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WO2012098604A1 - Radiation tomography device - Google Patents

Radiation tomography device Download PDF

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Publication number
WO2012098604A1
WO2012098604A1 PCT/JP2011/006268 JP2011006268W WO2012098604A1 WO 2012098604 A1 WO2012098604 A1 WO 2012098604A1 JP 2011006268 W JP2011006268 W JP 2011006268W WO 2012098604 A1 WO2012098604 A1 WO 2012098604A1
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WO
WIPO (PCT)
Prior art keywords
tomography apparatus
marker
subject
radiation
radiation tomography
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/JP2011/006268
Other languages
French (fr)
Japanese (ja)
Inventor
允信 佐藤
善之 山川
礼子 赤澤
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Shimadzu Corp
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Shimadzu Corp
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Shimadzu Corp filed Critical Shimadzu Corp
Priority to JP2012553473A priority Critical patent/JP5644867B2/en
Publication of WO2012098604A1 publication Critical patent/WO2012098604A1/en
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/04—Positioning of patients; Tiltable beds or the like
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/50—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
    • A61B6/508—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 non-human patients

Definitions

  • the present invention relates to a radiation tomography apparatus used when imaging a plurality of subjects at once.
  • This apparatus is capable of generating a tomographic image of a subject, and an operator can know the internal structure of the subject by referring to this image.
  • the conventional apparatus has a gantry 51 provided with an opening. Inside the gantry 51 is a detector ring 62 for detecting radiation generated from a radiopharmaceutical injected into a subject. Is provided. The subject is introduced into the opening of the detector ring 62.
  • the conventional configuration includes a holder that can store a plurality of subjects.
  • a tomographic image is taken in a state where the holder is placed inside the gantry 51 (see, for example, Patent Document 1, Patent Document 2, and Patent Document 3).
  • the acquired tomographic image shows the entire holder. Since a plurality of subjects are stored in the holder, a plurality of subjects are reflected in the tomographic image.
  • the experimenter performs various analyzes on the cross-sectional image of the subject appearing in the tomographic image and derives the experimental result.
  • the conventional configuration has the following problems. That is, there is a problem that analysis work becomes difficult when cross-sectional images of a plurality of subjects are reflected in one tomographic image.
  • the cross-sectional images of the subject are captured in tomographic images in different states. For example, the luminance of the tomographic image reflected in one tomographic image varies among a plurality of subjects.
  • the brightness so that the tomographic image is easily visible
  • the other tomographic image of the subject that appears darker will be too dark. Visibility deteriorates.
  • the other tomographic image of the subject appearing brighter becomes too bright and the visibility deteriorates.
  • Such circumstances are not limited to brightness adjustment. That is, a similar trimming operation is required when correcting the generation intensity of the radiopharmaceutical with the body weight of the subject.
  • the present invention has been made in view of such circumstances, and an object of the present invention is to improve the work efficiency of an experiment in a radiation tomography apparatus used when imaging a plurality of subjects at once. It is an object of the present invention to provide a radiation tomography apparatus capable of performing
  • the radiation tomography apparatus is based on a detection means for detecting radiation, a holder for holding a plurality of subjects provided with markers indicating the position of the subject, and a detection signal output by the detection means.
  • a data generating means for generating three-dimensional spatial data including a plurality of markers and a plurality of subjects, a marker specifying means for specifying the position of each marker in the three-dimensional spatial data, and a position of the specified marker
  • the image forming apparatus includes a dividing unit that divides the three-dimensional space data to generate divided data including a single subject.
  • a radiation tomography apparatus with improved work efficiency can be provided. That is, according to the present invention, the holder is provided with the marker indicating the position of the subject. After the three-dimensional space data is generated, the position of each marker included therein is specified, and the three-dimensional space data is divided based on the position of each marker. As a result, the three-dimensional spatial data is surely divided into divided data including a single subject. That is, since the experimenter can perform data analysis for each subject without performing complicated trimming work, the working efficiency of the radiation tomography apparatus of the present invention is high.
  • the holder is provided with three markers indicating the positions of the subjects in three orthogonal directions for each subject.
  • the above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. That is, if three markers indicating the position of the subject in three orthogonal directions are provided for one subject on the holder, the three-dimensional position of the subject in the three-dimensional space data is surely one. Will be determined.
  • the marker specifying unit generates a tomographic image of three-dimensional spatial data and specifies the position of the marker by searching an image in which the marker is reflected from each tomographic image. More desirable.
  • the above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention.
  • the marker identification is performed.
  • the means can reliably specify the position of the marker in the three-dimensional space data.
  • the holder is provided with a tray on which the subject is individually placed and a recess for introducing the tray, and it is more desirable that the marker be provided on the tray.
  • the above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. That is, if the marker is provided on the tray on which the subject is individually placed, the position of the marker in the three-dimensional space data surely indicates the position of each subject in the three-dimensional space data.
  • the marker is provided on a handle when the tray is pulled out from the recess.
  • the above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. If the marker serves as a handle for pulling out the tray from the concave portion of the holder, the experimenter can easily introduce the subject into the holder, so that a radiation tomography apparatus with further improved work efficiency can be provided.
  • the marker is a symbol for identifying each subject in the three-dimensional spatial data.
  • a top plate on which the holder is placed and a top plate moving means for moving the top plate in a direction orthogonal to the opening of the radiation tomography apparatus.
  • the above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. If the holder is provided with a slidable top plate, a radiation tomography apparatus capable of easily introducing the subject into the field of view can be provided.
  • the radiation tomography apparatus includes a radiation source that emits radiation, and a rotation unit that rotates the radiation source and the detection unit.
  • the detection unit emits radiation generated from the radiation source and transmitted through the subject. It is more desirable if it is detected.
  • the above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention.
  • a radiation tomography apparatus capable of easily obtaining a CT image can be provided.
  • the detection means is a detector ring for detecting radiation emitted from the subject, and it is more desirable if it is configured as a positron emission tomography apparatus.
  • the above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. If the present invention is applied to a positron emission tomography apparatus, a radiation tomography apparatus capable of easily acquiring a PET image can be provided.
  • a radiation tomography apparatus with improved work efficiency can be provided. That is, according to the present invention, the holder is provided with the marker indicating the position of the subject. After the three-dimensional space data is generated, the position of each marker included therein is specified, and the three-dimensional space data is divided based on the position of each marker. As a result, the three-dimensional spatial data is surely divided into divided data including a single subject. That is, since the experimenter can perform data analysis for each subject without performing complicated trimming work, the working efficiency of the radiation tomography apparatus of the present invention is high.
  • FIG. 1 is a functional block diagram illustrating a configuration of an X-ray tomography apparatus according to Embodiment 1.
  • FIG. It is a top view about the structure of the holder which concerns on Example 1.
  • FIG. 3 is a perspective view of a configuration of a tray according to Embodiment 1.
  • FIG. 3 is a cross-sectional view of the configuration of the tray according to the first embodiment.
  • FIG. 3 is a schematic diagram illustrating spatial data according to the first embodiment.
  • 6 is a schematic diagram illustrating data processing according to Embodiment 1.
  • FIG. 6 is a schematic diagram illustrating data processing according to Embodiment 1.
  • FIG. 6 is a schematic diagram illustrating data processing according to Embodiment 1.
  • FIG. 3 is a schematic diagram illustrating divided data according to the first embodiment.
  • FIG. 3 is a flowchart for explaining the operation of the X-ray tomography apparatus according to Embodiment 1;
  • FIG. 3 is a cross-sectional view illustrating the operation of the X-ray tomography apparatus according to Embodiment 1.
  • FIG. 6 is a functional block diagram for explaining the operation of the radiation tomography apparatus according to Embodiment 2. It is a perspective view about the structure of the tray which concerns on one modification of this invention. It is a schematic diagram explaining the data processing which concerns on 1 modification of this invention. It is a schematic diagram explaining operation
  • the radiation tomography apparatus according to the first embodiment is a CT apparatus that performs tomography of the structure of the subject M.
  • the X-ray in Example 1 corresponds to the radiation in the present invention, and FPD is an abbreviation for flat panel detector. Further, the radiation tomography apparatus according to the first embodiment is for small animal photography.
  • the X-ray tomography apparatus 1 includes a top plate 2 on which a subject M is placed and a gantry 10 having a through hole penetrating in the direction in which the top plate 2 extends.
  • the top plate 2 is inserted through the through hole of the gantry 10 and moves so as to be able to advance and retract in the direction in which the top plate 2 extends (perpendicular to the opening of the radiation tomography apparatus) with respect to the support base 2a that supports the top plate 2. can do.
  • the top plate 2 is moved by a top plate moving mechanism 15.
  • the top plate movement control unit 16 controls the top plate movement mechanism 15.
  • the top plate moving mechanism 15 corresponds to the top plate moving means of the present invention.
  • an X-ray tube 3 for irradiating X-rays and an FPD 4 for detecting X-rays are provided inside the gantry 10.
  • the X-rays irradiated from the X-ray tube 3 pass through the through hole of the gantry and reach the FPD 4.
  • the X-ray tube 3 corresponds to the radiation source of the present invention
  • the FPD 4 corresponds to the detection means of the present invention.
  • the X-ray tube control unit 6 is provided for the purpose of controlling the X-ray tube 3 with a predetermined tube current, tube voltage, and pulse width.
  • the FPD 4 detects X-rays emitted from the X-ray tube 3 and transmitted through the subject M, and generates a detection signal. This detection signal is sent to the image generation unit 11, where a perspective image P0 in which a projection image of the subject M is reflected is generated.
  • the spatial data generation unit 12 generates three-dimensional spatial data D1 in which the luminance representing the X-ray absorption coefficient is three-dimensionally arranged based on the fluoroscopic image P0 generated by the image generation unit 11.
  • the spatial data generation unit 12 corresponds to data generation means of the present invention.
  • a holder 5 for holding the subject M is placed on the top plate 2.
  • the structure of the holder 5 will be described.
  • the holder 5 has an opening 5 a having a shape of five circles (a cylinder extending in the Z direction if captured as a solid).
  • the subject M is inserted into each of the openings 5a.
  • the cylinder 5b forming the inner wall of the opening 5a is supported by being embedded in each of the through-holes in a polystyrene support 5b1 made of polystyrene foam in which a plurality of through-holes extending in the Z direction are opened in a lotus shape.
  • the cylinder 5b is made of an acrylic resin that easily transmits X-rays.
  • the holder 5 has a shape in which three openings 5 a are formed in the first stage on the side close to the top board 2 and two openings 5 a are formed in the second stage on the side far from the top board 2.
  • the opening 5a corresponds to the concave portion of the present invention.
  • the holder 5 in FIG. 2 is a holder for holding a plurality of subjects that can hold five subjects M at a time.
  • the tray 5c is a bowl-shaped member extending in the Z direction as shown in FIG. Surfaces (end faces) orthogonal to the Z direction are provided at both ends of the tray 5c in the Z direction. Therefore, the inside of the tray 5c is a semi-cylindrical notch that opens in the vertical direction.
  • the subject M is placed in the notch. When the subject M is placed in the notch, the subject M is surrounded by the tray 5c, so that the positional relationship between the tray 5c and the subject M does not deviate.
  • the tray 5c is made of, for example, an acrylic resin.
  • a plate-like marker 5m provided for the purpose of clarifying the position of the subject M is provided on one of the two end faces provided on the tray 5c.
  • the tray 5c is provided with three markers 5m having the same shape, and one of the markers 5m is attached to the end face.
  • the remaining two markers 5m are provided on a pulling handle 5d that protrudes in a direction in which the tray 5c, which has a bowl shape extending in the Z direction, is further extended.
  • the handle 5d has an L shape having two surfaces, one surface of the handle 5d is along the vertical direction, and the other surface is orthogonal to the vertical direction. The two surfaces are orthogonal to the end surface of the tray 5c.
  • One marker 5m is provided on each of both surfaces of the handle 5d.
  • the marker 5m is formed of a member different from the tray 5c such as metal.
  • the marker 5m may be configured by cutting out the tray 5c.
  • the marker 5m is provided for the purpose of indicating the position of the subject M. Accordingly, the tray 5c is provided with three markers 5m indicating the position of the subject M in three orthogonal directions with respect to one subject M. Note that the intersection point p in FIG. 3 is an intersection point where the three planes on which the three markers 5m are pasted each other.
  • the shape of the marker 5m will be described. Since the holder 5 has five openings 5a, the holder 5 has five trays 5c. The shape of the marker 5m provided on the tray 5c is different for each tray 5c. That is, each of the three markers 5m provided on the tray 5c in FIG. 3 represents the letter A of the alphabet. Although not shown, each of the other four trays 5c provided in the holder 5 is provided with three markers 5m each representing the alphabets B, C, D, and E. The marker 5m also functions as a symbol for identifying each subject M. The marker 5m having a different shape depending on the tray 5c serves as an index for identifying each tray 5c for both the experimenter and the marker specifying unit 17 described later. The marker specifying unit 17 corresponds to the marker specifying means of the present invention.
  • FIG. 4 shows how the tray 5c is used.
  • the tray 5 c can be inserted into the opening 5 a of the holder 5 with the subject M placed in the cutout portion.
  • the experimenter can easily insert the tray 5c into the opening 5a by holding the handle 5d, or can easily pull out the tray 5c from the opening 5a.
  • the bottom of the tray 5c has a bowl-shaped curved surface that follows the columnar shape of the cylinder 5b so that the tray 5c can be smoothly introduced into the cylinder 5b.
  • the three-dimensional space data D1 related to the marker specifying unit 17 and the dividing unit 13 will be described.
  • the three-dimensional space data D1 is three-dimensional matrix data including a plurality of subjects (mouse) in the three-dimensional space.
  • the three-dimensional space data D1 is data (for example, luminance) detected by the radiation tomography apparatus arranged in each voxel.
  • the three-dimensional space data D1 is acquired in a state where a plurality of subjects M are introduced into the field of view of the radiation tomography apparatus, and the marker 5m that displays the position of each subject M is also this three-dimensional space. It is represented in the data D1.
  • the three-dimensional space data D1 is configured by arranging voxels in a rectangular parallelepiped space.
  • the reason why the three-dimensional space data D1 represents a rectangular parallelepiped is that this is convenient for holding data.
  • the dividing unit 13 corresponds to the dividing unit of the present invention.
  • the three-dimensional space data D1 corresponds to three-dimensional reconstruction data at a stage before the radiation tomography apparatus generates a tomographic image.
  • the marker specifying unit 17 is provided for the purpose of specifying the position of each marker in the three-dimensional space data D1. The operation of the marker specifying unit 17 will be described.
  • the marker specifying unit 17 generates a tomographic image based on the three-dimensional space data D1. Specifically, the marker specifying unit 17 generates a tomographic image parallel to one of the six surfaces forming the rectangular parallelepiped shape of the three-dimensional space data D1. Since the marker specifying unit 17 generates the tomographic image while changing the cutting position, a plurality of tomographic images are generated.
  • specification part 17 searches among the some tomographic images produced
  • the marker specifying unit 17 When the marker specifying unit 17 tries to acquire a marker-containing cross section for the A shape, first, an image pattern indicating the A shape stored in the storage unit 28 is read. And the marker specific
  • the marker specifying unit 17 performs the same operation on three surfaces orthogonal to each other among the six surfaces forming the rectangular parallelepiped shape. That is, as shown in FIG. 7, the marker specifying unit 17 searches for two marker-containing cross sections orthogonal to the marker-containing cross section obtained by the previous search. By doing in this way, the marker specific
  • the marker specifying unit 17 specifies the position of the intersection point for each of the five trays 5c. Thereby, the position of the intersection for each of the trays 5c is specified. At this time, the pattern used for the pattern matching process is changed in accordance with the search for the marker 5m having a different shape. Thus, the marker specifying unit 17 specifies the positions of the A to E shapes existing in the three-dimensional space data D1 and the intersection points pA to pE corresponding to these positions.
  • the five intersection points p specified by the marker specifying unit 17 are distinguished and set as pA, pB, pC, pD, and pE. As shown in FIG. 8, the marker specifying unit 17 specifies the positions in the three-dimensional space data D1 of the intersections pA to pE unique to the five subjects M.
  • the divided data D2 is three-dimensional matrix data including a single subject M in a three-dimensional space. Similar to the three-dimensional space data D1, the divided data D2 is obtained by arranging data detected by the radiation tomography apparatus in each voxel. The divided data D2 is configured by arranging voxels, and the three-dimensional space data D1 is cut into a cylindrical shape. Further, for the purpose of facilitating data retention, null data voxels may be added outside the divided data D2 having a cylindrical shape and shaped into a rectangle.
  • the dividing unit 13 extracts a part of the three-dimensional space data D1 and generates divided data D2. By performing such an operation, the three-dimensional space data D1 including a plurality of subjects M is converted into divided data D2 including a single subject M. The dividing unit 13 generates divided data D2 for each subject M included in the three-dimensional space data D1. Therefore, a plurality of divided data D2 is generated from the three-dimensional space data D1.
  • the dividing unit 13 cuts out the three-dimensional space data D1 based on the intersection points pA to pE specified by the marker specifying unit 17. That is, when the dividing unit 13 tries to extract the subject M corresponding to the intersection point pA from the three-dimensional space data D1, the dividing unit 13 recognizes a cylindrical region having a predetermined positional relationship with respect to the intersection point pA. This area is extracted from the three-dimensional space data D1 to generate the divided data D2. Data indicating the positional relationship between the cylindrical area recognized by the dividing unit 13 and the intersection point p is stored in the storage unit 28.
  • the columnar region recognized by the dividing unit 13 is defined so that the entire region of the notch portion for placing the specimen on the tray 5c in FIG.
  • the positional relationship between the intersection point p and the cutout portion of the tray 5 c is constant no matter where the tray 5 c is located on the holder 5. Therefore, also in the three-dimensional space data D1, the position of the intersection point pA specified by the marker specifying unit 17 and the position of the region corresponding to the cutout portion of the tray 5c to which the A marker 5m is attached are always constant. In other words, if the position of the intersection point pA in the three-dimensional space data D1 is known, the position of the subject M in the three-dimensional space data D1 is naturally known.
  • the divided data D2 is sent to the analysis image generation unit 14.
  • the analysis image generation unit 14 generates a two-dimensional image P using the divided data D2 that is three-dimensional matrix data. Examples of the generated two-dimensional image P include a tomographic image.
  • the tomographic image is an image in which a tomographic image of the subject M is captured.
  • the analysis image generation unit 14 performs data processing such as brightness adjustment on the entire divided data D2, and generates a tomographic image in which a tomographic image when the subject M is cut along a certain plane is reflected.
  • the rotation of the X-ray tube 3 and the FPD 4 will be described.
  • the X-ray tube 3 and the FPD 4 are integrally rotated around the central axis extending in the direction in which the top plate 2 extends by the rotation mechanism 7.
  • the rotation control unit 8 controls the rotation mechanism 7.
  • the rotation mechanism 7 corresponds to the rotation means of the present invention.
  • the display unit 25 is provided for the purpose of displaying a two-dimensional image P acquired by X-ray imaging.
  • the console 26 is provided for the purpose of inputting an instruction such as an X-ray irradiation start by an experimenter.
  • the main control unit 27 is provided for the purpose of comprehensively controlling each control unit.
  • the main control unit 27 is constituted by a CPU, and realizes the control units 6, 8, 16 and the units 11, 12, 14, 17 by executing various programs. Further, each of the above-described units may be divided and executed by an arithmetic device that takes charge of them.
  • the storage unit 28 stores all parameters relating to control of the X-ray tomography apparatus 1 such as parameters used for imaging and intermediate images generated in accordance with image processing.
  • the X-ray tomography apparatus is performed by executing the steps shown in the flowchart of FIG. Hereinafter, these steps will be described in order.
  • the following description of the operation is performed when a plurality of subjects M are photographed at a time and an analysis image for each of the subjects M is acquired.
  • ⁇ Subject placement step S1> Prior to imaging, the subject M is anesthetized so that the subject M does not move during imaging. A plurality of subjects M are stored in the holder 5. The holder 5 storing a plurality of subjects M is placed on the top 2.
  • ⁇ Shooting start step S2> When the experimenter instructs the X-ray tomography apparatus 20 to start tomography through the console 26, the top 2 slides and the subject M is introduced into the through hole of the gantry 10 (see FIG. 5). ).
  • the X-ray tube control unit 6 irradiates X-rays intermittently according to the irradiation time, tube current, and tube voltage stored in the storage unit 28. Meanwhile, the rotation mechanism 7 rotates the X-ray tube 3 and the FPD 4.
  • the FPD 4 detects X-rays that have passed through the subject M among X-rays irradiated by the X-ray tube 3, and sends detection data at this time to the image generation unit 11.
  • the image generation unit 11 converts the detection data sent from the FPD 4 into an image, and generates a fluoroscopic image P0 in which the X-ray intensity is mapped. Since the FPD 4 sends detection data to the image generation unit 11 every time the X-ray tube 3 emits X-rays, the image generation unit 11 generates a plurality of fluoroscopic images P0. Since a plurality of fluoroscopic images P0 are acquired while the X-ray tube 3 and the FPD 4 are rotated, each of the fluoroscopic images P0 is reflected while changing the direction in which the fluoroscopic image of the subject M is seen through. It will be. When the X-ray tube 3 and the FPD 4 make one rotation from the start of imaging, the X-ray tube 3 ends the X-ray irradiation.
  • the movement of the top 2 after the start of shooting will be described.
  • the X-ray tomography apparatus 20 can image only a part of the subject M by one imaging. This is because the width in the Z direction in the field of view of the X-ray tomography apparatus 20 is smaller than the width of the subject M in the Z direction. Therefore, according to the configuration of the first embodiment, a tomographic image of the entire image of the subject M is acquired by performing imaging a plurality of times when the above-described X-ray tube 3 and FPD 4 complete one rotation. . That is, as shown on the left side of FIG. 11, first, the tail of the subject M is imaged, and then the relative position between the subject M and the gantry 10 is changed by sliding the top board 2. 11, the abdomen of the subject M is imaged. Thereafter, the top plate 2 is slid again, and the head of the subject M is imaged as shown on the right side of FIG. In this way, the fluoroscopic image P0 is acquired for the entire subject.
  • the fluoroscopic image P0 is sent to the spatial data generation unit 12.
  • the spatial data generation unit 12 reconstructs a series of fluoroscopic images P0 having information related to the three-dimensional structure of the subject M by photographing while changing the direction, and expresses the ease of passage of X-rays.
  • the three-dimensional space data D1 in which the luminances are arranged three-dimensionally is generated.
  • the three-dimensional space data D1 is sent to the marker specifying unit 17 and the dividing unit 13.
  • the marker specifying unit 17 specifies the position of the intersection point p of each tray 5c in the three-dimensional space data D1 by performing marker specifying processing on the three-dimensional space data D1.
  • the position information Dm is sent to the dividing unit 13.
  • an identification number for distinguishing the tray 5c is given to the position information Dm.
  • the marker specifying unit 17 attaches a different identification number to the position information Dm every time a different intersection is searched. This makes it clear which tray 5c the intersection point p indicated by the position information Dm is about.
  • the dividing unit 13 divides the three-dimensional space data D1 based on the position information Dm, and generates divided data D2 including a single subject M for each intersection p included in the three-dimensional space data D1. .
  • the identification number assigned to the position information Dm by the marker specifying unit 17 is inherited.
  • the divided data D2 is sent to the analysis image generation unit 14.
  • the analysis image generation unit 14 performs image processing on the divided data D2 that is three-dimensional voxel data, and generates a two-dimensional image P1 such as a tomographic image.
  • the analysis image generation unit 14 superimposes the identification number assigned to the divided data D2 on the two-dimensional image P1, and sends it to the display unit 25.
  • the two-dimensional image P1 is displayed on the display unit 25, and the operation of the X-ray tomography apparatus ends.
  • the X-ray tomography layer apparatus 1 with improved work efficiency can be provided. That is, according to the structure of Example 1, the holder 5 provided with the marker 5m which shows the position of the subject M is provided. After the three-dimensional space data D1 is generated, the specification of the position of each marker 5m included therein is specified, and the three-dimensional space data D1 is divided based on the position of each marker 5m. As a result, the three-dimensional space data D1 is reliably divided into divided data D2 including a single subject M. As a result, since the data analysis can be performed for each of the subjects M without an experimenter performing complicated trimming operations, the work efficiency of the X-ray tomography layer apparatus 1 is high.
  • the holder 5 is provided with three markers 5m indicating the position of the subject M in three orthogonal directions for one subject M, the three-dimensional of the subject M in the three-dimensional space data D1 is provided. The position is surely set to one.
  • the marker specifying unit 17 can reliably specify the position of the marker 5m in the three-dimensional space data D1.
  • the position of the marker 5m in the three-dimensional space data D1 is surely the position of the subject M in the three-dimensional space data D1. Each position will be shown.
  • the experimenter can easily introduce the subject M into the holder 5, and the working efficiency is further improved.
  • the X-ray tomography layer apparatus 1 can be provided.
  • each subject M can be identified for both the experimenter and the marker specifying unit 17. It is possible to prevent the experimenter from confusing the subject M and deriving the experimental result.
  • the radiation tomography apparatus 20 according to the second embodiment is incorporated in a PET (Positron Emission Tomography) apparatus.
  • Gamma rays correspond to radiation in the present invention.
  • the radiation tomography apparatus according to the first embodiment is for small animal photography.
  • the radiation tomography apparatus 20 has a gantry 10a as shown in FIG.
  • the gantry 10a has a through hole extending in the Z direction, and the top plate 2 is inserted therethrough.
  • a detector ring 32 having an opening and a ring shape following the shape of the gantry 10a.
  • the detector ring 32 is configured by arranging detectors capable of detecting ⁇ rays in a ring shape.
  • the detector ring 32 corresponds to the detection means of the present invention.
  • the coincidence unit 33 is provided for the purpose of performing coincidence processing on the detection data output from the detector ring 32.
  • the coincidence counting unit 33 specifies the detection frequency and the detection position of the annihilation ⁇ -ray pairs incident simultaneously on different portions of the detector ring 32.
  • the coincidence counting unit 33 outputs the result of coincidence counting to the spatial data generation unit 34.
  • the spatial data generation unit 34 calculates the generation position of the annihilation ⁇ -ray pair based on the detection frequency and detection position of the annihilation ⁇ -ray pair specified by the coincidence counting unit 33, and the generation intensity of the annihilation ⁇ -ray pair is three-dimensional.
  • the three-dimensional spatial data D1 mapped automatically is generated.
  • the radiation tomography apparatus 20 includes a dividing unit 13, an analysis image generating unit 14, and a marker specifying unit 17 as in the first embodiment.
  • a positron emitting radiopharmaceutical is injected into the subject M.
  • the radiopharmaceutical has a property of concentrating on a specific part such as a lesion of the subject M.
  • Radiopharmaceuticals emit positrons, which generate annihilation gamma ray pairs that fly 180 degrees in the opposite direction. Therefore, an annihilation gamma ray pair is emitted from the subject M. Since the distribution of the radiopharmaceutical is different within the subject, the frequency of occurrence of annihilation ⁇ -ray pairs differs depending on the portion of the subject M.
  • the subject M is anesthetized, introduced into the tray 5c and stored in the holder 5 as in the first embodiment.
  • the tray 5c is provided with a plate-like marker 5m provided for the purpose of clarifying the position of the subject M as in the first embodiment. Since the marker 5m is configured as three-dimensional spatial data of PET, it is configured as a sealed radiation source member that generates pair annihilation radiation or a container into which a radiopharmaceutical can be injected. Then, the holder 5 in a state in which a plurality of subjects M are stored is placed on the top 2.
  • the experimenter instructs the radiation tomography apparatus 20 to start imaging the PET image through the console 26, the top 2 slides and the subject M is introduced into the through hole of the gantry 10a (see FIG. 12). ). From this point, the detector ring 32 starts detecting the annihilation ⁇ -ray pairs, and the spatial data generation unit 34 generates the three-dimensional spatial data D1 in which the generation intensity of the annihilation ⁇ -ray pairs is three-dimensionally mapped.
  • the three-dimensional space data D1 is generated while sliding the top 2 in the Z direction. You may make it do.
  • the three-dimensional space data D1 includes the radiopharmaceutical distribution of the subject M and the marker 5m.
  • the three-dimensional space data D1 is sent to the marker specifying unit 17 and the dividing unit 13 and divided into divided data D2.
  • the divided data D2 is sent to the analysis image generation unit 14 and converted into a two-dimensional image P1 such as a tomographic image or an SUV image. Therefore, the dividing unit 13, the analysis image generating unit 14, and the marker specifying unit 17 generate the two-dimensional image P1 by performing image processing independently for each subject M.
  • the two-dimensional image P1 generated in this way is displayed on the display unit 25 together with an identification number for distinguishing each subject M, and the imaging is completed.
  • An SUV (Standardized Uptake Value) image is a tomographic image in which SUV values obtained by normalizing the distribution of radiopharmaceuticals when two-dimensional spatial data D1 is acquired by a positron emission tomography apparatus are two-dimensionally arranged.
  • the analysis image generation unit 14 acquires the SUV value by normalizing the entire divided data D2 based on the amount of the radiopharmaceutical administered to the subject M and the weight of the subject M.
  • the configuration described above is an application of the present invention to the radiation tomography apparatus 20. That is, if the dividing unit 13, the analysis image generating unit 14, and the marker specifying unit 17 are applied to a radiation tomography apparatus 20 that acquires a tomographic image by measuring radiation emitted from the subject M, radiation tomography Even if a plurality of subjects M are imaged at once with the apparatus 20, the radiation tomography apparatus 20 can be provided in which the work efficiency of the experiment does not decrease.
  • the present invention is not limited to the above-described configuration, and can be modified as follows.
  • the handle 5d of the tray 5c in the first embodiment has an L shape as shown in FIG. 3, the handle 5d may have a T shape as shown on the left side of FIG. 13 instead.
  • one of the markers 5m is provided on the surface of the tray 5c on which the handle 5d is provided. Instead, the marker 5m is shown on the right side of FIG. As described above, the marker 5m may be provided on the end surface of the tray 5c where the handle 5d is not provided.
  • the arrangement of the markers 5m can be changed as appropriate. If the position of the marker 5m on the tray 5c is changed, the position of the intersection point p is also changed accordingly.
  • the divided data D2 is generated by cutting the three-dimensional space data D1 into a cylindrical shape, but the present invention is not limited to this.
  • the shape when the dividing unit 13 cuts out the three-dimensional space data D1 can be changed as appropriate.
  • the experimenter may be made to select the cut shape through the console 26.
  • the dividing unit 13 may cut out the divided data D2 by dividing each of the data of the subject M in which the three-dimensional space data D1 is arranged in series. That is, the dividing unit 13 refers to the three-dimensional space at the position of the broken line shown in FIG. 14 so as to cut out the data of the subject M arranged in series as shown in FIG. Data D1 may be divided to generate divided data D2.
  • the data processing apparatus is not limited to the X-ray imaging apparatus and the PET apparatus, and can be mounted on other tomography apparatuses such as MRI and SPECT. It can also be mounted on a device combining a plurality of tomographic devices, for example, a PET-CT device.
  • the present invention is suitable for a radiation tomography apparatus for research.

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Abstract

Provided is a radiation tomography device used when a plurality of subjects is imaged at once, wherein it is possible to improve the work efficiency of an experiment. The present invention makes it possible to provide an X-ray tomography device (1) having improved work efficiency. Specifically, according to the present invention, a holder is provided, to which is provided a marker (5m) indicating the position of a subject (M). Three-dimensional spatial data is generated, and subsequently the position of each of the markers (5m) contained therein is specified, and the three-dimensional spatial data is allocated on the basis of the positions of each of the markers (5m). The three-dimensional spatial data is thereby reliably allocated into allocated data containing a single subject (M). This makes it possible for data to be analyzed with respect to each of the subjects (M) without the need for an experimenter to perform a complicated trimming operation, and therefore the X-ray tomography device (1) has a higher work efficiency.

Description

放射線断層撮影装置Radiation tomography equipment

　本発明は、複数の被検体を一括して撮影するときに用いられる放射線断層撮影装置に関する。 The present invention relates to a radiation tomography apparatus used when imaging a plurality of subjects at once.

　研究対象としての被検体をイメージングする装置の一つに放射線断層撮影装置がある。この装置は、被検体の断層画像を生成することができるものであり、術者は、この画像を参照して被検体の内部の構造を知ることができる。 There is a radiation tomography device as one of the devices for imaging a subject as a research object. This apparatus is capable of generating a tomographic image of a subject, and an operator can know the internal structure of the subject by referring to this image.

　この様な放射線断層撮影装置の従来の構成について説明する。従来装置は、図１５に示す様に、開口が設けられたガントリ５１を有し、このガントリ５１の内部には、被検体に注射投与された放射性薬剤から発生する放射線を検出する検出器リング６２が設けられている。被検体は検出器リング６２の開口の内部に導入される。 The conventional configuration of such a radiation tomography apparatus will be described. As shown in FIG. 15, the conventional apparatus has a gantry 51 provided with an opening. Inside the gantry 51 is a detector ring 62 for detecting radiation generated from a radiopharmaceutical injected into a subject. Is provided. The subject is introduced into the opening of the detector ring 62.

　ところで生理的な実験一般においては、実験条件を変更させながら複数の実験を行うのが一般的である。つまり、小動物を用いた実験においては、実験処理を少しずつ違えながら複数の小動物について行い、何らかの傾向を示した実験結果を得ることがよく行われる。従って、小動物用放射線断層撮影装置のイメージングは、複数の小動物について行うのが通常である。 By the way, in general physiological experiments, it is common to conduct a plurality of experiments while changing the experimental conditions. That is, in an experiment using small animals, it is often performed to perform a plurality of small animals while slightly changing the experiment process, and obtain experimental results showing some tendency. Therefore, the imaging of the radiation tomography apparatus for small animals is usually performed for a plurality of small animals.

　実験の作業効率を高めるには、一度の撮影で複数の被検体を撮影するようにすればよい。そこで、従来の構成においては、複数の被検体を収納できるホルダを備えている。このホルダがガントリ５１内部に載置された状態で断層画像の撮影が行われる（例えば特許文献１，特許文献２，特許文献３参照）。 In order to increase the work efficiency of the experiment, a plurality of subjects may be imaged with a single imaging. Therefore, the conventional configuration includes a holder that can store a plurality of subjects. A tomographic image is taken in a state where the holder is placed inside the gantry 51 (see, for example, Patent Document 1, Patent Document 2, and Patent Document 3).

　取得された断層画像は、ホルダ全体が写り込んでいる。ホルダには複数の被検体が収納されているのであるから、断層画像には複数の被検体が写り込んでいることになる。実験者は断層画像に現れた被検体の断面像について種々の解析をして、実験結果を導き出す。 The acquired tomographic image shows the entire holder. Since a plurality of subjects are stored in the holder, a plurality of subjects are reflected in the tomographic image. The experimenter performs various analyzes on the cross-sectional image of the subject appearing in the tomographic image and derives the experimental result.

特開２００４－１２１２８９号公報JP 2004-121289 A 特開２００５－１４０５６０号公報JP 2005-140560 A 特開２００５－１４０５６１号公報JP 2005-140561 A

　しかしながら、従来の構成によれば、次のような問題点がある。
　すなわち、１つの断層画像に複数の被検体の断面像が写り込んでいると、解析作業が困難となるという問題点がある。被検体の条件を変えて実験を行う場合、被検体の断面像は互いに異なった様子で断層画像写り込む。例えば、１つの断層画像に写り込む断層像の輝度が複数の被検体の間でまちまちとなる。断層画像を視認しやすいように輝度調節をするときに、断層画像に明るく写り込んでいる被検体の断層像に基準にすると、他の暗く写り込んでいる被検体の断層像が更に暗くなりすぎて視認性が悪化する。逆に輝度調節の際、断層画像に暗く写り込んでいる被検体の断層像に基準にすると、他の明るく写り込んでいる被検体の断層像が更に明るくなりすぎて視認性が悪化する。 However, the conventional configuration has the following problems.
That is, there is a problem that analysis work becomes difficult when cross-sectional images of a plurality of subjects are reflected in one tomographic image. When an experiment is performed while changing the conditions of the subject, the cross-sectional images of the subject are captured in tomographic images in different states. For example, the luminance of the tomographic image reflected in one tomographic image varies among a plurality of subjects. When adjusting the brightness so that the tomographic image is easily visible, if the tomographic image of the subject that appears bright in the tomographic image is used as a reference, the other tomographic image of the subject that appears darker will be too dark. Visibility deteriorates. On the other hand, when adjusting the brightness, if the tomographic image of the subject appearing dark in the tomographic image is used as a reference, the other tomographic image of the subject appearing brighter becomes too bright and the visibility deteriorates.

　このように、被検体の断層像個別に輝度調節などの画像処理を行わなければならない場合は、実験者が１つの断層画像に写り込む複数の被検体の断層像を個別にトリミングして、単一の断層像が写り込んだ画像を生成しなければならない。この作業は実験者にとってかなり煩雑である。 In this way, when image processing such as brightness adjustment must be performed for each tomographic image of the subject, the experimenter individually trims the tomographic images of the plurality of subjects that appear in one tomographic image, An image with a single tomographic image must be generated. This work is quite complicated for the experimenter.

　この様な事情は輝度調節に限らない。すなわち、被検体の体重で放射性薬剤の発生強度を補正しようとするときも同様なトリミング作業が必要となる。 Such circumstances are not limited to brightness adjustment. That is, a similar trimming operation is required when correcting the generation intensity of the radiopharmaceutical with the body weight of the subject.

　本発明は、この様な事情に鑑みてなされたものであって、その目的は、複数の被検体を一括して撮影するときに用いられる放射線断層撮影装置において、実験の作業効率を向上することができる放射線断層撮影装置を提供することにある。 The present invention has been made in view of such circumstances, and an object of the present invention is to improve the work efficiency of an experiment in a radiation tomography apparatus used when imaging a plurality of subjects at once. It is an object of the present invention to provide a radiation tomography apparatus capable of performing

　本発明は上述の課題を解決するために次のような構成をとる。
　すなわち、本発明に係る放射線断層撮影装置は、放射線を検出する検出手段と、被検体の位置を示すマーカが設けられた複数被検体保持用のホルダと、検出手段が出力する検出信号を基に、複数のマーカおよび複数の被検体を包含した３次元空間データを生成するデータ生成手段と、３次元空間データにおける各マーカの位置を特定するマーカ特定手段と、特定されたマーカの位置に基づいて３次元空間データを分割して単一の被検体を包含した分割データを生成する分割手段を備ることを特徴とするものである。 The present invention has the following configuration in order to solve the above-described problems.
That is, the radiation tomography apparatus according to the present invention is based on a detection means for detecting radiation, a holder for holding a plurality of subjects provided with markers indicating the position of the subject, and a detection signal output by the detection means. A data generating means for generating three-dimensional spatial data including a plurality of markers and a plurality of subjects, a marker specifying means for specifying the position of each marker in the three-dimensional spatial data, and a position of the specified marker The image forming apparatus includes a dividing unit that divides the three-dimensional space data to generate divided data including a single subject.

　［作用・効果］本発明によれば、作業効率が向上された放射線断層撮影装置が提供できる。すなわち、本発明によれば被検体の位置を示すマーカが設けられたホルダを備える。３次元空間データが生成された後、これに包含されている各マーカの位置が特定され、各マーカの位置の基づいて３次元空間データが分割される。これにより、３次元空間データは確実に単一の被検体を包含した分割データに分割される。つまり、実験者が煩雑なトリミング作業をすることなく被検体の各々についてデータ解析ができるので、本発明の放射線断層撮影装置の作業効率は高いものとなる。 [Operation / Effect] According to the present invention, a radiation tomography apparatus with improved work efficiency can be provided. That is, according to the present invention, the holder is provided with the marker indicating the position of the subject. After the three-dimensional space data is generated, the position of each marker included therein is specified, and the three-dimensional space data is divided based on the position of each marker. As a result, the three-dimensional spatial data is surely divided into divided data including a single subject. That is, since the experimenter can perform data analysis for each subject without performing complicated trimming work, the working efficiency of the radiation tomography apparatus of the present invention is high.

　また、上述の放射線断層撮影装置において、ホルダには、１つの被検体について、それぞれ直交する３方向における被検体の位置を示す３つのマーカが設けられていればより望ましい。 In the above-described radiation tomography apparatus, it is more desirable that the holder is provided with three markers indicating the positions of the subjects in three orthogonal directions for each subject.

　［作用・効果］上述の構成は、本発明の放射線断層撮影装置のより具体的な構成を示すものとなっている。すなわち、ホルダに１つの被検体について、それぞれ直交する３方向における被検体の位置を示す３つのマーカが設けられていれば、３次元空間データにおける被検体の３次元的な位置が確実に１つに定まることになる。 [Operation / Effect] The above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. That is, if three markers indicating the position of the subject in three orthogonal directions are provided for one subject on the holder, the three-dimensional position of the subject in the three-dimensional space data is surely one. Will be determined.

　また、上述の放射線断層撮影装置において、マーカ特定手段は３次元空間データの断層画像を生成して、各断層画像のうちからマーカが写り込んだ画像を検索することによりマーカの位置を特定すればより望ましい。 In the above-described radiation tomography apparatus, the marker specifying unit generates a tomographic image of three-dimensional spatial data and specifies the position of the marker by searching an image in which the marker is reflected from each tomographic image. More desirable.

　［作用・効果］上述の構成は、本発明の放射線断層撮影装置のより具体的な構成を示すものとなっている。すなわち、３次元空間データのマーカの位置を特定する際に、３次元空間データの断層画像を生成して、各断層画像のうちからマーカが写り込んだ画像を検索するようにすれば、マーカ特定手段は、３次元空間データにおけるマーカの位置を確実に特定することができる。 [Operation / Effect] The above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. In other words, when specifying the position of the marker of the three-dimensional spatial data, if a tomographic image of the three-dimensional spatial data is generated and an image in which the marker is reflected is retrieved from each tomographic image, the marker identification is performed. The means can reliably specify the position of the marker in the three-dimensional space data.

　また、上述の放射線断層撮影装置において、ホルダには被検体を個別に載置するトレイと、トレイを導入する凹部とが設けられており、マーカはトレイに備えられていればより望ましい。 In the above-described radiation tomography apparatus, the holder is provided with a tray on which the subject is individually placed and a recess for introducing the tray, and it is more desirable that the marker be provided on the tray.

　［作用・効果］上述の構成は、本発明の放射線断層撮影装置のより具体的な構成を示すものとなっている。すなわち、マーカが被検体を個別に載置するトレイに設けられていれば、３次元空間データにおけるマーカの位置は、確実に３次元空間データにおける被検体の各々の位置を示すことになる。 [Operation / Effect] The above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. That is, if the marker is provided on the tray on which the subject is individually placed, the position of the marker in the three-dimensional space data surely indicates the position of each subject in the three-dimensional space data.

　また、上述の放射線断層撮影装置において、マーカは、トレイを凹部から引き出すときの引手に設けられていればより望ましい。 In the above-mentioned radiation tomography apparatus, it is more desirable that the marker is provided on a handle when the tray is pulled out from the recess.

　［作用・効果］上述の構成は、本発明の放射線断層撮影装置のより具体的な構成を示すものとなっている。マーカがトレイをホルダの凹部から引き出すときの引手となっていれば、実験者は容易に被検体をホルダに導入することができるので、一段と作業効率が向上した放射線断層撮影装置が提供できる。 [Operation / Effect] The above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. If the marker serves as a handle for pulling out the tray from the concave portion of the holder, the experimenter can easily introduce the subject into the holder, so that a radiation tomography apparatus with further improved work efficiency can be provided.

　また、上述の放射線断層撮影装置において、マーカは、３次元空間データにおいて各被検体を識別する記号となっていればより望ましい。 In the radiation tomography apparatus described above, it is more desirable that the marker is a symbol for identifying each subject in the three-dimensional spatial data.

　［作用・効果］上述の構成は、本発明の放射線断層撮影装置のより具体的な構成を示すものとなっている。マーカが３次元空間データにおいて各被検体を識別する記号となっていれば、実験者にとってもマーカ特定手段にとっても各被検体を識別することができることになり、実験者が被検体を取り違えて実験結果を導出することが防止できる。 [Operation / Effect] The above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. If the marker is a symbol for identifying each subject in the three-dimensional space data, each subject can be identified for both the experimenter and the marker specifying means. Deriving results can be prevented.

　また、上述の放射線断層撮影装置において、ホルダを載置する天板と、天板を放射線断層装置の開口部の直交方向に移動させる天板移動手段とを備えればより望ましい。 In the above-described radiation tomography apparatus, it is more desirable to include a top plate on which the holder is placed and a top plate moving means for moving the top plate in a direction orthogonal to the opening of the radiation tomography apparatus.

　［作用・効果］上述の構成は、本発明の放射線断層撮影装置のより具体的な構成を示すものとなっている。ホルダが載置可能で摺動自在の天板を備えるようにすれば、容易に被検体を撮影視野内に導入することができる放射線断層撮影装置が提供できる。 [Operation / Effect] The above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. If the holder is provided with a slidable top plate, a radiation tomography apparatus capable of easily introducing the subject into the field of view can be provided.

　また、上述の放射線断層撮影装置において、放射線を照射する放射線源と、放射線源および検出手段を回転させる回転手段とを備え、検出手段は、放射線源から発生して被検体を透過してきた放射線を検出すればより望ましい。 The radiation tomography apparatus includes a radiation source that emits radiation, and a rotation unit that rotates the radiation source and the detection unit. The detection unit emits radiation generated from the radiation source and transmitted through the subject. It is more desirable if it is detected.

　［作用・効果］上述の構成は、本発明の放射線断層撮影装置のより具体的な構成を示すものとなっている。本発明をコンピューター断層撮影装置に適用すれば、容易にＣＴ画像が取得できる放射線断層撮影装置が提供できる。 [Operation / Effect] The above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. When the present invention is applied to a computer tomography apparatus, a radiation tomography apparatus capable of easily obtaining a CT image can be provided.

　また、上述の放射線断層撮影装置において、検出手段は被検体から発せられる放射線を検出する検出器リングであり、ポジトロン放出断層撮影装置として構成されていればより望ましい。 In the above-mentioned radiation tomography apparatus, the detection means is a detector ring for detecting radiation emitted from the subject, and it is more desirable if it is configured as a positron emission tomography apparatus.

　［作用・効果］上述の構成は、本発明の放射線断層撮影装置のより具体的な構成を示すものとなっている。本発明を陽電子放出型断層撮影装置に適用すれば、容易にＰＥＴ画像が取得できる放射線断層撮影装置が提供できる。 [Operation / Effect] The above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. If the present invention is applied to a positron emission tomography apparatus, a radiation tomography apparatus capable of easily acquiring a PET image can be provided.

　本発明によれば、作業効率が向上された放射線断層撮影装置が提供できる。すなわち、本発明によれば被検体の位置を示すマーカが設けられたホルダを備える。３次元空間データが生成された後、これに包含されている各マーカの位置が特定され、各マーカの位置の基づいて３次元空間データが分割される。これにより、３次元空間データは確実に単一の被検体を包含した分割データに分割される。つまり、実験者が煩雑なトリミング作業をすることなく被検体の各々についてデータ解析ができるので、本発明の放射線断層撮影装置の作業効率は高いものとなる。 According to the present invention, a radiation tomography apparatus with improved work efficiency can be provided. That is, according to the present invention, the holder is provided with the marker indicating the position of the subject. After the three-dimensional space data is generated, the position of each marker included therein is specified, and the three-dimensional space data is divided based on the position of each marker. As a result, the three-dimensional spatial data is surely divided into divided data including a single subject. That is, since the experimenter can perform data analysis for each subject without performing complicated trimming work, the working efficiency of the radiation tomography apparatus of the present invention is high.

実施例１に係るＸ線断層撮影装置の構成を説明する機能ブロック図である。1 is a functional block diagram illustrating a configuration of an X-ray tomography apparatus according to Embodiment 1. FIG. 実施例１に係るホルダの構成について平面図である。It is a top view about the structure of the holder which concerns on Example 1. FIG. 実施例１に係るトレイの構成について斜視図である。3 is a perspective view of a configuration of a tray according to Embodiment 1. FIG. 実施例１に係るトレイの構成について断面図である。FIG. 3 is a cross-sectional view of the configuration of the tray according to the first embodiment. 実施例１に係る空間データを説明する模式図である。FIG. 3 is a schematic diagram illustrating spatial data according to the first embodiment. 実施例１に係るデータ処理を説明する模式図である。6 is a schematic diagram illustrating data processing according to Embodiment 1. FIG. 実施例１に係るデータ処理を説明する模式図である。6 is a schematic diagram illustrating data processing according to Embodiment 1. FIG. 実施例１に係るデータ処理を説明する模式図である。6 is a schematic diagram illustrating data processing according to Embodiment 1. FIG. 実施例１に係る分割データを説明する模式図である。FIG. 3 is a schematic diagram illustrating divided data according to the first embodiment. 実施例１に係るＸ線断層撮影装置の動作を説明するフローチャートである。3 is a flowchart for explaining the operation of the X-ray tomography apparatus according to Embodiment 1; 実施例１に係るＸ線断層撮影装置の動作を説明する断面図である。FIG. 3 is a cross-sectional view illustrating the operation of the X-ray tomography apparatus according to Embodiment 1. 実施例２に係る放射線線断層撮影装置の動作を説明する機能ブロック図である。FIG. 6 is a functional block diagram for explaining the operation of the radiation tomography apparatus according to Embodiment 2. 本発明の１変形例に係るトレイの構成について斜視図である。It is a perspective view about the structure of the tray which concerns on one modification of this invention. 本発明の１変形例に係るデータ処理を説明する模式図である。It is a schematic diagram explaining the data processing which concerns on 1 modification of this invention. 従来構成の放射線線断層撮影装置の動作を説明する模式図である。It is a schematic diagram explaining operation | movement of the radiation ray tomography apparatus of a conventional structure.

　以降、本発明の実施例について説明する。 Hereinafter, examples of the present invention will be described.

　次に、実施例１に係る放射線断層撮影装置について説明する。実施例１における放射線断層撮影装置は、被検体Ｍの構造を断層撮影するＣＴ装置となっている。実施例１におけるＸ線は本発明における放射線に相当し、ＦＰＤはフラットパネル・ディテクタの略である。また、実施例１に係る放射線断層撮影装置は小動物撮影用となっている。 Next, the radiation tomography apparatus according to Embodiment 1 will be described. The radiation tomography apparatus according to the first embodiment is a CT apparatus that performs tomography of the structure of the subject M. The X-ray in Example 1 corresponds to the radiation in the present invention, and FPD is an abbreviation for flat panel detector. Further, the radiation tomography apparatus according to the first embodiment is for small animal photography.

　まず、実施例１に係るＸ線断層撮影装置について説明する。Ｘ線断層撮影装置１は、図１に示す様に被検体Ｍを載置する天板２と、天板２の伸びる方向に貫通した貫通孔を有するガントリ１０とを備えている。天板２は、ガントリ１０の貫通孔に挿通されており、天板２を支持する支持台２ａに対して天板２の伸びる方向（放射線断層装置の開口部の直交方向）に進退自在に移動することができる。この天板２の移動は天板移動機構１５が行う。天板移動制御部１６は、天板移動機構１５を制御するものである。天板移動機構１５は、本発明の天板移動手段に相当する。 First, the X-ray tomography apparatus according to the first embodiment will be described. As shown in FIG. 1, the X-ray tomography apparatus 1 includes a top plate 2 on which a subject M is placed and a gantry 10 having a through hole penetrating in the direction in which the top plate 2 extends. The top plate 2 is inserted through the through hole of the gantry 10 and moves so as to be able to advance and retract in the direction in which the top plate 2 extends (perpendicular to the opening of the radiation tomography apparatus) with respect to the support base 2a that supports the top plate 2. can do. The top plate 2 is moved by a top plate moving mechanism 15. The top plate movement control unit 16 controls the top plate movement mechanism 15. The top plate moving mechanism 15 corresponds to the top plate moving means of the present invention.

　ガントリ１０の内部には、Ｘ線を照射するＸ線管３と、Ｘ線を検出するＦＰＤ４とが設けられている。Ｘ線管３から照射されたＸ線は、ガントリの貫通孔を横切るように通過して、ＦＰＤ４に到達する。Ｘ線管３は、本発明の放射線源に相当し、ＦＰＤ４は、本発明の検出手段に相当する。 Inside the gantry 10, an X-ray tube 3 for irradiating X-rays and an FPD 4 for detecting X-rays are provided. The X-rays irradiated from the X-ray tube 3 pass through the through hole of the gantry and reach the FPD 4. The X-ray tube 3 corresponds to the radiation source of the present invention, and the FPD 4 corresponds to the detection means of the present invention.

　Ｘ線管制御部６は、所定の管電流、管電圧、パルス幅でＸ線管３を制御する目的で設けられている。ＦＰＤ４は、Ｘ線管３から発せられ、被検体Ｍを透過したＸ線を検出して検出信号を生成する。この検出信号は、画像生成部１１に送出され、そこで被検体Ｍの投影像が写り込んだ透視画像Ｐ０が生成される。空間データ生成部１２は、画像生成部１１で生成された透視画像Ｐ０を基に、Ｘ線の吸収係数を表した輝度が３次元的に配列された３次元空間データＤ１を生成する。空間データ生成部１２は、本発明のデータ生成手段に相当する。 The X-ray tube control unit 6 is provided for the purpose of controlling the X-ray tube 3 with a predetermined tube current, tube voltage, and pulse width. The FPD 4 detects X-rays emitted from the X-ray tube 3 and transmitted through the subject M, and generates a detection signal. This detection signal is sent to the image generation unit 11, where a perspective image P0 in which a projection image of the subject M is reflected is generated. The spatial data generation unit 12 generates three-dimensional spatial data D1 in which the luminance representing the X-ray absorption coefficient is three-dimensionally arranged based on the fluoroscopic image P0 generated by the image generation unit 11. The spatial data generation unit 12 corresponds to data generation means of the present invention.

　天板２には、被検体Ｍを保持するためのホルダ５が載置されている。このホルダ５の構造について説明する。ホルダ５は、図２に示す様に、５つの円（立体として捕らえればＺ方向に伸びた円柱）の形状の開口５ａを有している。この開口５ａの各々に被検体Ｍが一体ずつ挿入されることになる。開口５ａの内壁を形成する円筒５ｂは、Ｚ方向に伸びた複数の貫通孔がレンコン状に開けられた発泡スチロール製の円筒支持体５ｂ１における貫通孔の各々に埋め込まれることで支持されている。また、円筒５ｂは、Ｘ線を透過しやすいアクリル樹脂で構成される。ホルダ５は、天板２に近い側の一段目に３個の開口５ａが、天板２に遠い側の二段目に２個の開口５ａが形成されているような形状をしている。開口５ａは、本発明の凹部に相当する。 A holder 5 for holding the subject M is placed on the top plate 2. The structure of the holder 5 will be described. As shown in FIG. 2, the holder 5 has an opening 5 a having a shape of five circles (a cylinder extending in the Z direction if captured as a solid). The subject M is inserted into each of the openings 5a. The cylinder 5b forming the inner wall of the opening 5a is supported by being embedded in each of the through-holes in a polystyrene support 5b1 made of polystyrene foam in which a plurality of through-holes extending in the Z direction are opened in a lotus shape. The cylinder 5b is made of an acrylic resin that easily transmits X-rays. The holder 5 has a shape in which three openings 5 a are formed in the first stage on the side close to the top board 2 and two openings 5 a are formed in the second stage on the side far from the top board 2. The opening 5a corresponds to the concave portion of the present invention.

　開口５ａの各々には、被検体Ｍを載置するトレイ５ｃの各々が導入される。このトレイ５ｃの各々には被検体Ｍが個別に載置される。開口５ａは５個あることからすると、トレイ５ｃも５個あることになる。従って、図２におけるホルダ５は、５体の被検体Ｍを一度に保持することができる複数被検体保持用のホルダである。 Each of the trays 5c on which the subject M is placed is introduced into each of the openings 5a. A subject M is individually placed on each tray 5c. If there are five openings 5a, there are also five trays 5c. Therefore, the holder 5 in FIG. 2 is a holder for holding a plurality of subjects that can hold five subjects M at a time.

　トレイ５ｃの具体的な構成について説明する。トレイ５ｃは、図３に示す様にＺ方向に伸びる樋状の部材である。トレイ５ｃのＺ方向の両端には、Ｚ方向直交する面（端面）が設けられている。したがって、トレイ５ｃの内部は、鉛直方向に開いた半円柱状の切欠部となっている。この切欠部には被検体Ｍが載置される。切欠部に被検体Ｍを載置すると、被検体Ｍがトレイ５ｃに囲まれることになるので、トレイ５ｃと被検体Ｍの位置関係はズレることがない。トレイ５ｃは、例えばアクリル樹脂などで構成される。 A specific configuration of the tray 5c will be described. The tray 5c is a bowl-shaped member extending in the Z direction as shown in FIG. Surfaces (end faces) orthogonal to the Z direction are provided at both ends of the tray 5c in the Z direction. Therefore, the inside of the tray 5c is a semi-cylindrical notch that opens in the vertical direction. The subject M is placed in the notch. When the subject M is placed in the notch, the subject M is surrounded by the tray 5c, so that the positional relationship between the tray 5c and the subject M does not deviate. The tray 5c is made of, for example, an acrylic resin.

　トレイ５ｃに設けられている２面の端面のうち、１つの面には、被検体Ｍの位置を明確にする目的で設けられた板状のマーカ５ｍが設けられている。トレイ５ｃには同一形状のマーカ５ｍが３つ設けられており、マーカ５ｍのうちの１つは、端面に貼り付けられている。残り２つのマーカ５ｍは、Ｚ方向に伸びた樋状となっているトレイ５ｃを更に延伸する方向に突出した引手５ｄに設けられている。引手５ｄは、２つの面を有するＬ状となっており、引手５ｄの一面は鉛直方向に沿っており、もう一面は鉛直方向と直交する。そして、２つの面はトレイ５ｃの端面と直交する。マーカ５ｍは、引手５ｄの両面の各々に１つずつ設けられている。このマーカ５ｍは金属などのトレイ５ｃとは異なる部材で構成される。トレイ５ｃをくり抜いてマーカ５ｍを構成してもよい。 A plate-like marker 5m provided for the purpose of clarifying the position of the subject M is provided on one of the two end faces provided on the tray 5c. The tray 5c is provided with three markers 5m having the same shape, and one of the markers 5m is attached to the end face. The remaining two markers 5m are provided on a pulling handle 5d that protrudes in a direction in which the tray 5c, which has a bowl shape extending in the Z direction, is further extended. The handle 5d has an L shape having two surfaces, one surface of the handle 5d is along the vertical direction, and the other surface is orthogonal to the vertical direction. The two surfaces are orthogonal to the end surface of the tray 5c. One marker 5m is provided on each of both surfaces of the handle 5d. The marker 5m is formed of a member different from the tray 5c such as metal. The marker 5m may be configured by cutting out the tray 5c.

　このマーカ５ｍは、被検体Ｍの位置を表す目的で設けられている。従って、トレイ５ｃには、１つの被検体Ｍについて、それぞれ直交する３方向における被検体Ｍの位置を示す３つのマーカ５ｍが設けられていることになる。なお、図３における交点ｐは、３つのマーカ５ｍが貼り付けられている３平面が互いに交わる交点である。 The marker 5m is provided for the purpose of indicating the position of the subject M. Accordingly, the tray 5c is provided with three markers 5m indicating the position of the subject M in three orthogonal directions with respect to one subject M. Note that the intersection point p in FIG. 3 is an intersection point where the three planes on which the three markers 5m are pasted each other.

　マーカ５ｍの形状について説明する。ホルダ５は５つの開口５ａを有していることからするホルダ５は５つのトレイ５ｃを有することになる。トレイ５ｃに設けられているマーカ５ｍの形状は、トレイ５ｃ毎に異なる。すなわち、図３におけるトレイ５ｃに設けられた３つのマーカ５ｍはいずれもアルファベットのＡの文字を象っている。図示しないが、ホルダ５に設けられる他の４つのトレイ５ｃには、それぞれ、アルファベットのＢ，Ｃ，Ｄ，Ｅを象ったマーカ５ｍが３つずつ設けられている。マーカ５ｍは、各被検体Ｍを識別するときの記号としても機能する。トレイ５ｃによって形状の異なるマーカ５ｍは、実験者と後述のマーカ特定部１７との両者にとって各トレイ５ｃを識別する指標となっている。マーカ特定部１７は、本発明のマーカ特定手段に相当する。 The shape of the marker 5m will be described. Since the holder 5 has five openings 5a, the holder 5 has five trays 5c. The shape of the marker 5m provided on the tray 5c is different for each tray 5c. That is, each of the three markers 5m provided on the tray 5c in FIG. 3 represents the letter A of the alphabet. Although not shown, each of the other four trays 5c provided in the holder 5 is provided with three markers 5m each representing the alphabets B, C, D, and E. The marker 5m also functions as a symbol for identifying each subject M. The marker 5m having a different shape depending on the tray 5c serves as an index for identifying each tray 5c for both the experimenter and the marker specifying unit 17 described later. The marker specifying unit 17 corresponds to the marker specifying means of the present invention.

　図４は、トレイ５ｃが使用される様子を示している。図４に示すように、トレイ５ｃは、その切欠部に被検体Ｍを載置した状態でホルダ５の開口５ａに挿入されることができる。この動作の際、実験者は引手５ｄを保持することで容易にトレイ５ｃを開口５ａに挿入することもできるし、容易にトレイ５ｃを開口５ａから引き出すこともできる。また、トレイ５ｃの底部は、トレイ５ｃを円筒５ｂにスムーズに導入できるように、円筒５ｂの円柱形状に倣った樋状の曲面となっている。 FIG. 4 shows how the tray 5c is used. As shown in FIG. 4, the tray 5 c can be inserted into the opening 5 a of the holder 5 with the subject M placed in the cutout portion. During this operation, the experimenter can easily insert the tray 5c into the opening 5a by holding the handle 5d, or can easily pull out the tray 5c from the opening 5a. The bottom of the tray 5c has a bowl-shaped curved surface that follows the columnar shape of the cylinder 5b so that the tray 5c can be smoothly introduced into the cylinder 5b.

　マーカ特定部１７，分割部１３に関係する３次元空間データＤ１について説明する。３次元空間データＤ１は、図５に示す様に、複数の被検体（マウス）を３次元空間上に包含する３次元マトリックスデータとなっている。この３次元空間データＤ１は、放射線断層撮影装置により検出されたデータ（例えば輝度）が各ボクセルに配列されているものである。３次元空間データＤ１は、放射線断層撮影装置の撮影視野内に複数の被検体Ｍを導入した状態で取得されたものであり、被検体Ｍの各々の位置を表示するマーカ５ｍもこの３次元空間データＤ１に表されている。３次元空間データＤ１は、直方体の空間内にボクセルが配列されて構成される。３次元空間データＤ１が直方体を表すものとなっているのは、この様にするとデータの保持に都合がよいからである。分割部１３は、本発明の分割手段に相当する。 The three-dimensional space data D1 related to the marker specifying unit 17 and the dividing unit 13 will be described. As shown in FIG. 5, the three-dimensional space data D1 is three-dimensional matrix data including a plurality of subjects (mouse) in the three-dimensional space. The three-dimensional space data D1 is data (for example, luminance) detected by the radiation tomography apparatus arranged in each voxel. The three-dimensional space data D1 is acquired in a state where a plurality of subjects M are introduced into the field of view of the radiation tomography apparatus, and the marker 5m that displays the position of each subject M is also this three-dimensional space. It is represented in the data D1. The three-dimensional space data D1 is configured by arranging voxels in a rectangular parallelepiped space. The reason why the three-dimensional space data D1 represents a rectangular parallelepiped is that this is convenient for holding data. The dividing unit 13 corresponds to the dividing unit of the present invention.

　このように、３次元空間データＤ１は、放射線断層撮影装置が断層画像を生成する前の段階の３次元再構成データに相当している。 Thus, the three-dimensional space data D1 corresponds to three-dimensional reconstruction data at a stage before the radiation tomography apparatus generates a tomographic image.

　図５の３次元空間データＤ１には、５体の被検体Ｍと、これに対応する５個のマーカ５ｍとが表されている。図５においては、トレイ５ｃの端面に設けられたマーカ５ｍしか表されていないが、これは図面の簡潔化の結果であり、実際は、トレイ５ｃの端面と直交する平面に存する２つのマーカ５ｍも３次元空間データＤ１に表されている。 In the three-dimensional space data D1 of FIG. 5, five subjects M and five markers 5m corresponding thereto are represented. In FIG. 5, only the marker 5m provided on the end surface of the tray 5c is shown, but this is a result of simplification of the drawing, and actually two markers 5m existing on a plane orthogonal to the end surface of the tray 5c are also shown. It is represented in the three-dimensional space data D1.

　マーカ特定部１７は、３次元空間データＤ１における各マーカの位置を特定する目的で設けられている。マーカ特定部１７の動作について説明する。マーカ特定部１７は、３次元空間データＤ１を基に断層画像を生成する。具体的には、マーカ特定部１７は、３次元空間データＤ１の直方体形状を形成する６つの面のうちの１つと平行な断層画像を生成する。マーカ特定部１７は裁断位置を変更しながら断層画像を生成するので、断層画像は複数枚生成されることになる。そしてマーカ特定部１７は、図６に示すようにマーカ５ｍが写り込んでいる裁断面（マーカ含有断面）における断層画像を生成された複数の断層画像のうちから検索する。マーカ特定部１７は、３次元空間データＤ１におけるマーカ含有断面の位置を取得する。図６においては、トレイ５ｃの端面に設けられたマーカ５ｍについてのマーカ含有断面が取得されている（図３参照）。 The marker specifying unit 17 is provided for the purpose of specifying the position of each marker in the three-dimensional space data D1. The operation of the marker specifying unit 17 will be described. The marker specifying unit 17 generates a tomographic image based on the three-dimensional space data D1. Specifically, the marker specifying unit 17 generates a tomographic image parallel to one of the six surfaces forming the rectangular parallelepiped shape of the three-dimensional space data D1. Since the marker specifying unit 17 generates the tomographic image while changing the cutting position, a plurality of tomographic images are generated. And the marker specific | specification part 17 searches among the some tomographic images produced | generated for the tomographic image in the cut surface (marker containing cross section) in which the marker 5m is reflected, as shown in FIG. The marker specific | specification part 17 acquires the position of the marker containing cross section in the three-dimensional space data D1. In FIG. 6, a marker-containing cross section is obtained for the marker 5m provided on the end face of the tray 5c (see FIG. 3).

　マーカ特定部１７の実際の動作について説明する。マーカ特定部１７がＡの形状についてマーカ含有断面を取得しようとするときには、まず記憶部２８に記憶されているＡの形状を示す画像パターンを読み出す。そして、マーカ特定部１７は、各断層画像についてパターンマッチング処理をすることにより、断層画像に写り込むＡの形状を検索するのである。 The actual operation of the marker specifying unit 17 will be described. When the marker specifying unit 17 tries to acquire a marker-containing cross section for the A shape, first, an image pattern indicating the A shape stored in the storage unit 28 is read. And the marker specific | specification part 17 searches the shape of A reflected in a tomographic image by performing a pattern matching process about each tomographic image.

　マーカ特定部１７は、直方体形状を形成する６つの面のうち、互いに直交する３面について同様の動作をする。すなわち、マーカ特定部１７は、図７に示すように、先程検索して得られたマーカ含有断面と直交する２つのマーカ含有断面を検索する。この様にすることで、マーカ特定部１７は、互いに直交するマーカ含有断面上でトレイ５ｃに設けられた３つのマーカ５ｍをそれぞれ発見することになる（図３参照）。そして、マーカ特定部１７は、３つのマーカ含有断面の交点の位置を特定する。この交点の位置は、３次元空間データＤ１におけるトレイ５ｃの交点ｐ（図３参照）の位置を表している。 The marker specifying unit 17 performs the same operation on three surfaces orthogonal to each other among the six surfaces forming the rectangular parallelepiped shape. That is, as shown in FIG. 7, the marker specifying unit 17 searches for two marker-containing cross sections orthogonal to the marker-containing cross section obtained by the previous search. By doing in this way, the marker specific | specification part 17 each discovers the three markers 5m provided in the tray 5c on the marker containing cross section orthogonal to each other (refer FIG. 3). And the marker specific | specification part 17 specifies the position of the intersection of three marker containing cross sections. The position of this intersection represents the position of the intersection p (see FIG. 3) of the tray 5c in the three-dimensional space data D1.

　マーカ特定部１７は、５つのトレイ５ｃの各々について交点の位置の特定を行う。これによりトレイ５ｃの各々についての交点の位置が特定されることになる。このとき、パターンマッチング処理に用いられるパターンは、異なる形状のマーカ５ｍを探索する度にそれに合わせて変更されることになる。こうして、マーカ特定部１７は、３次元空間データＤ１に存するＡ～Ｅ形状の位置と、これらに対応する交点ｐＡ～ｐＥを特定する。マーカ特定部１７が特定した５つの交点ｐを区別してｐＡ，ｐＢ，ｐＣ，ｐＤ，ｐＥとする。マーカ特定部１７は、図８に示すように、５体の被検体Ｍに固有の交点ｐＡ～ｐＥの３次元空間データＤ１における位置を特定する。 The marker specifying unit 17 specifies the position of the intersection point for each of the five trays 5c. Thereby, the position of the intersection for each of the trays 5c is specified. At this time, the pattern used for the pattern matching process is changed in accordance with the search for the marker 5m having a different shape. Thus, the marker specifying unit 17 specifies the positions of the A to E shapes existing in the three-dimensional space data D1 and the intersection points pA to pE corresponding to these positions. The five intersection points p specified by the marker specifying unit 17 are distinguished and set as pA, pB, pC, pD, and pE. As shown in FIG. 8, the marker specifying unit 17 specifies the positions in the three-dimensional space data D1 of the intersections pA to pE unique to the five subjects M.

　次に、分割データＤ２について説明する。分割データＤ２は、図９に示す様に、単一の被検体Ｍを３次元空間上に包含する３次元マトリックスデータとなっている。この分割データＤ２は、３次元空間データＤ１と同様、放射線断層撮影装置により検出されたデータが各ボクセルに配列されているものである。分割データＤ２は、ボクセルが配列されて構成され、３次元空間データＤ１が円柱形に切り取られたものである。また、データの保持を容易とする目的で円柱形となっている分割データＤ２の外側にヌルデータのボクセルを付加して長方形に整形してもよい。 Next, the divided data D2 will be described. As shown in FIG. 9, the divided data D2 is three-dimensional matrix data including a single subject M in a three-dimensional space. Similar to the three-dimensional space data D1, the divided data D2 is obtained by arranging data detected by the radiation tomography apparatus in each voxel. The divided data D2 is configured by arranging voxels, and the three-dimensional space data D1 is cut into a cylindrical shape. Further, for the purpose of facilitating data retention, null data voxels may be added outside the divided data D2 having a cylindrical shape and shaped into a rectangle.

　分割部１３は、３次元空間データＤ１の一部を取り出して、分割データＤ２を生成する。このような動作をすることで、複数の被検体Ｍを包含していた３次元空間データＤ１は、単一の被検体Ｍを包含した分割データＤ２に変換される。分割部１３は、３次元空間データＤ１に包含される被検体Ｍの各々について分割データＤ２を生成する。したがって、３次元空間データＤ１から複数の分割データＤ２が生成されることになる。 The dividing unit 13 extracts a part of the three-dimensional space data D1 and generates divided data D2. By performing such an operation, the three-dimensional space data D1 including a plurality of subjects M is converted into divided data D2 including a single subject M. The dividing unit 13 generates divided data D2 for each subject M included in the three-dimensional space data D1. Therefore, a plurality of divided data D2 is generated from the three-dimensional space data D1.

　分割部１３は、マーカ特定部１７が特定した交点ｐＡ～ｐＥを基に３次元空間データＤ１の切り出しを実行する。すなわち、分割部１３が交点ｐＡに対応する被検体Ｍを３次元空間データＤ１から取り出そうとするとき、分割部１３は、交点ｐＡに対して所定の位置関係にある円柱形の領域を認識して、この領域を３次元空間データＤ１から取り出すことで分割データＤ２を生成するのである。分割部１３が認識する円柱形の領域と交点ｐとの位置関係を示すデータは、記憶部２８に記憶されている。 The dividing unit 13 cuts out the three-dimensional space data D1 based on the intersection points pA to pE specified by the marker specifying unit 17. That is, when the dividing unit 13 tries to extract the subject M corresponding to the intersection point pA from the three-dimensional space data D1, the dividing unit 13 recognizes a cylindrical region having a predetermined positional relationship with respect to the intersection point pA. This area is extracted from the three-dimensional space data D1 to generate the divided data D2. Data indicating the positional relationship between the cylindrical area recognized by the dividing unit 13 and the intersection point p is stored in the storage unit 28.

　分割部１３が認識する円柱形の領域は、図３におけるトレイ５ｃの有する被検体載置用の切欠部の全領域が収まるように定義されている。図３を参照すれば分かるように交点ｐとトレイ５ｃの切欠部の位置関係は、トレイ５ｃがホルダ５のどの位置にあろうとも一定である。したがって、３次元空間データＤ１においても、マーカ特定部１７が特定した交点ｐＡの位置と、Ａのマーカ５ｍが付されたトレイ５ｃの切欠部に相当する領域の位置とは、常に一定である。言い換えれば、３次元空間データＤ１における交点ｐＡの位置が分かれば、自ずと３次元空間データＤ１における被検体Ｍの位置が分かるということである。 The columnar region recognized by the dividing unit 13 is defined so that the entire region of the notch portion for placing the specimen on the tray 5c in FIG. As can be seen from FIG. 3, the positional relationship between the intersection point p and the cutout portion of the tray 5 c is constant no matter where the tray 5 c is located on the holder 5. Therefore, also in the three-dimensional space data D1, the position of the intersection point pA specified by the marker specifying unit 17 and the position of the region corresponding to the cutout portion of the tray 5c to which the A marker 5m is attached are always constant. In other words, if the position of the intersection point pA in the three-dimensional space data D1 is known, the position of the subject M in the three-dimensional space data D1 is naturally known.

　分割データＤ２は、解析画像生成部１４に送出される。解析画像生成部１４は、３次元マトリックスデータとなっている分割データＤ２を用いて２次元画像Ｐを生成する。生成される２次元画像Ｐとしては、例えば断層画像などがある。 The divided data D2 is sent to the analysis image generation unit 14. The analysis image generation unit 14 generates a two-dimensional image P using the divided data D2 that is three-dimensional matrix data. Examples of the generated two-dimensional image P include a tomographic image.

　断層画像は、被検体Ｍの断層像を写し込んだ画像である。解析画像生成部１４は、分割データＤ２の全体に輝度調節などのデータ処理をして、被検体Ｍをある平面で裁断したときの断層像が写り込んだ断層画像を生成する。 The tomographic image is an image in which a tomographic image of the subject M is captured. The analysis image generation unit 14 performs data processing such as brightness adjustment on the entire divided data D2, and generates a tomographic image in which a tomographic image when the subject M is cut along a certain plane is reflected.

　Ｘ線管３およびＦＰＤ４の回転について説明する。Ｘ線管３およびＦＰＤ４は、回転機構７により、天板２の伸びる方向に伸びた中心軸を中心に一体的に回転される。回転制御部８は回転機構７を制御するものである。回転機構７は、本発明の回転手段に相当する。 The rotation of the X-ray tube 3 and the FPD 4 will be described. The X-ray tube 3 and the FPD 4 are integrally rotated around the central axis extending in the direction in which the top plate 2 extends by the rotation mechanism 7. The rotation control unit 8 controls the rotation mechanism 7. The rotation mechanism 7 corresponds to the rotation means of the present invention.

　表示部２５は、Ｘ線撮影により取得された２次元画像Ｐを表示する目的で設けられている。操作卓２６は、実験者によるＸ線照射開始などの指示を入力させる目的で設けられている。また、主制御部２７は、各制御部を統括的に制御する目的で設けられている。この主制御部２７は、ＣＰＵによって構成され、各種のプログラムを実行することにより各制御部６，８，１６および各部１１，１２，１４，１７を実現している。また、上述の各部は、それらを担当する演算装置に分割されて実行されてもよい。記憶部２８は、撮影に用いられるパラメータ、画像処理に伴って生成される中間画像等のＸ線断層撮影装置１の制御に関するパラメータの一切を記憶する。 The display unit 25 is provided for the purpose of displaying a two-dimensional image P acquired by X-ray imaging. The console 26 is provided for the purpose of inputting an instruction such as an X-ray irradiation start by an experimenter. The main control unit 27 is provided for the purpose of comprehensively controlling each control unit. The main control unit 27 is constituted by a CPU, and realizes the control units 6, 8, 16 and the units 11, 12, 14, 17 by executing various programs. Further, each of the above-described units may be divided and executed by an arithmetic device that takes charge of them. The storage unit 28 stores all parameters relating to control of the X-ray tomography apparatus 1 such as parameters used for imaging and intermediate images generated in accordance with image processing.

　＜Ｘ線断層撮影装置の動作＞
　次に、Ｘ線断層撮影装置の動作について説明する。Ｘ線断層撮影装置は、図１０のフローチャートに示す各ステップを実行することにより行われる。以降これらの各ステップについて順を追って説明する。下記の動作説明は、複数の被検体Ｍを一度に撮影してその被検体Ｍの各々についての解析画像を取得する場合におけるものである。 <Operation of X-ray tomography apparatus>
Next, the operation of the X-ray tomography apparatus will be described. The X-ray tomography apparatus is performed by executing the steps shown in the flowchart of FIG. Hereinafter, these steps will be described in order. The following description of the operation is performed when a plurality of subjects M are photographed at a time and an analysis image for each of the subjects M is acquired.

　＜被検体載置ステップＳ１＞
　撮影に先立って、被検体Ｍが撮影中に移動しない様に被検体Ｍを麻酔しておく。ホルダ５に複数の被検体Ｍを収納する。そして、複数の被検体Ｍを収納したホルダ５は天板２に載置される。 <Subject placement step S1>
Prior to imaging, the subject M is anesthetized so that the subject M does not move during imaging. A plurality of subjects M are stored in the holder 5. The holder 5 storing a plurality of subjects M is placed on the top 2.

　＜撮影開始ステップＳ２＞
　実験者が操作卓２６を通じてＸ線断層撮影装置２０に断層撮影開始の指示を行うと、天板２が摺動し、被検体Ｍがガントリ１０の貫通孔の内部に導入される（図５参照）。Ｘ線管制御部６は、記憶部２８に記憶されている照射時間・管電流・管電圧に従い、Ｘ線を間欠的に照射する。その間に回転機構７は、Ｘ線管３およびＦＰＤ４を回転させる。ＦＰＤ４は、Ｘ線管３が照射したＸ線のうち被検体Ｍを通過してきたＸ線を検出し、このときの検出データを画像生成部１１に送出する。 <Shooting start step S2>
When the experimenter instructs the X-ray tomography apparatus 20 to start tomography through the console 26, the top 2 slides and the subject M is introduced into the through hole of the gantry 10 (see FIG. 5). ). The X-ray tube control unit 6 irradiates X-rays intermittently according to the irradiation time, tube current, and tube voltage stored in the storage unit 28. Meanwhile, the rotation mechanism 7 rotates the X-ray tube 3 and the FPD 4. The FPD 4 detects X-rays that have passed through the subject M among X-rays irradiated by the X-ray tube 3, and sends detection data at this time to the image generation unit 11.

　画像生成部１１は、ＦＰＤ４から送出された検出データを画像化して、Ｘ線の強さがマッピングされた透視画像Ｐ０を生成する。ＦＰＤ４は、Ｘ線管３がＸ線を照射する度に検出データを画像生成部１１に送出するので、画像生成部１１は、複数枚の透視画像Ｐ０を生成することになる。Ｘ線管３およびＦＰＤ４が回転移動されながら複数枚の透視画像Ｐ０が取得されるのであるから、透視画像Ｐ０の各々には、被検体Ｍの透視像が透視する方向を変えながら写り込んでいることになる。Ｘ線管３およびＦＰＤ４が撮影開始から一回転したところで、Ｘ線管３はＸ線の照射を終了する。 The image generation unit 11 converts the detection data sent from the FPD 4 into an image, and generates a fluoroscopic image P0 in which the X-ray intensity is mapped. Since the FPD 4 sends detection data to the image generation unit 11 every time the X-ray tube 3 emits X-rays, the image generation unit 11 generates a plurality of fluoroscopic images P0. Since a plurality of fluoroscopic images P0 are acquired while the X-ray tube 3 and the FPD 4 are rotated, each of the fluoroscopic images P0 is reflected while changing the direction in which the fluoroscopic image of the subject M is seen through. It will be. When the X-ray tube 3 and the FPD 4 make one rotation from the start of imaging, the X-ray tube 3 ends the X-ray irradiation.

　撮影開始後の天板２の移動について説明する。Ｘ線断層撮影装置２０は、一度の撮影で被検体Ｍの一部分しか撮影できない。Ｘ線断層撮影装置２０の撮影視野におけるＺ方向の幅が被検体ＭのＺ方向の幅よりも小さいからである。そこで、実施例１の構成によれば、上述のＸ線管３・ＦＰＤ４が一回転して終了する撮影を複数回行うことで、被検体Ｍの全体像について断層画像を取得するようにしている。すなわち、図１１の左側が示すように、まず被検体Ｍの尾部の撮影を行った後、天板２が摺動されることにより被検体Ｍとガントリ１０の相対位置を変更し、今度は図１１の中央が示すように、被検体Ｍの腹部の撮影を行う。その後、再び天板２を摺動して今度は図１１の右側が示すように被検体Ｍの頭部の撮影を行う。こうして、被検体全身について透視画像Ｐ０が取得される。 The movement of the top 2 after the start of shooting will be described. The X-ray tomography apparatus 20 can image only a part of the subject M by one imaging. This is because the width in the Z direction in the field of view of the X-ray tomography apparatus 20 is smaller than the width of the subject M in the Z direction. Therefore, according to the configuration of the first embodiment, a tomographic image of the entire image of the subject M is acquired by performing imaging a plurality of times when the above-described X-ray tube 3 and FPD 4 complete one rotation. . That is, as shown on the left side of FIG. 11, first, the tail of the subject M is imaged, and then the relative position between the subject M and the gantry 10 is changed by sliding the top board 2. 11, the abdomen of the subject M is imaged. Thereafter, the top plate 2 is slid again, and the head of the subject M is imaged as shown on the right side of FIG. In this way, the fluoroscopic image P0 is acquired for the entire subject.

　＜空間データ生成ステップＳ３＞
　透視画像Ｐ０は、空間データ生成部１２に送出される。空間データ生成部１２では、方向を変えながら撮影されることにより被検体Ｍの立体的な構造に関する情報を有している一連の透視画像Ｐ０を再構成してＸ線の通過の易さを表した輝度が３次元的に配列された３次元空間データＤ１を生成する。 <Spatial data generation step S3>
The fluoroscopic image P0 is sent to the spatial data generation unit 12. The spatial data generation unit 12 reconstructs a series of fluoroscopic images P0 having information related to the three-dimensional structure of the subject M by photographing while changing the direction, and expresses the ease of passage of X-rays. The three-dimensional space data D1 in which the luminances are arranged three-dimensionally is generated.

　＜マーカ特定ステップＳ４＞
　３次元空間データＤ１は、マーカ特定部１７および分割部１３に送出される。マーカ特定部１７は、３次元空間データＤ１にマーカ特定処理を施すことにより、３次元空間データＤ１における各トレイ５ｃが有する交点ｐの位置を特定する。この位置情報Ｄｍは、分割部１３に送出される。位置情報Ｄｍには、交点ｐの位置情報の他、トレイ５ｃを区別するための識別番号が付与されている。マーカ特定部１７は、異なる交点ｐＡ～ｐＥを検索する過程において、異なる交点を検索する度にこの位置情報に異なる識別番号を位置情報Ｄｍに付す。これにより、位置情報Ｄｍが示す交点ｐがどのトレイ５ｃについてのものなのかが判然とする。 <Marker specifying step S4>
The three-dimensional space data D1 is sent to the marker specifying unit 17 and the dividing unit 13. The marker specifying unit 17 specifies the position of the intersection point p of each tray 5c in the three-dimensional space data D1 by performing marker specifying processing on the three-dimensional space data D1. The position information Dm is sent to the dividing unit 13. In addition to the position information of the intersection point p, an identification number for distinguishing the tray 5c is given to the position information Dm. In the process of searching for different intersections pA to pE, the marker specifying unit 17 attaches a different identification number to the position information Dm every time a different intersection is searched. This makes it clear which tray 5c the intersection point p indicated by the position information Dm is about.

　＜分割データ生成ステップＳ５＞
　分割部１３は、位置情報Ｄｍを基に、３次元空間データＤ１を分割して単一の被検体Ｍを包含した分割データＤ２を３次元空間データＤ１に包含されている交点ｐ毎に生成する。この分割データＤ２には、マーカ特定部１７が位置情報Ｄｍに付した識別番号が受継されている。 <Divided data generation step S5>
The dividing unit 13 divides the three-dimensional space data D1 based on the position information Dm, and generates divided data D2 including a single subject M for each intersection p included in the three-dimensional space data D1. . In this divided data D2, the identification number assigned to the position information Dm by the marker specifying unit 17 is inherited.

　＜２次元画像生成ステップＳ６＞
　分割データＤ２は解析画像生成部１４に送出される。解析画像生成部１４は、３次元ボクセルデータとなっている分割データＤ２に画像処理を施し、断層画像などの２次元画像Ｐ１を生成する。解析画像生成部１４は、分割データＤ２に付された識別番号を２次元画像Ｐ１に重ねて、表示部２５に送出する。表示部２５に２次元画像Ｐ１が表示されてＸ線断層撮影装置の動作は終了となる。 <Two-dimensional image generation step S6>
The divided data D2 is sent to the analysis image generation unit 14. The analysis image generation unit 14 performs image processing on the divided data D2 that is three-dimensional voxel data, and generates a two-dimensional image P1 such as a tomographic image. The analysis image generation unit 14 superimposes the identification number assigned to the divided data D2 on the two-dimensional image P1, and sends it to the display unit 25. The two-dimensional image P1 is displayed on the display unit 25, and the operation of the X-ray tomography apparatus ends.

　以上のように、実施例１の構成によれば、作業効率が向上されたＸ線断層撮影層装置１が提供できる。すなわち、実施例１の構成によれば被検体Ｍの位置を示すマーカ５ｍが設けられたホルダ５を備える。３次元空間データＤ１が生成された後、これに包含されている各マーカ５ｍの位置を特定が特定され、各マーカ５ｍの位置の基づいて３次元空間データＤ１が分割される。これにより、３次元空間データＤ１は確実に単一の被検体Ｍを包含した分割データＤ２に分割される。これにより、実験者が煩雑なトリミング作業をすることなく被検体Ｍの各々についてデータ解析ができるので、Ｘ線断層撮影層装置１の作業効率は高いものとなる。 As described above, according to the configuration of the first embodiment, the X-ray tomography layer apparatus 1 with improved work efficiency can be provided. That is, according to the structure of Example 1, the holder 5 provided with the marker 5m which shows the position of the subject M is provided. After the three-dimensional space data D1 is generated, the specification of the position of each marker 5m included therein is specified, and the three-dimensional space data D1 is divided based on the position of each marker 5m. As a result, the three-dimensional space data D1 is reliably divided into divided data D2 including a single subject M. As a result, since the data analysis can be performed for each of the subjects M without an experimenter performing complicated trimming operations, the work efficiency of the X-ray tomography layer apparatus 1 is high.

　また、ホルダ５に１つの被検体Ｍについて、それぞれ直交する３方向における被検体Ｍの位置を示す３つのマーカ５ｍが設けられていれば、３次元空間データＤ１における被検体Ｍの３次元的な位置が確実に１つに定まることになる。 Further, if the holder 5 is provided with three markers 5m indicating the position of the subject M in three orthogonal directions for one subject M, the three-dimensional of the subject M in the three-dimensional space data D1 is provided. The position is surely set to one.

　また、上述のように３次元空間データＤ１のマーカ５ｍの位置を特定する際に、３次元空間データＤ１の断層画像を生成して、各断層画像のうちからマーカ５ｍが写り込んだ画像を検索するようにすれば、マーカ特定部１７は、３次元空間データＤ１におけるマーカ５ｍの位置を確実に特定することができる。 Further, as described above, when specifying the position of the marker 5m of the three-dimensional space data D1, a tomographic image of the three-dimensional space data D1 is generated, and an image in which the marker 5m is reflected is searched from each tomographic image. By doing so, the marker specifying unit 17 can reliably specify the position of the marker 5m in the three-dimensional space data D1.

　上述のように、マーカ５ｍが被検体Ｍを個別に載置するトレイ５ｃに設けられていれば、３次元空間データＤ１におけるマーカ５ｍの位置は、確実に３次元空間データＤ１における被検体Ｍの各々の位置を示すことになる。 As described above, if the marker 5m is provided on the tray 5c on which the subject M is individually placed, the position of the marker 5m in the three-dimensional space data D1 is surely the position of the subject M in the three-dimensional space data D1. Each position will be shown.

　また、マーカ５ｍがトレイ５ｃをホルダ５の開口５ａから引き出すときの引手５ｄとなっていれば、実験者は容易に被検体Ｍをホルダ５に導入することができるので、一段と作業効率が向上したＸ線断層撮影層装置１が提供できる。 Further, if the marker 5m is a handle 5d for pulling out the tray 5c from the opening 5a of the holder 5, the experimenter can easily introduce the subject M into the holder 5, and the working efficiency is further improved. The X-ray tomography layer apparatus 1 can be provided.

　上述のように、マーカ５ｍが３次元空間データＤ１において各被検体Ｍを識別する記号となっていれば、実験者にとってもマーカ特定部１７にとっても各被検体Ｍを識別することができることになり、実験者が被検体Ｍを取り違えて実験結果を導出することが防止できる。 As described above, if the marker 5m is a symbol for identifying each subject M in the three-dimensional space data D1, each subject M can be identified for both the experimenter and the marker specifying unit 17. It is possible to prevent the experimenter from confusing the subject M and deriving the experimental result.

　続いて実施例２に係る放射線断層撮影装置２０について説明する。実施例２に係る放射線断層撮影装置２０は、ＰＥＴ(Positron Emission Tomography)装置に組み込んだものとなっている。γ線は本発明における放射線に相当する。また、実施例１に係る放射線断層撮影装置は小動物撮影用となっている。 Subsequently, the radiation tomography apparatus 20 according to the second embodiment will be described. The radiation tomography apparatus 20 according to the second embodiment is incorporated in a PET (Positron Emission Tomography) apparatus. Gamma rays correspond to radiation in the present invention. Further, the radiation tomography apparatus according to the first embodiment is for small animal photography.

　放射線断層撮影装置２０は、図１２に示す様に、ガントリ１０ａを有している。このガントリ１０ａは、Ｚ方向に伸びた貫通孔を有しており、天板２が挿通されている。 The radiation tomography apparatus 20 has a gantry 10a as shown in FIG. The gantry 10a has a through hole extending in the Z direction, and the top plate 2 is inserted therethrough.

　ガントリ１０ａの内部にはガントリ１０ａの形状にならって開口を有し、リング状となっている検出器リング３２が設けられている。この検出器リング３２は、γ線を検出可能な検出器がリング状に配列されて構成されている。検出器リング３２は、本発明の検出手段に相当する。 Inside the gantry 10a, there is provided a detector ring 32 having an opening and a ring shape following the shape of the gantry 10a. The detector ring 32 is configured by arranging detectors capable of detecting γ rays in a ring shape. The detector ring 32 corresponds to the detection means of the present invention.

　同時計数部３３は、検出器リング３２から出力された検出データに同時計数処理を施す目的で設けられている。この同時計数部３３により検出器リング３２の異なる部分に同時に入射した消滅γ線対の検出頻度と検出位置とが特定される。同時計数部３３は、同時計数の結果を空間データ生成部３４に出力する。空間データ生成部３４は、同時計数部３３が特定した消滅γ線対の検出頻度と検出位置とを基に、消滅γ線対の発生位置を算出し、消滅γ線対の発生強度が３次元的にマッピングされた３次元空間データＤ１を生成する。放射線断層撮影装置２０は、実施例１と同様に分割部１３，解析画像生成部１４，およびマーカ特定部１７を有している。 The coincidence unit 33 is provided for the purpose of performing coincidence processing on the detection data output from the detector ring 32. The coincidence counting unit 33 specifies the detection frequency and the detection position of the annihilation γ-ray pairs incident simultaneously on different portions of the detector ring 32. The coincidence counting unit 33 outputs the result of coincidence counting to the spatial data generation unit 34. The spatial data generation unit 34 calculates the generation position of the annihilation γ-ray pair based on the detection frequency and detection position of the annihilation γ-ray pair specified by the coincidence counting unit 33, and the generation intensity of the annihilation γ-ray pair is three-dimensional. The three-dimensional spatial data D1 mapped automatically is generated. The radiation tomography apparatus 20 includes a dividing unit 13, an analysis image generating unit 14, and a marker specifying unit 17 as in the first embodiment.

　放射線断層撮影装置２０を用いて２次元画像Ｐ１を生成するには、まず、被検体Ｍに陽電子放出型の放射性薬剤が注射される。放射性薬剤は、被検体Ｍの病巣などの特定の部分に集中する性質を有している。放射性薬剤は陽電子を放出し、この陽電子は１８０度反対方向に飛び去る消滅γ線対を発生させる。したがって、被検体Ｍからは、消滅γ線対が放射されることになる。放射性薬剤の分布は被検体内で異なっているのであるから、消滅γ線対の発生の頻度は被検体Ｍの部分によって異なっていることになる。 In order to generate the two-dimensional image P1 using the radiation tomography apparatus 20, first, a positron emitting radiopharmaceutical is injected into the subject M. The radiopharmaceutical has a property of concentrating on a specific part such as a lesion of the subject M. Radiopharmaceuticals emit positrons, which generate annihilation gamma ray pairs that fly 180 degrees in the opposite direction. Therefore, an annihilation gamma ray pair is emitted from the subject M. Since the distribution of the radiopharmaceutical is different within the subject, the frequency of occurrence of annihilation γ-ray pairs differs depending on the portion of the subject M.

　放射性薬剤の注射から十分に時間が経過した後、被検体Ｍは麻酔され、実施例１と同様にトレイ５ｃに導入され、ホルダ５に収納される。このときトレイ５ｃには実施例１と同様に被検体Ｍの位置を明確にする目的で設けられた板状のマーカ５ｍが設けられている。このマーカ５ｍは、ＰＥＴの３次元空間データとして構成するため、対消滅放射線を発生する密封線源部材または放射性薬剤を注入できる容器として構成される。そして、複数の被検体Ｍを収納した状態となったホルダ５は、天板２に載置される。実験者が操作卓２６を通じて放射線断層撮影装置２０にＰＥＴ画像撮影開始の指示を行うと、天板２が摺動し、被検体Ｍがガントリ１０ａの貫通孔の内部に導入される（図１２参照）。この時点から検出器リング３２は、消滅γ線対の検出を開始し、空間データ生成部３４が消滅γ線対の発生強度が３次元的にマッピングされた３次元空間データＤ１を生成する。なお、撮影の際に、放射線断層撮影装置２０のＺ方向における視野範囲が被検体Ｍの全身をカバーしきれないときは、天板２をＺ方向に摺動させながら３次元空間データＤ１の生成をするようにしてもよい。 After a sufficient amount of time has elapsed since the injection of the radiopharmaceutical, the subject M is anesthetized, introduced into the tray 5c and stored in the holder 5 as in the first embodiment. At this time, the tray 5c is provided with a plate-like marker 5m provided for the purpose of clarifying the position of the subject M as in the first embodiment. Since the marker 5m is configured as three-dimensional spatial data of PET, it is configured as a sealed radiation source member that generates pair annihilation radiation or a container into which a radiopharmaceutical can be injected. Then, the holder 5 in a state in which a plurality of subjects M are stored is placed on the top 2. When the experimenter instructs the radiation tomography apparatus 20 to start imaging the PET image through the console 26, the top 2 slides and the subject M is introduced into the through hole of the gantry 10a (see FIG. 12). ). From this point, the detector ring 32 starts detecting the annihilation γ-ray pairs, and the spatial data generation unit 34 generates the three-dimensional spatial data D1 in which the generation intensity of the annihilation γ-ray pairs is three-dimensionally mapped. When imaging, if the visual field range in the Z direction of the radiation tomography apparatus 20 cannot cover the whole body of the subject M, the three-dimensional space data D1 is generated while sliding the top 2 in the Z direction. You may make it do.

　この３次元空間データＤ１は、被検体Ｍの放射性薬剤分布とマーカ５ｍを包含している。この３次元空間データＤ１は、マーカ特定部１７および分割部１３に送出され、分割データＤ２に分割される。そして、分割データＤ２は、解析画像生成部１４に送出され断層画像やＳＵＶ画像などの２次元画像Ｐ１に変換される。従って、分割部１３，解析画像生成部１４，マーカ特定部１７では、画像処理を被検体Ｍごとに独立して施すことにより２次元画像Ｐ１を生成するのである。この様にして生成された２次元画像Ｐ１が各被検体Ｍを区別する識別番号とともに表示部２５に表示されて撮影は終了となる。 The three-dimensional space data D1 includes the radiopharmaceutical distribution of the subject M and the marker 5m. The three-dimensional space data D1 is sent to the marker specifying unit 17 and the dividing unit 13 and divided into divided data D2. Then, the divided data D2 is sent to the analysis image generation unit 14 and converted into a two-dimensional image P1 such as a tomographic image or an SUV image. Therefore, the dividing unit 13, the analysis image generating unit 14, and the marker specifying unit 17 generate the two-dimensional image P1 by performing image processing independently for each subject M. The two-dimensional image P1 generated in this way is displayed on the display unit 25 together with an identification number for distinguishing each subject M, and the imaging is completed.

　ＳＵＶ(Standardized Uptake Value)画像は、ポジトロン放出断層撮影装置で３次元空間データＤ１を取得する場合に、放射性薬剤の分布を正規化して得られたＳＵＶ値を２次元的に配列した断層画像である。解析画像生成部１４は、被検体Ｍに投与した放射性薬剤の量と、被検体Ｍの体重とによって分割データＤ２の全体を正規化して、ＳＵＶ値を取得する。 An SUV (Standardized Uptake Value) image is a tomographic image in which SUV values obtained by normalizing the distribution of radiopharmaceuticals when two-dimensional spatial data D1 is acquired by a positron emission tomography apparatus are two-dimensionally arranged. . The analysis image generation unit 14 acquires the SUV value by normalizing the entire divided data D2 based on the amount of the radiopharmaceutical administered to the subject M and the weight of the subject M.

　上述の構成は、本発明を放射線断層撮影装置２０に適用したものとなっている。すなわち、分割部１３，解析画像生成部１４，マーカ特定部１７を被検体Ｍから放射される放射線を測定することにより断層像を取得するタイプの放射線断層撮影装置２０に適用すれば、放射線断層撮影装置２０で一度に複数の被検体Ｍの撮影をしたとしても、実験の作業効率が低下しない放射線断層撮影装置２０が提供できる。 The configuration described above is an application of the present invention to the radiation tomography apparatus 20. That is, if the dividing unit 13, the analysis image generating unit 14, and the marker specifying unit 17 are applied to a radiation tomography apparatus 20 that acquires a tomographic image by measuring radiation emitted from the subject M, radiation tomography Even if a plurality of subjects M are imaged at once with the apparatus 20, the radiation tomography apparatus 20 can be provided in which the work efficiency of the experiment does not decrease.

　本発明は、上述の構成に限られず、下記のように変形実施をすることができる。 The present invention is not limited to the above-described configuration, and can be modified as follows.

　（１）実施例１におけるトレイ５ｃの引手５ｄは、図３に示すようなＬ状となっていたが、これに代えて引手５ｄを図１３の左側に示すようなＴ状としてもよい。また、図３に示すように、実施例１においてはトレイ５ｃの引手５ｄが設けられている面にマーカ５ｍの１つが設けられていたが、これに代えてマーカ５ｍを図１３の右側に示すようにトレイ５ｃの端面のうち、引手５ｄが設けられていない面にマーカ５ｍを設けるようにしてもよい。このようにマーカ５ｍの配置は、適宜変更することができる。トレイ５ｃにおけるマーカ５ｍの位置を変更すれば、交点ｐの位置もこれに合わせて変更されることになる。 (1) Although the handle 5d of the tray 5c in the first embodiment has an L shape as shown in FIG. 3, the handle 5d may have a T shape as shown on the left side of FIG. 13 instead. Further, as shown in FIG. 3, in the first embodiment, one of the markers 5m is provided on the surface of the tray 5c on which the handle 5d is provided. Instead, the marker 5m is shown on the right side of FIG. As described above, the marker 5m may be provided on the end surface of the tray 5c where the handle 5d is not provided. Thus, the arrangement of the markers 5m can be changed as appropriate. If the position of the marker 5m on the tray 5c is changed, the position of the intersection point p is also changed accordingly.

　（２）上述の構成によれば、分割データＤ２は、３次元空間データＤ１を円柱形に切り出して生成されたものであるが、本発明はこれに限らない。分割部１３が３次元空間データＤ１を切り出すときの形状は、適宜変更可能である。また、操作卓２６を通じて切り出しの形状を実験者に選択させるようにしてもよい。 (2) According to the above configuration, the divided data D2 is generated by cutting the three-dimensional space data D1 into a cylindrical shape, but the present invention is not limited to this. The shape when the dividing unit 13 cuts out the three-dimensional space data D1 can be changed as appropriate. In addition, the experimenter may be made to select the cut shape through the console 26.

　（３）また、分割部１３は、３次元空間データＤ１を直列に並ぶ被検体Ｍのデータの各々を分断するようにして分割データＤ２を切り出すようにしてもよい。すなわち、分割部１３は、交点ｐを参照しながら図１４に示すように３体直列して並ぶ被検体Ｍのデータを被検体Ｍごとに切り出すように図１４に示す破線の位置で３次元空間データＤ１を分割して分割データＤ２を生成するようにしてもよい。 (3) Further, the dividing unit 13 may cut out the divided data D2 by dividing each of the data of the subject M in which the three-dimensional space data D1 is arranged in series. That is, the dividing unit 13 refers to the three-dimensional space at the position of the broken line shown in FIG. 14 so as to cut out the data of the subject M arranged in series as shown in FIG. Data D1 may be divided to generate divided data D2.

　（４）実施例１に係るデータ処理装置は、Ｘ線撮影装置やＰＥＴ装置に限られず、ＭＲＩやＳＰＥＣＴなどのその他の断層撮影装置にも搭載できる。また複数の断層装置を組み合わせた装置たとえばＰＥＴ－ＣＴ装置にも搭載できる。 (4) The data processing apparatus according to the first embodiment is not limited to the X-ray imaging apparatus and the PET apparatus, and can be mounted on other tomography apparatuses such as MRI and SPECT. It can also be mounted on a device combining a plurality of tomographic devices, for example, a PET-CT device.

　本発明は、研究用の放射線断層撮影装置に適している。 The present invention is suitable for a radiation tomography apparatus for research.

Ｄ１   ３次元空間データ
Ｄ２   分割データ
２     天板
３     Ｘ線管（放射線源）
４     ＦＰＤ（検出手段）
５     ホルダ
５ａ   開口（凹部）
５ｃ   トレイ
５ｄ   引手
５ｍ   マーカ
７     回転機構（回転手段）
１２   空間データ生成部（データ生成手段）
１３   分割部（分割手段）
１５   天板移動機構（天板移動手段）
１７   マーカ特定部（マーカ特定手段）
３２   検出器リング（検出手段） D1 3D space data D2 Division data 2 Top plate 3 X-ray tube (radiation source)
4 FPD (detection means)
5 Holder 5a Opening (concave)
5c tray 5d handle 5m marker 7 rotating mechanism (rotating means)
12 Spatial data generator (data generator)
13 Dividing part (dividing means)
15 Top plate moving mechanism (top plate moving means)
17 Marker specifying part (marker specifying means)
32 Detector ring (detection means)

Claims (9)

　放射線を検出する検出手段と、
　被検体の位置を示すマーカが設けられた複数被検体保持用のホルダと、
　前記検出手段が出力する検出信号を基に、複数の前記マーカおよび複数の被検体を包含した３次元空間データを生成するデータ生成手段と、
　前記３次元空間データにおける各マーカの位置を特定するマーカ特定手段と、
　特定された前記マーカの位置に基づいて前記３次元空間データを分割して単一の被検体を包含した分割データを生成する分割手段を備ることを特徴とする放射線断層撮影装置。 Detection means for detecting radiation;
A holder for holding a plurality of subjects provided with markers indicating the positions of the subjects;
Data generating means for generating three-dimensional spatial data including a plurality of the markers and a plurality of subjects based on the detection signal output by the detecting means;
Marker specifying means for specifying the position of each marker in the three-dimensional space data;
A radiation tomography apparatus comprising: a dividing unit that divides the three-dimensional spatial data based on the specified position of the marker to generate divided data including a single subject. 　請求項１に記載の放射線断層撮影装置において、
　前記ホルダには、１つの被検体について、それぞれ直交する３方向における被検体の位置を示す３つの前記マーカ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。 The radiation tomography apparatus according to claim 1,
3. The radiation tomography apparatus according to claim 1, wherein the holder is provided with three markers indicating the position of the subject in three directions orthogonal to each other. 　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、
　前記マーカ特定手段は前記３次元空間データの断層画像を生成して、各断層画像のうちから前記マーカが写り込んだ画像を検索することにより前記マーカの位置を特定することを特徴とする放射線断層撮影装置。 The radiation tomography apparatus according to claim 1 or 2,
The marker specifying means generates a tomographic image of the three-dimensional spatial data, and specifies a position of the marker by searching an image in which the marker is reflected from each tomographic image. Shooting device. 　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、
　前記ホルダには被検体を個別に載置するトレイと、前記トレイを導入する凹部とが設けられており、前記マーカは前記トレイに備えられていることを特徴とする放射線断層撮影装置。 The radiation tomography apparatus according to any one of claims 1 to 3,
The radiation tomography apparatus according to claim 1, wherein the holder is provided with a tray for individually placing an object and a recess for introducing the tray, and the marker is provided on the tray. 　請求項４に記載の放射線断層撮影装置において、
　前記マーカは、前記トレイを前記凹部から引き出すときの引手に設けられていることを特徴とする放射線断層撮影装置。 The radiation tomography apparatus according to claim 4,
The radiation tomography apparatus according to claim 1, wherein the marker is provided on a handle for pulling out the tray from the recess. 　請求項１ないし請求項５のいずれかに記載の放射線断層撮影装置において、
　前記マーカは、前記３次元空間データにおいて各被検体を識別する記号となっていることを特徴とする放射線断層撮影装置。 The radiation tomography apparatus according to any one of claims 1 to 5,
The radiation tomography apparatus according to claim 1, wherein the marker is a symbol for identifying each subject in the three-dimensional space data. 　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、
　前記ホルダを載置する天板と、
　前記天板を放射線断層装置の開口部の直交方向に移動させる天板移動手段とを備えることを特徴とする放射線断層撮影装置。 The radiation tomography apparatus according to any one of claims 1 to 6,
A top plate on which the holder is placed;
A radiation tomography apparatus comprising: a top plate moving means for moving the top plate in a direction orthogonal to the opening of the radiation tomography apparatus. 　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、
　放射線を照射する放射線源と、
　前記放射線源および前記検出手段を回転させる回転手段とを備え、
　前記検出手段は、前記放射線源から発生して被検体を透過してきた放射線を検出することを特徴とする放射線断層撮影装置。 The radiation tomography apparatus according to any one of claims 1 to 7,
A radiation source that emits radiation;
A rotation means for rotating the radiation source and the detection means,
The radiation tomography apparatus according to claim 1, wherein the detection means detects radiation generated from the radiation source and transmitted through the subject. 　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、
　前記検出手段は被検体から発せられる放射線を検出する検出器リングであり、
　ポジトロン放出断層撮影装置として構成されていることを特徴とする放射線断層撮影装置。 The radiation tomography apparatus according to any one of claims 1 to 7,
The detection means is a detector ring for detecting radiation emitted from the subject;
A radiation tomography apparatus configured as a positron emission tomography apparatus.
PCT/JP2011/006268 2011-01-19 2011-11-09 Radiation tomography device Ceased WO2012098604A1 (en)

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JPH067161B2 (en) * 1989-02-07 1994-01-26 浜松ホトニクス株式会社 Small animal immobilization device for positron CT device
JP2003302500A (en) * 2002-04-05 2003-10-24 Chubu Medical:Kk Sample container for soft x-ray radiography
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Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS60214244A (en) * 1984-04-11 1985-10-26 Hitachi Medical Corp Sample supporter for x-ray ct
JPH067161B2 (en) * 1989-02-07 1994-01-26 浜松ホトニクス株式会社 Small animal immobilization device for positron CT device
JP2003302500A (en) * 2002-04-05 2003-10-24 Chubu Medical:Kk Sample container for soft x-ray radiography
JP2005140561A (en) * 2003-11-05 2005-06-02 Aloka System Engineering Co Ltd X-ray ct apparatus and vessel therefor
JP2006084467A (en) * 2004-09-14 2006-03-30 Hitachi Ltd Method and apparatus for performing computed tomography
JP2009281764A (en) * 2008-05-20 2009-12-03 Aloka Co Ltd Sample holder for x-ray photographing

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