WO2009153860A1 - 放射線断層撮影装置 - Google Patents
放射線断層撮影装置 Download PDFInfo
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- WO2009153860A1 WO2009153860A1 PCT/JP2008/061051 JP2008061051W WO2009153860A1 WO 2009153860 A1 WO2009153860 A1 WO 2009153860A1 JP 2008061051 W JP2008061051 W JP 2008061051W WO 2009153860 A1 WO2009153860 A1 WO 2009153860A1
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- radiation
- tomography apparatus
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Images
Classifications
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- G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
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- A61B6/03—Computed tomography [CT]
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- A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
- A61B6/502—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for diagnosis of breast, i.e. mammography
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- G21F—PROTECTION AGAINST X-RADIATION, GAMMA RADIATION, CORPUSCULAR RADIATION OR PARTICLE BOMBARDMENT; TREATING RADIOACTIVELY CONTAMINATED MATERIAL; DECONTAMINATION ARRANGEMENTS THEREFOR
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- A61B6/5235—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image combining images from the same or different ionising radiation imaging techniques, e.g. PET and CT
Definitions
- the present invention relates to a radiation tomography apparatus for imaging radiation, and more particularly, to a radiation tomography apparatus including a radiation detector group in which block-shaped radiation detectors are arranged in a ring shape.
- a radiation tomography apparatus that detects radiation (for example, ⁇ -rays) emitted from a radiopharmaceutical administered to a subject and localized at a site of interest, and obtains a tomographic image of the radiopharmaceutical distribution at the site of interest of the subject (ECT: Emission Computed Tomography).
- ECT mainly includes a PET (Positionon Emission Tomography) apparatus, a SPECT (Single PhotoEmission Computed Tomography) apparatus, and the like.
- the PET apparatus has a group of radiation detectors in which block-shaped radiation detectors are arranged in an arc shape.
- the radiation detector group is provided to surround the subject and is configured to detect the radiation that has passed through the subject.
- a mammography PET device for breast cancer screening (hereinafter referred to as a mammo PET device) has a feature that the dose of radiation flying from the outside of the gantry toward the device is larger than that of a general PET device. is there. For this reason, the mammo PET apparatus is provided with a shield for shielding the entrance of radiation flying from the outside of the gantry.
- a conventional mammo PET apparatus 50 is provided so as to surround a gantry 51 having an opening for introducing a region of interest B (breast) of a subject M, and the opening of the gantry 51 from the outer peripheral side.
- a radiation detector group 52 that detects radiation, and a ring-shaped shield 53 are provided on one end side of the radiation detector group 52 adjacent to the subject M.
- the whole body of the subject M is not introduced into the opening of the gantry 51.
- a radiopharmaceutical is injected and administered to the subject M in advance, and this radiopharmaceutical is distributed throughout the body of the subject M. That is, the radiation is released from the whole body of the subject M, and the radiation flies toward the radiation detector group 52 not only from the region of interest B inside the gantry but also from a portion other than the breast of the subject M.
- the radiation 54 derived from the outside of the gantry interferes with the imaging of the radiopharmaceutical distribution in the region of interest B.
- the conventional mammographic PET apparatus 50 is provided with a ring-shaped shield 53 on one end side adjacent to the subject M of the radiation detector group 52. This prevents radiation 54 derived from the outside of the gantry from entering the radiation detector group 52 (see, for example, Patent Document 1).
- the conventional mammo PET apparatus has the following problems. That is, the conventional shield 53 has a problem that it is difficult to manufacture.
- the shield 53 is made of, for example, tungsten having a large effective atomic number.
- the shield 53 is a sintered metal formed by heating a powder containing tungsten as a main component to a temperature close to the melting point. Since this tungsten is a difficult-to-process material with a high melting point and high hardness, a large and expensive furnace is required to form the shield 53, and it is difficult to manufacture the conventional shield 53.
- the conventional shield 53 has a problem that it is difficult to assemble the mammo PET apparatus 50. Since tungsten is a high-density metal, the weight of the shield 53 is considerable. Therefore, when manufacturing the mammo PET apparatus 50, the process of attaching the shield 53 to the inside of the gantry becomes complicated.
- the configuration of the conventional shield 53 has a problem that it makes maintenance of the mammo PET apparatus 50 difficult.
- the mammo PET apparatus 50 needs to replace the radiation detectors constituting the radiation detector group 52 due to aging degradation or the like. At that time, an operation of once separating the shielding body 53 from the radiation detector group 52 is required.
- the shielding body 53 is a member having a considerable weight as described above, this operation is complicated. It will be a thing. Therefore, the conventional mammo PET apparatus 50 requires high cost for maintenance.
- the present invention has been made in view of such circumstances, and by dividing and forming a shield that shields radiation originating from the outside of the gantry, the manufacturing cost is low and the radiation is easy to maintain. It is to provide a tomographic apparatus.
- the radiation tomography apparatus is a radiation detector group formed by arranging radiation detectors for detecting radiation at least in an arc shape, and one side which is a plane of the radiation detector group.
- the shield is formed by combining a plurality of shield fragments.
- the shield that shields radiation is formed by combining a plurality of shield pieces. Therefore, the shield of the present invention is easy to manufacture.
- the shield of the present invention is, for example, a sintered metal formed by heating a powder containing tungsten as a main component to a temperature close to the melting point. According to the configuration of the present invention, since the shield pieces can be manufactured individually and then combined, it is not necessary to manufacture the shield in a large and expensive furnace. Thereby, it is possible to provide a radiation tomography apparatus that is easy to manufacture and has a reduced cost.
- the assembly of the radiation tomography apparatus can be facilitated.
- the weight of the shield is considerable.
- the shield fragments can be individually incorporated into the radiation tomography apparatus, so that the assembly of the radiation tomography apparatus becomes easy.
- maintenance of the radiation tomography apparatus is facilitated. That is, the configuration of the present invention enables maintenance without removing the entire shield by removing the shield fragment. Therefore, since it is not necessary to take out a shield having a considerable weight at the time of maintenance, the maintenance in the radiation tomography apparatus of the present invention becomes easy.
- the number of adjacent radiation detectors included in the radiation detector group configured as described above and arranged adjacent to the shield is the same as the number of shield fragments, and each of the shield fragments is an adjacent radiation detector. It is more desirable that the shields are arranged so as to cover each of these.
- the shield piece configured as described above has a first shield piece having a notch on a predetermined side, and a second shield having a protrusion that contacts the first shield piece and protrudes toward the notch. It is more desirable that the first shielding piece and the second shielding piece are in contact with each other by providing the body piece and fitting the notch and the protrusion.
- the first shielding piece and the second shielding piece adjacent to each other constituting the shielding piece constituting the shielding can be reliably brought into contact with each other. Since the notch part which the 1st shield piece has, and the projection part which the 2nd shield piece has fitted, both shield pieces contact, and a gap will arise between both shield pieces. Absent. Therefore, it is possible to reliably prevent the radiation derived from the outside of the gantry from entering the radiation detector group.
- a bottom plate that supports each radiation detector constituting the radiation detector group is provided on the other side end opposite to the one side end in the radiation detector group having the above-described configuration. It is more desirable that a plurality of support columns extending toward one side end of the group are provided, and each of the shield pieces is fixed and supported by the support columns.
- the shield piece can be integrated and fixed. That is, the shield piece is fixed to the bottom plate via the plurality of support columns. Therefore, according to the said structure, since each shield piece is fixed and integrated, a more robust shield can be comprised.
- the support column having the above-described configuration fixes each of the shield pieces in a detachable manner, and when the fixation of the third shield piece by the support columns is released, the third shield piece becomes the center of curvature of the arc-shaped portion in the radiation detector group. If the third shield piece can be moved back and forth along a predetermined direction so that the third shield piece can be detached from the shield and fitted into the shield in a reversible manner. More desirable.
- the shield piece and the support column having the above configuration are provided with pin holes for determining the relative positions of each other.
- the shield piece and the support column are provided with pin holes. That is, the shield piece and the support column can be temporarily fixed by inserting a pin through the pin hole. Then, for example, when the shield piece and the column are fixed with screws, the shield piece does not move with the rotation of the screw.
- the shield piece and the support column are coupled without shifting the relative position between the shield piece and the support column. Therefore, the shield fragments constituting the shield are arranged more orderly, and it is possible to configure a shield that can surely prevent radiation originating from the outside of the gantry from entering the radiation detector group.
- the radiation detector group having the above-described configuration can be C-shaped.
- a radiation tomography apparatus capable of reliably inserting a region of interest of a subject into an opening of a gantry.
- the arm of the subject obstructs the insertion of the subject's breast into the opening of the gantry.
- the radiation detector group having the above configuration can be formed in an annular ring shape.
- a radiation tomography apparatus having a radiation detector group capable of reliably detecting a disappearing radiation pair emitted from a region of interest of a subject can be provided.
- the dead angle at which the radiation detector group cannot detect radiation can be reduced as much as possible, so that data that can be used for tomography in the radiation tomography apparatus can be increased.
- a radiation tomography apparatus with reduced manufacturing costs can be provided.
- the shield pieces can be manufactured individually and then combined to form a shield that shields radiation originating from the outside of the gantry. There is no need to manufacture.
- maintenance of the radiation tomography apparatus is facilitated. That is, according to the present invention, maintenance can be performed without removing the entire shield by removing the shield piece. Therefore, since it is not necessary to take out a shield having a considerable weight at the time of maintenance, the maintenance in the radiation tomography apparatus of the present invention becomes easy.
- FIG. 1 is a perspective view of a radiation detector according to Embodiment 1.
- FIG. 1 is a partially broken sectional view illustrating a configuration of a radiation tomography apparatus according to Embodiment 1.
- FIG. 3 is an exploded perspective view illustrating the configuration of the radiation detector group according to the first embodiment.
- 3 is a plan view illustrating the configuration of a shield according to Embodiment 1.
- FIG. It is a perspective view explaining the structure of the shielding body fragment
- FIG. FIG. 3 is a plan view for explaining a superposed portion according to Example 1.
- FIG. 3 is a plan view illustrating a configuration of a detector unit according to the first embodiment. It is a top view explaining the shield fragment
- FIG. 1 is a functional block diagram illustrating a configuration of a radiation tomography apparatus according to Embodiment 1.
- FIG. It is a top view explaining the composition of one modification of the present invention. It is a perspective view explaining the structure of one modification of this invention. It is a perspective view explaining the structure of one modification of this invention. It is sectional drawing explaining the structure of the conventional radiation tomography apparatus.
- FIG. 1 is a perspective view of the radiation detector according to the first embodiment.
- the radiation detector 1 according to the first embodiment includes a scintillator crystal layer 2D, a scintillator crystal layer 2C, a scintillator crystal layer 2B, and a scintillator crystal layer 2A, each of which is laminated in the z direction.
- the scintillator 2 formed in this way, a photomultiplier tube (hereinafter referred to as a photodetector) 3 provided on the lower surface of the scintillator 2 and having a position discrimination function for detecting fluorescence emitted from the scintillator 2, A light guide 4 for transmitting and receiving fluorescence is provided at a position interposed between the light detector 3 and the light detector 3. Accordingly, each of the scintillator crystal layers is laminated in the direction toward the photodetector 3.
- the scintillator crystal layer 2 ⁇ / b> A is a radiation incident surface in the scintillator 2.
- Each scintillator crystal layer 2A, 2B, 2C, 2D is optically coupled, and a transmissive material t is provided between the respective layers.
- a thermosetting resin made of silicon resin can be used as the material of the transmission material t.
- the scintillator crystal layer 2A is a light-receiving portion for ⁇ rays emitted from a radioactive ray source, and 32 block scintillator crystals in the x direction and 32 in the y direction are based on the scintillator crystal a (1, 1). It is configured to be two-dimensionally arranged in an individual matrix.
- scintillator crystals a (1,1) to scintillator crystals a (1,32) are arranged in the y direction to form a scintillator crystal array, and 32 scintillator crystal arrays are arranged in the x direction to form a scintillator crystal layer.
- 2A is formed.
- the scintillator crystal layers 2B, 2C, and 2D also have 32 scintillator crystals in the x direction based on each of the scintillator crystals b (1,1), c (1,1), and d (1,1).
- the configuration is such that 32 pieces are arranged two-dimensionally in a matrix in the y direction.
- a transmission material t is also provided between adjacent scintillator crystals. Accordingly, each of the scintillator crystals is surrounded by the transmission material t.
- the thickness of the transmission material t is about 25 ⁇ m. Note that ⁇ rays correspond to the radiation of the present invention.
- the scintillator crystal layers 2A, 2B, 2C, 2D provided in the scintillator 2 are provided with a first reflector r extending in the x direction and a second reflector s extending in the y direction. Both the reflectors r and s are inserted in the gaps between the arranged scintillator crystals.
- the scintillator 2 is configured by three-dimensionally arranging scintillator crystals suitable for detecting ⁇ rays. That is, the scintillator crystal is composed of Lu 2 (1-X) Y 2X SiO 5 (hereinafter referred to as LYSO ) in which Ce is diffused.
- LYSO Lu 2 (1-X) Y 2X SiO 5
- Each of the scintillator crystals is a rectangular parallelepiped having a length in the x direction of 1.45 mm, a width in the y direction of 1.45 mm, and a height in the z direction of 4.5 mm regardless of the scintillator crystal layer. Further, the four side end surfaces of the scintillator 2 are covered with a reflection film (not shown).
- the photodetector 3 is a multi-anode type, and can discriminate the positions of incident fluorescence with respect to x and y.
- FIG. 2 is a partially broken sectional view illustrating the configuration of the radiation tomography apparatus according to the first embodiment.
- the radiation tomography apparatus 10 according to the first embodiment includes a gantry 11 having an opening for introducing a subject, and an opening of the gantry 11 provided inside the gantry 11.
- C-shaped fracture ring 12 formed.
- the fracture ring 12 is configured by arranging block-shaped radiation detectors 1p, 1q, and 1r in a C shape. The ⁇ rays irradiated from the subject are incident on the fracture ring 12.
- the radiation tomography apparatus 10 is configured such that the intensity, incident time, and incident position of the incident ⁇ -ray are specified by the fracture ring 12.
- the broken ring corresponds to the radiation detector group of the present invention.
- the gantry 11 according to the first embodiment has a C shape along the shape of the fracture ring 12.
- the radiation tomography apparatus 10 includes a C-shaped shield 13 that prevents radiation derived from the outside of the gantry 11 from entering the fracture ring 12.
- the shield 13 is disposed so as to cover one side end that is a flat surface of the fracture ring 12.
- the shield 13 is one side end adjacent to an opening for introducing a region of interest of the subject M in the radiation tomography apparatus 10 among a pair of side ends that are flat surfaces of the fracture ring 12. Is provided.
- the shield 13 is provided so as to extend the fracture ring 12 in the axial direction. That is, the part other than the part of interest B of the subject M located outside the gantry 11 and the fracture ring 12 are separated by the ring-shaped shield 13.
- the shield 13 is made of, for example, tungsten.
- FIG. 3 is an exploded perspective view illustrating the configuration of the radiation detector group according to the first embodiment.
- the fracture ring 12 is configured by arranging a plurality of detector units 15 in an arc shape along the shape of the bottom plate 14 having a C shape.
- the center of curvature of this arc is defined as the center of curvature D.
- the detector unit 15 includes, for example, a detector array 15a in which three radiation detectors 1p, 1q, and 1r are arranged in series in the x direction and an L-shaped support 16 coupled in the d direction away from the center of curvature D in the fracture ring 12. (See FIG. 7).
- the radiation detector closest to the shield 13 is defined as a radiation detector 1p.
- This radiation detector 1p corresponds to an adjacent radiation detector disposed adjacent to the shield in the present invention.
- the scintillator 2 provided in the detector unit 15 is arranged so as to face the inner direction of the bottom plate 14 when the fracture ring 12 is viewed from the x direction. Therefore, the inside of the fracture ring 12 is covered by the scintillator 2.
- the detector unit 15 is fastened to the bottom plate 14 with bolts and nuts via a later-described sub plate 16b. Further, the sub-plate 16b is provided with a hole 16c for inserting a bolt.
- the bottom plate 14 is provided with a long hole 14 a through which the bolt passes for each detector unit 15. In the configuration of the first embodiment, seven detector units 15 are arranged in a C shape.
- the tip of the fracture ring 12 extending from the bottom plate 14 in the x direction is a C-shaped flat surface and forms a tip surface.
- This front end surface is composed of seven radiation detectors 1p and corresponds to one end of the radiation detector group in the present invention.
- the bottom plate 14 is provided with eight first columns 21 and eight second columns 22 extending in the x direction for supporting the shield 13.
- the first support column 21 is arranged in an annular shape so as to surround the inner hole 14b of the bottom plate 14, and the second support column 22 is arranged in an annular shape so as to surround the annular shape of the first support column 21 from the outside. Yes.
- Both struts 21 and 22 are provided in a V-shaped dead space on the bottom plate 14 extending to the detector units 15 adjacent to each other.
- the lengths in the x direction of both the columns 21 and 22 are substantially the same as the lengths in the x direction of the detector unit 15 provided on the bottom plate 14.
- the bottom plate 14 is provided with eight first support columns 21 and eight second support columns 22.
- FIG. 4 is a plan view illustrating the configuration of the shield according to the first embodiment.
- the shield 13 is composed of seven shield pieces 13a, 13b, and 13c.
- the shield pieces 13a, 13b, 13c are plates made of tungsten having a trapezoidal shape.
- the thickness in the x direction is set to 5 mm, for example.
- a pair of shield pieces 13a, 13b, and 13c adjacent to each other partially overlap in the x direction to form a superposed portion 13d.
- Each of the shield pieces 13a, 13b, and 13c covers the tip in the x direction of the single detector unit 15, and is arranged in an arc shape as a whole, and is a C-shaped shield.
- the radiation tomography apparatus 10 forms a tip surface of the fracture ring 12 in the x direction.
- the same number of shield pieces 13a, 13b, 13c as the number of radiation detectors 1p (seven) are provided.
- the first support column 21 is provided with a screw hole 21a for fixing the shield pieces 13a, 13b, and 13c.
- pillar 22 is also provided with the screw hole 22a for fixing the shield piece 13a, 13b, 13c.
- thread 22b are provided in the superposition
- the screw 21b and the screw 22b are screwed into the screw hole 21a and the screw hole 22a, respectively. Therefore, one drill hole 13k through which the screw 21b and the screw 22b are inserted is provided in each of the inclined side portions of the trapezoidal shield pieces 13a, 13b, and 13c in the x direction. (See FIG. 5). Therefore, when one of the shield pieces 13a, 13b, 13c is viewed, four drill holes 13k through which the screws 21b, 22b are inserted are provided. As described above, the single shield piece 13 a, 13 b, 13 c is configured to be supported by the two first support columns 21 and the two second support columns 22.
- the second support column 22 is provided with a pin hole 22e for inserting a positioning pin described later.
- the shield pieces 13a, 13b, and 13c are also provided with pin insertion holes 13e extending in the x direction through which the positioning pins are inserted [see FIG. 4 (a)]. If one shield piece 13a, 13b, 13c is supported by the two second support columns 22, the trapezoidal shield pieces 13a, 13b, 13c are inclined with respect to each other.
- One pin insertion hole 13e is provided in each of the side portions. This pin insertion hole corresponds to the pin hole of the present invention.
- FIG. 5 is a perspective view illustrating the configuration of the shield piece according to the first embodiment.
- the shield fragments 13a, 13b, and 13c constituting the shield 13 include a first fragment 13a, a second fragment 13b, and a third fragment 13c.
- the first fragment 13a is located on one end side of the C-shaped shielding body 13, and as shown in FIG. 5A, the pair of the first fragment 13a having the trapezoid shape are inclined with respect to each other.
- a cutout portion 13f is provided on one side of the side portions. More specifically, the cutout portion 13f is provided so as to cut out the upper surface of the side portion of the first fragment 13a.
- one side of the above-described side side portions corresponds to a predetermined side having a notch portion of the present invention.
- the third piece 13c is located on the other end side of the shield 13, and is formed of a pair of side portions that are inclined with respect to the trapezoidal third piece 13c.
- a protruding portion 13g is provided on one side. More specifically, the protrusion 13g is provided so as to extend the upper surface of the side portion of the third fragment 13c.
- the second piece 13b is also trapezoidal as shown in FIG. 5B, and any one of the shield pieces 13a, 13b, 13c is provided on both sides of the pair of side edges inclined to each other. Adjacent to each other.
- a cutout portion 13f similar to the first fragment 13a is provided on one side of the pair of side portions of the second fragment 13b, and a protruding portion similar to the third fragment 13c is provided on the other side. 13g is provided.
- FIG. 6 is a plan view illustrating the overlapping portion according to the first embodiment.
- the fragment 13p and the adjacent fragment 13q partially overlap in the x direction to form a superposed portion 13d.
- a notch 13f provided in the fragment 13p and a protrusion 13g provided in the fragment 13q and projecting toward the notch 13f provided in the fragment 13p are fitted to each other. (See FIG. 5).
- the fragment 13p and the fragment 13q come into contact with each other.
- the notch part 13f and the protrusion part 13g are mutually fitting. Note that the fragment 13p and the fragment 13q correspond to the first shield fragment and the second shield fragment of the present invention, respectively.
- FIG. 7 is a plan view illustrating the configuration of the detector unit according to the first embodiment.
- the detector unit 15 includes three radiation detectors 1 arranged in series in the x direction.
- the detector unit 15 includes an L-shaped support 16 and a bleeder circuit that is coupled to the support 16 by being screwed to the support 16 from the d direction and supplies a voltage to the radiation detector 1.
- the bleeder unit 17 and the radiation detector 1 connected so as to extend the bleeder unit 17 in the d direction are provided. More specifically, the photodetector 3 of the radiation detector 1 is connected to the bleeder unit 17.
- the detector unit 15 includes three photodetectors 3, and these photodetectors 3 are bonded from the x direction via plate-like spacers 18.
- the scintillator 2 is configured by arranging nine scintillator crystals in the x direction, because this simplifies the drawing so as to be suitable for explanation.
- the scintillator 2 has 32 scintillator crystals arranged in the x direction.
- the three scintillators 2 of the detector unit 15 are integrally covered with a box-shaped cover 25 made of aluminum or the like.
- the radiation tomography apparatus 10 is configured to be easily maintained. Subsequently, the radiation tomography apparatus 10 will be described with respect to a maintenance method that is performed when it is necessary to replace the radiation detector constituting the fracture ring 12 due to deterioration over time.
- FIG. 8 is a plan view illustrating the shield fragment detachment process according to the first embodiment.
- the detector unit 15r to be replaced is covered with the fragment 13r.
- the four screws 21b and 22b fixing the fragment 13r are screwed out from the shield 13 and removed. Then, the fragment 13r can be moved in the d direction away from the center of curvature D in the fracture ring 12.
- the fragment 13r is moved in the d direction and detached from the shield 13.
- the shield fragment detachment step is completed, as shown in FIG. 8B, when the broken ring 12 is viewed from the x direction, the detector unit 15r is exposed.
- the fragment 13r is an example of a third shield fragment according to the present invention.
- FIG. 9 is a perspective view for explaining a shield fragment fitting step according to the first embodiment.
- the fragment 13r is fixed to both the columns 21 and 22 by screwing.
- the fragment 13r is first positioned in advance with respect to the both columns 21 and 22. This positioning will be described.
- the fragment 13r is fitted to the shield 13 by inserting the fragment 13r in a direction approaching the center of curvature D (see FIG. 8) of the fracture ring 12.
- the pin 23e is inserted into each of the two pin insertion holes 13e provided in the fragment 13r.
- the tip of this pin 23e abuts on the tip of the second support post 22 after passing through the pin insertion hole 13e. Then, the position of the fragment 13r with respect to the second column 22 is adjusted, and the tip of the pin 23e is inserted into the pin hole 22e (see FIG. 4) provided in the second column 22. In this way, first, the fragment 13r is positioned with respect to both the columns 21 and 22. Further, since the two pin insertion holes 13e are provided in the fragment 13r, the fragment 13r is temporarily fixed to the second support column 22 by the two pins 23e. Therefore, once the two pins 23 e are inserted and the fragment 13 r is positioned with respect to both the columns 21 and 22, the fragment 13 r is not glazed with respect to both the columns 21 and 22.
- the base end portion of the pin 23e is connected to the base portion 23 having a diameter larger than that of the pin insertion hole 13e. Therefore, when the pin 23e is inserted into the pin insertion hole 13e, the base 23 is engaged with the outer periphery of the pin insertion hole 13e, and thus the pin 23e is prohibited from being inserted into the pin insertion hole 13e any more.
- the fragment 13r is temporarily fixed to the second support post 22 by the two pins 23e, and the trapezoidal fragments 13r have side edges that are inclined with respect to each other.
- the screw 21b and the screw 22b are inserted into the four drill holes 13k provided in each, and both the screws 21b and 22b are screwed into the screw holes 21a and 22a provided in the both columns 21 and 22, respectively. 13r is fixed to both supports 21,22.
- the above description of the maintenance illustrates the case of removing the second fragment 13b.
- the pins 23e may be once inserted into the two pin insertion holes 13e in the fragment 13r before removing the four screws 21b and 22b from the fragment 13r. By doing so, the fragment 13r is temporarily fixed to the second support post 22 by the two pins 23e, so that the fragment 13r does not move with the rotation of the screws 21b and 22b.
- the fragment 13r can be moved back and forth in a direction approaching the center of curvature D (see FIG. 8) of the fracture ring 12, so that the fragment 13r can be detached from and fitted to the shield 13 reversibly.
- FIG. 10 is a functional block diagram illustrating the configuration of the radiation tomography apparatus according to the first embodiment.
- the radiation tomography apparatus 10 according to the first embodiment includes a gantry 11, a C-shaped fracture ring 12 provided inside the gantry 11, and radiation originating from the outside of the gantry 11.
- a C-shaped shielding body 13 that prevents entry into the outer ring 12, an external radiation source 33 that irradiates a ⁇ -ray fan beam provided on the inner surface side of the fracture ring 12, and an external radiation source drive unit 34 that drives the external radiation source 33 Is provided.
- the external radiation source driving unit 34 is controlled according to the external radiation source control unit 35.
- the radiation tomography apparatus 10 is further provided with each unit for acquiring a tomographic image of the region of interest B of the subject M.
- the radiation tomography apparatus 10 receives a ⁇ -ray detection signal representing the detection position, detection intensity, and detection time of ⁇ -rays from the fracture ring 12 and performs simultaneous counting of annihilation ⁇ -ray pairs.
- a fluorescence generation position discriminating unit 41 for discriminating the incident position of the ⁇ ray in the fracture ring 12 from the two ⁇ ray detection data determined by the coincidence counting unit 40 as an annihilation ⁇ ray pair, and transmission data described later
- an image forming unit 43 that forms a radiation tomographic image of the region of interest B.
- the radiation tomography apparatus 10 includes a main control unit 36 that comprehensively controls the external radiation source control unit 35 and the like, and a display unit 37 that displays a radiation tomographic image.
- the main control unit 36 is constituted by a CPU, and by executing various programs, the external source control unit 35 and the coincidence counting unit 40, the fluorescence generation position discriminating unit 41, the absorption correcting unit 42, and the image forming unit 43 Is realized.
- a region of interest B (breast) of a subject M previously injected with a radiopharmaceutical is inserted into the opening of the gantry 11.
- the transmission data which show the gamma ray absorption distribution of the region of interest B are acquired. That is, a fan-like ⁇ -ray fan beam is irradiated from the external radiation source 33 toward the region of interest B. This ⁇ -ray beam passes through the region of interest B and is detected by the fracture ring 12. Then, while moving the external radiation source 33 along the arc-shaped trajectory along the inner peripheral surface of the fracture ring 12, such detection is performed over the entire circumference of the region of interest B, A gamma ray absorption coefficient map is obtained.
- emission data for detecting annihilation gamma ray pairs released from the radiopharmaceutical localized at the site of interest B is acquired.
- the external radiation source 33 that has hindered the acquisition of the emission data is moved in the axial direction of the fracture ring 12 and stored in a radiation source shield (not shown).
- emission data is acquired. That is, the annihilation ⁇ -ray pair in which the traveling direction emitted from the inside of the site of interest B is opposite to 360 ° is detected by the fracture ring 12.
- the ⁇ -ray detection signal detected by the breaking ring 12 is sent to the coincidence counting unit 40, and only when two ⁇ -ray photons are detected at different positions on the breaking ring 12 at the same time, the subsequent data processing is performed. To be done. And by continuing acquisition of such emission data, the emission data of the count number sufficient to image the internal localization of the radiopharmaceutical in the region of interest B is obtained. Finally, the region of interest B of the subject M is withdrawn from the opening of the gantry 11 and the examination is completed.
- Transmission detection data Tr and emission detection data Em output from the fracture ring 12 are sent to the fluorescence generation position discriminating unit 41 to specify which scintillator crystal is sensed.
- the detection data sent from the multi-anode type photodetector 3 includes fluorescence intensity distribution information detected by the photodetector 3. Based on this, the fluorescence generation position discriminating unit 41 obtains the center of gravity of the fluorescence. As a result, the fluorescent positions in the x, y, and z directions in FIG. 1 are discriminated.
- transmission detection data and emission detection data including the incident position of the ⁇ -ray are formed and sent to the absorption correction unit 42 at the subsequent stage.
- the emission correction data Em is subjected to absorption correction excluding the influence of the ⁇ -ray absorption distribution of the region of interest B superimposed on the emission detection data Em while referring to the transmission detection data Tr described above.
- the detection data representing the radiopharmaceutical distribution in the site of interest B more accurately is sent to the image forming unit 43, where a radiation tomographic image is reconstructed. Finally, it is displayed on the display unit 37.
- rupture ring 12 is C shape, the reason is demonstrated.
- the region of interest B of the subject M is more closely attached to the gantry 11.
- a recess for introducing the arm of the subject M is provided so as to expand the opening of the gantry 11, and the gantry 11 has a C shape.
- the detector unit 15 cannot be provided at a portion corresponding to the position of the recess in the breaking ring 12. Therefore, the radiation detector group formed by arranging the radiation detectors in the first embodiment is a C-shaped fracture ring 12.
- the shield 13 that shields radiation is formed by combining a plurality of shield pieces 13a, 13b, and 13c. Therefore, the shield 13 of Example 1 is easy to manufacture.
- the shielding body 13 of Example 1 is a sintered metal formed by heating a powder mainly composed of tungsten to a temperature close to the melting point, for example.
- the structure of Example 1 since it can be set as the structure which combines this after manufacturing separately the shield piece 13a, 13b, 13c, it is not necessary to manufacture the shield 13 with a large and expensive furnace. Thereby, it is possible to provide the radiation tomography apparatus 10 that is easy to manufacture and has a reduced cost.
- the assembly of the radiation tomography apparatus 10 can be facilitated.
- the weight of the shield 13 is considerable.
- the shield pieces 13a, 13b, and 13c can be individually incorporated into the radiation tomography apparatus 10, the radiation tomography apparatus 10 can be easily assembled.
- maintenance of the radiation tomography apparatus 10 is facilitated. That is, according to Example 1, maintenance can be performed without removing the entire shield 13 by removing the shield fragments 13a, 13b, and 13c. Accordingly, since it is not necessary to take out the shield 13 having a considerable weight during maintenance, the maintenance in the radiation tomography apparatus 10 according to the first embodiment is easy.
- the present invention is not limited to the above embodiment, and can be modified as follows.
- the scintillator crystal referred to in the above-described embodiments is composed of LYSO
- the scintillator crystal may be composed of other materials such as GSO (Gd 2 SiO 5 ) instead. Good. According to this modification, it is possible to provide a method of manufacturing a radiation detector that can provide a cheaper radiation detector.
- the scintillator is provided with four scintillator crystal layers, but the present invention is not limited to this.
- a scintillator composed of one scintillator crystal layer may be applied to the present invention.
- the number of scintillator crystal layers can be freely adjusted according to the application of the radiation detector.
- the fluorescence detector is composed of a photomultiplier tube, but the present invention is not limited to this. Instead of the photomultiplier tube, a photodiode, an avalanche photodiode, or the like may be used.
- the fracture ring has a C shape, but a ring-shaped radiation detector group can be mounted instead. That is, as shown in FIG. 13, the shield 13 and the bottom plate 14 are O-shaped rings, and instead of the fracture ring 12, the detector unit 15 includes a detector ring 12 a arranged in an annular shape. be able to. Note that the gantry 11 according to this modification has an O-shaped ring shape corresponding to the shape of the detector ring 12a.
- the shield piece in the above-described embodiment has a trapezoidal shape, but the present invention is not limited to this. As shown in FIG. 11, the shield piece may be a sector.
- the second fragment 13b has the notch and the protrusion, but the present invention is not limited to this.
- Fig.12 (a) it is good also as a structure which has the notch part 13f in each of the mutually inclined side part which the 2nd trapezoid 2b 13b has.
- the second fragments 13b are arranged in a C shape while selecting the front and back sides of the second fragments 13b so that the adjacent second fragments 13b are reversed.
- the shield 13 can be formed.
- the fracture ring includes seven detector units, but the present invention is not limited to this.
- the detector units constituting the fracture ring can be increased or decreased according to the use of the radiation tomography apparatus. Along with this, the number of shield pieces constituting the shield can be increased or decreased.
- the present invention is suitable for a radiation tomography apparatus used in the medical field.
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Abstract
Description
すなわち、従来の遮蔽体53は、製造が困難であるという問題点がある。遮蔽体53は、実効原子番号が大きな、例えば、タングステンなどからなっている。この遮蔽体53は、タングステンを主成分とする粉体を融点近い温度まで加熱して形成される焼結金属である。このタングステンは、高融点、高硬度の難加工材であるので、遮蔽体53を形成するには大型で高価な炉が必要となり、従来の遮蔽体53の製造は困難である。
すなわち、請求項1に記載の放射線断層撮影装置は、放射線を検出する放射線検出器を少なくとも円弧状に配列されて形成された放射線検出器群と、放射線検出器群の平面となっている1側端を覆うように設けられた放射線を遮蔽する遮蔽体とを備えた放射線断層撮影装置において、遮蔽体は、複数の遮蔽体断片を組み合わせて形成されることを特徴とするものである。
10 放射線断層撮影装置
12 破断リング(放射線検出器群)
13 遮蔽体
13a,13b,13c 遮蔽体断片
13e ピン挿通孔(ピン穴)
13f 切欠き部
13g 突出部
13p 断片(第1遮蔽体断片)
13q 断片(第2遮蔽体断片)
13r 断片(第3遮蔽体断片)
14 底板
21 第1支柱(支柱)
22 第2支柱(支柱)
22e ピン穴
破断リング12を構成する放射線検出器を交換するには、破損した放射線検出器を有する検出器ユニット15rを破断リング12から取り外す必要がある。それに先立って、この作業の邪魔となる遮蔽体断片13a,13b,13cを遮蔽体13から脱離させる。図8は、実施例1に係る遮蔽体断片脱離工程を説明する平面図である。図8(a)の場合、交換の対象となっている検出器ユニット15rは、断片13rに覆われているものとする。まず、断片13rを固定している4本のネジ21b,22b(図4参照)を遮蔽体13から螺出させて、取り除く。すると、断片13rは、破断リング12における曲率中心Dから遠ざかるd方向に移動可能となる。この時点で断片13rをd方向に移動させて遮蔽体13から脱離される。この遮蔽体断片脱離工程が終了すると、図8(b)に示すように、x方向から破断リング12を見たとき、検出器ユニット15rが露出した状態となる。なお、断片13rは、本発明の第3遮蔽体断片の一例である。
この時点で、x方向から破断リング12を見たとき、検出器ユニット15rを底板14に固定するボルト26も露出することになる。検出器ユニット交換工程においては、このボルト26を緩めて、検出器ユニット15rをd方向に引き抜いて、その代わりに新しい検出器ユニット15を破断リング12における曲率中心Dに近づく方向に移動させることにより破断リング12に挿入する。そして、ボルト26を用いて新たな検出器ユニット15を底板14に固定すれば、本工程は終了となる。
次に、断片13rを再び遮蔽体13に嵌合させて、これを再装着する。図9は、実施例1に係る遮蔽体断片嵌合工程を説明する斜視図である。本工程で断片13rは、両支柱21,22にネジ止めされて固定されることになるが、これに先立って、まず断片13rの両支柱21,22に対する位置決めを予め行う。この位置決めについて説明する。まず、断片13rを破断リング12における曲率中心D(図8参照)に近づく方向に挿入することにより、断片13rを遮蔽体13に嵌合させる。そして、図9(a)に示すように、断片13rに設けられた2つのピン挿通孔13eのそれぞれにピン23eを挿通させる。すると、このピン23eの先端は、ピン挿通孔13eを貫通した後、第2支柱22の先端に当接する。そして、第2支柱22に対する断片13rの位置を調節して、ピン23eの先端が第2支柱22に設けられたピン穴22e(図4参照)に嵌入させる。この様にすることで、まず断片13rの両支柱21,22に対する位置決めが行われることになる。また、断片13rに2つのピン挿通孔13eが設けられていることからすると、断片13rは、2本のピン23eによって第2支柱22に仮止めされることになる。したがって、いったん2本のピン23eを挿通して断片13rの両支柱21,22に対する位置決めがなされると、断片13rは、両支柱21,22に対してグラつくことがない。
Claims (8)
- 放射線を検出する放射線検出器を少なくとも円弧状に配列されて形成された放射線検出器群と、
前記放射線検出器群の平面となっている1側端を覆うように設けられた放射線を遮蔽する遮蔽体とを備えた放射線断層撮影装置において、
前記遮蔽体は、複数の遮蔽体断片を組み合わせて形成されることを特徴とする放射線断層撮影装置。 - 請求項1に記載の放射線断層撮影装置において、
前記放射線検出器群が有するとともに前記遮蔽体に隣接して配置された隣接放射線検出器の個数と前記遮蔽体断片の個数は同数となっており、
前記遮蔽体断片の各々は前記隣接放射線検出器の各々を覆うように配列されて前記遮蔽体を構成していることを特徴とする放射線断層撮影装置。 - 請求項1または請求項2に記載の放射線断層撮影装置において、
前記遮蔽体断片は、所定の辺に切欠き部を有する第1遮蔽体断片と、
前記第1遮蔽体断片に当接するとともに前記切欠き部に向かって突出した突出部を有する第2遮蔽体断片とを備え、
前記切欠き部と前記突出部とが嵌合することにより、前記第1遮蔽体断片と前記第2遮蔽体断片とが当接されていることを特徴とする放射線断層撮影装置。 - 請求項1ないし請求項3のいずれかに記載の放射線断層撮影装置において、
前記放射線検出器群における前記1側端の反対側の他側端には、前記放射線検出器群を構成する各放射線検出器を支持する底板が設けられており、
前記底板には前記放射線検出器群の前記1側端に向けて伸びた複数の支柱が設けられており、
前記遮蔽体断片の各々は、前記支柱に固定されて支持されることを特徴とする放射線断層撮影装置。 - 請求項4に記載の放射線断層撮影装置において、
前記支柱は前記遮蔽体断片の各々を着脱自在に固定し、
前記支柱による第3遮蔽体断片の固定を解除すると、前記第3遮蔽体断片は、放射線検出器群における円弧状部の曲率中心から遠ざかる方向に移動可能となり、
前記第3遮蔽体断片は、前記所定方向に沿って進退されることにより、遮蔽体からの脱離および、遮蔽体への嵌合が可逆的に可能となることを特徴とする放射線断層撮影装置。 - 請求項4または請求項5に記載の放射線断層撮影装置において、
前記遮蔽体断片と前記支柱には、互いの相対的な位置を決定するためのピン穴が設けられていることを特徴とする放射線断層撮影装置。 - 請求項1ないし請求項6のいずれかに記載の放射線断層撮影装置において、前記放射線検出器群は、C形状となっていることを特徴とする放射線断層撮影装置。
- 請求項1ないし請求項7のいずれかに記載の放射線断層撮影装置において、前記放射線検出器群は、円環状のリング形状となっていることを特徴とする放射線断層撮影装置。
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JP2010517584A JP5195910B2 (ja) | 2008-06-17 | 2008-06-17 | 放射線断層撮影装置 |
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US20130070894A1 (en) * | 2011-09-17 | 2013-03-21 | Hiromichi Tonami | Sectional radiographic apparatus for breast examination |
WO2013038452A1 (ja) * | 2011-09-15 | 2013-03-21 | 株式会社島津製作所 | 医療用データ処理装置およびそれを備えた放射線断層撮影装置 |
JP5195935B2 (ja) * | 2009-02-16 | 2013-05-15 | 株式会社島津製作所 | 放射線断層撮影装置 |
JP2013092453A (ja) * | 2011-10-26 | 2013-05-16 | Shimadzu Corp | 乳房検診用放射線撮影装置 |
CN106163406A (zh) * | 2014-04-02 | 2016-11-23 | 皇家飞利浦有限公司 | 挤压和屏蔽设备 |
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US8487264B2 (en) * | 2008-07-31 | 2013-07-16 | Shimadzu Corporation | Radiation tomography apparatus |
CN102970930B (zh) * | 2010-07-06 | 2015-01-21 | 株式会社岛津制作所 | 放射线摄影装置 |
US9297910B2 (en) * | 2011-12-27 | 2016-03-29 | Koninklijke Philips N.V. | Tile mounting for pet detectors |
JP6366260B2 (ja) | 2013-11-20 | 2018-08-01 | キヤノン株式会社 | 乳房断層撮影装置 |
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JP5195935B2 (ja) * | 2009-02-16 | 2013-05-15 | 株式会社島津製作所 | 放射線断層撮影装置 |
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CN106163406A (zh) * | 2014-04-02 | 2016-11-23 | 皇家飞利浦有限公司 | 挤压和屏蔽设备 |
Also Published As
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JP5195910B2 (ja) | 2013-05-15 |
US8581197B2 (en) | 2013-11-12 |
US20110096897A1 (en) | 2011-04-28 |
JPWO2009153860A1 (ja) | 2011-11-24 |
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