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    • 专利摘要:
    The invention describes a gamma-ray compton camera system with flight time measurement comprising: - a plurality of detector modules (3), each comprising a material sensitive to gamma radiation and arranged in layers formed by one or more detector modules, said layers being arranged so as to interfere with an incoming gamma ray to absorb it partially or completely after one or more compton interactions, and are spatially separated to allow determining the temporal order of each gamma ray interaction within the camera system, - reading electronics and data acquisition system in which the signals from the detector modules will be read, digitized and sent to a processing unit, and capable of obtaining the 3d position, energy and the temporal sequential order of the interactions individual - compton photoelectric - produced by a single incident gamma ray, allowing the determination of the complete time sequence of all gamma-ray interactions within the gamma-ray detection volume. (Machine-translation by Google Translate, not legally binding)
    公开号:ES2629092A1
    申请号:ES201531580
    申请日:2015-11-04
    公开日:2017-08-07
    发明作者:José María Benlloch Baviera；Filomeno Sánchez Martínez；Antonio Javier GONZÁLEZ MARTÍNEZ
    申请人:Consejo Superior de Investigaciones Cientificas CSIC；Universidad Politecnica de Valencia；
    IPC主号:
    专利说明:

    GAMMA RAY COMPTON CAMERA SYSTEM WITH FLIGHT TIME MEASUREMENT
    TECHNICAL FIELD OF THE INVENTION
    The present invention is encompassed in the field of imaging and, more specifically in thefield of gamma ray imaging. The invention relates to the design of devices5 capable of detecting gamma radiation and obtaining information from it, for example,medical devices such as those used in imaging systems withnuclear techniques such as single-photon emission computed tomographyComputed Tomography ”(SPECT) or Positron Emission TomographyTomography ”) (PET) for medical diagnostic purposes or dose monitoring during
    10 irradiation in hadron therapy.
    However, it should be understood that the present invention is also applicable in many other fields of the art, such as gamma ray telescopes in astrophysics, nuclear power plant dismantling monitoring and national security.
    BACKGROUND OF THE INVENTION
    15 Compton cameras have been used in the past, especially in the field of gamma-ray astrophysics, to determine the energy and position in the sky of high-energy celestial gamma-ray emitters (Schönfelder, V. et al. , “Instrument description and performance of the imaging gamma ray telescope COMPTEL aboard the Compton Gamma-Ray Observatory.” ("Instrument description and performance of the COMPTEL telescope for gamma-ray imaging, on board the
    20 Compton Gamma Ray Observatory ”) The Astrophysical Journal Supplement Series, 86: 657–692, 1993, Boggs, S. et al.,“ Overview of the nuclear Compton telescope. ”New Astronomy Reviews, 48: 251-256, 2004). More recently, these types of devices have been proposed for imaging in Nuclear Medicine for diagnostic purposes, since they allow the reconstruction of radioisotope distributions that emit gamma rays.
    25 (Kahora, R. et al., "Advanced Compton camera system for nuclear medicine: Prototype system study.") Nuclear Science Symposium Conference Record, 2008 , Harkness, LJ et al., "Semiconductor detectors for Compton imaging in nuclear medicine", 2012, JINST 7 C01004.) ("Semiconductor detectors for Compton imaging in nuclear medicine",). Compton cameras have recently been proposed
    30 based on Si or CdTe (Studen, A. et al., “First coincidences in pre-clinical Compton camera prototype for medical imaging.” (Nucl first prototype matches for medical imaging, preclinical. ") Nucl . Instr. & Meth. 531 (2004) 258–264, Takeda, S. et al., “Applications and Imaging Techniques of a Si / CdTe Compton Gamma-Ray Camera.” (“Applications and imaging techniques of a Si camera / CdTe Compton of Gamma Rays. ") Physics Procedia 37 (2012) 859–866 due to
    35 excellent energy resolution of semiconductor technology. However, the semiconductor time resolution is very poor and does not allow a sequential development of all gamma ray interactions.
    All these devices, including the present invention, are based on the determination of the impact position of gamma ray interactions due to the dispersion by Compton effect (Fig. 1). The
    40 Compton dispersion dominates the gamma ray detection process for energies between 150 keV and 5 MeV.
    However, the most important limitation of the current Compton cameras is that the temporal resolution of the current systems does not allow to determine the order of the interactions detected in the different layers. In fact, one of the main challenges of data analysis of a Compton camera
    Combined is the reconstruction of the parameters of each original gamma ray from the measured data, which consist only of various measurements of energy and position.
    For the complex task of the reconstruction of the Compton time sequence, the detailed description of a multidimensional space destined to event data naturally leads to a discussion of the quality selection criteria of the possible events and their applicability to the different types of events. events, therefore it is very demanding from the point of view of computing, while still producing low quality images. Recently Compton cameras with recoil electron tracking capabilities have been proposed (Boggs, S. et al., "Report on the Advanced Compton Telescope vision mission study. 'Technical report", NASA, 2005.), ("Report on study of the advanced vision mission of the Compton Telescope. 'Technical report ", NASA, 2005), which allows the direction of the incident gamma ray to be confined within a reduced region of cone arc. However, these newly developed Compton cameras still lack information with the time accuracy necessary to effectively determine the Compton time sequence. In US 4124804 A "Compton scatter scintillation camera system" by S. Mirell, a method and apparatus for producing tomographic or transverse radiographic images 10 for which radiation is shown it is substantially confined to a single plane, and a conventional scintillation chamber located to detect the gamma radiation dispersed by the object In US Patent 20140110592 A1 "Compton camera detector systems for novel integrated compton-Pet and CT-compton-Pet radiation imaging "(" Compton camera detection systems for the new radiation imaging integrated by Compton-PET and CT
    15 compton-Pet "), by RS Nelson and WB Nelson, describes new designs of Compton camera detector, and systems for enhanced radiographic imaging with integrated detection systems that incorporate Compton imaging and imaging capabilities of nuclear medicine, PET imaging and X-ray CT imaging.
    In US-7573039 B2 "Compton camera configuration and imaging method"
    20 Compton camera and imaging method ") by BD Smith describes an approach to the selection of Compton camera shapes, configurations, positions, orientations, pathways, and sets of detector elements, for data collection for analysis using surface integral methods and integral line integral methods for reconstruction of Compton data In US-8384036 B2 "Positron emission tomography (PET) imaging using scattered
    25 and unscattered photons ”(“ Positron Emission Tomography (PET) imaging using scattered and non-dispersed photons ”) by M. Conti, the difference in TOF between the two gamma rays produced after positron annihilation is obtained . However, in this patent only coincident events are considered when a full energy gamma ray is detected in a first detector and a dispersed partial energy gamma ray in a second detector. In the patent
    30 US-8785864 B2 “Organic-scintillator Compton gamma ray telescope” (Kenneth N. Ricci et al. An apparatus and methods for imaging gamma ray sources with a large area are described, and a comparatively low-cost Compton telescope is claimed. In US-8809791 B2 "Continuous time-of-flight scatter simulation method" by P.
    35 Olivier and P. Khurd show a method to correct PET imaging data by simulating flight time dispersion.
    However, none of the designs shown in these patents allow to determine the complete temporal sequence of the interactions produced by a single incident gamma ray.
    The inability of current Nuclear Medicine devices to include Compton events
    40 scattered without degrading image quality is the most serious problem in increasing sensitivity in commercial scanners (PET and SPECT). This is due to the fact that current designs do not allow to properly determine the order of the interactions detected, produced by a single gamma ray incident within the gamma ray detection volume.
    When it comes to PET scanners, current technology focuses on detecting events
    45 photoelectric, since the position of the first interaction by Compton effect is unknown, and it is also not possible to distinguish Compton events in the detector, from Compton events that occur inside the body. Therefore, events that occur outside the photoelectric peak are rejected because they produce noise and blur in the image. However, these events could account for more than 50% of the events. Since PET works in coincident mode, the probability of detecting two
    50 photoelectric events is less than 25% (of the order of 20%). Therefore, a factor 5 in sensitivity could be gained if Compton events were recovered.
    PET image quality is limited due to several factors, including Compton events scattered inside the human body. Compton events scattered inside the body are rejected with current technology through the power window around the photoelectric peak. The contribution of the events dispersed within the photoelectric peak that come from dispersion in the crystal, or in the human body, is estimated and corrected. The proposed invention will significantly improve image quality by more efficient elimination of random and scattered events. The temporal resolution of the present invention will be used to directly reject random events. In addition, the detection of the temporal sequence of Compton and photoelectric events will be used to eliminate scattered events within the human body and random events by analyzing the kinematics of the complete positronelectron annihilation event.
    Brief Description of the Invention
    The present invention describes a Compton gamma camera system with TOF measurement ("flight time") capable of obtaining the 3D position and the energy of the interactions (Compton and photoelectric) and their relative time sequence by means of a determination accurate TOF for each interaction. The combination of the geometric design and the high temporal resolution of the system of the invention will allow the determination of the complete temporal sequence of all gamma ray interactions within the detector, including Compton interactions.
    With the present invention, the temporal sequence information will allow to completely determine the photoelectric Compton + temporal sequence. For these reasons, a milestone in the energy regime dominated by the Compton effect can be achieved by means of an instrument capable of effectively recording events that are the result of dispersion by the Compton effect. We assume that the gamma radiation incident with energy E0 is completely absorbed and that it deposits the energies E1, E2, and E3 in detectors 1, 2 and 3 (Fig. 1) at times t1, t2 and t3 respectively. Once the spatial situations, temporal sequences and energies of the interactions have been measured, the Compton kinematics will allow us to calculate the energy and direction (like a cone) of the incident gamma ray following the
    Compton equation:
    cos 1  2m ce2E 13E1E2 1 E3E  (one)
    The above equation can be easily extended if 2 or more than 3 interactions take place in the different detector modules.
    The present invention will allow to recover Compton events, including those in the reconstruction of the image, thus raising the total sensitivity.
    The present invention will improve the image quality of current Nuclear Medicine scanners, due to a much more efficient way of rejecting random and Compton scattering events. This will change the situation of the current scanners that 1) reject events that involve dispersion due to Compton effect, due to the lack of information with sufficient accuracy (while with the present invention such events are recovered and used in the reconstruction of the image) and 2) at the same time the current scanners accept events that involve dispersion by the Compton effect in the patient, while with the present invention such events are rejected.
    Even for SPECT the present invention will allow to reduce even more the background noise produced by the dispersion by Compton effect (in the body and / or in the collimator) and the external environmental contribution of the body.
    On the other hand, individual TOF measurements for each interaction of a gamma radiation event will improve image quality. Since different TOF measurements are connected through the well-known physical evolution of gamma ray event interactions, it is possible
    easily relate them through simple equations. For example, if the first gamma interaction occurred at position x1, y1, z1 and at time t1, and a second gamma interaction occurred at position x2, y2, z2 and at time t2, the delay time between these interactions gamma should be:
    t2  t1 
    x  x 2 y  and 2 z  z 2 / c (2)
    21 2121
    in which c is the speed of light. Therefore, if these interactions really belong to the same event, they must comply with the above equation. Otherwise, they are produced by different incident gamma rays. Thus, the application of the above equation should contribute to the reduction of events that produce false LORs (“response lines”) in PET and a reduction in the contribution of background noise in any device based on this invention (ie PET , SPECT, gamma ray telescopes, monitoring and dismantling of nuclear power plants, national security, among others).
    Each original gamma ray can suffer several interactions sequentially, giving rise, after each of these interactions, to a new gamma ray with different energy and direction. In accordance with the present invention, TOF is measured for each of these interactions, all of them belonging to the same event, generated by a single incident gamma ray. A key aspect of the invention is the differentiation between interaction and event, in accordance with the definitions given below.
    The proposed invention will increase the sensitivity of Nuclear Medicine devices, which will also imply a reduction in the dose administered to a patient, improving the diagnostic capacity thanks to the improved quality of the acquired image.
    Brief description of the figures
    Figure 1 shows the impact position of gamma ray interactions due to Compton dispersion.
    Figure 2 shows a modular design of a gamma ray detector. The invention is based on a modular design (Fig. 2, element 3).
    Figure 3 shows one of the preferred configurations of the Compton camera with flight time measurement, of the present invention, in which all the detector modules (3) are identical and are arranged such that they interfere with the incoming gamma ray ( 7), to fully absorb it after one or more Compton interactions.
    Figure 4 shows WLS fibers (wavelength shifters) (4) that can be used to drive the light from the different scintillator layers (1) towards the photosensors (2).
    Figure 5 shows another embodiment of the invention, in which the major scintillation surfaces of the detector modules are optically coupled to a reflective surface (5) and optionally, a front plate (6) can be optically coupled between the reflective surface ( 5) and the scintillator face.
    Figure 6 shows a detector module having one of its major scintillation surfaces covered with WLS fibers (4) coupled to photosensors (2) at one end of the WLS fibers, while the other major scintillation surface - opposite to the aforementioned - is covered by the reflecting surface (5).
    Figure 7 shows another embodiment similar to that of Figure 6, but in which the detector module has one of its largest scintillation surfaces covered with WLS fibers (4) coupled to photosensors (2) at both ends of the WLS fibers.
    Figure 8 shows a detector module having one of its major scintillation surfaces covered with WLS fibers (4) coupled to photosensors (2) at one end of the WLS fibers, while the other large scintillation surface is covered by a front plate (6) optically coupled between the reflecting surface (5) and the scintillator face.
    5 Figure 9 shows another embodiment similar to that of Figure 8, but the detector module has one of its largest scintillation surfaces covered with WLS fibers (4) coupled to photosensors (2) at both ends of the WLS fibers.
    Figure 10 shows a Positron Emission Tomography device according to the invention, in which the detector modules form concentric cylinders surrounding the object being
    10 studying.
    Figure 11 shows a cone angle in PET and how true coincidence events can be treated properly, regardless of whether they have suffered dispersion in the body or in the detector module (above) .
    Figur 11 - bottom left -: coincident event in which one of the gamma rays has suffered 15 dispersion within the human body.
    Figur 11 - bottom right -: event in random coincidence in which two positron interactions coincide by chance.
    Detailed description
    The invention will be described in more detail below with reference to the figures because they are illustrative of the different embodiments and are useful for understanding the invention.
    The present invention is essentially characterized in that the gamma ray detector is designed to distinguish in space and time between different interactions of Compton and photoelectric gamma rays within the gamma ray detector, measuring the 3D position of impact and time, and recording this information to be analyzed later.
    25 Definitions
    "Monolithic crystal", "monolithic scintillation crystal", "continuous crystal" and "continuous scintillator crystal" are used interchangeably.
    - "Detector module" refers to a structure, flat or curved, preferably flat or laminar, comprising any material sensitive to gamma radiation. Detector Modules
    According to the invention they can have any shape, such as polygonal shape, and any size. However, unless otherwise specified, when referring to particular embodiments, the detector modules have a parallelogram shape - for example rectangular -, in which we distinguish two "larger surfaces" such as large flat surfaces and four "surfaces narrower sides ”“ narrower edge surfaces ”such as side edges.
    35 "" major surface "," large scintillator face "," scintillator face "," scintillator surface "and" major scintillator surface "are used interchangeably when referring to the larger surfaces of the detector modules that They comprise scintillating material.
    “Interaction: each of the impacts suffered by an incident gamma ray against a surface such as a detector module.
    40 "event" defines the total number of interactions that a single incident gamma ray undergoes until its energy is totally or partially lost.
    "Light reflecting surface" and "reflective optical surface" are synonyms.
    "Gamma ray detector" and "gamma ray detector volume" are used interchangeably.
    "Temporal order" and "temporal sequence" are expressions used interchangeably.
    The present invention relates to a Compton gamma ray camera system with measurement of flight time comprising:
    - a plurality of detector modules (3), each detector module comprises a gamma radiation sensitive material, preferably a scintillator crystal (1), for example, as shown in Figure 1,
    - said detector modules (3) are arranged in layers formed by individual detector modules, or by sets of detector modules, said layers are arranged such that they interfere with an incident gamma ray to absorb it completely or partially after one or more Compton interactions, and are spatially separated to allow order determination
    10 temporal sequence of each gamma ray interaction within the camera system,
    - Reading electronics and Data Acquisition System in which the signals from the detector modules (3) will be read, digitized and sent to the processing unit for further analysis, and that is capable of obtaining the 3D position, energy and the order of the temporal sequence of the individual interactions - Compton and photoelectric - produced by a single gamma ray
    15 incident, allowing the determination of the complete temporal sequence of all gamma ray interactions within the volume of the gamma ray detector.
    The detector modules exclusively comprise a gamma-sensitive material in the case of using solid state detectors, and additionally comprise photodetectors in the case of using scintillation crystals and / or Cherenkov radiators.
    The present invention also relates to a Compton gamma ray camera system with measurement of flight time according to any one of the dependent claims.
    According to particular embodiments of the TOF Compton gamma camera system of the invention, at least one detector module comprises a scintillator crystal (1) as a gamma radiation sensitive material, optically coupled to series of photosensors (2).
    The photosensors (2) can be coupled to the scintillator crystal (1) through at least one of the narrowest lateral surfaces of each scintillator crystal (1).
    The scintillator crystal (1) can be a monolithic scintillator crystal or a pixelated scintillator crystal. In a Compton chamber with TOF measurement according to the invention, the detector modules comprising a monolithic scintillator crystal can be combined with detector modules that
    30 comprises a pixilated scintillator crystal, or all detector modules may be identical in terms of their composition and / or structure
    Each detector module may be adjacent to another in a particular assembly and each assembly may be arranged with respect to another forming a layer structure, which may have the appearance of a closed structure as in Figure 10, or of an open structure. With this provision each
    35 set corresponds to one layer. The layers are separated from each other by a distance ranging from several millimeters to several centimeters, as mentioned above.
    In the system of the invention a set of detector modules (3) can be formed by two or more detector modules (3), depending on the size of the device and the needs imposed by the intended use. For example, in Figure 10 the smallest set of detector modules is the
    40 which forms the dodecagon in the center, which includes twelve detector modules, while in the outermost set corresponding to the tenth layer, the number of detector modules is considerably higher.
    The detector modules in a particular specific set may be identical or different. Sets of detector modules in a Compton gamma camera system with TOF measurement according to
    The invention may be identical or different with respect to the number of detector modules, the shape of the detector modules, as well as the composition and / or structure of the detector modules.
    The detector modules in a set can be identical with respect to their shape, or different. They can be flat or curved, although planes are preferred. They are always arranged so that they interfere with the incoming gamma ray, in order to absorb it completely after one or more Compton interactions. The way in which the detector modules are arranged can be, by
    5 example, parallel to each other, but other configurations are possible, provided they reach the objective mentioned here.
    The detector modules may have a polygonal shape, preferably parallelogram, and more preferably have a rectangular shape.
    In particular embodiments of the Compton camera system with gamma ray TOF measurement of
    10 the invention, the photosensors are coupled to the detector modules through at least one of their faces. In the case that the detector modules have a parallelogram shape, they are coupled to photosensors at least through one of their lateral surfaces (narrower surfaces) or at least through one of their larger surfaces. The photosensors can be arranged on both side edges of a detector module, or through one or both major surfaces, or
    15 combinations of any of these alternatives mentioned. When the photosensors are arranged on the "larger surfaces" it is preferable that they are coupled through light guides, as shown in Figure 4.
    The gamma-sensitive material in the detector modules can be of any type. Detector modules or sets of detector modules in a system according to the invention
    20 may comprise the same gamma-sensitive material or different materials.
    Materials can be used as solid-state detectors for the gamma ray detection volume, with the proviso that their decay time is fast enough to provide accurate time sequence information. It is also desirable that the gamma ray detector be constructed with a material with low atomic number (Z) to favor interaction
    25 Compton of the gamma ray Compton within its sensitive volume.
    Examples of solid state detectors are semiconductors such as Si, Ge, CdTe, GaAs, PbI2, HgI2, CZT, or HgCdTe (also known as CTM). Cherenkov radiators such as PbF2, NaBi (WO4) 2, PbWO4, MgF2, C6F14, C4F10, silica airgel can also be used. Scintillators such as organic scintillation crystals, inorganic scintillation crystals, liquid scintillators or gaseous scintillators can also be used. The scintillators can produce a signal that is due to both scintillation processes and Cherenkov processes. The invention is not limited to reading and processing by the Data Acquisition System (DAQ) the light produced by the scintillation process as usual. The Cherenkov light component can also be processed in the same way as the scintillation light, and be used for the precise determination of the time in the
    35 that the interaction occurs.
    For example, detector modules may comprise scintillating organic crystals such as anthracene, stilbene, naphthalene, liquid scintillators (for example, organic liquids such as pterfenyl (C18H14), 2- (4-biphenyl) -5-phenyl-1,3,4- oxadiazole PBD (C20H14N2O), butyl PBD (C24H22N2O), PPO (C15H11NO) dissolved in solvents such as toluene, xylene, benzene, phenylcyclohexane, triethylbenzene or
    40 decalin), gaseous scintillators (such as nitrogen, helium, argon, krypton, or xenon), inorganic crystal scintillators, or combinations of any of them. "Combination" means that a detector module - or several - can be made for example of an inorganic scintillator crystal and another - or others - can comprise a liquid scintillator.
    Commonly known scintillation crystals can be used, for example, cesium iodide (CsI),
    45 cesium iodide doped with thallium (CsI (Tl)), bismuth germanate (BGO), sodium iodide doped with thallium (NaI (Tl)), barium fluoride (BaF2), calcium fluoride doped with europium (CaF2 (Eu )), cadmium tungstate (CdWO4), lanthanium chloride doped with cerium (LaCb (Ce)), yttrium silicate doped with cerium (LuYSiOs (Ce) (YAG (Ce)), zinc sulphide doped with silver (ZnS (Ag)) or cerium doped aluminum garnet (III) Y3Al5O12 (Ce), LYSO Additional examples are CsF, KI (Tl), CaF2 (Eu), Gd2SiO5 [Ce]
    50 (GSO), LSO.
    The scintillators used in any of the embodiments described herein, and in general, the scintillators according to the present invention, can be monolithic crystals or pixelated crystals, or combinations thereof. Preferably the scintillator is, however, a single crystal since the pixelated crystals introduce more areas of dead space into the lightning detector
    5 gamma, thus providing a lower sensitivity of the detector compared to that of the monocrystals.
    According to particular embodiments, the monolithic scintillator crystal for the different detector modules (3) is selected from LaBr3 (Ce) or liquid Xe, or combinations thereof.
    In accordance with additional particular embodiments the monolithic scintillator crystal is
    10 selected from LaBr3 (Ce) for one or more detector modules and LYSO for other detector modules.
    The photosensors (2) can be series of SiPms, single photon avalanche diodes (SPADs), digital SiPms, avalanche photodiodes, position sensitive photomultipliers, photomultipliers, phototransistors, photodiodes, photo-ICs or combinations thereof for the various detector modules (3).
    This means that a detector module can be coupled, for example, to a series of SiPms and another detector module can be coupled to a series of phototransistors in a system according to the invention. Alternatively, all detector modules can be coupled to the same type of photosensors.
    In particular embodiments of the system according to the invention, those for which the
    20 detector modules comprise scintillation crystals, wavelength shifters - WLS - can be used. According to particular embodiments, at least one of the detector modules comprises a scintillator crystal, preferably a rectangular scintillator crystal, comprising wavelength shifting fibers - WLS - (4) coupled to one or more of the scintillator surfaces to drive the light of the scintillating glass (1) towards the photosensors (2).
    In accordance with particular embodiments of the invention, those in which the detector modules comprise scintillation crystals, at least one of the detector modules has one of, or both, greater scintillation surfaces optically coupled to a reflective surface (5) . In addition, for these embodiments there may be a faceplate (6), optionally, optically coupled between the reflecting surface (5) and one of the major scintillation surfaces.
    30 The function of the reflecting surface is to reflect the light that reaches the surface of the scintillator with which it is in contact, so that the photosensors can detect this light. The reflective surface may be any reflective surface, such as an optical reflective surface.
    The faceplate, also called fiber optic faceplate, is a surface or sheet made of tiny optical fibers, which have the function of transmitting only light that meets a requirement
    35 specific to the angle of incidence. Thanks to its design, only photons with an incidence angle below a critical value are transmitted (which depends on the type of front plate and the refractive index of the medium to which the plate is attached). The function of the faceplate is therefore to limit the angle of acceptance of the light produced by the scintillator. They can also be used to avoid the edge effect in the light produced by the scintillation crystals.
    According to particular additional embodiments, at least one of the detector modules comprises a scintillating material, preferably a scintillating crystal, and has one of its largest scintillation surfaces covered with WLS fibers (4), coupled to photosensors (2) in one or at both ends of the WLS fibers, while the other major scintillating surface - opposite to that mentioned - is covered by the reflector (5) (Fig. 6-7). For these particular embodiments, at
    At least one of the detector modules can have one or both major scintillating surfaces covered with WLS fibers (4) coupled to photosensors (2) at one or both ends of the WLS fibers.
    In other embodiments of the invention (Fig. 5), those in which the detector modules comprise scintillating crystals, one or both major scintillating surfaces of at least one detector module is optically coupled to a reflecting surface (5), for example, a retroreflector.
    Optionally, a faceplate (6) can be optically coupled between the reflecting surface (5) and the scintillator face (Fig. 5).
    According to particular additional embodiments, those in which the detector modules comprise scintillation crystals, at least one of the detector modules has one of its
    5 major scintillating surfaces covered with WLS fibers (4) coupled to photosensors (2) at one or both ends of the WLS fibers, while the other of the major scintillating surfaces is optionally covered with an optically coupled front plate (6) between the reflector (5) and the scintillator face, as shown in Figs. 8 and 9.
    According to particular additional embodiments, the reflecting surface (5) present in at least
    10 one of the detector modules is selected between a retroreflector and a light absorbing surface.
    The present invention also relates to a gamma radiation imaging device comprising a Compton gamma ray camera system with TOF measurement, as defined above.
    According to particular embodiments, said device is a Positron Emission Tomography device.
    A Positron Emission Tomography device according to the invention may have detector modules forming concentric cylinders surrounding an object under study as shown in Fig. 10, or the detector modules may form concentric cylinders that do not constitute a
    20 closed geometry - open geometry -.
    There may be different implementations of the invention, but the main feature for all of them is that Compton and photoelectric interactions can be distinguished in space and time.
    According to additional particular embodiments of the invention, there may be photosensors connected to the reading electronics and the Data Acquisition System (DAQ) in which the
    25 signals from the detection modules can be read simultaneously, digitized and sent to the processing unit for further analysis. The position of the interaction point can be determined from the distribution of the light produced in the scintillator crystal.
    The present invention can be used to implement PET or SPECT detectors compatible with MRI ("Magnetic Resonance Imaging," nuclear magnetic resonance imaging) set
    30 that the photosensors may be located well outside the sensitive region of the MRI (if the WLS + PSPMT configuration is used) or may be located even within the sensitive region MRI, in which strong magnetic fields are produced by the MRI (in in this case, SiPMs photosensors and / or APDs are used as photosensors).
    The flight time according to the present invention and for any embodiment thereof, can be
    35 obtained using conventional methods known in the art Phys. Med. Biol. 60 (2015) 4635-4649, "Sub-100 ps coincidence time resolution for positron emission tomography with LSO: Ce codoped with Ca", (coincidence time resolution Sub-100 ps for Positron Emission Tomography with LCS: Ce co-doped with Ca ”) by Stefan Gundacker et. to the. it discloses how to obtain the temporal sequence of all the interactions that a single incident gamma ray has suffered.
    Different aspects and embodiments of the invention are illustrated in the figures that are described in greater detail below:
    Fig. 1: In this figure we show a schematic view of a Compton chamber with TOF measurement comprising several layers - each formed by a set of detector modules - in which gamma radiation undergoes multiple Compton dispersions. The thickness of each layer depends on the scintillation material and the energy of the gamma ray and can vary from an order of mm to an order of centimeters (ie, approximately 3 mm thick if LaBr3 (Ce) is used). It should be noted that although the interaction positions are shown in Figure 3, the conceptual design does not change at all and can be easily extended if only 2, or more than 3 interactions take place.
    different detector modules. Compton cameras of the state of the art do not allow the temporal sequential determination of these interactions.
    Each detector module may be adjacent to another in a specific assembly and may be arranged with respect to another assembly forming a layer structure as shown in this figure, or 5 may have a closed cylindrical structure as shown in Figure 10, or An open structure.
    In the system of the invention a set of detector modules may be formed by two or more detector modules (3), depending on the size of the device and the needs imposed or the intended use. In Figure 1 you can see five detector modules in each set, or layer. For example, in Figure 10 the smallest set of detector modules is the one that forms a
    10 dodecagon in the center, including twelve detector modules, while the outermost set corresponding to the tenth layer has a considerably larger number of detector modules.
    Fig. 2: concept of detector module. In one of the preferred configurations as shown in Figure 2, each detector module (left, 3) consists of a single monolithic scintillator crystal (also called continuous) (Fig. 2, right, element 1) coupled to photosensors (Fig. 2, right, item 2) to read the light produced in the crystal by the interaction of the gamma ray. The monolithic scintillator crystal may comprise any of the materials mentioned above. In a preferred configuration the monolithic scintillator crystal (1) will comprise LaBr3 (Ce) and will be surrounded on the narrowest surfaces (side edges) by series of SiPM pixels as photosensors (2). The combination of fast decay and high performance light scintillator together
    20 with the rapid reading of light produced by the SiPMs photosensors will ensure the ability of the proposed invention to completely determine the photoelectric Compton + sequence of the incident gamma ray, both in space and time.
    Fig. 3: In this figure we show one of the preferred configurations of the Compton camera with flight time measurement, in which all the detector modules (3) are identical and are arranged in such a way that they interfere with the incoming gamma ray ( 7), to fully absorb it after one or more Compton interactions. The thickness of these layers of detector modules or individual detector modules is selected so as to minimize the occurrence of multiple Compton dispersions in the same detector module originating from the same incoming gamma ray ray (i.e., approximately 3 mm thick if use LaBr3 (Ce) as scintillator). Without
    However, the preferred thickness range in this case may vary between 1 mm to 4 mm. However, it should be mentioned that the preferred thickness depends on the scintillation material used and the energy of the incident gamma ray. For an incident energy of 511 keV the preferred thickness, if another material other than LaBr3 (Ce) is used, should have the same probability of gamma ray absorption as that of the previously mentioned preferred thickness range (1-4 mm) of LaBr3 ).
    35 The separation distance between two layers of detector modules can vary over a range that depends on how accurately the time at which the interaction occurs can be measured. Therefore, it is not appropriate to give numerical values for the interval, but it is sufficient to indicate that it varies between a magnitude of the order of millimeters and an order of centimeters. In fact, the upper limit will be imposed simply by the size of the Compton camera, while the lower limit will come
    40 imposed by the accuracy of the device. For practical reasons (full detector size and cost) the smaller the distance between layers of detector modules the better, while ensuring the identification of the temporal order of impact sequence.
    The different layers of detector modules can be separated, for example, by a distance (from several millimeters to even several centimeters) to allow order determination
    45 of each gamma ray interaction within the camera system. The number of layers of Compton camera modules with flight time measurement (10 in this figure) can vary arbitrarily without limiting the generality of the foregoing.
    Fig. 4: above, left, in a further embodiment, WLS ("Wave Length Shifter") fibers (Fig. 4, element 4) can be used to drive the light of the various scintillation detector modules (1) towards the 50 photosensors ( 2). Some WLS fibers have good properties that not only adjust the length of
    Light wave emitted with the absorption length, but also have a long attenuation of the light re-emitted (typically around 4 meters).
    In accordance with this embodiment, series of SiPMs, APDs or position sensitive photomultipliers (Position Sensitive Photomultipliers (PSPMTs)) can be used. Both major surfaces
    5 scintillators of a detector module may be covered by WLS fibers - as in the figure - or, according to an alternative embodiment, only one of the major scintillating surfaces is covered by WLS fibers.
    WLS fibers can be arranged in different configurations to optimize the amount of light collected and the spatial information of the light distribution (directly related to the
    10 spatial resolution).
    WLS fibers may be made of any material known in the art for this purpose, such as p-terphenyl (PT) and tetraphenyl butadiene (TPB). The decision on the material depends on the light generated by the scintillator and the optical window of the photomultiplier used. The thickness of the WLS fibers may vary depending on the size of the Compton chamber and the particular needs depending on the use that
    15 is intended. For example, they can be 1.5 mm thick.
    Above, right, Fig. 4b: a hybrid solution can be used for the photosensor configuration, as follows:
    - WLS can be present on one of the major scintillating surfaces coupled to photosensors (here you can use series of SiPMs, digital SiPMs, APDs, avalanche diodes of
    20 single photon (SPADs) or position sensitive photomultipliers (PSPMTs) while around narrower edge surfaces can be used as photosensors (2 ’) series of SiPMs, digital SiPMs, APDs and / or SPADs.
    - WLS can be present on both - as shown in the figure - major scintillating surfaces coupled to photosensors (here you can use series of SiPMs, digital SiPMs, APDs,
    25 single photon avalanche diodes (SPADs) or position sensitive photomultipliers (PSPMTs) while around narrower edge surfaces can be used as photosensors (2 ’) SiPMs, digital SiPMs, APDs and / or SPADs.
    Bottom center: Photosensors (2) can be arranged at both ends of the WLS fibers (4) to increase the amount of light emitted by the scintillator that can be collected by the system. This
    30 configuration maximizes the amount of light transmitted from the scintillator (1) to the photosensory devices (2). Alternatively, photosensors (2) can be arranged at the end of the WLS fibers (4) in the case where only one of the major scintillating surfaces is covered by WLS fibers. This embodiment can also be considered without photosensors all around the narrowest edge surfaces (2 ’).
    Fig. 5: Left: in this figure we show another embodiment of the detector module, in which both major scintillating surfaces are optically coupled to a reflector (5) such as a retroreflector. Right: Additionally, a faceplate (6) can be attached between the reflector (5) and the scintillator face. In both cases both scintillator surfaces are coupled to photosensors (1 + 2).
    Fig. 6: in this figure we show another embodiment, in which one of the major scintillating surfaces of at least one detector module is covered with WLS fibers (4) coupled to photosensors (2) at one end of the WLS fibers , while the other major scintillating surface is covered with the reflector (5). The narrower surfaces of the edge of the scintillator can be covered (right), or not covered (left), with photosensors (2).
    Fig. 7: in this figure we show another embodiment, in which one of the major scintillating surfaces of at least one detector module is covered with WLS fibers (4) coupled to photosensors (2) at both ends of the WLS fibers, while that the other major scintillating surface is covered with the reflector (5). The narrower surfaces of the edge of the scintillator can be covered (right), or not covered (left), with photosensors (2).
    Fig. 8: in this figure we show another embodiment, in which one of the major scintillating surfaces of at least one detector module is covered with WLS fibers (4) coupled to photosensors (2) at one end of the WLS fibers, while the other major scintillating surface is covered by a front plate (6) optically coupled between the reflector (5) and the face
    5 of the scintillator. The narrower surfaces of the edge of the scintillator can be covered (right), or not covered (left), with photosensors (2).
    Fig. 9: in this figure we show another embodiment, in which one of the major scintillating surfaces of at least one detector module is covered with WLS fibers (4) coupled to photosensors (2) at both ends of the WLS fibers, while the other major surface
    The scintillator is covered by a front plate (6) optically coupled between the reflector (5) and the scintillator face. The narrower surfaces of the edge of the scintillator can be covered (right), or not covered (left), with photosensors (2).
    Fig. 10: In this figure we show an embodiment of the invention for PET applications in which the detector modules (3) form concentric cylinders surrounding the object under study. Ten layers
    15 of detector modules can be seen and each of them is composed of an increasing number of "detector modules" as we move away from the center, to achieve a closed geometry. An essential aspect is that the distance between the layers is sufficient for the precision in the TOF measurement to distinguish the temporal sequence of impacts ("interactions") produced by a single incident gamma ray ("event").
    20 The dimensions (D, d, H, and h), including the number of layers of the device can be adjusted for different applications. The detector modules may include WLS (4) coupled to photosensors (2) as shown in Fig. 4 and / or to a reflector (5) / faceplates (6) as shown in Figs. 5-9.
    The annular structure allows a complete coverage of the desired field of vision, while the
    The number of layers allows a high detection efficiency for 511 keV gamma rays. The dimensions (D, d, H, and h), including the number of layers of the device can be adjusted for different applications. In a preferred embodiment the layers of detector modules (3) comprise LaBr3 (Ce) approximately 3 mm thick separated by approximately 3 cm from each other. In this case, a flight time resolution of 80 ps is assumed to sequentially distinguish the
    30 different Compton interactions in the detector module layers. In Fig. 10, the detector modules may include WLS (4) coupled to photosensors (2) as shown in Fig. 4, to effectively increase the amount of light collected and / or a reflector (5) / faceplates (6) optically coupled to major scintillating surfaces not covered by WLS (Figs. 5-9). The amount of light collected is directly related to the resolution of the energy and the temporal sequence. A good one
    Energy resolution is crucial for an accurate determination of the angle of the Compton cone (Fig. 1, equation. 1). The PET Compton cone angle will be used to reject scattering events within the body to be examined, and random events that produce casual coincidental events (Fig. 11).
    Fig. 11: in a PET application of the invention the events in true coincidence can be
    40 handled properly, regardless of whether they have been dispersed in the body or in the detector module. Above: a true coincidence event in which both gamma rays whose initial energy was E0 = 511 keV, produced a Compton interaction within the detector. The gamma ray that goes down (up) interacts with t1 (t3) by depositing the energy E1 (E3) and the scattered gamma ray interacts with t2 (t4) by depositing the energy E2 (E4). In the current PET this event would be ruled out.
    45 since there is no way to know the time sequence and consequently the LOR cannot be determined uniquely. It should be noted that both cones of the possible directions of the two original rays intersect with the LOR. Bottom left: a coincidence event in which one of the gamma rays has suffered dispersion within the human body. These events produce noise in the image due to the false LOR (8) that is obtained as a result of joining the two with a straight line
    50 interaction points in the detector. In the current PET scanners these events are rejected purely based on energy information. The present invention allows a much more effective rejection of these events based on the careful analysis of the event: neither of Compton's two cones intersects the false LOR (8). Bottom right: random coincidence event in which two positron interactions coincide casually over time. A careful analysis of the event also allows to reject random events. In these cases it is also possible to determine the true LOR (9).
    权利要求:
    Claims (16)
    [1]
    1. A Compton gamma camera system with measurement of flight time comprising:
    - a plurality of detector modules (3), each detector module comprises a material sensitive to gamma radiation,
    5 - said detector modules (3) are arranged in layers formed by individual detector modules, or by sets of detector modules, said layers are arranged such that they interfere with an incident gamma ray to absorb it completely or partially after one or more Compton interactions , and are spatially separated to allow the determination of the temporal sequence order of each gamma ray interaction within
    10 camera system,
    - Reading electronics and Data Acquisition System in which the signals from the detector modules (3) will be read, digitized and sent to the processing unit for further analysis, and that is capable of obtaining the 3D position, energy and the order of the temporal sequence of individual interactions - Compton and photoelectric - produced by a single incident gamma ray,
    15 allowing the determination of the complete temporal sequence of all gamma ray interactions within the volume of the gamma ray detector.
    [2]
    2. A system according to claim 1, wherein at least one detector module comprises scintillation crystals (1) as radiation sensitive material, optically coupled to series of photosensors (2).
    A system according to claim 2, in which there are photosensors (2) coupled to the scintillator crystal
    (1) through at least one of the narrowest lateral surfaces of each scintillator crystal (1).
    [4]
    Four. A system according to any one of claims 2 to 3, wherein the scintillation crystal is a monolithic scintillator crystal (1).
    [5]
    5. A system according to claim 4, wherein the monolithic scintillator crystal (1) is selected
    25 between an organic scintillator crystal, inorganic scintillator crystal, liquid scintillator, gas scintillator or combinations thereof for the various detector modules (3).
    [6]
    6. A system according to claim 4, wherein the monolithic scintillator crystal (1) is selected from LaBr3 (Ce) or liquid Xe or combinations thereof for the different detector modules (3).
    [7]
    7. A system according to claim 2, wherein the scintillating crystal (1) is a pixelated crystal.
    A system according to claim 2, wherein the scintillator crystal (1) is a combination of a pixelated crystal for at least one detector module and at least one monolithic scintillator crystal for at least another of the detector modules.
    [9]
    9. A system according to any one of claims 2 to 8, wherein the photosensors (2) are series of SiPms, single photon avalanche diodes (SPADs), digital SiPms, avalanche photodiodes,
    35 position-sensitive photomultipliers, photomultipliers, phototransistors, photodiodes, photo-ICs or combinations thereof for the different detector modules (3).
    [10]
    10. A system according to any one of claims 2 to 9, wherein at least one of the detector modules (3) comprises wavelength shifting fibers -WLS- (4) coupled to one or more of its scintillating surfaces for lead the light from the scintillator glass (1) towards the
    40 photosensors (2).
    [11]
    11. A system according to any one of claims 2 to 10, wherein at least one of the detector modules (3) has one of the two, or both, major scintillating surfaces optically coupled to a reflecting surface (5).
    [12]
    12. A system according to any one of claims 2 to 11, wherein at least one of the 45 detector modules (3) has a front plate (6) optically coupled between the surface of the reflector
    (5) and at least one of its major scintillating surfaces.
    [13]
    13. A system according to any one of claims 2 to 10, wherein at least one of the detector modules (3) has one of its largest scintillating surfaces covered with WLS fibers (4) coupled to photosensors (2) in each other. both ends of the WLS fibers, while the opposite end of the major scintillating surface is coupled to a reflective surface (5).
    A system according to any one of claims 2 to 10, wherein at least one of the detector modules (3) has one of its largest scintillating surfaces covered with WLS fibers (4) coupled to photosensors (2) in one at both ends of the WLS fibers, while the other of the major scintillating surfaces is covered by a front plate (6) optically coupled between the reflector (5) and a scintillator face.
    A system according to any one of claims 11 to 14, wherein the reflective surface (5) in at least one of the detector modules (3) is selected between a retroreflector and a light absorbing surface.
    [16]
    16. A system according to claim 1, wherein at least one of the detector modules (3) is made of a solid state detector.
    A system according to any one of claims 1 to 4, or any one of claims 7 to 15, wherein at least one of the detector modules (3) comprises Cherenkov radiators as a gamma radiation sensitive material ( one).
    [18]
    18. An imaging device with gamma ray sources, comprising the system defined in any one of claims 1 to 17.
    A device according to claim 18, which is a Positron Emission Tomography device comprising the system defined in any one of claims 1 to 17.
    [20]
    20. A device according to claim 19, which is a Positron Emission Tomography device in which the detector modules form concentric cylinders surrounding the object under study.
    21. A device according to claim 19, which is a Positron Emission Tomography device in which the detector modules form concentric cylinders that are not closed - open geometry -.
    [22]
    22. Use of the system defined in any one of claims 1 to 17, or of the device of any one of claims 18 to 21, in obtaining images by nuclear techniques.
    Use of the system defined in any one of claims 1 to 17, or of the device of any one of claims 18 to 21, in gamma ray astrophysics telescopes.
    [24]
    24. Use of the system defined in any one of claims 1 to 17, or of the device of any one of claims 18 to 21 in the monitoring or dismantling of nuclear power plants.
     Fig. 1
     Fig. 2 Fig. 3
     Fig. 4 Fig. 5
    Fig. 6 Fig. 7
    Fig. 8 Fig. 9
     Fig. 10 Fig. 11
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    PCT/ES2016/070783| WO2017077164A1|2015-11-04|2016-11-04|Compton gamma-ray camera system with time-of-flight measurement|
    US15/970,174| US10281594B2|2015-11-04|2018-05-03|Gamma-ray Compton TOF camera system|
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