WO2014136734A1 - 放射線検出器とそれを備えたx線ct装置 - Google Patents
放射線検出器とそれを備えたx線ct装置 Download PDFInfo
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- WO2014136734A1 WO2014136734A1 PCT/JP2014/055347 JP2014055347W WO2014136734A1 WO 2014136734 A1 WO2014136734 A1 WO 2014136734A1 JP 2014055347 W JP2014055347 W JP 2014055347W WO 2014136734 A1 WO2014136734 A1 WO 2014136734A1
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- radiation
- ray
- collimator plate
- plate support
- radiation detector
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Classifications
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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
- A61B6/06—Diaphragms
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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]
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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
- A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
- A61B6/4233—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
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- A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4266—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a plurality of detector units
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- A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4291—Arrangements for detecting radiation specially adapted for radiation diagnosis the detector being combined with a grid or grating
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- A—HUMAN NECESSITIES
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- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/44—Constructional features of apparatus for radiation diagnosis
- A61B6/4429—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units
- A61B6/4435—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit and the detector unit being coupled by a rigid structure
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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
- A61B6/46—Arrangements for interfacing with the operator or the patient
- A61B6/461—Displaying means of special interest
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
- G01T1/2914—Measurement of spatial distribution of radiation
- G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)
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- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
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- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5205—Devices using data or image processing specially adapted for radiation diagnosis involving processing of raw data to produce diagnostic data
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- G—PHYSICS
- G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
- G21K—TECHNIQUES FOR HANDLING PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
- G21K1/00—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating
- G21K1/02—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators
- G21K1/025—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using multiple collimators, e.g. Bucky screens; other devices for eliminating undesired or dispersed radiation
Definitions
- the present invention relates to a radiation detector that detects X-rays, ⁇ -rays, and the like, and more particularly to a support unit that supports a collimator plate provided on the radiation source side of the radiation detector to remove scattered radiation. Moreover, it is related with the X-ray CT apparatus provided with such a radiation detector.
- An X-ray CT (Computed Tomography) device which is one of medical diagnostic imaging devices, is an X-ray tube device that irradiates a subject with X-rays, and an X-ray distribution that detects the distribution of the X-ray dose transmitted through the subject as projection data.
- the tomographic image of the subject is reconstructed using projection data from a plurality of angles obtained by rotating the line detector around the subject, and the reconstructed tomographic image is displayed.
- the image displayed by the X-ray CT apparatus describes the shape of an organ in the subject and is used for diagnostic imaging.
- indirect conversion type detectors equipped with a detection element that combines a phosphor element such as a ceramic scintillator and a light detection element such as a photodiode. Is mainly used.
- a direct conversion detector provided with a semiconductor element as a detection element is being used.
- a structure is adopted in which a plurality of detection element arrays, in which about 1000 detection elements are arranged on an arc centered on the X-ray focal point, are arranged in the rotation axis direction. ing.
- the collimator plate is made of a thin metal plate that can sufficiently shield X-rays, and is arranged radially toward the X-ray focal point.
- Patent Document 1 discloses an X-ray detector capable of reducing deformation of a collimator plate and an X-ray CT apparatus using the same.
- Patent Document 1 a groove provided on a resin support plate arranged in parallel with the X-ray incident surface of the X-ray detector, and provided at one end of the collimator plate in the groove provided along the rotation axis direction. Is inserted and joined.
- the collimator plate and the groove become longer in the direction of the rotation axis, so that it becomes difficult to fit the collimator plate into the groove.
- an object of the present invention is to provide a radiation detector and an X-ray CT apparatus in which the collimator plate is easily arranged.
- the present invention provides a radiation detection element array in which a plurality of radiation detection elements for detecting radiation generated from a radiation source are arranged in a first direction and a second direction orthogonal to the first direction.
- a collimator plate disposed along the first direction on the radiation source side of the radiation detection element array, for removing scattered radiation, and a groove for supporting the collimator plate, and between the radiation detection elements And a collimator plate support portion disposed along the second direction.
- FIG. 3 is a diagram showing a main part of the first embodiment, and an enlarged view in B of FIG.
- FIG. 5 is a diagram showing a main part of the first embodiment, and is a cross-sectional view taken along the line CC in FIG.
- the figure which shows an example of the arrangement position of the collimator board support part 323 The figure which shows the principal part of 2nd embodiment. It is a figure which shows the structure of 3rd embodiment, and is AA sectional drawing of FIG.
- FIG. 9 is a view showing a main part of the third embodiment, and is a cross-sectional view taken along line EE of FIG.
- the radiation detector includes a radiation detection element array in which a plurality of radiation detection elements for detecting radiation generated from a radiation source are arranged in a first direction and a second direction orthogonal to the first direction.
- a collimator plate disposed along the first direction on the radiation source side of the radiation detection element array, for removing scattered radiation, and a groove for supporting the collimator plate, and between the radiation detection elements And a collimator plate support portion arranged along the second direction.
- the collimator plate support is an even number, and is provided at a symmetrical position with respect to the center position in the first direction.
- the width between the radiation detection elements on which the collimator plate support portions are disposed is wider than the width between the radiation detection elements on which the collimator plate support portions are not disposed.
- the radiation detection element includes a scintillator element that emits visible light when radiation is incident, and a light detection element that outputs an electrical signal when the visible light is incident, and the visible light is interposed between the scintillator elements.
- the collimator plate support portion is made of the same material as that of the reflective material.
- the X-ray CT apparatus includes the radiation source, the radiation detector disposed to face the radiation source and detecting radiation transmitted through the subject, the radiation source, and the radiation detection.
- a rotating disk that is mounted around the subject and rotates around the subject, an image reconstruction device that reconstructs a tomographic image of the subject based on the amount of transmitted radiation from a plurality of angles detected by the radiation detector, And an image display device for displaying a tomographic image reconstructed by the image reconstruction device.
- the position at which the collimator plate support portion of the radiation detector is disposed is a joint position of the maximum slice thickness at the time of image reconstruction.
- FIG. 1 is a block diagram showing the overall configuration of the X-ray CT apparatus 1.
- the X-ray CT apparatus 1 includes a scan gantry unit 100 and an operation unit 120.
- the scan gantry unit 100 includes an X-ray tube device 101, a rotating disk 102, a collimator 103, an X-ray detector 106, a data collection device 107, a bed device 105, a gantry control device 108, and a bed control device 109.
- the X-ray tube apparatus 101 is an apparatus that irradiates the subject placed on the bed apparatus 105 with X-rays.
- the collimator 103 is a device that limits the radiation range of X-rays emitted from the X-ray tube device 101.
- the rotating disk 102 includes an opening 104 into which the subject placed on the bed apparatus 105 enters, and is equipped with an X-ray tube device 101 and an X-ray detector 106, and rotates around the subject. .
- the X-ray detector 106 is a device that measures the spatial distribution of transmitted X-rays by detecting X-rays that are disposed opposite to the X-ray tube device 101 and transmitted through the subject. These are two-dimensionally arranged in the circumferential direction in the rotation plane (XY plane) of the rotary disk 102 and the rotation axis direction (direction parallel to the Z axis). Details of the X-ray detector 106 will be described later.
- the data collection device 107 is a device that collects the X-ray dose detected by the X-ray detector 106 as digital data.
- the gantry control device 108 is a device that controls the rotation of the rotary disk 102.
- the bed control device 109 is a device that controls the vertical and horizontal movements of the bed device 105.
- the high voltage generator 111 is a device that generates a high voltage applied to the X-ray tube apparatus 101.
- the X-ray control device 110 is a device that controls the output of the high voltage generator 111.
- the console 120 includes an input device 121, an image calculation device 122, a display device 125, a storage device 123, and a system control device 124.
- the input device 121 is a device for inputting a subject's name, examination date and time, imaging conditions, and the like, specifically a keyboard or a pointing device.
- the image computation device 122 is a device that performs CT processing on the measurement data sent from the data collection device 107 and performs CT image reconstruction.
- the display device 125 is a device that displays the CT image created by the image calculation device 122, and is specifically a CRT (Cathode-Ray Tube), a liquid crystal display, or the like.
- the storage device 123 is a device that stores data collected by the data collection device 107 and image data of a CT image created by the image calculation device 122, and is specifically an HDD (Hard Disk Disk Drive) or the like.
- the system control device 124 is a device that controls these devices, the gantry control device 108, the bed control device 109, and the X-ray control device 110.
- the X-ray controller 110 controls the high-voltage generator 111 based on the imaging conditions input from the input device 121, in particular, the tube voltage and the tube current. Power is supplied. With the supplied power, the X-ray tube apparatus 101 irradiates the subject with X-rays according to the imaging conditions.
- the X-ray detector 106 detects X-rays irradiated from the X-ray tube apparatus 101 and transmitted through the subject with a large number of X-ray detection elements, and measures the distribution of transmitted X-rays.
- the rotating disk 102 is controlled by the gantry control device 108, and rotates based on the imaging conditions input from the input device 121, particularly the rotation speed.
- the couch device 105 is controlled by the couch control device 109 and operates based on the imaging conditions input from the input device 121, particularly the helical pitch.
- X-ray irradiation from the X-ray tube apparatus 101 and transmission X-ray distribution measurement by the X-ray detector 106 are repeated along with the rotation of the rotating disk 102, whereby projection data from various angles is acquired.
- the projection data is associated with a view representing each angle, a channel (ch) number and a column number that are detection element numbers of the X-ray detector 106.
- the acquired projection data from various angles is transmitted to the image processing device 122.
- the image processing device 122 reconstructs the CT image by performing back projection processing on the transmitted projection data from various angles.
- the CT image obtained by the reconstruction is displayed on the display device 125.
- the X-ray detector 106 will be described with reference to FIG.
- FIG. 2 is a diagram showing the positional relationship between the X-ray focal point 201 and the X-ray detector 106.
- the X-ray detector 106 includes a scattered radiation removal unit 202 and a detection element module 203.
- the scattered radiation removing unit 202 removes scattered radiation generated in the subject or the like, and a thin metal plate capable of sufficiently shielding X-rays is arranged radially toward the X-ray focal point 201 as will be described later. Composed.
- X-rays including scattered radiation are detected by the X-ray detector 106, the X-ray dose attenuated by the subject is not correctly measured, and the image quality of the reconstructed tomographic image deteriorates.
- the detection element module 203 measures the spatial distribution of X-rays transmitted through the scattered radiation removal unit 202, and is configured by two-dimensionally arranging X-ray detection elements for measuring X-ray dose on a flat plate. .
- the X-ray detector 106 is provided with a plurality of detection element modules 203 so as to form a polygonal shape formed by a tangent line of an arc centering on the X-ray focal point 201 on the rotating surface (XY plane) of the rotating disk 102.
- Each detection element module 203 is arranged. By arranging the detection element modules 203 in this way, the X-ray detection elements are substantially arranged on an arc centered on the X-ray focal point 201. In FIG. 2, only seven detection element modules 203 are drawn to simplify the drawing, but the number of detection element modules 203 is not limited to seven.
- FIG. 3 is a cross-sectional view taken along the line AA in FIG.
- FIG. 4 is an enlarged view in B in FIG. 5 is a cross-sectional view taken along the line CC in FIG. 4, and the direction perpendicular to the paper surface is the direction of the rotation axis of the rotating disk 102 (direction parallel to the Z axis).
- the detection element module 203 includes a substrate 333, a light detection element array 332, and a scintillator element array 331.
- the scattered radiation removing unit 202 includes a collimator plate 321, a grooved column 322, and a collimator plate support unit 323.
- the substrate 333 holds the light detection element array 332 and the grooved pillar 322, and is made of glass epoxy or the like.
- the light detection element array 332 is installed on the upper surface of the substrate 333, and the light detection elements 332a for detecting the light emission of the scintillator element array 332 are two-dimensionally arranged.
- a photodiode is used as the light detection element 332a.
- the scintillator element array 331 is installed on the upper surface of the light detection element array 332, and a scintillator element 331a that emits visible light in an amount corresponding to an X-ray amount by receiving X-rays is partitioned by a light reflecting material 331b to be two-dimensional. Are arranged.
- Each scintillator element 331a is in one-to-one correspondence with each light detection element 332a, and one set of scintillator element 331a and light detection element 332a constitutes one X-ray detection element.
- the light reflecting material 331b reflects visible light emitted from the scintillator element 331a, and is configured by solidifying a white powder such as titanium oxide with a transparent adhesive such as an epoxy resin. As the thickness of the light reflecting material 331b is larger and the density of the white powder in the light reflecting material 331b is higher, the leakage of visible light to the adjacent X-ray detection element can be reduced.
- the number of X-ray detection elements arranged may be increased by dividing and combining at least one of the light detection element array 332, the scintillator element array 331, and the substrate 333.
- FIG. 3 shows an example in which a light detection element array 332 and a scintillator element array 331 that are divided into two in the rotation axis direction are combined on one substrate 333. The form of division is not limited to FIG.
- the collimator plate 321 is a metal thin plate that can sufficiently shield X-rays, and is made of a heavy metal plate material such as tungsten or molybdenum.
- the collimator plate 321 has a shadow formed by the collimator plate 321 when the X-ray detector 106 is viewed from the X-ray focal point 201, and the rotation axis direction (Z-axis) between the X-ray detection elements arranged almost on an arc. (Direction parallel to the direction).
- the collimator plate 321 is arranged radially toward the X-ray focal point 201 on the rotation plane (XY plane) of the rotary disk 102 and parallel to the rotation axis direction (direction parallel to the Z axis).
- the collimator plate 321 By arranging the collimator plate 321 in this way, the direct line from the X-ray focal point 201 is incident on the X-ray detection element, and the scattered radiation generated in the subject or the like is shielded by the collimator plate 321 to the X-ray detection element. Is blocked.
- the grooved column 322 supports the collimator plate 321 at the end in the rotation axis direction (direction parallel to the Z axis), has a groove (not shown) on the side surface, and is installed on the substrate 333.
- the grooves of the grooved column 322 are formed radially toward the X-ray focal point 201 on the rotation plane (XY plane).
- the collimator plate 321 is fitted into the groove of the grooved column 322, the collimator plate 321 is arranged radially toward the X-ray focal point 201 on the rotation surface (XY plane).
- the collimator plate 321 and the grooved column 322 may be fixed by an adhesive.
- the collimator plate support 323 supports the collimator plate 321 from the X-ray detector 106 side, and is installed on the scintillator element array 331.
- the collimator plate support 323 is disposed between X-ray detection elements arranged along the rotation axis direction (direction parallel to the Z axis), and has a groove 324 into which the collimator plate 321 is fitted.
- the groove 324 is formed between the X-ray detection elements arranged on a substantially circular arc on the rotation plane (XY plane).
- the shape of the groove 324 may be any shape as long as the collimator plate 321 to be fitted is not obstructed from being radially arranged toward the X-ray focal point 201.
- the collimator plate 321 fitted in the groove 324 may be fixed with an adhesive.
- the thickness of the collimator plate support portion 323 is determined by the interval between the X-ray detection elements arranged along the rotation axis so that the scintillator element 331a forming the X-ray detection device does not need to be covered with the collimator plate support portion 323. It is formed thinner.
- the material of the collimator plate support 323 is preferably a material having a low X-ray absorption rate, such as an epoxy resin.
- the material of the collimator plate support portion 323 is preferably the same material as the light reflecting material 331b.
- the collimator plate support 323 may be disposed at any position between the X-ray detection elements arranged along the rotation axis direction, but preferably the center position of the X-ray detector in the rotation axis direction is set.
- the collimator plate support 323 is preferably arranged at a symmetrical position as a reference. Since the collimator plate support 323 is arranged at a symmetrical position in the rotation axis direction, the collimator plate 321 can be supported more evenly.
- the collimator plate support 323 is arranged at the joint position of the maximum slice thickness at the time of image reconstruction in the rotation axis direction.
- image reconstruction is possible for each X-ray detection element array, and the slice thickness can be increased by adding the measurement data of the plurality of lines.
- a thick image can be obtained.
- 64 images can be obtained by one measurement, and 4 images can be obtained with 16 times the slice thickness by adding 16 rows of measurement data.
- FIG. 6 is a schematic diagram of a 64-slice multi-slice detector.
- FIG. 6 (a) shows a case where 16 rows of measurement data are added
- FIG. 6 (b) shows a case where 8 rows of measurement data are added.
- the positions of Z0 and Z1 in the figure are the joint positions of the maximum slice thickness.
- the collimator plate support 323 may be arranged so as to be removed from the position that becomes the center of the X-ray detector in the rotation axis direction.
- the position that becomes the center of the X-ray detector in the rotation axis direction that is, the position of Z0 in FIG. Position. If a foreign substance such as the collimator plate support 323 is present at such a position, the image quality of a high-quality tomographic image may be deteriorated.
- the collimator plate support 323 may be disposed by removing the position that is the center of the X-ray detector in the rotation axis direction. By disposing the collimator plate support 323 in this way, it is possible to prevent image quality deterioration at a position where a high-quality tomographic image can be easily obtained.
- the material of the collimator plate support portion 323 it is possible to reduce the decrease in the output of the X-ray detector due to the collimator plate support portion 323. Further, the image quality can be prevented from deteriorating by arranging the collimator plate support 323 at an appropriate position.
- the collimator plate support 323 formed thinner than the interval between the X-ray detection elements arranged along the rotation axis direction is mechanical to support the collimator plate 321. May be insufficient. In order to compensate for insufficient mechanical strength of the collimator plate support 323, the thickness of the collimator plate support 323 may be increased. However, if the collimator plate support part 323 is made thicker than the interval between the X-ray detection elements arranged along the rotation axis direction, the collimator plate support part 323 interferes with the X-ray detection element and is adjacent to the collimator plate support part 323. The output signal of the X-ray detection element decreases.
- the width between the X-ray detection elements where the collimator plate support 323 is arranged is wider than the width between the X-ray detection elements where the collimator plate support 323 is not arranged, and the mechanical strength is insufficient. Therefore, even if the thickness of the collimator plate support portion 323 is increased, the collimator plate support portion 323 is prevented from interfering with the X-ray detection element.
- the width between the X-ray detection elements where the collimator plate support 323 is arranged is set to D + ⁇ with respect to the width D between the X-ray detection elements where the collimator plate support 323 is not arranged. ( ⁇ ⁇ 0).
- the X-ray detection element intervals in the rotation axis direction are partially unequal, so that the image calculation device 122 can rotate the measurement data sent from the data collection device 107 in the rotation axis direction.
- the back projection process is performed after the process of correcting the positional deviation is performed.
- the collimator plate 321 it is possible to easily fit the collimator plate 321 into the groove 324 of the collimator plate support portion 323 even when the number of detection element rows is increased, and the arrangement of the collimator plate 321 is facilitated.
- a radiation detector, and an X-ray CT apparatus equipped with such a radiation detector can be provided. Furthermore, the radiation detector can be configured without causing the mechanical strength of the collimator plate support 323 to be insufficient.
- FIG. 8 can be replaced with FIG. 3 of the first embodiment.
- FIG. 9 is a cross-sectional view taken along the line EE in FIG. 8, which can be substituted for FIG. 5 of the first embodiment.
- the column 721 supports the grooved flat plate 722 and is installed on the substrate 333.
- the height of the column 721 is lower than the height in which the light detection element array 332, the scintillator element array 331, the collimator plate support 323, and the collimator plate 321 are assembled.
- the grooved flat plate 722 supports the collimator plate 321 from the rotation axis direction, and is installed at the upper end of the column 721.
- the grooved flat plate 722 has a groove 723 into which the collimator plate 321 is fitted, and the position of the groove 723 is between the X-ray detection elements on the rotation plane (XY plane).
- the interval between the grooves 723 is slightly narrower than the interval between the grooves 324 provided in the collimator plate support 323, and the grooves 723 and 324 are provided so that the collimator plate 321 is arranged radially toward the X-ray focal point 201. .
- the shape of the groove 723 may be any shape as long as the collimator plate 321 does not hinder the collimator plate 321 from being arranged radially toward the X-ray focal point 201. Further, the collimator plate 321 fitted in the groove 723 may be fixed by an adhesive.
- the processing cost can be reduced. Further, in the direction connecting the X-ray focal point 201 and each X-ray detection element, the length of the groove 723 of the grooved flat plate 722 is shorter than the length of the groove of the grooved column 322 of the first embodiment. Further, the collimator plate 321 can be more easily inserted.
- the collimator plate 321 it is possible to easily fit the collimator plate 321 into the groove 324 of the collimator plate support portion 323 even when the number of detection element rows is increased, and the arrangement of the collimator plate 321 is facilitated.
- a radiation detector, and an X-ray CT apparatus equipped with such a radiation detector can be provided. Further, the collimator plate 321 can be easily fitted into the groove 723 included in the grooved flat plate 722.
- the above-described embodiment is not intended to limit the structure of the present invention, but is an example showing a specific embodiment, and the present invention can be realized in other forms having the same effect. Is possible.
- the indirect conversion type detector in which the scintillator element array 331 and the light detection element array 332 are combined has been described.
- the combination of the scintillator element array 331 and the light detection element array 332 is replaced with a semiconductor element array.
- the present invention can also be realized in a direct conversion detector.
- a radiation detector such as a detector for detecting ⁇ -rays is also included in the present invention.
- an X-ray tube apparatus has been described as an example of a radiation source, a ⁇ -ray generation source using an isotope element may be used.
- 1 X-ray CT apparatus 100 scan gantry section, 101 X-ray tube apparatus, 102 rotating disk, 103 collimator, 104 opening, 105 bed apparatus, 106 X-ray detector, 107 data collection apparatus, 108 gantry control apparatus, 109 bed Control device, 110 X-ray control device, 111 High voltage generation device, 120 console, 121 input device, 122 image calculation device, 123 storage device, 124 system control device, 125 display device, 201 X-ray focal point, 202 scattered radiation removal Part, 203 detection element module, 321 collimator plate, 322 grooved column, 323 collimator plate support, 324 groove, 331 scintillator element array, 331a scintillator element, 331b light reflector, 332 light detection element array, 332a light detection element, 333 substrates, 721 pillars, 722 flat plates with grooves, 723 grooves
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Abstract
Description
まず、図1を用いて本実施形態の医用画像診断装置の一例であるX線CT装置の全体構成を説明する。図1は、X線CT装置1の全体構成を示すブロック図である。図1に示すようにX線CT装置1は、スキャンガントリ部100と操作ユニット120とを備える。
図7を用いて第二の実施形態について説明する。第一の実施形態と異なる点は、回転軸方向(Z軸と平行な方向)において、X線検出素子が一部不等間隔となっている点であり、それ以外については第一の実施形態と同様であるので説明を省略する。なお、図7は第一の実施形態の図4に代わりうるものである。
図8と図9を用いて第三の実施形態について説明する。第一の実施形態と異なる点は、溝付き柱322の代わりとして柱721と溝付き平板722を用いる点であり、それ以外については第一の実施形態と同様であるので説明を省略する。なお、図8は第一の実施形態の図3に代わりうるものである。また図9は図8中のE-E断面図であり、第一の実施形態の図5に代わりうるものである。
Claims (6)
- 放射線源から発生した放射線を検出する複数の放射線検出素子が第1の方向及び第1の方向と直交する第2の方向に配置された放射線検出素子アレイと、
前記放射線検出素子アレイの前記放射線源の側に第1の方向に沿って配置され、散乱線を除去するコリメータ板と、
前記コリメータ板を支持する溝を有し、前記放射線検出素子の間に第2の方向に沿って配置されるコリメータ板支持部と、を備えることを特徴とする放射線検出器。 - 請求項1に記載の放射線検出器において、
前記コリメータ板支持部は偶数個であって、第1の方向における中心位置を基準として対称な位置に備えられることを特徴とする放射線検出器。 - 請求項1に記載の放射線検出器において、
前記コリメータ板支持部が配置される放射線検出素子間の幅は、前記コリメータ板支持部が配置されない放射線検出素子間の幅よりも広いことを特徴とする放射線検出器。 - 請求項1に記載の放射線検出器において、
前記放射線検出素子は、放射線が入射すると可視光を発光するシンチレータ素子と、前記可視光が入射すると電気信号を出力する光検出素子とで構成され、
前記シンチレータ素子間には、前記可視光を反射する反射材が設けられ、
前記コリメータ板支持部は前記反射材と同じ材質で構成されることを特徴とする放射線検出器。 - 前記放射線源と、前記放射線源に対向配置され被検体を透過した放射線を検出する請求項1に記載の放射線検出器と、前記放射線源と前記放射線検出器を搭載し前記被検体の周囲を回転する回転円盤と、前記放射線検出器により検出された複数角度からの透過放射線量に基づき前記被検体の断層画像を再構成する画像再構成装置と、前記画像再構成装置により再構成された断層画像を表示する画像表示装置と、を備えたことを特徴とするX線CT装置。
- 請求項5に記載のX線CT装置であって、
前記放射線検出器のコリメータ板支持部が配置される位置は画像再構成時の最大スライス厚のつなぎ目の位置であることを特徴とするX線CT装置。
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US10646176B2 (en) * | 2015-09-30 | 2020-05-12 | General Electric Company | Layered radiation detector |
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