JP2005127899A - Radiation detector, and radiation image diagnostic device using the same - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a radiation detector having excellent spatial resolution very narrow in a crosstalk between elements, and high in detection sensitivity. <P>SOLUTION: In this radiation detector provided with the plurality of phosphor elements arrayed along a one-dimensional or two-dimensional direction orthogonal to a radiation incident face, using one face as the radiation incident face, a separator layer arranged between the adjacent phosphor elements and a photoelectric transfer element bonded on each of the other faces of the phosphor elements, the separator layer contains white inorganic compound powder, a light reflecting auxiliary material such as silver and aluminum, and/or a photoabsorbing auxiliary material for absorbing light having an emission light wavelength of the each phosphor element, in a resin. <P>COPYRIGHT: (C)2005,JPO&NCIPI

Description

  The present invention relates to a radiation detector that detects X-rays, γ-rays, and the like and a radiation image diagnostic apparatus using the same, and more particularly to a radiation detector suitable for an X-ray CT apparatus and the like.

  Radiation detectors used in X-ray CT apparatuses and the like are mainly combined with phosphor elements and photodiodes, and such radiation detectors have a plurality of phosphor elements arranged one-dimensionally or two-dimensionally. The scintillator array has a structure in which a scintillator array is arranged on a substrate on which a diode array is formed corresponding to each element position. In a radiation detector such as an X-ray CT apparatus, if there is signal leakage (crosstalk) between each detection element, there is a problem that the spatial resolution of the CT image decreases, and the variation in crosstalk is an artifact. Cause. Therefore, a separator layer is formed between the scintillators of the radiation detector to shield radiation and prevent signal leakage (crosstalk) between elements.

  Conventionally, a radiation shielding metal plate such as Mo, W, and Pb, a white film that reflects scintillation light, and the like have been used as the separator layer. Further, a composite material of these has been proposed. For example, Patent Document 1 describes a separator layer in which a light reflection layer is formed by applying a white paint or the like on both surfaces of a metal thin film such as Mo, W, or Pb, and Patent Document 2 describes a white light with high light reflectance. A separator having a structure in which a metal thin film is sandwiched between molecular sheets is described. In order to improve the effect of preventing crosstalk, various reflecting materials other than the white film have been proposed. For example, in Patent Document 3, a white pigment such as titanium dioxide, barium sulfate, or magnesium oxide mixed with a resin to form a slurry is filled in a gap between scintillator elements and dried to form a separator layer. It is described. Further, in Patent Document 4, a high reflectance and low absorptivity metal using either silver, aluminum or gold as a reflector, and a composition comprising titanium oxide and a castable polymer is used as a reflector. It is described to be used. This document further describes that a light absorber such as chromium oxide may be added to a polymer composition containing titanium oxide in order to reduce crosstalk.

JP 2000-180555 A JP-A-5-256949 JP-A-6-160538 JP 11-2331060 A

  However, the separators having the structures described in Patent Document 1 and Patent Document 2 have a sufficient crosstalk prevention effect, but the problem is that the sensitivity of each detection element is not sufficient because the light reflectance on the separator surface is low. there were. Moreover, in the separator which consists of a reflecting material as described in patent document 3 and patent document 4, the light transmittance of a separator layer is about 2 to 5%, and the crosstalk prevention effect was inadequate. The light transmittance of the separator can be lowered by increasing the thickness between the elements. However, in the case of a detection element having a width of the scintillator element of 1 mm or less, there is a limit to increase the thickness between the elements. . Further, as described in Patent Document 4, it is possible to lower the light transmittance by adding a light absorber, but this method is not always effective because the emission wavelength of the scintillator varies depending on the material.

  Therefore, an object of the present invention is to provide a radiation detector having extremely small crosstalk between elements, high detection sensitivity, and excellent spatial resolution. Another object of the present invention is to provide a radiological image diagnostic apparatus capable of performing high-speed scanning, obtaining a high-quality image with good spatial resolution and few artifacts by using such a radiation detector. To do.

  A radiation detector according to the present invention that solves the above-described problems includes a phosphor incident surface on one side and a plurality of phosphor elements arranged in a one-dimensional direction or a two-dimensional direction orthogonal to the radiation incident surface, and an adjacent phosphor. A separator layer disposed between the elements, and a photoelectric conversion element bonded to each of the other surfaces of the phosphor element, the separator layer comprising white inorganic compound powder in the resin, a light-reflective auxiliary material, and And / or a light-absorbing auxiliary material that absorbs light having the emission wavelength of the phosphor element.

  As the light reflective auxiliary material, for example, one or more metal powders selected from silver, aluminum, platinum, tin, lead, molybdenum, and tungsten are used.

  As the light-absorbing auxiliary material, a substance that absorbs light having the emission wavelength of the phosphor element is used. For example, in the case where the phosphor element is a rare earth oxide phosphor composed of a base crystal having a garnet structure containing Ce as a light emitting element and containing Gd, Al, Ga, and O, it is a substance that selectively absorbs light near 550 nm. It is preferable. Specifically, for example, one or more pigments selected from inorganic pigments such as cobalt blue, cerulean blue, Prussian blue, and ultramarine and organic dyes such as phthalocyanine blue and cobalt naphthenate can be used.

  The light-reflecting auxiliary material and the light-absorbing auxiliary material may be used alone or in combination. In each case, the total of both is 1 part by weight with respect to the total of 100 parts by weight of the white inorganic compound and the resin. It is preferable not to exceed. That is, the light-reflective auxiliary material and / or the light-absorbing auxiliary material is preferably 1 part by weight or less, more preferably 0.0001 to 0.5 part by weight or less with respect to 100 parts by weight of the total of the white inorganic compound and the resin.

  The radiological image diagnostic apparatus of the present invention includes a radiation source, a radiation detector disposed opposite to the radiation source, a rotating circle that holds the radiation source and the radiation detector, and is driven to rotate around a subject. A plate and image reconstruction means for reconstructing a tomographic image of the subject based on the radiation intensity detected by the radiation detector, and using the radiation detector as a radiation detector.

The radiation detector of the present invention includes a material composed of a white pigment and a resin as a material for a separator layer provided between phosphor elements, a material powder having light reflectivity and / or an emission wavelength of a phosphor as an auxiliary material. By adding a material powder that absorbs light, a high light reflectance can be obtained on the separator surface, thereby improving the sensitivity of the device, reducing the light transmittance, and reducing crosstalk between devices. be able to.
The radiological image diagnostic apparatus of the present invention can perform high-speed scanning by using the above-mentioned radiation detector as a radiation detector, and in that case, a high-quality image with good spatial resolution can be obtained.

Hereinafter, embodiments of the radiation detector of the present invention will be described.
FIG. 1 is a diagram showing an embodiment of a radiation detector to which the present invention is applied. The radiation detector 10 has a structure in which a plurality of detection elements each including a columnar scintillator element 11 and a photodiode 13 bonded to the bottom surface thereof are arranged in a one-dimensional or two-dimensional direction. The photodiode 13 is a photodiode substrate 14. It is formed at a position corresponding to the arrangement of the scintillator elements 11 on the top. Further, a separator layer 12 is formed so as to surround the four side surfaces of the scintillator element 11, and on the side facing the surface to which the photodiode 13 of the scintillator element 11 is bonded, the light reflecting layer 15 is covered so as to cover the entire upper surface of the detector 10. Is formed.

As the scintillator, known phosphor materials such as rare earth oxides and rare earth oxysulfides can be used. For example, rare earth oxidation made of a base crystal having a garnet structure containing Ce as a light emitting element and containing Gd, Al, Ga, and O. A material scintillator can be used. This rare earth oxide scintillator is described in Patent Document 5 and Patent Document 6, for example. As the photodiode 13, a Si photodiode, particularly a SiPIN diode, or the like is used.
Japanese Patent Laid-Open No. 2001-4753 JP 2002-189080 JP

  The separator layer 12 is made of a material having a high reflectance and a low light transmittance. Specifically, the resin contains a white inorganic compound powder and a light reflecting or light absorbing auxiliary agent. As the resin, a resin such as an epoxy resin, an acrylic resin, or an unsaturated polyester can be used. The white inorganic compound powder is a material for imparting a high light reflectance to the separator layer 12, and for example, titanium oxide, aluminum oxide, barium sulfate, magnesium oxide, or the like can be used. Such a white inorganic compound powder varies depending on the thickness of the separator layer 12 in order to achieve sufficient light reflectance and light transmittance, but is preferably 30 to 300 parts by weight, more preferably 100 parts by weight of the resin. Contains 100 to 200 parts by weight.

  The light-reflecting auxiliary agent is a material that further improves the light reflectivity of the separator layer 12 and decreases the light transmittance of the separator layer 12, and specifically, silver, aluminum, platinum, tin, lead, molybdenum, tungsten A metal powder such as can be used. Among these metal powders, silver and aluminum are particularly preferable because they have a high light reflectance in the entire visible light region. Metal plates such as lead, molybdenum, and tungsten are conventionally used as radiation shielding materials, but in the present invention, by adding such a metal as a powder to a resin together with a white powder, It was possible to improve the reflectance and reduce the light transmittance. Silver has a property of absorbing light once and then releasing it, and also functions as a light-absorbing auxiliary material.

  The particle diameter of the metal powder is not particularly limited, but is preferably about 0.01 to 50 μm. By setting the particle diameter within such a range, it is possible to realize good light reflection and low transmittance. The addition amount of the light-reflecting auxiliary agent is preferably 1 part by weight or less, more preferably 0.005 to 0.5 part by weight, and still more preferably 0.01 to 0.15 part by weight with respect to the total 100 parts by weight of the resin and the white inorganic compound. . As the amount of the light-reflecting auxiliary added increases, the detection sensitivity also decreases. Therefore, it is desirable not to exceed 4 parts by weight in order to obtain a light transmittance reduction effect within an acceptable detection sensitivity range. Further, if it is less than 0.005 parts by weight, a sufficient effect cannot be obtained.

  The light-absorbing auxiliary agent is a material having absorption at a wavelength overlapping with the emission wavelength of scintillation light, and reduces the light transmittance of the separator layer 12 by absorbing light. As such a light-absorbing auxiliary agent, for example, in the case where the scintillator material is a rare earth oxide phosphor having Ce as a light-emitting element as described above, an inorganic or organic pigment that selectively absorbs light at a peak wavelength of about 550 nm. Alternatively, a dye can be used. Specifically, inorganic pigments such as cobalt blue, cerulean blue, Prussian blue, ultramarine blue, copper chromomanganate, and organic pigments such as phthalocyanine blue, oxazine dye (Violet B: Ciba Specialty Chemicals), and cobalt naphthenate Or a dye can be mentioned. The addition amount of the light-absorbing auxiliary agent varies depending on the type of auxiliary agent to be used, but is preferably 1 part by weight or less, more preferably 0.0001 to 0.5 part by weight with respect to 100 parts by weight of the total of the resin and the white inorganic compound. .

The above-described light-reflecting auxiliary agent and light-absorbing auxiliary agent may be used in combination, and in that case, the effect of preventing optical crosstalk is obtained in the same manner. Furthermore, a known additive such as a dispersant can be added to the separator layer 12 as long as its properties are not impaired.
As the reflective layer 15 formed on the upper surface of the scintillator element 11, a white polymer sheet or a white paint can be used. Further, as shown in FIG. 2, the above-described separator material may be provided as a coating layer.

  Next, a method for manufacturing the radiation detector 10 having the above configuration will be described. The radiation detector 10 of the present invention can be manufactured by a known manufacturing method, and an example thereof will be described, but the present invention is not limited to this. First, the scintillator block is grooved in the vertical and horizontal directions. At that time, the groove is processed leaving the bottom of the groove, and a predetermined amount of white inorganic compound powder, light-reflecting auxiliary agent and / or light-absorbing auxiliary agent is added to the resin in the groove, and a solvent is appropriately added as necessary. The separator layer material added and dispersed is poured and cured. At this time, by using a centrifuge, it is possible to quickly fill the groove with the separator layer material and to prevent generation of bubbles. The scintillator block that has been subjected to the element separation in this way is cut into a plane orthogonal to the depth direction of the groove, thereby obtaining a scintillator that is separated from one another. This is adhered to a substrate on which photodiodes are formed in a predetermined arrangement, and a reflection layer such as a white sheet is formed on the upper surface to obtain the radiation detector 10.

  The radiation detector 10 of the present invention uses a material having excellent light reflectivity and light shielding properties as the separator layer 12, so that a sufficient shielding effect can be obtained without using a metal plate or a metal thin film together. However, it does not prevent the combined use with a metal plate or the like. In this case, after the groove processing, after inserting the metal plate into the groove, the separator layer material is poured and cured. The subsequent steps are the same as those described above.

  In the radiation detector 10 having such a configuration, when radiation (X-rays) to be detected is incident through the light reflecting layer 15, each scintillator element 11 emits light having an intensity corresponding to the amount of radiation incident thereon. This light is photoelectrically converted by the photodiodes 13, and an electric signal corresponding to the incident radiation is output from each photodiode 13. The light emitted from the scintillator element 11 is reflected by the light reflecting layer 15 and the separator layer 12, and is efficiently detected by the photodiode 13. Further, since light transmitted through the separator layer 12 to the adjacent scintillator elements is minimized, optical crosstalk is prevented and high-precision detection can be performed.

Next, an embodiment of the radiation image diagnostic apparatus of the present invention will be described.
The radiation image diagnostic apparatus of the present invention uses the above-described radiation detector as a radiation detector, and the other configuration is the same as that of a known image diagnostic apparatus. An embodiment applied to an X-ray CT apparatus will be briefly described. FIG. 3 is a diagram showing an outline of an X-ray CT apparatus to which the present invention is applied. This X-ray CT apparatus includes a scan gantry unit 310 and an image reconstruction unit 320. A rotating disk 311 having an opening 314 into which a specimen is carried, an X-ray tube 312 mounted on the rotating disk 311, and a collimator 313 attached to the X-ray tube 312 and controlling the radiation direction of the X-ray flux An X-ray detector 315 mounted on a rotating disk 311 facing the X-ray tube 312; a detector circuit 316 that converts X-rays detected by the X-ray detector 315 into a predetermined signal; A scan control circuit 317 for controlling the rotation of the disk 311 and the width of the X-ray beam is provided.

  The image reconstruction unit 320 includes an input device 321 for inputting a subject's name, examination date and time, examination conditions, and the like, and an image computation circuit that performs CT image reconstruction by computing the measurement data S1 sent from the detector circuit 316 322, an image information adding unit 323 for adding information such as a subject's name, examination date, examination conditions, and the like input from the input device 321 to the CT image created by the image calculation circuit 322, and a CT to which the image information is added A display circuit 324 that adjusts the display gain of the image signal S2 and outputs it to the display monitor 330.

  In this X-ray CT apparatus, X-rays are irradiated from an X-ray tube 312 in a state where a subject is placed on a bed (not shown) installed in an opening 314 of a scan gantry unit 310. The X-rays have directivity by the collimator 313 and are detected by the X-ray detector 315. At this time, by rotating the rotating disk 311 around the subject, the X-ray transmitted through the subject is detected while changing the direction of X-ray irradiation. A tomographic image created by the image reconstruction unit 320 based on the measurement data is displayed on the display monitor 330.

  Here, the X-ray detector 315 has a plurality of (eg, 960) scintillator elements in which scintillators and photodiodes are combined arranged in an arc shape, and each detection element array substrate has the above-described configuration of the radiation detector. Have. That is, the separator layer that separates the elements includes white inorganic compound powder and a specific auxiliary material in the resin, and has high reflectance and low light transmittance. Therefore, it is possible to obtain a high-quality tomographic image in which a reduction in spatial resolution and artifacts due to optical crosstalk are suppressed.

  Examples of the radiation detector of the present invention will be described below.

[Examples 1 to 6]
Gd ₃ (Al, Ga) ₅ O ₁₂ : Ce ceramic scintillator is used as the scintillator material, and a multi-wire saw with a wire diameter of 0.13 mm is used for this scintillator plate (dimensions: X × Y × Z = 24 mm × 36 mm × 3 mm) Then, a grid-like grooving process perpendicular to the XY plane was performed. Grooves are formed in parallel to the Y direction, 23 at 1 mm pitch in the X direction, 15 in parallel to the X direction, and 15.25 mm pitch in the Y direction. The depth of each groove is 2 mm, reaching the bottom of the scintillator plate It was not deep.

On the other hand, a separator layer material prepared by mixing titanium oxide TiO ₂ (150 g / 100 g of resin) and auxiliary materials shown in Table 1 in an epoxy resin is prepared and poured into a groove of a scintillator plate formed as described above to be cured. To form a separator layer. Thereafter, the upper and lower surfaces were cut and polished parallel to the XY plane, finished to a thickness of 1.8 mm, and a 24 × 16 channel scintillator element array was produced. This was adhered to a substrate on which a 24 × 16 photodiode array was formed with a transparent adhesive to produce a detection element array.

  The detection element array thus produced is placed 110 cm away from the X-ray source (120 kV, 200 mA), X-rays are irradiated only to specific elements through a 0.2 mm lead slit, and the output of the element (X-rays) Sensitivity) and the output of the adjacent element. The ratio (%) of the output of the adjacent element to the output of the element was determined as the amount of optical crosstalk. The results are shown in Table 1. The X-ray sensitivity is shown as a relative value with respect to the comparative example.

[Comparative example]
A detection element array was prepared in the same manner as in Example except that the separator material did not contain an auxiliary material, and the optical crosstalk amount and X-ray sensitivity were measured. The results are also shown in Table 1.

  As can be seen from the results shown in Table 1, by adding an auxiliary material in addition to the white pigment, the amount of crosstalk is greatly reduced without substantially reducing the X-ray sensitivity compared to the case of using only the white pigment. We were able to. In particular, when silver and aluminum were used as auxiliary materials, and when silver and a light-absorbing material were used in combination, good results were obtained in both crosstalk amount and X-ray sensitivity.

[Example 7]
Example except that the amount of silver powder added to the separator material as an auxiliary material (addition amount with respect to 100 g of resin and titanium oxide in total) is 0.02 g, 0.04 g, 0.08 g, 0.1 g, 0.2 g A detection element array was prepared in the same manner as in Example 1, and the amount of optical crosstalk and X-ray sensitivity were measured. The results are shown in FIG. Also in this case, the X-ray sensitivity is shown as a relative value when no auxiliary material is added.

  As can be seen from the results shown in FIG. 4, the X-ray sensitivity and the optical crosstalk amount decrease as the amount of added silver increases, but the X-ray sensitivity is moderate, whereas the optical crosstalk amount is less than that of silver. It decreased rapidly by adding a small amount. Accordingly, if the allowable value for the decrease in X-ray sensitivity is 15%, 0.1 g can be added, whereby the optical crosstalk amount that was 4.0% can be reduced to 1/4.

The figure which shows one Embodiment of the radiation detector of this invention The figure which shows other embodiment of the radiation detector of this invention. The figure which shows one Embodiment of the radiographic image diagnostic apparatus of this invention The graph which shows the element characteristic of the radiation detector of Example 7

Explanation of symbols

11 ... scintillator element, 12 ... separator layer, 13 ... photodiode, 14 ... substrate, 15 ... light reflecting layer, 311 ... rotating disk, 312 ... X-ray tube 315 ... X-ray detector 320 ... Image reconstruction unit

Claims (3)

  A plurality of phosphor elements arranged in a one-dimensional direction or a two-dimensional direction perpendicular to the radiation incident surface as one surface, a separator layer disposed between adjacent phosphor elements, and the phosphor In the radiation detector comprising a photoelectric conversion element bonded to each of the other surfaces of the element, the separator layer includes a white inorganic compound powder, a light-reflective auxiliary material, and / or a phosphor element in a resin. A radiation detector comprising: a light-absorbing auxiliary material that absorbs light having an emission wavelength.   The radiation detector according to claim 1, wherein the light-reflecting auxiliary material and / or the light-absorbing auxiliary material is contained in an amount of 1 part by weight or less based on 100 parts by weight of the total of the white inorganic compound and the resin.   A radiation source, a radiation detector arranged opposite to the radiation source, a rotating disk that holds the radiation source and the radiation detector and is driven to rotate around the subject, and is detected by the radiation detector A radiation image diagnostic apparatus comprising: an image reconstruction unit that reconstructs a tomographic image of the subject based on the radiation intensity that is used. The radiation detector according to claim 1 or 2 is used as the radiation detector. A radiological image diagnostic apparatus.

Images