US20050211906A1 - Radiation detector and a method of manufacturing the detector - Google Patents

Radiation detector and a method of manufacturing the detector Download PDF

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Publication number
US20050211906A1
US20050211906A1 US11/072,411 US7241105A US2005211906A1 US 20050211906 A1 US20050211906 A1 US 20050211906A1 US 7241105 A US7241105 A US 7241105A US 2005211906 A1 US2005211906 A1 US 2005211906A1
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United States
Prior art keywords
elements
radiation detector
scintillators
scintillator array
light
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US11/072,411
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English (en)
Inventor
Hiromichi Tonami
Junichi Ooi
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Shimadzu Corp
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Shimadzu Corp
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Assigned to SHIMADZU CORPORATION reassignment SHIMADZU CORPORATION ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: TONAMI, HIROMICHI, OOI, JUNICHI
Publication of US20050211906A1 publication Critical patent/US20050211906A1/en
Priority to US11/882,795 priority Critical patent/US7355180B2/en
Abandoned legal-status Critical Current

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    • 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
    • G01T1/202—Measuring radiation intensity with scintillation detectors the detector being a crystal

Definitions

  • This invention relates to a radiation detector having scintillators, a light guide and photomultiplier tubes arranged in the stated order and optically combined to one another, and to a method of manufacturing the radiation detector.
  • This type of radiation detector is used in a medical diagnostic apparatus such a PET (Positron Emission Tomography) apparatus or a SPECT (Single Photon Emission Computed Tomography) apparatus for detecting radiation (e.g. gamma rays) released from radioisotopes (RI) introduced into a patient and accumulated in a region of interest, and obtaining sectional images of RI distribution in the region of interest.
  • the radiation detector includes scintillators that emit light in response to incident gamma rays released from the patient, and photomultiplier tubes for converting the light emitted from the scintillators to pulsed electric signals.
  • FIG. 1 is a schematic view showing an outward appearance of a conventional radiation detector.
  • FIG. 2 is a section taken on line 100 - 100 of FIG. 1 .
  • FIGS. 1 and 2 show an example disclosed in Japanese Patent Publication No. 06-95146 (1994).
  • This radiation detector RDA includes a scintillator array SA, a light guide LA optically combined to the scintillator array SA, a plurality of (four in FIGS. 1 and 2 ) photomultiplier tubes K 1 , K 2 , K 3 (not seen in the figures) and K 4 optically combined to the light guide LA.
  • the scintillator array SA is an aggregate of scintillators S divided by numerous light reflecting elements DA inserted peripherally thereof.
  • the scintillator array SA may be surrounded by light reflectors (not shown).
  • the light guide LA is formed of an optically transparent material defining numerous slits MA of predetermined depths cut by a dicing saw or wire saw.
  • the slits MA have optical elements (e.g. light reflecting elements or light transmitting elements) inserted therein.
  • the slits MA have larger lengths from inner to outer positions of the light guide LA. This construction adjusts quantities of light from the scintillators S distributed to the four photomultiplier tubes K 1 -K 4 to discriminate positions of incidence of gamma rays.
  • the conventional radiation detector RDA noted above has the following drawbacks.
  • the radiation detector RDA is a high-resolution detector using the scintillators S of high sensitivity as proposed in recent years, and the scintillator array SA has far more scintillators than the scintillator array of an earlier detector. Consequently, each scintillator S has a smaller section than a scintillator in the earlier detector. Generally, the smaller scintillators S provide, by absorption or diffusion, the lower probability of photons produced inside moving into the light guide LA. This reduces the capability of discriminating, and thus detecting, positions of incidence of gamma rays.
  • scintillator array SA is designed such that individual scintillators S surrounded by numerous light reflecting elements DA, great numbers of scintillators S and light reflecting elements DA are required. This will results in a complicated manufacturing process, and thus high cost.
  • a reduced discriminating ability results in a reduction in resolution.
  • a medical diagnostic apparatus such as a PET apparatus or SPECT apparatus
  • images obtained by the apparatus will have poor quality.
  • the tumor may not be accurately outputted on the image.
  • the light reflecting elements DA or light transmitting elements inserted or filled as optical elements between the scintillator S make an accurate discrimination of positions even more difficult, particularly where light transmitting elements are used. That is, it is common practice to use a highly transmissive optical adhesive to form the light transmitting elements. However, since the optical adhesive forms adhesive layers, it is difficult to control the thickness of the light transmitting elements. As a result, variations will occur in the thickness of the light transmitting elements, so that the scintillators are not arranged at equal intervals. This further encumbers an accurate discrimination of positions of gamma ray incidence.
  • This invention has been made having regard to the state of the art noted above, and its object is to provide a radiation detector, and a method of manufacturing the radiation detector, capable of maintaining high image quality with high resolution, which may be realized simply.
  • a radiation detector having a scintillator array formed of a plurality of scintillators in a compact, two-dimensional arrangement, a light guide optically combined to the scintillator array, and a plurality of photomultiplier tubes smaller in number than the scintillators and optically combined to the light guide, wherein the scintillator array is formed of at least the scintillators and a lattice frame having plate-like optical elements combined crosswise, the lattice frame defining a plurality of cubicles.
  • the radiation detector when radiation impinges on one scintillator, in one of the cubicles defined by the optical elements, in the scintillator array having a plurality of scintillators in a compact, two-dimensional arrangement, that scintillator will absorb the radiation and emit light. Part of this light is transmitted through adjacent scintillators, but a major part of the light enters the light guide while repeating passage and dispersion due to reflections inside the scintillator. The light incident on the light guide is dispersed inside the light guide, and enters the photomultiplier tubes.
  • the cubicles in this lattice frame are also easy to form as designed.
  • the scintillators in the respective cubicles are also easy to form as designed. This results in a reduced chance of gaps being formed between the scintillators and optical elements interposed between the scintillators. Thus, the discriminating ability is improved to maintain high resolution and high image quality.
  • the optical elements are light transmitting elements interposed between the scintillators
  • the light transmitting elements are formed of positioning elements arranged at equal intervals at least on a plane of the scintillator array opposed to the light guide, and an optical adhesive for transmitting light, the positioning elements being positioning reflecting elements or positioning transparent films.
  • the light transmitting elements are arranged at equal intervals at least on the plane of the scintillator array opposed to the light guide.
  • the scintillators are arranged at equal intervals on the plane of the scintillator array opposed to the light guide. This further promotes the discriminating ability.
  • the positioning elements may be arranged at least on the plane of the scintillator array opposed to the light guide. Thus, the positioning elements may be arranged only on the plane of the scintillator array opposed to the light guide, and also on the plane of the scintillator array remote from the light guide.
  • the light transmitting elements are formed of positioning elements and an optical adhesive
  • the positioning elements have an overall total area at most a quarter of a total area of the light transmitting elements. Still more desirably, the overall total area of the positioning elements is at most one tenth of the total area of the light transmitting elements.
  • (A) a step of fabricating a lattice frame by combining a plurality of plate-like optical elements crosswise;
  • (B) a step of pouring a transparent liquid resin into a rectangular vessel for receiving the lattice frame, before or after placing the lattice frame in the rectangular vessel;
  • (C) a step of placing the scintillators in the rectangular vessel after placing the lattice frame in the rectangular vessel and pouring the liquid resin into a rectangular vessel;
  • the optical elements may be arranged in the scintillator array through the steps (A) to (D), without being cut with a dicing saw or wire saw. This realizes a radiation detector with high finishing accuracy.
  • the radiation detector is manufactured simply through the steps (A) to (D).
  • a release agent is applied to the rectangular vessel before executing the step (B) of pouring the transparent liquid resin into the rectangular vessel. Then, when executing the step (D), i.e. removing from the rectangular vessel a cured resin object integrating the liquid resin having cured, the lattice frame and the scintillators, and contouring the resin object to make the scintillator array, the resin object may be removed from the rectangular vessel easily.
  • the liquid resin is defoamed when executing the step (B) of pouring the transparent liquid resin into the rectangular vessel.
  • the liquid resin By defoaming the liquid resin, the cured resin becomes free from voids formed therein, thus avoiding lowering of resolution due to such voids.
  • the liquid resin may be poured in after being defoamed, or the liquid resin may be poured in while carrying out vacuum degassing, after placing the rectangular vessel in a space that may be vacuum-degassed.
  • FIG. 1 is a view showing an outward appearance of a conventional radiation detector
  • FIG. 2 is a section of the conventional radiation detector taken on line 100 - 100 of FIG. 1 ;
  • FIG. 3 is a view showing an outward appearance, in an X-direction seen from a Y-direction, of a radiation detector in one embodiment of this invention
  • FIG. 4 is a view showing an outward appearance, in the Y-direction seen from the X-direction, of the radiation detector;
  • FIG. 5 is a view showing an outward appearance, in the Y-direction seen from the X-direction, of the radiation detector in which light transmitting elements are formed of an optical adhesive only;
  • FIG. 6 is a view showing an outward appearance, in the Y-direction seen from the X-direction, of a modified radiation detector
  • FIG. 7 is a block diagram showing a position calculating circuitry of the radiation detector
  • FIG. 8 is a perspective view of a lattice frame of a scintillator array
  • FIG. 9 is an exploded perspective view showing optical elements constituting the lattice frame.
  • FIG. 10 is a perspective view of a trestle for use in manufacture of the radiation detector.
  • FIG. 3 is a view (side view) showing an outward appearance, in an X-direction seen from a Y-direction, of a radiation detector in one embodiment of this invention.
  • FIG. 4 is a view (front view) showing an outward appearance, in the Y-direction seen from the X-direction, of the radiation detector;
  • the radiation detector RDA in this embodiment includes a scintillator array 10 , a light guide 20 optically combined to the scintillator array 10 , and four photomultiplier tubes 301 , 302 , 303 and 304 optically combined to the light guide 20 .
  • FIG. 3 shows the photomultiplier tube 301 and photomultiplier tube 302 .
  • FIG. 4 shows the photomultiplier tube 301 and photomultiplier tube 303 .
  • the scintillator array 10 has scintillators 1 S in a compact, two-dimensional arrangement, the scintillators 1 S being defined by light reflecting elements 11 and light transmitting elements 12 .
  • 90 scintillators 1 S in total are arranged two-dimensionally, with nine arranged in the X-direction and ten in the Y-direction.
  • the light guide 20 has a lattice frame (not shown) with strips (not shown) of optical elements such as light reflecting elements 21 combined crosswise. This lattice frame defines numerous cubicles.
  • the scintillators 1 S are formed of an inorganic crystal such as Bi 4 Ge 3 O 12 (BGO), Gd 2 SiO 5 (GSO), Lu 2 SiO 5 :Ce (Lu 2 SiO 5 doped with Ce, i.e. LSO), LuYSiO 5 : Ce (LuYSiO 5 doped with Ce, i.e. LYSO), NaI (sodium iodide), BaF 2 (barium fluoride) or CsF (cesium fluoride).
  • BGO Bi 4 Ge 3 O 12
  • GSO Gd 2 SiO 5
  • Lu 2 SiO 5 :Ce Lu 2 SiO 5 doped with Ce, i.e. LSO
  • LuYSiO 5 : Ce LuYSiO 5 doped with Ce, i.e. LYSO
  • NaI sodium iodide
  • BaF 2 barium fluoride
  • CsF cesium fluoride
  • the scintillator array 10 also has a lattice frame 50 with strips 51 - 53 of optical elements such as light reflecting elements 11 and light transmitting elements 12 ( FIG. 8 ). This lattice frame 50 defines numerous cubicles.
  • the scintillators 1 S absorb the gamma rays and emit light. Specifically, the gamma rays are converted to visible light. This light is led to the photomultiplier tubes 301 - 304 through the light guide 20 combined optically. The positions, lengths and angles of the respective light reflecting elements 21 in the light guide 20 are adjusted so that the photomultiplier tube 301 ( 303 ) and photomultiplier tube 302 ( 304 ) arranged in the X-direction have a power ratio varying at a predetermined rate.
  • the lengths of the light reflecting elements 21 and intervals between the reflecting elements 21 are adjusted to predetermined intervals and angles relative to the direction of arrangement of the scintillator array 10 so that a calculation (P 1 ⁇ P 2 )/(P 1 +P 2 ), where P 1 is the output of photomultiplier tube 301 and P 2 is the output of photomultiplier tube 302 , changes at a predetermined rate according to the position of each scintillator 1 S.
  • the longer reflecting elements 21 result in the higher discriminating ability of the scintillators 1 S, but also in the greater attenuation of light. The discriminating ability is improved without reducing the quantity of light only by slightly changing the positions, angles and lengths.
  • the ten scintillators 1 S arranged in the Y-direction as do the scintillators 1 S arranged in the X-direction, emit light which is led to the photomultiplier tubes 301 - 304 through the light guide 20 optically combined.
  • the positions, lengths and angles of the respective light reflecting elements 21 in the light guide 20 are adjusted so that the photomultiplier tube 301 ( 302 ) and photomultiplier tube 303 ( 304 ) arranged in the Y-direction have a power ratio varying at a predetermined rate.
  • a coupling adhesive 15 is interposed between the scintillator array 10 and light guide 20 .
  • a coupling adhesive 16 is interposed between the light guide 20 and photomultiplier tubes 301 - 304 . These adhesives 15 and 16 optically combine the scintillator array 10 and light guide 20 , and the light guide 20 and photomultiplier tubes 301 - 304 , respectively.
  • light transmitting elements 12 are interposed between the four scintillators 1 S in the middle of the ten scintillators 1 S arranged in the Y-direction. It is common practice to use a highly transmissive optical adhesive to form the light transmitting elements 12 in accordance with the light emitting wavelength characteristic of the scintillators. Transparent film would attenuate light and weaken its output. As a result, it would be impossible to discriminate positions of incidence of gamma rays accurately.
  • the light transmitting elements 12 are formed of a thicker optical adhesive 31 than the other light transmitting elements 12 , resulting in unequal intervals between the scintillators 1 S.
  • the scintillators 1 S are arranged at equal intervals particularly on the plane of the scintillator array 10 opposed to the light guide 20 , i.e. the coupling plane between the scintillator array 10 and light guide 20 .
  • This embodiment therefore uses, in the portions of light transmitting elements 12 , a highly transmissive optical adhesive 13 and positioning reflecting elements 14 arranged at equal intervals on the plane of the scintillator array 10 opposed to the light guide 20 .
  • the positioning reflecting elements 14 have the same thickness as the light reflecting elements 11 . It is desirable that the positioning reflecting elements 14 are formed of the same material and quality as the light reflecting elements 11 from the viewpoint of manufacturing cost and structural simplicity.
  • the positioning reflecting elements 14 correspond to the positioning light reflecting elements in this invention, and also to the positioning members in this invention.
  • the light transmitting elements 12 are formed of the optical adhesive 13 and positioning reflecting elements 14 , with the positioning reflecting elements 14 arranged at equal intervals.
  • the light transmitting elements 12 are arranged at equal intervals on the plane of the scintillator array 10 opposed to the light guide 20 .
  • the scintillators 1 S are arranged at equal intervals on the plane of the scintillator array 10 opposed to the light guide 20 , thereby promoting the discriminating ability.
  • the positioning reflecting elements 14 it is desirable to provide the positioning reflecting elements 14 in a way to present no obstruction to the transmission of light. Specifically, it is desirable that the positioning reflecting elements 14 have an overall total area not exceeding a quarter of the total area of the light transmitting elements 12 . It is more desirable that the positioning reflecting elements 14 have an overall total area not exceeding one tenth of the total area of the light transmitting elements 12 .
  • transparent film may be used instead of the positioning light reflecting elements (positioning reflecting elements 14 ).
  • transparent film attenuates light and weakens its output light, the transparent film will serve the purpose as long as its area does not obstruct the transmission of light, as in the case of the positioning reflecting elements 14 . That is, the transparent film should have an overall total area not exceeding a quarter, and preferably not exceeding one tenth, of the total area of the light transmitting elements 12 .
  • the transparent film corresponds to the positioning transparent films in this invention, and also to the positioning elements in this invention.
  • the portions of light transmitting elements 12 have positioning reflecting elements 14 of the same thickness as the light reflecting elements 11 are arranged on the plane of the scintillator array 10 opposed to the light guide 20 (i.e. the cutting plane between the scintillator array 10 and light guide 20 ), and also on the plane of the scintillator array 10 remote from the light guide 20 .
  • the optical adhesive 13 is interposed between the positioning reflecting elements 14 arranged on the two opposite planes.
  • the scintillators 1 S are arranged, with increased precision, at equal intervals on the plane of the scintillator array 10 remote from the light guide 20 as well as on the plane of the scintillator array 10 opposed to the light guide 20 .
  • the positioning reflecting elements 14 should be arranged in a way to present no obstruction to the transmission of light.
  • the positioning reflecting elements 14 arranged on the opposite surfaces should have an overall total area not exceeding a quarter, and preferably not exceeding one tenth, of the total area of the light transmitting elements 12 .
  • transparent film may be used instead of the positioning reflecting elements 14 .
  • the positioning members should be arranged at equal intervals at least on the plane of the scintillator array 10 opposed to the light guide 20 .
  • FIG. 7 is a block diagram showing a position calculating circuitry of the radiation detector.
  • the position calculating circuitry includes adders 1 , 2 , 3 and 4 , and position discriminating circuits 5 and 6 .
  • output P 1 of the photomultiplier tube 301 and output P 3 of the photomultiplier tube 303 are inputted to the adder 1
  • output P 2 of the photomultiplier tube 302 and output P 4 of the photomultiplier tube 304 are inputted to the adder 2 .
  • Added outputs (P 1 +P 3 ) and (P 2 +P 4 ) of the two adders 1 and 2 are inputted to the position discriminating circuit 5 , and positions of incidence of gamma rays in the X-direction are determined from the two added outputs.
  • output P 1 of the photomultiplier tube 301 and output P 2 of the photomultiplier tube 302 are inputted to the adder 3
  • output P 3 of the photomultiplier tube 303 and output P 4 of the photomultiplier tube 304 are inputted to the adder 4
  • Added outputs (P 1 +P 2 ) and (P 3 +P 4 ) of the two adders 3 and 4 are inputted to the position discriminating circuit 6 , and positions of incidence of gamma rays in the Y-direction are determined from the two added outputs.
  • FIG. 8 is a perspective view of the lattice frame of the scintillator array 10 .
  • the scintillator array 10 is formed mainly of a transparent material with the lattice frame 50 laid therein as shown in FIG. 8 .
  • the scintillators 1 S are arranged in the cubicles formed by the lattice frame 50 , respectively.
  • the lattice frame 50 is formed by combining optical elements such as the light reflecting elements 11 and light transmitting elements 12 (i.e. strips 51 - 53 ).
  • the light reflecting elements 11 between the scintillators 1 S, and the light reflecting elements 21 of the light guide 20 are formed of polyester film having a multilayer structure of silicon oxide and titanium oxide, polished aluminum, a thin substrate coated with titanium oxide or barium sulfate, a thin substrate covered by white tape, or a thin smooth substrate with aluminum formed thereon by vapor deposition.
  • FIG. 9 is an exploded perspective view showing the optical elements constituting the lattice frame.
  • the optical elements comprise the above light reflecting elements or transparent film, or a combination thereof.
  • the optical elements are in the form of thin strips 51 - 53 each defining slits M therein.
  • the optical elements are combined by means of the slits M to form the lattice frame 50 .
  • the strips 53 correspond to the positioning reflecting elements 14 shown in FIG. 4 .
  • the fabrication of the lattice frame 50 corresponds to step (A) in this invention.
  • the strips 51 - 53 may be contoured by dicing, laser cutting, cutting with a cutting tool, etching or punching.
  • the strips 51 - 53 because they are thin, may be cut easily and precisely.
  • FIG. 10 is a perspective view of a trestle for use in manufacture of the radiation detector.
  • a rectangular trestle 60 is prepared, which has a recess 61 for receiving the lattice frame 50 therein.
  • the lattice frame 50 shown in FIG. 8 is placed in the recess 61 of the trestle 60 .
  • the recess 61 has an area and depth for completely surrounding the lattice frame 50 .
  • a release agent is applied to inner surfaces of the recess 61 beforehand for allowing the scintillator array as a finished product (not shown) to be removed easily from the recess 61 .
  • the trestle 60 corresponds to the rectangular vessel in this invention.
  • the trestle 60 is formed of fluororesin which has excellent release action, or is formed of metal such as aluminum or stainless steel and has surfaces coated with fluororesin.
  • a thoroughly defoamed, optically transparent optical adhesive is poured as liquid resin into the recess 61 of the trestle 60 .
  • the lattice frame 50 is placed in the trestle 60 , and then the scintillators 1 S are arranged in place.
  • the optical adhesive may overflow the trestle 60 in time of arranging the scintillators 1 S
  • the arranging operation may be carried out while wiping off the overflows from time to time.
  • the transparent optical adhesive is further applied in drips from above.
  • a vacuum degassing operation is carried out so that the optical adhesive dripped completely fills the spaces between the scintillators 1 S and lattice frame 50 and the spaces between the scintillators 1 S.
  • the optical adhesive elements 13 shown in FIG. 4 are formed also. After the optical adhesive cures, the lattice frame 50 and optical adhesive are integrated as a cured resin object.
  • the object is removed, and contoured by cutting and polishing to make the scintillator array 10 as shown in FIGS. 3 and 4 .
  • the pouring of the optical adhesive corresponds to step (B) in this invention.
  • the process up to the arranging of the scintillators 1 S corresponds to step (C) in this invention.
  • the process up to the contouring corresponds to step (D) in this invention.
  • the optical adhesive preferably, is a silicone adhesive or epoxy adhesive.
  • a method of defoaming is not limited to the time of pouring in of the defoamed optical adhesive.
  • the optical adhesive may be poured in while carrying out vacuum degassing.
  • the lattice frame 50 is placed in the recess 61 of the trestle 60 .
  • the optical adhesive may be poured in and allowed to cure.
  • the scintillator array 10 manufactured as described above is optically combined with the light guide 20 by the coupling adhesive 15 shown in FIGS. 3 and 4 .
  • the optically combined scintillator array 10 and light guide 20 are optically combined with the photomultiplier tubes 301 - 304 by the coupling adhesive 16 shown in FIGS. 3 and 4 , to form the radiation detector RDA.
  • the radiation detector RDA of high resolution may be realized simply.
  • the above manufacturing method assures a high degree of shaping accuracy even where the scintillators 1 S have a small sectional area, for example.
  • a thickness and angles of the light reflecting elements 11 may be selected freely, and the transparent optical adhesive fills the spaces between the scintillators 1 S and light reflecting elements 11 and the spaces between the scintillators 1 S, thereby assuring high reflecting efficiency. Besides, the number of components may be minimized.
  • the optical elements may be arranged in the scintillator array 10 without cutting them with a dicing saw or wire saw, thereby realizing the radiation detector 20 with high finishing accuracy.
  • the cubicles in this lattice frame 50 are also easy to form as designed.
  • the scintillators 1 S in the respective cubicles are also easy to form as designed. This results in a reduced chance of gaps being formed between the scintillators 1 S and the light reflecting elements 11 or light transmitting elements 12 interposed between the scintillators 1 S. Thus, the discriminating ability is improved to maintain high resolution and high image quality.
  • the light transmitting elements 12 are formed of the optical adhesive 13 and positioning reflecting elements 14 , with the positioning reflecting elements 14 arranged at equal intervals.
  • the scintillators 1 S are arranged at equal intervals on the plane of the scintillator array 10 opposed to the light guide 20 . This further promotes the discriminating ability.
  • the radiation detector RDA of high resolution and high image quality is used in a diagnostic apparatus such as a PET apparatus or SPECT apparatus
  • images of high quality may be obtained from the apparatus also.
  • a region of interest has a tumor
  • the tumor may be outputted on the images easily and accurately.
  • the scintillators 1 S arranged at intervals of 2.5 mm allow an accurate output of a tumor with a diameter of about 3.0 mm in the center of a visual field.
  • the radiation detector is constructed for detecting gamma rays.
  • the invention is applicable also to a detector for detecting radiation other than gamma rays, e.g. X rays.
  • the light reflecting elements 11 and light transmitting elements 12 are used as the optical elements forming the scintillator array 10 .
  • the light reflecting elements 11 may be used as the optical elements.
  • the light transmitting elements 12 it is not absolutely necessary to form the light transmitting elements 12 of positioning elements and optical adhesive.
  • the liquid resin is poured in after a release agent is applied to facilitate removal of the scintillator array as a finished product from the trestle 60 . It is not absolutely necessary to apply the release agent.
  • the optical adhesive is poured in as liquid resin.
  • the scintillator array 10 may be manufactured by pouring in a liquid resin other than the optical adhesive.
  • the transparent optical adhesive is applied in drips from above the trestle 60 , so that the optical adhesive dripped completely fills the spaces between the scintillators 1 S and lattice frame 50 and the spaces between the scintillators 1 S. It is not absolutely necessary to drip the optical adhesive as long as the adhesive fills the spaces between the scintillators 1 S and lattice frame 50 and the spaces between the scintillators 1 S.
  • the liquid resin is defoamed when poured, but it is not necessary to defoam the liquid resin.
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US20100200763A1 (en) * 2007-09-04 2010-08-12 Koninklijke Philips Electronics N.V. Silicon photomultiplier energy resolution
US20100294940A1 (en) * 2009-05-20 2010-11-25 Koninklijke Philips Electronics N.V. Pixelated scintillator array
US20110017916A1 (en) * 2007-08-22 2011-01-27 Koninklijke Philips Electronics N.V. Reflector and light collimator arrangement for improved light collection in scintillation detectors
US20110056618A1 (en) * 2008-06-05 2011-03-10 Hiromichi Tonami Method of manufacturing radiation detector
US20130170805A1 (en) * 2011-12-28 2013-07-04 General Electric Method of manufacturing a light guide assembly
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US9360563B2 (en) 2009-08-24 2016-06-07 Saint-Gobain Ceramics & Plastics, Inc. Scintillation detector assembly
US9696439B2 (en) 2015-08-10 2017-07-04 Shanghai United Imaging Healthcare Co., Ltd. Apparatus and method for PET detector
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US10890670B2 (en) 2004-08-09 2021-01-12 Saint-Gobain Cristaux Et Detecteurs Dense high-speed scintillator material of low afterglow
US10901099B2 (en) 2015-02-26 2021-01-26 Saint-Gobain Cristaux & Detecteurs Scintillation crystal including a co-doped rare earth silicate, a radiation detection apparatus including the scintillation crystal, and a process of forming the same
US10907096B2 (en) 2010-11-16 2021-02-02 Saint-Gobain Cristaux & Detecteurs Scintillation compound including a rare earth element and a process of forming the same
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