JP2009031304A - Manufacturing method of radiation detector - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a manufacturing method of a radiation detector capable of keeping high image quality with high resolution, and of being simply realized. <P>SOLUTION: A scintillator group is composed by two-dimensionally tightly arranging scintillators partitioned by interposing a light reflecting material and an optically-transparent material. That is to say, the scintillator group has a lattice frame body 50 formed by combining strips 51-53 each formed of an optical member such as a light reflecting material or an optically-transparent material in the form of a lattice, and multiple small sections are formed by the lattice frame body 50. A transparent optical adhesive material is poured into an oblong frame base capable of housing the lattice frame body 50 to house the lattice frame body 50 therein, and thereafter the scintillators are housed. By manufacturing the radiation detector through a process of extracting a hardened resin body formed by integrating the hardened optical adhesive material, the lattice frame body 50 and the scintillators with one another, and shaping the outline thereof, the optical member can be arranged in the scintillator group without executing cutting by a dicing saw or a wire saw. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to a method of manufacturing a radiation detector optically coupled in the order of a scintillator, a light guide, and a photomultiplier tube.

  This type of radiation detector detects radiation (for example, gamma rays) emitted from a radioisotope (RI) administered to a subject and accumulated in a region of interest, and obtains a tomographic image of the RI distribution of the region of interest. For example, a medical diagnostic apparatus such as a PET (Positron Emission Tomography) apparatus and a SPECT (Single Photon Emission Computed Tomography) apparatus. The radiation detector includes a scintillator that emits light upon incidence of gamma rays emitted from a subject, and a photomultiplier that converts light emitted from the scintillator into a pulsed electric signal. For such radiation detectors, scintillators and photomultiplier tubes have conventionally been in a one-to-one correspondence, but in recent years, a plurality of photomultiplier tubes less than the number of scintillators have been combined. (For example, refer to Patent Document 1). In this method, the resolution is improved by determining the incident position of the gamma ray from the output ratio of these photomultiplier tubes. Hereinafter, a configuration of a conventional radiation detector will be described with reference to the drawings.

  9 is an external view showing a conventional radiation detector, and FIG. 10 is a cross-sectional view taken along the 100-100 plane of FIG. 9 and 10 show the appearance of the example disclosed in Japanese Patent Publication No. 06-95146. The radiation detector RDA includes a scintillator group SA, a light guide LA optically coupled to the scintillator group SA, and a plurality of optically coupled light guides LA (FIG. 9, FIG. 9). 10 comprises four photomultiplier tubes K1, K2, K3 (not shown in the figure) and K4. The scintillator group SA is composed of an assembly of scintillators S partitioned by a large number of light reflecting materials DA being sandwiched around. Note that the scintillator group SA may be configured to be sandwiched between the outer periphery of the scintillator group SA by a light reflecting material (not shown).

In this radiation detector RDA, the light guide LA is manufactured from an optically transparent material, and a plurality of slits MA having a predetermined depth are formed by cutting with a dicing saw or a wire saw. An optical member (for example, a light reflecting material or a light transmitting material) is inserted into the slit MA. The length of each slit MA is adjusted so as to increase as it goes from the inside to the outside of the light guide LA. By adjusting in this way, the light quantity from each scintillator S distributed to four photomultiplier tubes K1-K4 is adjusted, and the incident position of a gamma ray is discriminated.
Japanese Patent Publication No. 06-95146

However, the conventional radiation detector RDA described above has the following problems.
In recent years, a high-resolution radiation detector RDA using a high-sensitivity scintillator S has been proposed, and the number of scintillator groups SA is much larger than that of the conventional one. Therefore, the cross section of one scintillator S is further smaller than the conventional one. In general, the smaller the size of the scintillator S, the lower the probability that photons generated internally by absorption or scattering will jump out to the light guide LA, and the gamma ray incident position discrimination ability will decrease, resulting in the gamma ray incident position detection ability. Decreases.

  Here, in the scintillator group SA, if an attempt is made to sandwich the periphery of each scintillator S with a large number of light reflecting materials DA, the number of parts of each scintillator S and light reflecting material DA is very large, which makes the manufacturing complicated. It will be expensive.

  In addition, when an appropriate light reflecting material DA is inserted into the slit MA after processing, a gap is generated between the light reflecting material DA and the slit MA, which causes a problem that the reflection efficiency is lowered. Due to these factors, if the output due to the incident gamma ray is reduced and position discrimination cannot be performed accurately, the overall image quality is also deteriorated.

  More specifically, when the discrimination capability is lowered, the resolution is lowered as a result. When such a radiation detector RDA is used in a medical diagnostic apparatus such as a PET apparatus or a SPECT apparatus, the image quality of an image obtained by the apparatus deteriorates. For example, when the region of interest is a tumor, the tumor may not be accurately output on the image.

  Further, when the light reflecting material DA or the light transmitting material is inserted or filled as an optical member between the scintillators S, there is a problem that the position discrimination cannot be performed more accurately particularly when the light transmitting material is used. That is, it is common to use an optical adhesive material with good transparency for the portion constituting the light transmitting material. However, when an optical adhesive is used, it is an adhesive layer, so it is difficult to control the thickness of the light transmitting material. As a result, the thickness of each light transmitting material varies, the scintillators are not arranged at equal intervals, and the position discrimination of gamma rays cannot be performed more accurately.

  The present invention has been made in view of such circumstances, and an object of the present invention is to provide a method of manufacturing a radiation detector that can maintain high image quality with high resolution and can be easily realized.

  In order to achieve such an object, the present invention has the following configuration.

  That is, the invention according to claim 1 is directed to a scintillator group composed of a plurality of scintillators that are two-dimensionally closely arranged, a light guide optically coupled to the scintillator group, and the light guide. In a method of manufacturing a radiation detector including a plurality of photomultiplier tubes that are optically coupled and less than the number of scintillators, the scintillator group includes: (A) a plurality of plate-like optical members that are latticed; And (B) before or after storing the lattice frame in a rectangular container that can accommodate the lattice frame, and after storing the lattice frame in the rectangular container A step of pouring, (C) a step of storing the lattice frame in a rectangular container, and a step of storing the scintillator in the rectangular container after pouring the liquid resin into the rectangular container; and (D) curing. And it is characterized in that the liquid resin and the grid frame and the cured resin body scintillator and is integrated with the outer configuration shaped taken out from a rectangular-shaped container produced through a step of the scintillator array.

  [Operation / Effect] According to the invention described in claim 1, the optical member is manufactured in the scintillator group without being cut by a dicing saw or a wire saw by being manufactured through the steps (A) to (D). A radiation detector with high processing accuracy can be realized. Thus, a radiation detector is easily realizable by manufacturing through the process of (A)-(D).

  In the invention of the radiation detector manufacturing method described above, the optical member interposed between the scintillators includes a positioning member disposed at equal intervals on the light guide side of the scintillator group and a portion other than the positioning member between the scintillators. It is preferable that the positioning member is a reflective material or a transparent film.

  By arranging the positioning members at equal intervals, the scintillators are arranged at equal intervals on the light guide side of the scintillator group by the positioning members, and the discrimination ability is further improved.

  According to the manufacturing method of the radiation detector concerning this invention, a radiation detector is simply realizable by manufacturing through the process of (A)-(D).

Embodiments of the present invention will be described below with reference to the drawings.
FIG. 1 is an external view (side view) in the X direction of a radiation detector according to an embodiment of the present invention when viewed from the Y direction, and FIG. 2 is an external view of the radiation detector in the Y direction when viewed from the X direction. Front view).

  The radiation detector RDA according to the present embodiment includes a scintillator group 10, a light guide 20 optically coupled to the scintillator group 10, and four optically coupled light guides 20. It is composed of photomultiplier tubes 301, 302, 303, 304. 1 shows a photomultiplier tube 301 and a photomultiplier tube 303, and FIG. 2 shows a photomultiplier tube 301 and a photomultiplier tube 302.

The scintillator group 10 is configured by two-dimensionally arranging scintillators 1 </ b> S partitioned by sandwiching the light reflecting material 11 and the light transmitting material 12. In the present embodiment, nine scintillators 1S, nine in the X direction and ten in the Y direction, are two-dimensionally arranged. The light guide 20 has a lattice frame (not shown) in which strips (not shown) formed of optical members such as the light reflecting material 21 are combined in a lattice shape. A large number of small sections are formed by the lattice frame. Examples of the scintillator 1S include Bi ₄ Ge ₃ O ₁₂ (BGO), Gd ₂ SiO ₅ (GSO), Lu ₂ SiO ₅ : Ce (Lu ₂ SiO ₅ or LSO doped with Ce), and LuYSiO ₅ : Ce (Ce). Inorganic crystals such as LuYSiO ₅ doped with LYSO, or NaI (sodium iodide), BaF ₂ (barium fluoride), CsF (cesium fluoride) are used.

  In the present embodiment, the light reflecting material 11 is entirely interposed between the scintillators 1S arranged in the X direction, and the ten scintillators 1S arranged in the Y direction have four central scintillators 1S. A light transmissive material 12 is interposed between them, and a light reflecting material 11 is interposed between the other scintillators 1S. That is, similarly to the light guide 20 described above, the scintillator group 10 is also formed by combining strips 51 to 53 (see FIG. 6) formed of optical members such as the light reflecting material 11 and the light transmitting material 12 in a lattice pattern. It has a lattice frame 50 (see FIG. 6). A large number of small sections are formed by the lattice frame 50.

  As shown in FIG. 1, when gamma rays are incident on nine scintillators 1S arranged in the X direction, the scintillators 1S absorb the gamma rays and emit light. Specifically, it is converted into visible light. This light is guided to the photomultiplier tubes 301 to 304 through the optically coupled light guide 20. At that time, each light reflecting material in the light guide 20 so that the output ratio of the photomultiplier tube 301 (303) and the photomultiplier tube 302 (304) arranged in the X direction changes at a predetermined rate. The position, length, and angle of 21 are adjusted.

  More specifically, assuming that the output of the photomultiplier tube 301 is P1 and the output of the photomultiplier tube 302 is P2, the calculated value (P1-P2) / (P1 + P2) is a predetermined value depending on the position of each scintillator 1S. The predetermined length of the light reflecting material 21 and the interval between the light reflecting materials 21 are adjusted to a predetermined interval and angle with respect to the arrangement direction of the scintillator group 10 so as to change at a ratio. Note that the longer the light reflecting material 21 is, the more the discrimination ability of the adjacent scintillators 1S is improved, but the light attenuation is large. In addition, the ability to discriminate can be improved without reducing the amount of light by changing the position, angle and length slightly.

  On the other hand, as shown in FIG. 2, in the case of ten scintillators 1S arranged in the Y direction, light is transmitted to the photomultiplier tubes 301 to 304 through the optically coupled light guide 20 as in the X direction. Is guided. The position of each light reflecting material 21 in the light guide 20 is changed so that the output ratio between the photomultiplier tubes 301 (302) and the photomultiplier tubes 303 (304) arranged in the Y direction changes at a predetermined rate. Length and angle are adjusted.

  A coupling adhesive 15 is interposed between the scintillator group 10 and the light guide 20, and a coupling adhesive 16 is interposed between the light guide 20 and the photomultiplier tubes 301 to 304. . By interposing the adhesives 15 and 16, the scintillator group 10 and the light guide 20 are optically coupled to each other, and the light guide 20 and the photomultiplier tubes 301 to 304 are optically coupled to each other.

  Here, as described above, among the ten scintillators 1S arranged in the Y direction, the light transmitting material 12 is inserted between each of the four central scintillators 1S. For the portion constituting the light transmitting material 12, it is common to use an optical adhesive material having good transparency according to the emission wavelength characteristic of the scintillator. If a transparent film or the like is used, the light is attenuated and the output is attenuated. As a result, it is impossible to accurately discriminate the incident position of gamma rays.

  However, if only the optical adhesive material is used for the portion constituted by the light transmitting material 12, it is an adhesive layer, and therefore it is difficult to control the thickness of the light transmitting material 12. As a result, the thickness of each optical adhesive 31 varies as shown in FIG. As a result, the scintillators 1S do not line up at equal intervals. In the example of FIG. 3, the thick optical adhesive 31 is formed in the portion of the light transmissive material 12 at the right end as compared with the other light transmissive materials 12, and the gap between the scintillators 1 </ b> S is offset. In particular, if the scintillators 1S are not arranged at equal intervals on the surface of the scintillator group 10 on the light guide 20 side, that is, the coupling surface of the scintillator group 10 and the light guide 20, the incident position of gamma rays can be accurately distinguished. become unable.

  Therefore, in the present embodiment, with respect to the portion constituting the light transmitting material 12, the optical adhesive material 13 having good transparency and the positioning reflecting material 14 disposed at equal intervals on the surface of the scintillator group 10 on the light guide 20 side. And are used. Here, the positioning reflecting material 14 has the same thickness as the light reflecting material 11. Further, if the positioning reflecting material 14 is the same material / material as the light reflecting material 11, it is more preferable in terms of manufacturing price and simplicity of structure. The positioning reflecting material 14 corresponds to the positioning light reflecting material in the present invention, and also corresponds to the positioning member in the present invention.

  The light transmissive material 12 is composed of an optical adhesive material 13 and a positioning reflecting material 14, and the positioning reflecting materials 14 are arranged at equal intervals, so that light is transmitted to the surface of the scintillator group 10 on the light guide 20 side. The materials 12 are arranged at equal intervals. Therefore, the scintillators 1S are arranged at equal intervals on the surface of the scintillator group 10 on the light guide 20 side by the positioning reflecting material 14, and the discrimination ability is improved.

  Note that the positioning reflecting material 14 is preferably configured so as not to prevent light transmission. Specifically, the total area of the positioning reflecting material 14 is preferably ¼ or less of the entire area of the light transmitting material 12. Furthermore, it is more preferable that the total area of the positioning reflecting material 14 is 1/10 or less of the entire area of the light transmitting material 12.

  As a modification of the positioning member, a transparent film may be used instead of the positioning light reflecting material (positioning reflecting material 14). When a transparent film is used, the light is attenuated and the output is lowered. However, as in the case of the positioning reflecting material 14, a transparent film having an area that does not hinder the transmission of light may be used. That is, the total area of the transparent film is preferably ¼ or less of the entire area of the light transmitting material 12, and more preferably the total area of the transparent film is 1/10 or less of the entire area of the light transmitting material 12. The transparent film corresponds to the positioning transparent film in the present invention, and also corresponds to the positioning member in the present invention.

  As a modification of the arrangement of the positioning reflecting material 14, as shown in FIG. 4, the positioning reflecting material 14 having the same thickness as that of the light reflecting material 11 is attached to the scintillator group 10 for the portion constituting the light transmitting material 12. It is arranged on the surface on the light guide 20 side (coupling surface between the scintillator group 10 and the light guide 20) and also on the surface opposite to the light guide 20 side. Then, the optical adhesive 13 is sandwiched between the positioning reflectors 14 disposed on both sides.

  By arranging the positioning reflecting material 14 on the opposite surface as described above, the scintillator group 10 is arranged at equal intervals on the surface of the scintillator group 10 on the light guide 20 side. The scintillators 1S can be arranged at equal intervals with higher accuracy.

  Also in this case, the positioning reflecting material 14 preferably has a total area of the positioning reflecting materials 14 on both surfaces, that is, a total area of the positioning reflecting material 14 so that light transmission is not hindered. 12 or less, more preferably, the total area of the positioning reflecting material 14 is 1/10 or less of the entire area of the light transmitting material 12. Also in this case, the positioning member may be formed of a transparent film in place of the positioning reflecting material 14.

  As described above, when the light transmissive material 12 is composed of a positioning member such as the positioning reflecting material 14 or the transparent film and the optical adhesive, the positioning member is a surface on the light guide 20 side of the scintillator group 10. It suffices to arrange them at regular intervals.

  FIG. 5 is a block diagram showing the configuration of the position calculation circuit of the radiation detector. The position calculation circuit is composed of adders 1, 2, 3, 4 and position discrimination circuits 5, 6. As shown in FIG. 5, in order to detect the incident position of the gamma rays in the X direction, the output P1 of the photomultiplier tube 301 and the output P3 of the photomultiplier tube 303 are input to the adder 1, and the photomultiplier The output P2 of the double tube 302 and the output P4 of the photomultiplier tube 304 are input to the adder 2. The addition outputs (P1 + P3) and (P2 + P4) of both adders 1 and 2 are input to the position discriminating circuit 5, and the incident position of the gamma ray in the X direction is obtained based on both addition outputs.

  Similarly, in order to detect the incident position of the gamma ray in the Y direction, the output P1 of the photomultiplier tube 301 and the output P2 of the photomultiplier tube 302 are input to the adder 3, and the photomultiplier tube 303 The output P3 and the output P4 of the photomultiplier tube 304 are input to the adder 4. The addition outputs (P1 + P2) and (P3 + P4) of both adders 3 and 4 are input to the position discriminating circuit 6, and the incident position of the gamma ray in the Y direction is obtained based on both addition outputs.

  Next, a specific configuration of the scintillator group 10 will be described with reference to FIG. FIG. 6 is a perspective view of a lattice frame body of the scintillator group 10. That is, the scintillator group 10 is mainly made of a transparent body, and as shown in FIG. 6, a lattice frame body 50 is embedded in the inside thereof. A scintillator 1S is housed in each small section formed by the lattice frame 50. The lattice frame 50 is configured by combining optical members (that is, strips 51 to 53) such as the light reflecting material 11 and the light transmitting material 12 described above in a lattice shape.

  The light reflecting material 11 between the scintillators 1S and the light reflecting material 21 of the light guide 20 are a polyester film having a multilayer structure of silicon oxide and titanium oxide, polished aluminum, titanium oxide or barium sulfate on the surface of a thin substrate. A thin film coated with white tape, a thin smooth substrate coated with aluminum, or the like is applied.

  Next, a method for manufacturing the scintillator group 10 will be described with reference to FIG. FIG. 7 is an exploded perspective view of the optical members constituting the lattice frame. As this optical member, either the light reflecting material or the transparent film, or a combination of both is used. The optical member is formed in thin strips 51 to 53 as shown in FIG. 5, and slits M are formed in the respective strips 51 to 53. A lattice frame 50 is formed by combining the slits M with each other. The strips 53 correspond to the positioning reflector 14 shown in FIG. The creation of the lattice frame 50 corresponds to the step (A) in the present invention.

  As the outer shape processing of the strips 51 to 53, any method such as dicing cutting, laser cutting, cutting with a blade, etching, punching, or the like may be used. Since the strips 51 to 53 are thin plates, they can be easily and precisely cut.

  Next, the manufacturing method of the radiation detector using this scintillator group 10 is demonstrated with reference to FIGS. FIG. 8 is a perspective view of a frame used for manufacturing the radiation detector. In this manufacture, as shown in FIG. 8, a rectangular frame base 60 having a recess 61 in which the lattice frame 50 can be stored is prepared. A lattice frame 50 shown in FIG. 6 is accommodated inside the recess 61 of the frame base 60. The recess 61 has an area and a depth sufficient to completely cover the lattice frame 50. Note that a release agent or the like is applied to the inner surface of the recess 61 before storage so that the finished scintillator (not shown) can be easily taken out from the recess 61. The frame base 60 corresponds to the rectangular container in this invention. The frame base 60 is preferably made of a fluororesin excellent in releasing action, or a metal processed product such as aluminum or stainless steel having a fluororesin coating on the surface.

  Then, the completely defoamed optically transparent optical adhesive is poured into the recess 61 of the frame base 60 as a transparent liquid resin. The lattice frame body 50 is accommodated in the frame base 60 until the optical adhesive is cured by pouring, and then the scintillator 1S is accommodated.

  Here, when the scintillator 1S is stored, the optical adhesive material may overflow from the frame base 60. In each case, the storing operation may be performed while wiping. If all the scintillators 1S are accommodated, a transparent optical adhesive is further dropped from above, and the optical adhesive dropped into the gap between the scintillator 1S and the lattice frame 50 or between the scintillators 1S is completely filled. Perform vacuum defoaming as shown. At this time, the optical adhesive 13 shown in FIG. 2 is also formed. After the optical adhesive is cured, the lattice frame 60 and the optical adhesive are integrated as a cured resin body. The scintillator group 10 as shown in FIGS. 1 and 2 can be obtained by performing cutting and polishing such as taking out this and adjusting the outer shape. The process up to the pouring of the optical adhesive corresponds to the process (B) in the present invention, and the process up to the storage of the scintillator 1S corresponds to the process (C) in the present invention. ). The optical adhesive is preferably a silicon-based adhesive or an epoxy-based adhesive.

  In addition, by pouring the defoamed optical adhesive material, it is possible to prevent voids from being formed in the cured resin, and it is possible to prevent a reduction in resolution due to the voids. Note that the defoaming method is not limited to pouring the defoamed optical adhesive material, but after the frame base 60 is housed in a vacuum degassable space (for example, a chamber), the optical bonding is performed while vacuum degassing. Material may be poured. In addition, after pouring the optical adhesive into the recess 61 of the frame base 60 and before it is cured, the lattice frame body 50 is stored. However, after the lattice frame body 50 is stored in the recess 61 of the frame base 60, An optical adhesive may be poured and cured.

  The scintillator group 10 thus manufactured is optically coupled to the light guide 20 by the coupling adhesive 15 shown in FIGS. 1 and 2, and the scintillator group 10 and the light guide 20 are optically coupled. Are coupled optically to the photomultiplier tubes 301 to 304 by the coupling adhesive 16 shown in FIGS. 1 and 2 to manufacture a radiation detector RDA. As a result, a high-resolution radiation detector RDA can be easily realized. For example, even when the scintillator 1S has a small cross section, the shape accuracy is high by the manufacturing method described above. Moreover, the thickness and angle of the light reflecting material 11 can be freely selected, and a transparent optical adhesive is filled between the scintillator 1S and the light reflecting material 11 or between the scintillators 1S, so that the reflection efficiency does not deteriorate. . In addition, the number of parts can be minimized. Further, the optical member can be disposed in the scintillator group 10 without cutting such as a dicing saw or a wire saw, and a radiation detector RDA with high processing accuracy can be realized.

  Further, since the lattice frame 50 is relatively easy to create as designed, the small sections formed by the lattice frame 50 are also easily formed as designed, and the scintillators 1S of the small sections are also designed. It becomes easy to be formed. Accordingly, it is difficult for a gap to be generated between the scintillator 1S and the light reflecting material 11 or the light transmitting material 12 interposed between the scintillators 1S, the discrimination ability is improved, and high image quality can be maintained with high resolution. is there.

  Further, the light transmitting material 12 is composed of the optical adhesive material 13 and the positioning reflecting material 14, and the positioning reflecting material 14 is arranged at equal intervals, so that the surface of the scintillator group 10 on the light guide 20 side is provided. The scintillators 1S are arranged at equal intervals by the positioning reflecting material 14, and the discrimination ability is further improved.

  When such a high-resolution and high-quality radiation detector RDA is used in a diagnostic apparatus such as a PET apparatus or a SPECT apparatus, an image obtained by the apparatus also has a high image quality. For example, even when the region of interest is a tumor, the tumor is likely to be accurately output on the image. In addition, when the space | interval of the scintillator 1S is 2.5 mm, the tumor about 3.0 mm in diameter can be correctly output by the visual field center part.

  The present invention is not limited to the above-described embodiment, and can be modified as follows.

  (1) In the embodiment described above, the radiation detector detects gamma rays, but may be applied to a detector that detects radiation other than gamma rays, for example, X-rays.

  (2) In the above-described embodiment, the light reflecting material 11 and the light transmitting material 12 are used as the optical members constituting the scintillator group 10, but only the light reflecting material 11 may be used. When the light transmissive material 12 is not used, the light transmissive material 12 is not necessarily composed of the positioning member and the optical adhesive material.

  (3) In the above-described embodiment, in order to easily take out the scintillator group as a finished product from the frame base 60, the liquid resin is poured after the release agent is applied, but it is not always necessary to apply the release agent. .

  (4) In the embodiment described above, the optical adhesive is poured as the liquid resin, but the scintillator group 10 may be manufactured by pouring a liquid resin other than the optical adhesive.

  (5) In the above-described embodiment, a transparent optical device is provided from above the frame base 60 so that the optical adhesive dropped into the gap between the scintillator 1S and the lattice frame 50 or the gap between the scintillators 1S is completely filled. Although the adhesive is dropped, it is not always necessary to drop the optical adhesive as long as it fills the gap between the scintillator 1S and the lattice frame 50 or the gap between the scintillators 1S without dropping.

  (6) In the above-described embodiment, the liquid resin is defoamed when the liquid resin is poured, but it is not always necessary to defoam.

  As described above, the present invention is suitable for medical diagnosis apparatuses such as PET apparatuses and SPECT apparatuses.

It is the external view of the X direction which looked at the radiation detector concerning one example of this invention from the Y direction. It is the external view of the Y direction which looked at the radiation detector from the X direction. It is the external view of the Y direction which looked at the radiation detector at the time of comprising a light transmissive material only with an optical adhesive material from the X direction. It is the external view of the Y direction which looked at the radiation detector concerning a modification from the X direction. It is a block diagram which shows the structure of the position calculating circuit of a radiation detector. It is a perspective view of the lattice frame of a light guide. It is the figure which decomposed | disassembled and showed the optical member which comprises a lattice frame. It is a perspective view of the frame used for manufacture of a radiation detector. It is an external view which shows the radiation detector of a prior art example. It is sectional drawing of the 100-100 surface of FIG. 9 in the radiation detector of a prior art example.

Explanation of symbols

RDA ... Radiation detector 10, SA ... Scintillator group 1S, S ... Scintillator 11, DA ... Light reflecting material 12 ... Light transmitting material 13 ... Optical adhesive material 14 ... Reflecting material for positioning 20, LA ... Light guide 21 ... Light reflecting material 301, 302, 303, 304 ... Photomultiplier tube 50 ... Lattice frame 51, 52, 53 ... Strip 60 ... Frame base

Claims (2)

  A scintillator group composed of a plurality of scintillators arranged closely in two dimensions, a light guide optically coupled to the scintillator group, and the number of scintillators optically coupled to the light guide In the manufacturing method of a radiation detector provided with a plurality of photomultiplier tubes less than the above, (A) a step of creating a lattice frame by combining the scintillator group with a plurality of plate-like optical members in a lattice shape And (B) a step of pouring a transparent liquid resin into the rectangular container before or after storing the lattice frame in a rectangular container that can accommodate the lattice frame, and (C) A step of storing the scintillator in a rectangular container after being stored in a rectangular container and pouring the liquid resin into the rectangular container; and (D) a cured liquid resin, a lattice frame, and a scintillator. Method of manufacturing a radiation detector, characterized in that bets are produced and a process of a scintillator array and to adjust the outline is taken out cured resin body integrally from a rectangular shaped container.   The method of manufacturing a radiation detector according to claim 1, wherein the optical member interposed between each of the scintillators is between a positioning member disposed at equal intervals on the light guide side of the scintillator group and the scintillator. A method of manufacturing a radiation detector, comprising: an optical adhesive that transmits light, disposed in a portion other than the positioning member, wherein the positioning member is a reflector or a transparent film.

Images