WO1997044684A1 - Detecteur d'imagerie pour imageur polyvalent de medecine nucleaire - Google Patents

Detecteur d'imagerie pour imageur polyvalent de medecine nucleaire Download PDF

Info

Publication number
WO1997044684A1
WO1997044684A1 PCT/US1997/007714 US9707714W WO9744684A1 WO 1997044684 A1 WO1997044684 A1 WO 1997044684A1 US 9707714 W US9707714 W US 9707714W WO 9744684 A1 WO9744684 A1 WO 9744684A1
Authority
WO
WIPO (PCT)
Prior art keywords
light
layers
scintillation crystal
detector
scintillation
Prior art date
Application number
PCT/US1997/007714
Other languages
English (en)
Inventor
Vladimir Bosnjakovic
Original Assignee
Adac Laboratories
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Adac Laboratories filed Critical Adac Laboratories
Priority to AU31181/97A priority Critical patent/AU3118197A/en
Publication of WO1997044684A1 publication Critical patent/WO1997044684A1/fr
Priority to US09/165,160 priority patent/US6194728B1/en

Links

Classifications

    • 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
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/164—Scintigraphy
    • G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
    • G01T1/1648—Ancillary equipment for scintillation cameras, e.g. reference markers, devices for removing motion artifacts, calibration devices
    • 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
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/164—Scintigraphy
    • G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
    • G01T1/1642—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras using a scintillation crystal and position sensing photodetector arrays, e.g. ANGER cameras
    • 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

Definitions

  • the present invention pertains to the field of medical imaging equipment. More particularly, the present invention relates to a system for performing both planar studies as well as single-photon emission and positron emission tomography. BACKGROUND OF THE INVENTION
  • GSCs gamma scintillation cameras
  • position sensitive continuous-area detectors
  • PET scanners the second type of PET scanners.
  • the first type deals with the single photon gamma emitters enabling planar static and dynamic studies as well as SPECT, while the second type enables tomographic imaging of the positron emitters, i.e., PET studies.
  • Both techniques enable direct imaging of biochemical processes "in vivo” (especially, the PET technique) and the study of physiological processes and dysfunctions in a quantitative manner.
  • imaging systems for both types of techniques are rather expensive.
  • Position sensitive area detectors of the GSC type are made with the thin Nal(TI) crystals for optimal imaging detection of the low energy single photon gamma emitters; here, optimal imaging detection assumes an optimal spatial resolution for energies up to 150 KeV, with a shortage of the detection efficiency for medium and higher energies of single photon gamma emitters (250 and 360 KeV) being significantly reduced. Such a reduced efficiency makes the detection of high energy photon emissions, such as the ones of 511 KeV from positron emitters, difficult or impossible.
  • References which may be of interest include the following, which concern the design of position sensitive GSC type detectors:
  • the present invention includes a radiation detector comprising a plurality of scintillation crystal layers and a light collimator system optically coupled to the scintillation crystal layers for determining a depth of interaction associated with a scintillation event.
  • Figure 1 illustrates a cross-section of a Universal Nuclear Medicine Imager (UNMI).
  • UNMI Universal Nuclear Medicine Imager
  • Figure 2 illustrates a horizontal cross-section of a Universal Nuclear Medicine Imager (UNMI) with two depth of interaction (DOI) layers.
  • UNMI Universal Nuclear Medicine Imager
  • DOI depth of interaction
  • FIG 3 is a diagram illustrating the theoretical background of the UNMI.
  • Figure 4 is a diagram illustrating the relations existing by determining vertical geometric efficiency (VGE) factors.
  • FIG. 5 is a diagram illustrating the relations concerning horizontal geometric efficiency (HGE).
  • FIG. 6 illustrates, in vertical cross-section, an embodiment of an UNMI which has slopes narrowing the light collimators (LCs) in the direction from the crystal toward the fiber optics.
  • LCs light collimators
  • Figure 7 illustrates schematically the UNMI design of Figures 1 and 2.
  • Figure 8 is a block diagram of the UNMI's electronics.
  • Figure 9 is a diagram which illustrates the significance and influence of parallax error
  • the technical problem to be solved by the present invention is the design of a universal imaging detector for nuclear medicine which incorporates one or more detectors, referred to herein as the "Universal Nuclear Medicine Imager” (UNMI), which enable both the performance of planar studies (static, with the adequate spatial resolution and fast dynamic - metabolic with adequate temporal resolution), and optimal emission tomography studies with single photon emitters (“SPECT”) and positron emitters (“PET”).
  • UNMI Universal Nuclear Medicine Imager
  • the solution of the technical problem is to remove the shortage of GSCs to detect efficiently higher single photon and positron gamma energies, as well as the shortage of PET scanners to perform planar and SPECT studies with single photon gamma emitters; thus, the solution assumes a new design of a detector for the universal nuclear medicine imager (UNMI).
  • UNMI universal nuclear medicine imager
  • UNMI design has to be technically solved in such a way to have a thick Nal(TI) crystal (for the efficient detection of high photon energies in PET) enabling it to provide a satisfactory spatial resolution to image the low single-photon energies (in planar and SPECT studies).
  • a solution for such a technical problem lies in the possibility to determine exactly the "third dimension - location" of an event, i.e., the depth of interaction (DOI) of a gamma photon of any energy in a thick, large Nal(TI) scintillation crystal.
  • DOI depth of interaction
  • a precisely known DOI of a gamma photon in a thick crystal would provide the means for employment of the adequate correction schemes and principles for a distorted spatial resolution, both in planar - SPECT and PET studies.
  • the solution of the present invention concerns a DOI determination in any kind of a scintillation crystal of lower or higher density, but in this description, only the DOI determination in a thick Nal(TI) crystal will be considered.
  • Good characteristics of Nal(TI) crystal in comparison with certain others are: the best yield of scintillation light, negligible attenuation of light in the crystal, excellent energy resolution (enabling an efficient removal of Compton scatter), ability to grow large crystals (needed for GSC "large field of view” type of detectors) thus obtaining a large acceptance angle in configuration of large "position sensitive" area detectors (important for the efficient three-dimensional (3D) PET detection), and finally, but not least important, that it is the most widely used and applied crystal with broadly elaborated technology of production making it convenient for its fabrication in various shapes and sizes, being the cheapest one at the same time.
  • the solution of the technical problem is achieved by an innovation in designing the imaging "position sensitive” detectors, i.e., by the addition of a new, original design of a "light collimators” (LC) system.
  • the LC system (which includes its own electronics) in combination with a thick Nal(TI) crystal and standard electronics for the two-dimensional (2D) location of an interaction of gamma photon (IGP), enables the determination of the DOI of gamma photons in such a crystal and detector system.
  • This determination is enabled by dividing the unique whole of the crystal (as existing in conventional standard GSCs) into isolated DOI layers by inserting a non-scintillating but light-transparent material of different refractive-reflective characteristics, as compared to the Nal, in a thick crystal; as a result, the inserted material does not stop the gamma photons which are normally absorbed in various depths of scintillation crystal according to the exponential law probability.
  • the new system of UNMI detector is presented in Figure 1 in a vertical cross-section by a proportional drawing of the parts.
  • the system is presented in a simple embodiment, being a highly acceptable one from the commercial and performance predictability aspects, i.e., having only two DOI layers of 3/8 inch (in.) thickness each (which is the sole total thickness of Nal crystal in standard contemporary GSCs) within the total 6/8 in. thickness of Nal(TI) crystal.
  • the cross-section in Fig. 1 through a part of the UNMI detector shows the thick Nal(TI) crystal separated in two layers (1, 1'), each being 3/8 in.
  • FIG. 1 shows the following additional parts of detector and electronics: a lead collimator (6) of gamma photons; a conventional array (5) of PM tubes 3 in. in diameter, which in "position sensitive" detectors determine a 2D, (x,y) location of an IGP; a UNMI-original array of PM tubes (7) that are 2 in.
  • the specificity and characteristics of the UNMI design lie in the LC system in block with a thick crystal and the additional UNMI PM tubes array and electronics system, which together with the conventional (x,y) locating electronics (and PM tubes array), determine the DOI of a gamma photon event.
  • the LC system itself (shown in Fig. 1) consists of two parts, an internal part (2,3,4) and external part (8), and it is made of quartz glass (Si ⁇ 2).
  • the internal part of the LC is the one which forms the DOI layers of Nal scintillator (1, 1') of the predetermined desired thicknesses (in this case, the two layers of Nal of 3/8 in.
  • Optical couplings of the scintillating and non-scintillating materials have smooth, polished surfaces for enabling (partial) reflection of the light within the DOI layers of Nal, depending on the ratio of refraction indices of the Nal and Si ⁇ 2-
  • the external surface of the lowest outlining thin quartz layer (3) is diffuse reflectively painted (and /or scratched) in order to help the collection of light by the conventional, "position sensitive" PM tubes array.
  • the "channeled" scintillation light within each of the scintillator DOI layers is “collected” on the side of a thick, large Nal crystal by means of the corresponding external LCs (8), which fit in height the DOI layer thicknesses of Nal scintillator.
  • the external LCs differ in design, depending on the number and thicknesses of DOI layers in the crystal.
  • the external LCs are coupled to the fiber optic light guides (9), and these are, by means of the quartz glass layer(s) (10), optically coupled to the specific UNMI (array of) PM tubes (7) (and additional electronics) for determining the DOI of gamma photons.
  • the blocks of the external LC system are mounted on the lateral (vertical) sides of a thick Nal(TI) crystal, of a "sandwich” type, serving at the same time as a part of a hermetic "cage" for the hygroscopic Nal scintillator, instead of a conventional part made of aluminum; the rest of the "cage", protecting the lower part of the crystal towards the lead collimator and covering the parts of light guides and external LCs, is made of aluminum (11).
  • Figure 2 illustrates a horizontal cross-section through the UNMI detector of Figure 1, with two DOI layers in a 6/8 in. thick Nal crystal (each layer of 3/8 in. thickness).
  • Dashed lines (13) show one of the possible locations of the vertical cross-section, given in Fig. 1.
  • the following elements correspond in shape and dimension to one of the commercial types of position sensitive "area" detectors, like one of the standard GSCs (most closely, to some of the GSCs made by companies such as ADAC Laboratories of Milpitas, California): a large Nal(TI) crystal (1), "rounded" at the corners, with dimensions of 25 in. x 18.75 in. (63.5 cm x 47.6 cm) (measures of rectangle which are not strictly specific for UNMI design can vary accordingly), and the total thickness of which is 2 in. x 3/8 in., this UNMI type being 3/8 in.
  • the essential function of the internal part of LC system is to "channel" the portion of light from a scintillation event through the corresponding Nal layer to the adequate external part of LC system (and UNMI PM tubes) for the determination of the DOI of gamma photon; the rest of the portion of light from a scintillation event, depending on the "critical angle", has to be captured by the conventional position sensitive PM tubes array for the determination of the two-dimensional location of the IGP.
  • ⁇ "critical" angle
  • C center of the sphere of isotropic spread of light (i.e., the site of an IGP in a DOI layer of the crystal);
  • r radius of the sphere;
  • t thickness of the DOI layer in crystal (i.e.
  • Figure 5 shows the relations concerning horizontal geometric efficiency (HGE), i.e., it shows an insight in the fraction(s) of the belt of the sphere as "seen” by the external LCs.
  • TGE HGE * VGE (5)
  • the given data indicate that about 11.6 % of the total number of isotropically emitted light photons from the geometric midpoint of a DOI layer in the crystal would be "captured” by this layer.
  • the data which would indicate whether such an efficiency might be sufficient for the intended goal i.e. for determining the layer of DOI of gamma photon in the crystal
  • energy of an incoming ⁇ photon amount of emitted light photons — "captured" fraction of light photons (by the UNMI's LC system) - amount of ejected primary photoelectrons from photocathode(s) of the UNMI PM tube(s).
  • any two-dimensional, (x,y) location of an IGP no matter to which one of the four external LCs quadrant LCs it is near (or distant from), as summed up via the UNMI DOI - LC system provides for a similar magnitude of the output signal indicative for a particular DOI layer.
  • the conversion relations become proportionally more optimal for higher than 100 KeV gamma photon energies.
  • Table 1 provides for a possibility to facilitate an optimum UNMI design concerning the number and thicknesses of DOI layers in a thick Nal crystal.
  • Three different embodiments are given in Table 1 (the embodiments with one 1 in. thick layer is just comparatively shown, as it does not belong to the UNMI type of design) which can be considered from the theoretical and practical (cost) aspects: a UNMI with
  • each could be also discarded as a practically senseless one (an insignificant gain in spatial resolving power, negligible contribution in sensitivity even from the last two layers, and from any standpoint too expensive).
  • two of the above- mentioned embodiments may be preferable for the UNMI design: the one with two Nal layers, each being 3/8 in. thick, and possibly the one with three Nal layers, each being 1/4 in. thick. In both cases the total thickness of Nal is the same - 3/4 in.
  • the embodiment with two Nal layers, each layer being 3/8 in. thick, as given in Figures 1, 2, and 7, may be the more preferable of these two embodiments.
  • Such an embodiment may be the simplest and the cheapest, because: it includes the smallest number of layers, it allows easy fabrication of the block of a "sandwich" type of crystal; it includes a reduced number of UNMI PM tubes, of ADCs, as well as of fiber optics; the Nal cuts of 3/8 in. thickness are in routine production; a UNMI PM tubes array of only eight 2 in. PM tubes matches the conventional position sensitive 3 in. PM tubes array and crystal block size in a way that it can fit the existing housings and shieldings routinely produced for matched sizes of large field of view rectangular GSC heads, as given in Fig.
  • the two- crystal (3/8 in. each) embodiment may also be the most important form the standpoint of performance parameters for single photon emitters from an Nal layer (cut) of 3/8 in. thickness in conventional GSCs, such as resolution, sensitivity, are widely accepted as the optimal ones in both planar and SPECT studies.
  • the suggested two embodiments of the UNMI design (2 x 3/8 in. and 3 x 1/4 in. of Nal layers) would also differ in the design of external LCs.
  • the proposed embodiment (b), 3 x 1 /4 in., as roughly shown in Figure 6, would have slopes narrowing the LCs (in vertical cross-section) in the direction from the crystal toward the fiber optics, determined by the "critical" angle, ⁇ .
  • the slopes on the sides towards the neighboring Nal layer would also be determined by the "critical" angle, ⁇ ; the slopes on the opposite sides of external LCs, i.e., towards the lead collimator and the conventional PM tubes array would be given, relative to horizontal borders of layers, by the angle: 45°-/?.
  • an angle of 45° would make a 90° angle at such a slope, with the opposite side slope of external LC being determined by the angle, ⁇ .
  • a slope angled, 45°-/? would prevent many of the undesired light photons from entering from the neighboring Nal layer at angles greater than, ⁇ , to be shifted towards fiber optics, reflecting them from this slope to the opposite slope angled, ⁇ , and then "back" towards the Nal layer.
  • Figure 8 illustrates a block diagram of UNMI electronics (16), which is added to the conventional electronics of position sensitive (PS) area detectors (serving to obtain the two-dimensional (x,y) location of an IGP).
  • the summing signal Z from the PS electronics in the UNMI detector is, by the UNMI coincidence circuit 20, put in coincidence with the signal coming from a DOI layer (in which an IGP has occurred), as determined by the UNMI electronics (obtained by the electronic comparator in a UNMI with two DOI crystal layers), to deposit the (x,y) address in one of two DOI memory stacks (22, 24) (available for each of the DOI layers).
  • planar - SPECT version upon the acquisition of the raw data from only one memory stack (coming from lower crystal layer, for the energies up to 140 KeV) or from both memory stacks (coming from both crystal layers for the energies up to 250, 360 KeV) are adequately digitally processed and filtered and are displayed as a planar image (or a SPECT projection) with an appropriately optimal resolution.
  • the processed data can be displayed from only one DOI layer, or it can be "mixed", i.e., summed from both DOI layers of one UNMI detector (adequate digital processing and filtering protocols to be evaluated upon the system fabrication).
  • located events (raw data from both memory stacks, both DOI layers) of one UNMI detector arc put in coincidence by the PET coincidence circuit with the located events from memory stacks of the other oppositely positioned UNMI detector.
  • Each memory stack (representing a particular DOI crystal layer) of one UNMI detector is in coincidence with each of the memory stacks of the other UNMI detector.
  • LSO lutetium oxyorthosilicate
  • Gamma photons coming from an object being imaged are absorbed in one of the two Nal(TI) crystal layers (1, 1', in Figure 1) after having passed through the holes of a lead collimator (6, in Fig. 1), (usually through a collimator with parallel holes - septa, as shown in proportionally drawn details in Fig. 1). No matter whether a photoelectric or a Compton effect has occurred, the absorbed gamma photons are recorded within a predetermined energy "photopeak".
  • a number of scintillation light photons are isotropically spread out, being "captured" by both PM tubes arrays, i.e., by the PS array (5) (for determining the 2D (x,y) location of IGP), and by the UNMI array (7) (via LC system, for determining DOI) according to the geometric efficiencies considered above and shown in Figures 4 and 5. Since the signals coming from both PM tubes arrays originate from the absorption of the same gamma photon, the two signals are put in coincidence by the UNMI coincidence circuit 20 within an adequate coincidence time "window". Depending on a DOI location of the absorbed gamma photon, the two-dimensional, (x,y) address is deposited in a particular memory stack available for that DOI.
  • the digital UNMI images originating from one, or two (or three, depending on the imager design) DOI crystal layers can be separately displayed.
  • a display from only the lower (shallow) layer in the proposed design with two crystal layers
  • the thickness of the upper crystal layer of 3/8 in. (0.375 in.) makes a total thickness of 0.5 in. together with the UNMI light guides (2, 4), which equals the usual light guide thickness in conventional GSCs.
  • gamma energies ranging 250 and 360 KeV can be imaged using both DOI crystal layers.
  • the UNMI system would be particularly advantageous, since the images acquired and stored in separate DOI memory stacks could be separately processed in a specific way. Namely, it can be supposed that the same images from two DOI layers will differ according to their essential characteristics (in particular, so far as the "intrinsic" spatial resolution represented by the "full with at half maximum” (FWHM) parameter, is concerned).
  • the line spread function LSF, with its FWHM parameter, can be obtained for each of the crystal layers (and each specific energy and lead collimator), and from LSF the "modulation transfer function" (MTF).
  • MTF being a Fourier transform of LSF
  • PET would be done with two opposing UNMI detectors, without lead collimators; electronically, a necessary prerequisite would be a coincident connection within one UNMI detector for DOI determination, as well as a coincident connection between each of the DOI layers of the two UNMI detectors for the detection of positron annihilation in situ (with its direct location within a defined volume of an organ), with improved spatial resolution (due to correction for parallax error).
  • the specific UNMI coincidence electronics is to be added to these, made of routinely produced parts (e.g., PM tubes, digital electronic circuits), besides the also routinely produced PM tubes of standard sizes (3 in., 2 in.) and digital electronics for the 2D location of IGPs.
  • PM tubes routinely produced parts
  • a system with one UNMI detector and lead collimator(s) on might serve for planar static and dynamic as well as for SPECT studies.
  • a system with two UNMI detectors with lead collimators on would serve as an efficient SPECT system, both for the "low" gamma energies up to 140 KeV (which is the chief goal of the existing SPECT systems) and as a particularly useful system for imaging the "medium” gamma energies of 250 and 360 KeV.
  • its advantages would be improved spatial resolution and large angle of acceptance (due to the corrected parallax error), enabling the direct optimized 3D imaging of the particular body volumes in a quantitative functional mode.
  • Four of the UNMI detectors might be also used in a UNMI PET system, out of which: a) two opposite detectors would be in coincidence mode, or, b) each of the detectors would be in coincidence with the remaining three ones (enabled by the large "angle of acceptance"), thus making the system maximally efficient.

Landscapes

  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • General Health & Medical Sciences (AREA)
  • Medical Informatics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Optics & Photonics (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Molecular Biology (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Nuclear Medicine (AREA)
  • Measurement Of Radiation (AREA)

Abstract

Imageur polyvalent de médecine nucléaire (UNMI) permettant de réaliser des études de type planar, par émission de photon unique et par émission de positrons. Cet imageur est un détecteur de type sensible à la position, possédant un cristal (1, 1') de NaI(Tl) relativement épais divisé optiquement par un matériau mince non scintillant (2) en deux couches de cristal de demi-épaisseur (1, 1'). Ce détecteur met en application un système collimateur de lumière (2, 3, 4, 8, 9) permettant de déterminer une profondeur d'interaction (DOI) en plus d'une localisation bidimensionnelle de photons dans les couches de cristal de demi-épaisseur (1, 1'). Ce système comprend une combinaison de matériau scintillant (1, 1'), de matériau non scintillant (2, 3, 4, 8, 9), de tubes photomultiplicateurs (5) et de circuits de coïncidence. Afin d'obtenir une résolution spatiale optimale dans les études de type planar et par émission de photon unique, une profondeur d'interaction connue permet d'utiliser la couche de cristal inférieure (1) (énergies de 150 KeV maximum) et les deux couches de cristal (1, 1') pour des énergies moyennes (250, 360 KeV), la résolution de chaque couche étant corrigée par des filtres numériques. Dans les études par émission de positrons d'une énergie de 511 KeV, une profondeur d'interaction connue améliore la résolution en corrigeant l'erreur de parallaxe.
PCT/US1997/007714 1996-05-17 1997-05-05 Detecteur d'imagerie pour imageur polyvalent de medecine nucleaire WO1997044684A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
AU31181/97A AU3118197A (en) 1996-05-17 1997-05-05 Imaging detector for universal nuclear medicine imager
US09/165,160 US6194728B1 (en) 1997-05-05 1998-10-01 Imaging detector for universal nuclear medicine imager

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
YUP-298/96 1996-05-17
YU29896A YU29896A (sh) 1996-05-17 1996-05-17 Vizualizacioni detektor za univerzalni nuklearno medicinski vizualizacioni sistem

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US09/165,160 Continuation US6194728B1 (en) 1997-05-05 1998-10-01 Imaging detector for universal nuclear medicine imager

Publications (1)

Publication Number Publication Date
WO1997044684A1 true WO1997044684A1 (fr) 1997-11-27

Family

ID=25549278

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1997/007714 WO1997044684A1 (fr) 1996-05-17 1997-05-05 Detecteur d'imagerie pour imageur polyvalent de medecine nucleaire

Country Status (3)

Country Link
AU (1) AU3118197A (fr)
WO (1) WO1997044684A1 (fr)
YU (1) YU29896A (fr)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN111929066A (zh) * 2020-08-06 2020-11-13 南京航空航天大学深圳研究院 一种面向内燃机流场状态在线监测方法及装置
CN113100795A (zh) * 2021-04-15 2021-07-13 清华大学 一种伽马探测器、成像系统及实时成像方法、设备及介质
CN115247557A (zh) * 2022-04-28 2022-10-28 兰州大学 一种量能器式井眼缪子探测器

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4675526A (en) * 1985-04-15 1987-06-23 Rogers Joel G Method and apparatus for 3-D encoding
US4677299A (en) * 1985-05-13 1987-06-30 Clayton Foundation For Research Multiple layer positron emission tomography camera
US4843245A (en) * 1986-06-06 1989-06-27 Universite De Sherbrooke Scintillation detector for tomographs

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4675526A (en) * 1985-04-15 1987-06-23 Rogers Joel G Method and apparatus for 3-D encoding
US4677299A (en) * 1985-05-13 1987-06-30 Clayton Foundation For Research Multiple layer positron emission tomography camera
US4843245A (en) * 1986-06-06 1989-06-27 Universite De Sherbrooke Scintillation detector for tomographs

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN111929066A (zh) * 2020-08-06 2020-11-13 南京航空航天大学深圳研究院 一种面向内燃机流场状态在线监测方法及装置
CN113100795A (zh) * 2021-04-15 2021-07-13 清华大学 一种伽马探测器、成像系统及实时成像方法、设备及介质
CN115247557A (zh) * 2022-04-28 2022-10-28 兰州大学 一种量能器式井眼缪子探测器
CN115247557B (zh) * 2022-04-28 2023-08-25 兰州大学 一种量能器式井眼缪子探测器

Also Published As

Publication number Publication date
YU29896A (sh) 1998-11-05
AU3118197A (en) 1997-12-09

Similar Documents

Publication Publication Date Title
US6194728B1 (en) Imaging detector for universal nuclear medicine imager
US5773829A (en) Radiation imaging detector
CA2252993C (fr) Detecteur pour scanners multimode
Song et al. A sub-millimeter resolution PET detector module using a multi-pixel photon counter array
US9335425B2 (en) Modelling of ToF-DOI detector arrays
US8884239B2 (en) High resolution medical imaging detector
US20050253073A1 (en) Gamma ray detector for positron emission tomography (pet) and single photon emisson computed tomography (spect)
JP4525123B2 (ja) 放射線検出器およびその製造方法
US20080093559A1 (en) Arrangement of a Scintillator and an Anti-Scatter-Grid
US5864141A (en) Compact, high-resolution, gamma ray imaging for scintimammography and other medical diagostic applications
Yamashita et al. High resolution block detectors for PET
JP2017538132A (ja) Ｘ線又はガンマ線ディテクタ用のディテクタコンポーネント
US8481947B2 (en) Method and system for nuclear imaging using multi-zone detector architecture
US8809790B2 (en) Method and system for nuclear imaging using multi-zone detector architecture
Burnham et al. Cylindrical PET detector design
US9612344B2 (en) Positron emission tomography and single photon emission computed tomography based on intensity attenuation shadowing methods and effects
JP2007101191A (ja) 放射線検出器
WO1997044684A1 (fr) Detecteur d'imagerie pour imageur polyvalent de medecine nucleaire
Inadama et al. Performance of 256ch flat panel PS-PMT with small crystals for a DOI PET detector
Bartzakos et al. A PET detector with depth-of-interaction determination
US20050029461A1 (en) Gamma camera using rotating scintillation bar detector and method for tomographic imaging using the same
Raylman et al. Arrays of segmented, tapered light guides for use with large, planar scintillation detectors
Bosnjakovic Depth of interaction in scintillation crystal by light collimation for the design of" universal nuclear medicine imager"
Degenhardt et al. Impact of intercrystal crosstalk on depth-of-interaction information in PET detectors
US20230055050A1 (en) Device for the detection of gamma rays with interaction depth and time-of-flight encoding

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AL AM AT AT AU AZ BA BB BG BR BY CA CH CN CU CZ CZ DE DE DK DK EE EE ES FI FI GB GE GH HU IL IS JP KE KG KP KR KZ LK LR LS LT LU LV MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK SK TJ TM TR TT UA UG US UZ VN YU AM AZ BY KG KZ MD RU TJ TM

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): GH KE LS MW SD SZ UG AT BE CH DE DK ES FI FR GB GR IE IT

DFPE Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)
121 Ep: the epo has been informed by wipo that ep was designated in this application
WWE Wipo information: entry into national phase

Ref document number: 09165160

Country of ref document: US

NENP Non-entry into the national phase

Ref country code: JP

Ref document number: 97542430

Format of ref document f/p: F

REG Reference to national code

Ref country code: DE

Ref legal event code: 8642

NENP Non-entry into the national phase

Ref country code: CA

122 Ep: pct application non-entry in european phase