WO2019167146A1 - Procédé de production d'un collimateur - Google Patents

Procédé de production d'un collimateur Download PDF

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Publication number
WO2019167146A1
WO2019167146A1 PCT/JP2018/007362 JP2018007362W WO2019167146A1 WO 2019167146 A1 WO2019167146 A1 WO 2019167146A1 JP 2018007362 W JP2018007362 W JP 2018007362W WO 2019167146 A1 WO2019167146 A1 WO 2019167146A1
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WO
WIPO (PCT)
Prior art keywords
radiation
ray
collimator
manufacturing
radiation shielding
Prior art date
Application number
PCT/JP2018/007362
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English (en)
Japanese (ja)
Inventor
久史 森井
隆治 奥之山
克之 都木
Original Assignee
株式会社ＡＮＳｅｅＮ
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 株式会社ＡＮＳｅｅＮ filed Critical 株式会社ＡＮＳｅｅＮ
Priority to PCT/JP2018/007362 priority Critical patent/WO2019167146A1/fr
Priority to JP2020503141A priority patent/JP6967312B2/ja
Priority to TW108102280A priority patent/TWI689947B/zh
Publication of WO2019167146A1 publication Critical patent/WO2019167146A1/fr

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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

Definitions

  • the present invention relates to a collimator manufacturing method.
  • Radiation inspection equipment such as X-ray CT (Computed Tomography), which inspects a subject non-destructively using radiation, irradiates the subject with radiation and generates a CT image based on the radiation transmitted through the subject. It is a device to do.
  • a radiation inspection apparatus includes a radiation generation apparatus and a radiation detection apparatus.
  • the radiation irradiated to the subject is partially scattered in the subject.
  • the radiation detection apparatus detects scattered radiation, the detection accuracy deteriorates.
  • the radiation detection apparatus is provided with a collimator.
  • a collimator for example, a two-dimensional collimator capable of removing scattered X-rays in the channel direction and the slice direction has been developed (for example, see Patent Document 1).
  • An object of this invention is to provide the collimator manufacturing method which can manufacture easily the collimator which has a radiation transmission part with a small and small aspect ratio.
  • a collimator manufacturing method comprising: a radiation shielding part; and a radiation transmissive part provided through the radiation shielding part and having a radiation shielding rate lower than that of the radiation shielding part, wherein the radiation transmissive part is formed.
  • An arrangement step of placing a columnar member standing member with a columnar member standing on a holding substrate in a casting mold, an inflow step of flowing the material of the radiation shielding portion into the casting mold in liquid form, and the radiation shielding portion A method for manufacturing a collimator, comprising: a step of taking out the columnar member standing member and the radiation shielding portion from the casting mold after curing.
  • the radiation transmitting part may be made of a material having a high visible light shielding rate.
  • the radiation transmitting part may be manufactured from a material having a higher melting point than the material of the radiation shielding part.
  • the radiation transmitting part may be made of carbon.
  • the radiation shielding part may be made of tin.
  • a removal step of removing the columnar member may be provided after the extraction step.
  • the present invention provides the following.
  • a method of manufacturing a collimator in which a liquid radiation shielding portion and a radiation transmission portion provided through the radiation shielding portion and having a radiation shielding rate lower than that of the radiation shielding portion are sealed in a container A standing step of standing a plurality of columnar members forming a transmission part in the opened container, an inflow step of flowing the liquid radiation shielding material into the container, and the container
  • a collimator manufacturing method comprising: a sealing step of sealing.
  • FIG. 1 is a schematic view of an X-ray CT apparatus 1 that is an embodiment of a radiation inspection apparatus. It is a section perspective view of one X-ray detection part 10 of a 1st embodiment. It is a figure explaining the manufacturing method of the collimator 20 of 1st Embodiment. It is a flowchart explaining the manufacturing method of the collimator 20 of 1st Embodiment. It is the graph which showed the simulation calculation value of the X-ray spectrum. It is the graph which showed the absorption factor of the X-ray by carbon (C), aluminum (Al), and copper (Cu).
  • C carbon
  • Al aluminum
  • Cu copper
  • FIG. 6 is a graph showing X-ray count values detected by the X-ray detection element 30 when X-rays are generated from the X-ray generator 2 and irradiated on the subject B; It is a figure explaining the manufacturing method of the collimator 120 of 2nd Embodiment.
  • FIG. 1 is a schematic view of an X-ray CT apparatus (X-ray inspection apparatus) 1 which is an embodiment of the radiation inspection apparatus of the present invention.
  • the present invention is not limited to the X-ray CT apparatus 1 and may be a radiation inspection apparatus using other radiation such as gamma rays.
  • the X-ray CT apparatus 1 includes an X-ray generation apparatus (radiation generation apparatus) 2, a gantry 3 on which the subject B is disposed, and an X-ray detection apparatus disposed along a circumference centered on the X-ray generation apparatus 2. (Radiation detection device) 4.
  • the X-ray detection apparatus 4 includes a plurality of X-ray detection units (radiation detection units) 10.
  • FIG. 2 is a cross-sectional perspective view of one X-ray detection unit 10 of the first embodiment.
  • Each X-ray detection unit 10 includes a collimator 20 and a plurality of X-ray detection elements (radiation detection elements) 30.
  • the X-ray detection elements 30 are arranged at an interval (pitch) a of about 0.1 to 2.00 mm.
  • the X-ray detection elements 30 are arranged corresponding to the individual X-ray transmission parts 21 provided in the collimator 20 described later.
  • the X-ray detection element 30 may be an indirect conversion type or a direct conversion type.
  • the indirect conversion type X-ray detection element 30 includes a scintillator and an optical sensor such as a photomultiplier tube, converts incident X-rays into light by the scintillator, and converts the converted light into an electrical signal by the photoelectric conversion element. Convert to The direct conversion type X-ray detection element 30 is composed of a plurality of cadmium telluride (CdTe) -based semiconductor elements, and converts incident X-rays directly into electrical signals.
  • CdTe cadmium telluride
  • the collimator 20 includes a plate-shaped X-ray shielding part (radiation shielding part) 22 having a predetermined thickness and a plurality of columnar X-ray transmission parts (radiation transmission parts) arranged in a lattice pattern through the X-ray shielding part 22. 21).
  • the X-ray shielding part 22 is made of a material having a high shielding rate (low transmittance) for X-rays and visible light.
  • the material of the X-ray shielding part 22 is tin.
  • the material of the X-ray shielding part 22 is not limited to this, and the material having a large atomic number such as molybdenum, tantalum, lead, tungsten, etc., a high visible light and high X-ray shielding ability (stopping ability), or a heavy metal, or these An alloy containing a heavy metal may be used.
  • the melting point of tin is 231 ° C., and in the case of manufacturing by the manufacturing method described later, the manufacturing can be easily performed by using a relatively low melting point similar to that of tin.
  • the thickness b of the X-ray shielding part 22 is about 1 to 50 mm.
  • the X-ray transmission part 21 is, for example, a columnar shape, is solid, and the center axis A of the column extends in a direction facing the X-ray generation device 2 or the subject B, respectively.
  • the corresponding X-ray detection elements 30 are closely attached to the surface opposite to the X-ray generator 2 or the subject B in the X-ray transmission part 21 so that visible light does not enter between them. ing.
  • the diameter R of the X-ray transmission part 21 is about 0.07 to 0.2 mm, and the depth of the X-ray transmission part 21 is equal to the thickness b of the X-ray shielding part 22 and is about 1 to 50 mm.
  • the X-ray transmission part 21 has a shape in which the diameter R is smaller than the depth b (a long and narrow aspect ratio).
  • the X-ray transmission part 21 is not limited to a cylindrical shape, and may be an elliptical column or a prismatic shape.
  • the X-ray transmission part 21 is made of a material having a low X-ray shielding rate (high transmittance) and a high visible light shielding rate (low transmittance), for example, carbon.
  • the present invention is not limited to this, and other materials such as aluminum other than carbon having an atomic number smaller than that of the X-ray shielding part 22, a low X-ray shielding rate, or light weight may be used.
  • the melting point of the material of the X-ray transmissive part 21 is higher than the melting point of the material of the X-ray shielding part 22.
  • X-rays generated by the X-ray generator 2 are applied to the subject B.
  • the light irradiated to the subject B passes through the subject B and is partially scattered.
  • the straight X-ray transmitted through the subject B and the scattered X-ray scattered by the subject B reach the collimator 20.
  • those other than the X-rays that enter the X-ray transmitting part 21 are shielded by the X-ray shielding part 22 because the X-ray shielding part 22 has a high X-ray shielding rate.
  • the X-rays that have reached the X-ray transmission part 21 enter the X-ray transmission part 21 because the shielding rate of the X-ray transmission part 21 is low. Visible light is shielded because the visible light shielding rate of the X-ray transmission part 21 is high.
  • the X-ray that has reached the X-ray detection element 30 is converted into light by the scintillator, and the converted light is converted into an electric signal by the photoelectric conversion element.
  • the incident X-ray is directly converted into an electric signal.
  • the X-ray intensity information converted into the electrical signal is processed by the processing unit 5 to generate X-ray CT image data, and the display unit 6 displays the X-ray CT image.
  • FIG. 3 is a diagram illustrating a method for manufacturing the collimator 20 of the first embodiment.
  • FIG. 4 is a flowchart illustrating a method for manufacturing the collimator 20 according to the first embodiment.
  • the collimator 20 of the first embodiment is manufactured by casting.
  • a columnar member standing member 24 is prepared in which a plurality of columnar members forming the X-ray transmission part 21 are erected on the holding substrate 23 (FIG. 3A).
  • the columnar member 21 a and the holding substrate 23, that is, the entire columnar member standing member 24 are made of carbon.
  • the present invention is not limited thereto, and the columnar member 21a and the holding substrate 23 may be separate.
  • the columnar member standing member 24 is disposed inside the casting mold 40 (FIG. 3B, FIG. 4 (step S1)).
  • the material of the X-ray shielding part 22 that is heated to the melting point or higher and becomes liquid, in the embodiment, tin, is caused to flow into the casting mold 40 (FIG. 3C, FIG. 4 (step S2)).
  • the melting point of tin is 231 degrees.
  • step S3 The temperature is lowered below the melting point and the X-ray shielding part 22 is cured (FIG. 4 (step S3)).
  • the X-ray shielding portion 22 that is cured and integrated with the columnar member standing member 24 is removed from the casting mold 40 (FIG. 3 (d), FIG. 4 (step S4)).
  • At least the surface of the holding substrate 23 of the integrated columnar member standing member 24 and the X-ray shielding portion 22 is polished to remove the holding substrate 23 (FIG. 3E, FIG. 4 (step S5)). Thereby, the collimator 20 of this embodiment is manufactured.
  • FIG. 5 is a graph showing a simulation calculation value of an X-ray spectrum in an X-ray light source according to an example suitably used for the X-ray generator 2, where the vertical axis represents the X-ray dose and the horizontal axis represents X The energy of the line.
  • the dose reaches a peak near the energy of 22 keV, and the dose decreases as the energy increases. In addition, the dose decreases on the low energy side from around 22 keV.
  • FIG. 6 is a graph showing the X-ray absorption rate of carbon (C), aluminum (Al), and copper (Cu) having a thickness of 30 mm.
  • carbon (C), aluminum (Al), and copper (Cu) have low X-ray absorption on the high energy side and high X-ray absorption on the low energy side.
  • Carbon in particular, has a high selective absorption of low energy X-rays, and the absorption rate is approximately 0% at an energy of about 150 keV or higher, but when the energy becomes smaller than about 150 keV, the absorption rate increases rapidly. This selective absorbency increases in the order of copper (Cu), aluminum (Al), and carbon (C).
  • FIG. 7 shows a count of X-rays generated by the X-ray generator 2 using the X-ray light source having the spectrum shown in FIG. It is a graph showing values.
  • the collimator 20 of the actually manufactured embodiment is arranged between the X-ray detection element 30 and the subject B, the count value Q is between the X-ray detection element 30 and the subject B. This is a case where the collimator itself is not arranged.
  • a 30 mm thick tin was used as the X-ray shielding part 22, and a through hole having a diameter of 0.2 mm and a length (30 mm) formed with an X-ray transmission part 21 filled with carbon was used. .
  • the collimator 20 filled with carbon of the actually manufactured embodiment is disposed between the X-ray detection element 30 and the subject B, the X-ray transmission unit 21 shown in FIG.
  • the count value P X-rays having an energy distribution (curve shape) similar to the shape of the X-ray spectrum of the simulation calculation value (FIG. 5) can be detected.
  • the X-ray transmission part 21 is not limited to carbon, and is appropriately selected to use other materials such as aluminum and copper as shown in FIG. 6, thereby removing light having an unnecessary wavelength depending on the application. be able to.
  • a light shielding structure for preventing the incidence of visible light to the X-ray detection element.
  • the X-ray transmission part 21 of the collimator 20 is filled with carbon and is solid.
  • the collimator 20 and the X-ray detection element 30 are in close contact so that no visible light is incident. Therefore, since visible light does not reach the X-ray detection element 30, it is not necessary to provide a separate light shielding structure. Therefore, the manufacturing cost can be reduced and the manufacturing process time can be shortened.
  • the X-ray shielding part is made of a metal having a large atomic number so that X-rays can be shielded. Therefore, it is not easy to make a through hole having high hardness, fineness and a small aspect ratio, and manufacturing cost and manufacturing time are increased. Furthermore, there is a case where it is more difficult to open a high-precision and fine through-hole by cutting a chip generated when a through-hole is drilled with a rotating drill.
  • the holding substrate 23 on which the columnar X-ray transmission part 21 is erected is placed in the casting mold 40, and the material of the X-ray shielding part 22 dissolved in the casting mold 40 flows into the collimator 20. It is manufactured by curing. That is, unlike the method of making a through hole with a drill, the X-ray transmission part 21 having a small and small aspect ratio can be easily manufactured. Therefore, the collimator 20 with higher directivity can be manufactured.
  • the X-ray transmission part 21 is filled with carbon and has a solid form.
  • the present invention is not limited to this, and the carbon filled in the X-ray transmission part 21 may be etched or the like. May be removed.
  • the X-ray transmissive part 21 having a through hole with a fine and small aspect ratio can be easily manufactured. Therefore, the collimator 20 with higher directivity can be manufactured.
  • the second embodiment differs from the first embodiment in the structure and manufacturing method of the collimator 120. Since other points are the same as those of the first embodiment, description of similar parts is omitted.
  • the collimator 20 of the first embodiment uses tin for the X-ray shielding part 22, but the collimator 120 of the second embodiment uses mercury or the like that is liquid at room temperature for the X-ray shielding part 122.
  • FIG. 8 is a diagram for explaining a method of manufacturing the collimator 120 of the second embodiment.
  • the collimator 120 according to the second embodiment includes a container 150, a liquid X-ray shield 122 that is mercury enclosed in the container 150, and an upper end and a lower end in the container 150.
  • a plurality of X-ray transmission parts 121 which are fixed between two opposing surfaces and have a lower X-ray shielding rate than the X-ray shielding part 122 and are made of a solid material, for example, carbon.
  • the container 150 includes a lower container 151 whose upper part is open, and a lid 152 that covers the upper part of the lower container 151.
  • a plurality of bottomed holes 151 a that can be held by inserting the lower end of the columnar X-ray transmission part 21 are provided on the inner surface side of the bottom part of the lower container 151.
  • a bottomed hole 152a that can be held by inserting the upper end of the columnar X-ray transmission part 21 is provided on the lower surface of the lid 152 at a position corresponding to the bottomed hole 151a.
  • the material of the container 150 is preferably a material that is rigid and resistant to mercury erosion. For example, resin, glass, or ceramic is used.
  • the collimator 120 of the second embodiment is manufactured as follows.
  • the X-ray transmitting part 21 is inserted and held in the bottomed hole 151a of the lower container 151 (FIG. 8A).
  • Mercury that becomes the X-ray shielding part 22 flows into the lower container 151 (FIG. 8B).
  • the upper end of the X-ray transmission part 121 protrudes above the surface of mercury.
  • the lower container 151 is covered with a lid 152, and mercury is sealed in the container 150.
  • the upper end of the X-ray transmission part 121 is fitted into the bottomed hole 152a of the lid 152 (FIG. 8C).
  • the collimator 120 is manufactured, which includes a plurality of X-ray transmission parts 121 made of a solid material having a low ray shielding rate, for example, carbon.
  • collimator 120 of the second embodiment various shapes of the collimator 120 can be manufactured by changing the shape of the container 150 in addition to the effects of the first embodiment. Therefore, for example, the curved collimator 120 can be easily manufactured. In addition, when the material of the container 150 is manufactured with a flexible material, deformation after the manufacturing is facilitated, so that the highly versatile collimator 120 can be manufactured.
  • a Central axis B Subject 1 X-ray CT apparatus (radiological examination apparatus) 2 X-ray generator (radiation generator) 3 frame 4 X-ray detection device (radiation detection device 5 processing unit 6 display unit 10 X-ray detection unit (radiation detection unit) 20 Collimator 21a Columnar member 21 X-ray transmission part (radiation transmission part) 22 X-ray shielding part (radiation shielding part) 23 holding substrate 24 columnar member standing member 30 X-ray detection element (radiation detection element) 40 Casting mold 120 Collimator 121 X-ray transmission part (radiation transmission part) 122 X-ray shielding part (radiation shielding part) 150 container 151 lower container 151a bottomed hole 152 lid 152a bottomed hole

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Abstract

L'invention concerne un procédé de production de collimateur permettant de produire facilement un collimateur à section de transmission des rayonnements de petite taille présentant un petit rapport d'aspect. Le procédé de production de collimateur 20 concerne un collimateur 20 comprenant : une section protection contre les rayonnements 22 ; et une section transmission des rayonnements 21 qui est agencée de façon à pénétrer dans la section protection contre les rayonnements 22 et ayant un taux de protection contre les rayonnements inférieur à celui de la section protection contre les rayonnements 22. Le procédé de production comprend : une étape agencement dans laquelle un élément d'installation érigée d'élément colonnaire 21a, comportant un élément colonnaire 21a qui forme la section transmission des rayonnements 21 monté érigé dans un substrat de maintien 23, est agencé dans un moule de coulée 40 ; une étape admission dans laquelle une matière pour la section protection contre les rayonnements 22 est versée dans le moule de coulée 40 à l'état liquide ; et une étape démoulage dans laquelle, après que la section protection contre les rayonnements a durci, l'élément d'installation érigée d'élément colonnaire 21a et la section protection contre les rayonnements sont retirés du moule de coulée 40.
PCT/JP2018/007362 2018-02-27 2018-02-27 Procédé de production d'un collimateur WO2019167146A1 (fr)

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PCT/JP2018/007362 WO2019167146A1 (fr) 2018-02-27 2018-02-27 Procédé de production d'un collimateur
JP2020503141A JP6967312B2 (ja) 2018-02-27 2018-02-27 コリメータ製造方法
TW108102280A TWI689947B (zh) 2018-02-27 2019-01-21 準直器的製造方法

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Cited By (1)

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Publication number Priority date Publication date Assignee Title
CN113397574A (zh) * 2020-03-16 2021-09-17 佳能医疗系统株式会社 准直器以及准直器模块

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JPH11104119A (ja) * 1997-07-10 1999-04-20 Siemens Ag 散乱線除去用格子及びその製造方法
JP2002040196A (ja) * 2000-07-24 2002-02-06 Fuji Photo Film Co Ltd 散乱線吸収グリッドおよびその製造方法
JP2012149982A (ja) * 2011-01-19 2012-08-09 Fujifilm Corp 放射線画像撮影用格子ユニット及び放射線画像撮影システム、並びに格子体の製造方法
JP2014006194A (ja) * 2012-06-26 2014-01-16 Canon Inc 構造体の製造方法

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DE10147947C1 (de) * 2001-09-28 2003-04-24 Siemens Ag Verfahren zur Herstellung eines Streustrahlenrasters oder Kollimators
CN102343500B (zh) * 2010-08-04 2014-04-02 中国科学院高能物理研究所 高精度准直器及其加工方法
CN102949200A (zh) * 2011-08-26 2013-03-06 通用电气公司 准直器及其制造方法及专用于制造该准直器的模具组合
JP2015203571A (ja) * 2014-04-10 2015-11-16 株式会社フジキン 散乱ｘ線除去用グリッドの製造方法
DE102014218462A1 (de) * 2014-09-15 2016-03-17 Siemens Aktiengesellschaft Verfahren zur Herstellung eines Kollimatormoduls und Verfahren zur Herstellung einer Kollimatorbrücke sowie Kollimatormodul, Kollimatorbrücke, Kollimator und Tomographiegerät

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Publication number Priority date Publication date Assignee Title
JPH11104119A (ja) * 1997-07-10 1999-04-20 Siemens Ag 散乱線除去用格子及びその製造方法
JP2002040196A (ja) * 2000-07-24 2002-02-06 Fuji Photo Film Co Ltd 散乱線吸収グリッドおよびその製造方法
JP2012149982A (ja) * 2011-01-19 2012-08-09 Fujifilm Corp 放射線画像撮影用格子ユニット及び放射線画像撮影システム、並びに格子体の製造方法
JP2014006194A (ja) * 2012-06-26 2014-01-16 Canon Inc 構造体の製造方法

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN113397574A (zh) * 2020-03-16 2021-09-17 佳能医疗系统株式会社 准直器以及准直器模块

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TW201937506A (zh) 2019-09-16

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