energy physics, nuclear physics, space physics, nuclear medicine, geological prospecting, and other industries.
  • LYSO crystal has the advantages of high light output and density, quick decay time, excellent energy resolution, and moderate cost. These properties make LYSO a good candidate for a range of detection applications in nuclear physics and nuclear medicine, which require improved timing and energy resolution. Not all scintillation materials are technically crystals.
  • the term "scintillation crystal” and "slat crystal” is defined to include a component formed from any suitable scintillation material.
  • the PET scanner 100 shown in FIGURE 2 comprises two scanner rings 110 and related front-end electronics 90.
  • FIGURE 3 shows a front view of the scanner ring 110.
  • the scanner rings 110 comprise a plurality of relatively narrow sensor modules 101 assembled to form an annulus. More or fewer scanner rings 110 are contemplated, and may be selected to accommodate a desired axial operative length.
  • the scanner ring 110 has 24 sensor modules 101. More or fewer modules may be used, and are contemplated by the present invention.
  • a scanner ring 110 in accordance with the present invention may include 100 detector modules 101, or more.
  • detector ring 110 includes between 50 and 70 detector modules 101.
  • the sensor modules 101 are generally trapezoidal in cross section and are formed with a plurality of elongate slat-shaped scintillation crystals (slat crystals) 103.
  • Light-blocking/reflecting element 106 for example, an opaque or reflective panel or coating, are interposed between opposing faces of the elongate scintillation crystals 103.
  • a light guide 105 is attached to a radially outer end of the scintillation crystals 103 in the sensor module 101.
  • An axially oriented row of photodetectors 104 are attached to the light guide 105, if present, or to the radially outer end of the scintillation crystals 103 in the sensor module 101.
  • ten or more photodetectors 104 may be provided along the length of the scintillation crystals 103.
  • the photodetectors 104 are configured to detect low-energy scintillation photons in the scintillator crystals 103.
  • the photodetectors 104 are operably connected to the front-end electronics 90.
  • the signals or information received from the photodetectors 104 is processed by front- end electronics 90 to determine the parameters or characteristics of the detected pulse (e.g., location, energy, timing).
  • the front-end electronics 90 may include, for example, one or more low-pass filters 96, analog-to-digital converters 97, and field programmable gate arrays 98.
  • the sensors comprise scintillators 103 and photodetectors 104.
  • the data is sent from the front-end electronics to a host computer 95 that performs tomographic image reconstruction.
  • FIGURE 4 An exploded view of the sensor module 101 is shown in FIGURE 4 (only one of the photodetectors 104 from the row of photodetectors is visible).
  • the sensor module 101 comprises five trapezoidal slat crystals 103A-103E.
  • the outboard slat crystals 103 A, 103E are similar in shape and mirror images in cross section.
  • Interior slat crystals 103B, 103D are similar in shape and mirror images in cross section.
  • the center slat crystal 103C has an isosceles cross-sectional shape. In other embodiments more or fewer slat crystals, and different crystal shapes may be used to form generally trapezoidal crystal modules.
  • the outboard slat crystal 103 A has an associated light-blocking or reflecting element 106A that is configured to extend along the outer face 113 A, from the inner end 114, and is sized to cover only a portion of the outer face 113A.
  • the light-blocking/reflecting element 106 A may cover between 50% and 80% of the area of the outer face 113 A.
  • the corresponding light-blocking/reflecting element 106 A from an adjacent sensor module 101 will similarly cover a portion of the outer face 113B of the outboard slat crystal 103E.
  • Two intermediate light-blocking/reflecting elements 106B are also provided.
  • One intermediate light-blocking/reflecting element 106B engages opposing faces of slat crystals 103 A and 103B, and is configured to cover only a portion of the opposing faces.
  • the other intermediate light-blocking/reflecting element 106B engages opposing faces of slat crystals 103D and 103E, and is configured to cover only a portion of the opposing faces.
  • the intermediate light-blocking/reflecting elements 106B may cover between 60% and 90% of the area of the opposing faces.
  • scintillation photons generated in slat crystals 103B or 103D may be shared with a neighboring outboard slat crystal 103 A, 103E and with a neighboring sensor module 101, by passing through adjacent slat crystals.
  • Two central light-blocking/reflecting elements 106C are also shown.
  • the central light-blocking/reflecting elements 106C are located on either side of the center slat crystal 103C and abut neighboring slat crystals 103B and 103D respectively.
  • the central light-blocking/reflecting elements 106C extend along the entire face of the associated slat crystals, and therefore prevent light sharing with or across the central slat crystal 103C.
  • the slat crystals 103 and light-blocking/reflecting elements 106 are joined with transparent glue 108.
  • the transparent glue 108 is provided between the light-sharing portions of the opposing faces of the slat crystals 103 that are not separated by a light-blocking/reflecting element.
  • the light guide 105 is fixed to an upper end of the slat crystals 103A-103E, and the row of photodetectors 104 are fixed to the light guide 105.
  • FIGURE 5 shows two adjacent sensor modules 101 from the scanner ring 110 shown in FIGURE 2.
  • the row of photodetectors 104 for the sensor module 101 on the left side is oriented at an angle A with respect to the row photodetectors 104 for the sensor module 101 on the right side.
  • a scintillation event S is illustrated schematically in slat crystal 103E of the sensor module 101 on the left side.
  • the scintillation photons generated are shared with slat crystal 103D of the sensor module 101 on the left side, and with slat crystals 103 A and 103B of the sensor module 101 on the right side.
  • the disclosed sensor module 101 has many advantages over related prior art PET detectors.
  • An important aspect of the sensor module 101 is that it is very compact, and therefore allows for the construction of very compact PET imaging systems.
  • All of the slat crystals 103 are trapezoidal in cross section, which has advantages in manufacturability and cost.
  • the trapezoidal slat crystals can be fabricated as relatively thin slats, allowing for greater image resolution.
  • each sensor module comprises six slats that are each 8 mm tall and 40 mm long.
  • the thickness of the slat crystals varies from 0.44 mm to 0.64 mm.
  • the sensor modules comprise four crystal slats that are each 10 mm tall and 40 mm long.
  • the thickness of the crystal slats varies from 0.71 mm to 1.11 mm. Therefore, in some embodiments the sensor module 101 comprises a plurality of slat crystals having a minimum thickness of less than 1.0 mm, and in some embodiments the sensor module 101 comprises a plurality of slat crystal having a minimum thickness of less than 0.5 mm.
  • a coincidence line source is stepped along the full length of the sensor module in 1 mm increments, and the light response function versus position is characterized.
  • the line source is perpendicular to the axial direction of the crystal array, and is created using a point source in coincidence with a thin linear array of discrete crystals. About 60,000 events are collected at each calibration position. The data are binned using simple Anger logic. The data are then separated into the crystal slat of interaction.
  • the detector After the detector is calibrated, two testing data sets are collected. The first is with the line source perpendicular to the crystal array, identical to the calibration data set. The second is with the line source entering the crystal array at a 45 degree angle.
  • the detectors were then evaluated for the following performance characteristics: slat decoding - peak to valley ration; energy resolution; intrinsic spatial resolution along the slat dimension; and the DOI positioning resolutions.
  • a new trapezoidal slat crystal PET detector is described above, using a shared photodetector design that can be implemented with thinner slats to improve spatial resolution and fewer slats, for better efficiency. Reducing the number of slat crystals in the sensor module allows taller slat crystals to be decoded without any loss in intrinsic spatial resolution along the axial and DOI directions.

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Abstract

L'invention concerne un scanner (100) de tomographie par émission de positrons (PET) comprenant des modules de détection trapézoïdaux (101) disposés de façon adjacente pour former un anneau de détection torique (110). Les modules de détection comprennent une pluralité de cristaux de scintillation (103) avec des éléments de blocage/réfléchissants de la lumière (106) entrelacés. Au moins l'élément réfléchissant de face d'extrémité recouvre uniquement une partie de la face du module de détection, de sorte que la lumière est partagée entre les modules de détection voisins. Un photodétecteur (104) et un guide de lumière (105) optionnel sont fixés à une face extérieure de la pluralité de cristaux de scintillation. Les photodétecteurs sont disposés selon un angle donné par rapport aux modules de détection voisins. Le partage de lumière entre les modules voisins permet aux modules d'être de petite taille, ce qui permet d'obtenir un dispositif très compact. Les signaux provenant des photodétecteurs sont traités avec un système informatique (90) configuré pour identifier l'emplacement tridimensionnel des événements de scintillation qui se produisent dans l'anneau de détection.
PCT/US2016/012386 2015-01-07 2016-01-06 Détecteur pet trapézoïdal compact avec partage de lumière WO2016112135A1 (fr)

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Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018214400A1 (fr) * 2017-05-25 2018-11-29 苏州瑞派宁科技有限公司 Système de tep hétérogène tridimensionnel
CN113009183A (zh) * 2019-12-20 2021-06-22 精工爱普生株式会社 传感器单元、电子设备以及移动体
US11841470B2 (en) 2019-01-08 2023-12-12 The Research Foundation For The State University Of New York Prismatoid light guide

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070096031A1 (en) * 2003-06-19 2007-05-03 Ideas As Modular radiation detector with scintillators and semiconductor photodiodes and integrated readout and method for assembly thereof
US20120138806A1 (en) * 2009-08-10 2012-06-07 Christopher John Holmes Novel radiation detector
US20120235047A1 (en) * 2009-10-27 2012-09-20 University Of Washington Through Its Center For Commercialization Optical-interface patterning for radiation detector crystals

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070096031A1 (en) * 2003-06-19 2007-05-03 Ideas As Modular radiation detector with scintillators and semiconductor photodiodes and integrated readout and method for assembly thereof
US20120138806A1 (en) * 2009-08-10 2012-06-07 Christopher John Holmes Novel radiation detector
US20120235047A1 (en) * 2009-10-27 2012-09-20 University Of Washington Through Its Center For Commercialization Optical-interface patterning for radiation detector crystals

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018214400A1 (fr) * 2017-05-25 2018-11-29 苏州瑞派宁科技有限公司 Système de tep hétérogène tridimensionnel
US11841470B2 (en) 2019-01-08 2023-12-12 The Research Foundation For The State University Of New York Prismatoid light guide
CN113009183A (zh) * 2019-12-20 2021-06-22 精工爱普生株式会社 传感器单元、电子设备以及移动体

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