WO2022224541A1 - Détecteur et dispositif de surveillance de rayonnement - Google Patents

Détecteur et dispositif de surveillance de rayonnement Download PDF

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Publication number
WO2022224541A1
WO2022224541A1 PCT/JP2022/004405 JP2022004405W WO2022224541A1 WO 2022224541 A1 WO2022224541 A1 WO 2022224541A1 JP 2022004405 W JP2022004405 W JP 2022004405W WO 2022224541 A1 WO2022224541 A1 WO 2022224541A1
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WIPO (PCT)
Prior art keywords
sensor
radiation
detector
photons
scatterer
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PCT/JP2022/004405
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English (en)
Japanese (ja)
Inventor
雄一郎 上野
孝広 田所
修一 畠山
徹 渋谷
敬介 佐々木
湧希 小泉
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株式会社日立製作所
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Publication of WO2022224541A1 publication Critical patent/WO2022224541A1/fr

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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
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/20—Measuring radiation intensity with scintillation detectors
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02E—REDUCTION OF GREENHOUSE GAS [GHG] EMISSIONS, RELATED TO ENERGY GENERATION, TRANSMISSION OR DISTRIBUTION
    • Y02E30/00—Energy generation of nuclear origin
    • Y02E30/30—Nuclear fission reactors

Definitions

  • the present disclosure relates to detectors and radiation monitors.
  • a radiation monitor is a radiation measuring device used for various applications such as nuclear power plants, medical radiation examinations, and radiation therapy. Ionization chambers are widely used as radiation monitors due to their good stability and reproducibility. In particular, when measuring the radiation dose under the harsh environment of a nuclear power plant, it is preferable that it is small, does not require voltage application, and has excellent environmental resistance due to restrictions on the measurement location. Also, when measuring the radiation dose inside a patient's body during radiotherapy, it is preferable that the sensor is minimally invasive, and that a sensor that is small and does not require voltage application is preferable.
  • semiconductor detectors which are relatively easy to miniaturize, have been used to measure radiation dose.
  • semiconductor detectors are subjected to voltage application and are subject to severe restrictions on usage conditions from the standpoint of environmental resistance.
  • an optical fiber type radiation monitor uses a scintillator element as a sensor, transmits photons generated from the scintillator element through an optical fiber, and remotely measures the radiation dose.
  • the optical fiber type radiation monitor has a small sensor, does not require voltage application, and is excellent in environmental resistance such as radiation resistance and heat resistance. Therefore, the optical fiber type radiation monitor is suitable for measuring the radiation dose in the harsh environment of a nuclear power plant and for measuring the radiation dose inside a patient's body during radiotherapy.
  • Claim 1 of Patent Document 1 states, "A plurality of radiation detection units each having a radiation detection element that emits light upon incidence of radiation and a housing that accommodates the radiation detection element, and a radiation detector that emits light generated by the plurality of radiation detection elements. an optical transmission line for transmitting and combining light that has been added, a photodetector that converts the combined light guided to itself via the optical transmission line into an electric pulse, and based on the counting rate of the electric pulse, and an analysis unit that calculates a dose rate of radiation, wherein the plurality of housings includes at least one housing made of a first material, and another housing made of a second material. A radiation monitor comprising a housing.”
  • the end face of the radiation detection element on the optical fiber side is optically polished (paragraph 0023). This makes it easier for light to pass through the end face.
  • photons that are transmitted through the end face but do not reach the entrance of the optical fiber are not detected, resulting in lower detection sensitivity.
  • Such a problem becomes significant when the environment has a low dose rate, such as when used as an area monitor for a nuclear power plant or other radiation facility.
  • the problem to be solved by the present disclosure is to provide a detector and radiation monitor with excellent detection sensitivity.
  • the detector of the present disclosure includes a radiation-emitting material that generates photons corresponding to the dose of incident radiation, a sensor that has an exit-side end face from which the photons are emitted, and a sensor that scatters the photons generated by the sensor. a scatterer; and an optical fiber having an entrance facing the exit-side end face of the sensor and transmitting the photons scattered by the scatterer to a photoelectric converter through the entrance.
  • a detector and radiation monitor with excellent detection sensitivity can be provided.
  • FIG. 1 is a block diagram of a radiation monitor according to a first embodiment
  • FIG. FIG. 2 is a conceptual diagram for explaining the process of photon generation by radiation; It is a figure explaining the relationship between a dose rate and a photon count rate. It is a figure explaining the structure of the detector of 1st Embodiment. It is a figure explaining the conventional detector. It is a figure explaining the relationship between a photon count rate and an electric pulse count rate. It is a figure explaining the structure of the detector of 2nd Embodiment. It is a figure explaining the projection part of the optical fiber to the output side end face of a sensor. It is a figure explaining the structure of the detector of 3rd Embodiment. It is a figure explaining the structure of the detector of 4th Embodiment. It is a figure explaining the structure of the detector of 5th Embodiment. It is a figure explaining the structure of the detector of 6th Embodiment.
  • FIG. 1 is a block diagram of the radiation monitor 1 (optical fiber radiation monitor) of the first embodiment.
  • the radiation monitor 1 includes a detector 70 , a photoelectric converter 30 , a counting device 40 , an arithmetic device 50 and a display device 60 .
  • the detector 70 detects radiation R and generates photons P corresponding to the detected radiation dose.
  • Detector 70 comprises sensor 10 , scatterer 100 and optical fiber 20 .
  • the sensor 10 is made of a radiation-emitting material that generates photons P (single photons) corresponding to the dose of incident radiation R (eg, gamma rays, X-rays, etc.).
  • the sensor 10 includes a radiation-emitting element (not shown) made of, for example, a radiation-emitting material. Radiation R enters, for example, the radiation-emitting element, and photons P are generated in the radiation-emitting element. The generation of photons P causes luminescence (including fluorescence).
  • FIG. 2 is a conceptual diagram explaining the process of generating photons P by radiation R.
  • the energy of the radiation R causes electrons in the ground state (energy level L1) in the radiation-emitting material to transition to an excited state (energy level L3) with a higher energy level. (arrow a1).
  • An electron in a high energy level excited state (energy level L3) transitions to a low energy level excited state (energy level L2) (arrow b1).
  • Sensor 10 generates photons P having an energy corresponding to the energy difference between energy level L3 and energy level L2.
  • the radioluminescent material has, for example, a material such as transparent yttrium aluminum garnet (YAG) as a base material, and one or more of ytterbium, neodymium, cerium, praseodymium, etc. as an additive to this material. of rare earth elements. Having one or more rare earth elements can further improve the linearity between the dose rate of the radiation R incident on the sensor 10 and the photon count rate. Linearity will be described later with reference to FIG. Then, even when radiation R with a high dose rate is incident on the sensor 10, the linearity between the dose rate and the photon count rate can be maintained, and the measurement accuracy of the dose rate can be improved.
  • YAG transparent yttrium aluminum garnet
  • the radiation-emitting material may be, for example, a material represented by formula (1) below.
  • ATaO 4 :B Formula (1) A and B are rare earth elements having a 4f-4f electron transition, and at least one or more of Pr, Nd, Sm, Eu, Gd, Tb, Dy, Ho, Er, Tm, and Tb It is a rare earth element.
  • the mass of B representing the additive is preferably 1 ⁇ 10 ⁇ 3 mass % to 30 mass % with respect to the total mass of the radiation-emitting material. Thereby, the emission intensity of the sensor 10 can be improved.
  • the radioluminescent material represented by formula (1) contains rare earth elements with 4f-4f electron transitions due to the high density matrix ATaO 4 and additive B.
  • the energy imparted to the base material ATaO 4 by the incident radiation R can be used as excitation energy for the additive B with high efficiency.
  • the sensitivity of the sensor 10 can be improved.
  • the radiation dose of the radiation R incident on the sensor 10 and the number of photons P generated by the sensor 10 have linearity. That is, the dose rate of the radiation R incident on the sensor 10 and the number of photons per unit time generated by the sensor 10 (hereinafter referred to as "photon count rate”) have linearity.
  • FIG. 3 is a diagram explaining the relationship between the dose rate and the photon count rate.
  • the dose rate of the radiation R and the photon count rate have linearity (proportional relationship). This relationship is due to the fact that the lifetimes of the sensor 10, such as the luminescence lifetime and the fluorescence lifetime, are relatively long.
  • the lifetime of the sensor 10 is preferably, for example, 1 ⁇ s or longer, and when the radiation-emitting material is, for example, YAG:Nd, the lifetime is, for example, 230 ⁇ s.
  • FIG. 4 is a diagram explaining the structure of the detector 70 of the first embodiment.
  • the Z-axis is the central axis direction of the optical fiber 20, and the R-axis is an axis extending in a direction perpendicular to the Z-axis.
  • the sensor 10 has an emission-side end surface 102 from which the photons P are emitted.
  • the optical fiber 20 is arranged so that the entrance 201 faces the output end face 102 of the sensor 10, and transmits the photons P through the entrance 201 to the photoelectric converter 30 (FIG. 1).
  • the optical fiber 20 is made of quartz, plastic, or the like, for example.
  • the detector 70 includes a scatterer 100 that scatters the photons P generated by the sensor 10.
  • the sensor 10 comprises a scatterer 100 , which is arranged on the output end face 102 .
  • a photon P generated at a point S inside the sensor 10 travels toward the emission-side end surface 102 and reaches the emission-side end surface 102 .
  • the photons P reaching the output end face 102 are emitted from the output end face 102 after being scattered by the scatterer 100 and enter the optical fiber 20 through the entrance 201 . Therefore, optical fiber 20 transmits photons P scattered by scatterer 100 . Due to the scattering, the number of photons P reaching the entrance 201 of the optical fiber 20 from the exit facet 102 is increased, and the detection sensitivity can be improved.
  • the detector 70 has an air gap 200 between the output side end face 102 of the sensor 10 and the entrance 201 of the optical fiber 20 .
  • An air gap 200 is provided within the housing (not shown), for example, by spacing the sensor 10 and the optical fiber 20 within the housing (not shown). Since the air gap 200 in which air or the like exists has a small refractive index, the transmission angle ⁇ 1, which will be described later in detail, can be increased by once emitting the light from the exit-side end face 102 into the air gap 200 having a smaller refractive index.
  • the interior of void 200 may be a vacuum, and the internal pressure may be less than or greater than atmospheric pressure.
  • the exit-side end face 102 and the entrance 201 are normally arranged parallel to each other, and a gap 200 is provided between them.
  • the size of the air gap 200 that is, the distance between the exit-side end face 102 and the entrance 201, is not particularly limited as long as it is a distance capable of suppressing attenuation of the photons P, but can be, for example, 1 mm or less. .
  • FIG. 5 is a diagram illustrating a conventional detector 80.
  • FIG. Detector 80 shown in FIG. 5 and detector 70 of the present disclosure (FIG. 4) are the same except for the presence or absence of scatterers 100 and the presence or absence of air gaps 200 .
  • the angle ⁇ is 10.7° from equation (2). That is, photons P that enter the entrance 201 at an angle ⁇ exceeding 10.7° are not properly transmitted inside the optical fiber 20 . Therefore, in order to increase the transmission efficiency of the optical fiber 20, it is preferable to increase the numerical aperture NA of the optical fiber 20 or decrease the refractive index n of the sensor 10 according to Equation (2). Furthermore, it is also preferable to increase the core diameter of the optical fiber 20 itself.
  • the transmittable angle ⁇ can be calculated at an arbitrary point on the sensor 10.
  • the emission probability of the photons P is equal, and the emission direction is, for example, isotropic. can.
  • the transmission probability of the photon P can be calculated by summing up all transmission probabilities at each point in the sensor 10 (volume integration). Specifically, when the shape of the sensor 10 is cylindrical with a diameter of 3 mm and a length of 3 mm, the refractive index n is 2.0, the core diameter of the optical fiber 20 is 400 ⁇ m, and the numerical aperture NA is 0.37, the transmission probability is 1.5 ⁇ 10 ⁇ 4 , which is a very small value. Therefore, in the prior art, the main reason for the very low transmission probability is the narrow angle ⁇ determined by the index of refraction of the sensor 10 .
  • the detector 70 of the present disclosure includes a scatterer 100.
  • the photons P can be scattered and the probability of the photons P reaching the entrance 201 can be improved.
  • the number of photons P incident at an angle of ⁇ or less can be increased, so that the detection sensitivity of the detector 70 can be improved.
  • the air gap 200 it is possible to increase the angle ⁇ 1, which is the incident angle to the entrance 201 through which light can propagate through the optical fiber 20.
  • ⁇ 1 is the incident angle to the entrance 201 through which light can propagate through the optical fiber 20.
  • the numerical aperture NA of the optical fiber 20 is 0.37
  • the refractive index of air is 1.0. °, doubling over the prior art.
  • the detection sensitivity of the detector 70 can be improved.
  • the transmission probability is 2.3 ⁇ 10 ⁇ 4 , which is the transmission probability of the prior art. It is 1.5 times 5 ⁇ 10 ⁇ 4 .
  • the scatterer 100 is arranged, for example, on the exit-side end surface 102 of the sensor 10 as described above. By arranging at this position, the scatterer 100 can be arranged by, for example, surface processing of the exit-side end face 102, so that the scatterer 100 can be arranged easily. Moreover, the effect of the scatterer 100 can be improved, and the characteristics of the scatterer 100 can be easily controlled. These allow the detector 70 and the radiation monitor 1 to be manufactured at low cost.
  • the surface processing includes, for example, scratching with a width capable of generating Rayleigh scattering, which will be described later, and the formed shape is, for example, grooves, unevenness, and the like.
  • the scatterer 100 is, for example, a scatterer that produces isotropic scattering.
  • isotropic scattering the probability of arrival at the entrance 201 and the probability of transmission of the photons P through the optical fiber 20 can be improved, and the detection sensitivity of the radiation monitor 1 can be further improved.
  • the scattering in the scatterer 100 is preferably isotropic. Therefore, a Rayleigh scattering capable scatterer 100 that scatters isotropically is preferred. Rayleigh scattering is scattering by particles much smaller than the wavelength of light. Thus, in another embodiment, the scatterer 100 is composed of particles smaller than the wavelength of the photons P generated by the sensor 10, for example.
  • the scatterer 100 is made of, for example, a polycrystal. Particles may be formed by surface processing. As a result, Rayleigh scattering can occur, and photons P can be isotropically scattered.
  • the wavelength is about 550 nm
  • the particles of the scatterer 100 should be sufficiently smaller than 550 nm. Therefore, it is preferable that the particles forming the scatterer 100 have a particle size of sub- ⁇ m or less.
  • the particle size can be measured by X-ray diffraction, and not all particles are necessarily smaller than the wavelength of light. Therefore, in the case of green photons P, the scatterer 100 may contain particles crushed to 550 nm or less, for example. Further, by confirming whether the particles are scattered isotropically, it can be determined whether or not the particles are smaller than the wavelength of the photons P.
  • the scatterer 100 is composed of particles smaller than the wavelength of the photons P, it is not necessary. That is, even a particle larger than the wavelength of the photon P has the effect of scattering to some extent.
  • the photoelectric converter 30 converts the photons P generated by the detector 70 into electrical signals (hereinafter referred to as electrical pulses). Photons P generated at 10 are transmitted to photoelectric converter 30 through optical fiber 20 . The photoelectric converter 30 converts each photon P transmitted by the optical fiber 20 into each electrical pulse. Therefore, the photoelectric converter 30 emits one electrical pulse corresponding to one photon P.
  • electrical pulses electrical signals
  • FIG. 6 is a diagram explaining the relationship between the photon count rate and the electrical pulse count rate.
  • the number of photons generated by the sensor 10 and the number of electrical pulses transmitted by the photoelectric converter 30 have linearity (proportional relationship).
  • the photon counting rate and the number of electrical pulses per unit time (electrical pulse counting rate) transmitted by the photoelectric converter 30 have linearity as shown in FIG. Therefore, the electric pulse coefficient rate can be uniquely calculated based on the photon coefficient rate.
  • the photoelectric converter 30 for example, a photomultiplier tube, an avalanche photodiode, or the like can be used. By using these, the photon P can be converted into an amplified electric pulse.
  • the counting device 40 counts the electric pulses (electric signals) converted by the photoelectric converter 30 and outputs the count value of the electric pulses.
  • the counting device 40 is connected to the photoelectric converter 30 by an electrical signal line (not shown).
  • the counting device 40 counts the electrical pulses emitted by the photoelectric converter 30 and outputs the count value of the electrical pulses (the number of electrical pulses) counted by the counting device 40 .
  • the computing device 50 computes the result of computing at least one of the radiation dose and the dose rate based on the count value of the electrical pulses (electrical signals) in the counting device 40 .
  • the computing device 50 is connected to the counting device 40 by an electric signal line (not shown).
  • the computing device 50 holds a relationship (for example, a relational expression, etc.) between a count value of electrical pulses (which may be an electrical pulse count rate) corresponding one-to-one and a radiation dose or a dose rate. This relationship is preset.
  • the computing device 50 is, for example, a CPU (Central Processing Unit), although not shown. , RAM (Random Access Memory), ROM (Read Only Memory), and the like. Arithmetic device 50 is embodied by developing a predetermined control program stored in ROM into RAM and executing it by the CPU.
  • CPU Central Processing Unit
  • RAM Random Access Memory
  • ROM Read Only Memory
  • the display device 60 displays the calculation result of at least one of radiation amount and dose rate.
  • the display device 60 is connected to the arithmetic device 50 by electrical signal lines (not shown).
  • the display device 60 also displays an abnormality of the sensor 10 and the like.
  • the arrival probability of the photons P to the entrance 201 of the optical fiber 20 and the transmission probability in the optical fiber 20 can be improved, and the detection sensitivity of the radiation monitor 1 can be improved.
  • improvement of the SN ratio, shortening of measurement time, and the like can be mentioned.
  • the radiation monitor 1 is provided with a plurality of detectors 70 to shorten the measurement time, and multi-channel measurement can be performed by switching the detectors 70 to be used.
  • FIG. 7A is a diagram explaining the structure of the detector 71 of the second embodiment.
  • Detector 71 is the same as detector 70 (FIG. 4) except that it has a portion of emission-side end face 102 that does not have scatterer 100 .
  • FIG. 7B is a diagram for explaining the projected portion of the optical fiber 20 onto the exit-side end face 102 of the sensor 10.
  • the scatterer 100 is detected on the output side end surface 102 of the sensor 10 other than the portion where the entrance 201 of the optical fiber 20 is projected onto the output side end surface 102 as indicated by the dashed line in FIG. 7B. 102.
  • the projected portion of the entrance 201 can be incident on the entrance 201 of the optical fiber 20 as it is without being scattered, and the incidence probability of the entrance 201 of the optical fiber 20 is caused by scattering from other portions. can be improved.
  • FIG. 8 is a diagram explaining the structure of the detector 72 of the third embodiment.
  • Detector 72 is similar to detector 70 except that the installation location of scatterer 100 is different from detector 70 (FIG. 4).
  • the scatterer 100 is arranged inside the sensor 10 so as to include at least the emission-side end face 102 of the sensor 10 . As a result, the photons P generated within the sensor 10 can be scattered, and the thickness of the scatterer 100 can be controlled.
  • the scatterers 100 are arranged over the entire sensor 10 .
  • the photons P generated at arbitrary positions on the entire sensor 10 can be rapidly scattered.
  • the scatterer 100 is composed of, for example, a polycrystal of a radiation-emitting material. Accordingly, the sensor 10 is composed of a scatterer 100 composed of a radioactive luminescent material. As a result, the sensor 10 and the scatterer 100 can be easily formed by changing the crystal growth conditions, so that the manufacturing cost can be reduced.
  • the scatterer 100 is composed of a single crystal of radiation-emitting material with crystal defects. Since a single crystal having crystal defects can be easily manufactured, the sensor 10 and the scatterer 100 can be easily formed, and manufacturing costs can be reduced.
  • the scatterer 100 is composed of a single crystal of radiation-emitting material with impurities. Since the physical properties of the scatterer 100 can be controlled by the physical properties of the impurities, the physical properties of the scatterer 100 that also serves as the sensor 10 can be easily controlled.
  • FIG. 9 is a diagram explaining the structure of the detector 73 of the fourth embodiment.
  • Detector 73 is similar to detector 72 except that the arrangement ratio of scatterers 100 to the entire sensor 10 is different from detector 72 (FIG. 8).
  • the scatterer 100 is arranged in a part inside the sensor 10 so as to include the emission-side end face 102.
  • the photons P can be incident on the scatterer 100 without being scattered by the parts of the sensor 10 other than the scatterer 100 , so that the photons P can be scattered at the part near the emission-side facet 102 .
  • the scattered photons P can be efficiently emitted from the emission-side facet 102 .
  • FIG. 10 is a diagram explaining the structure of the detector 74 of the fifth embodiment.
  • Detector 74 is similar to detector 70 (FIG. 2) except that it does not include air gap 200 (FIG. 2).
  • the exit-side end face 102 of the sensor 10 and the entrance 201 of the optical fiber 20 are in contact.
  • the sensor 10 and the optical fiber 20 can be arranged in contact with each other, so that the size of the detector 74 can be reduced.
  • the scatterer 100 arranged on the exit-side facet 102 and the entrance 201 are in contact with each other.
  • FIG. 11 is a diagram explaining the structure of the detector 75 of the sixth embodiment.
  • Detector 75 is similar to detector 73 (FIG. 9) except that it includes reflector 103 .
  • the detector 75 includes a reflector 103 that reflects the photons P so as to cover the portion of the sensor 10 other than the emission-side end surface 102 .
  • the reflector 103 By installing the reflector 103 on, for example, the side surface and the top surface that do not face the optical fiber 20, the photons P that were conventionally dispersed can be reflected. As a result, the photons P that are not directed toward the emission-side end face 102 are allowed to stay inside the scatterer 100, and the probability of incidence on the optical fiber 20 can be improved.
  • the reflecting material 103 may be any material as long as it can transmit the radiation R but not the photons P and can reflect the radiation, and is, for example, a plate or foil of silver, aluminum, or the like.
  • Radioelectric Monitor 10 Sensor 100 Scattering Body 102 Output Side End Face 103 Reflector 20 Optical Fiber 200 Air Gap 201 Entrance 30 Photoelectric Converter 40 Counting Device 50 Arithmetic Device 60 Display Device 70 Detector 71 Detector 72 Detector 73 Detector 74 Detection detector 75 detector 80 detector a1 arrow 1 arrow L1 energy level L2 energy level L3 energy level P photon R radiation S point ⁇ angle ⁇ 1 angle

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
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  • High Energy & Nuclear Physics (AREA)
  • Molecular Biology (AREA)
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  • Measurement Of Radiation (AREA)

Abstract

L'invention concerne un dispositif de surveillance de rayonnement présentant une sensibilité de détection supérieure. Un dispositif de surveillance de rayonnement (1) comprend : un détecteur (70) qui détecte un rayonnement et génère des photons correspondant à une dose de rayonnement détectée ; un convertisseur photoélectrique (30) qui convertit les photons générés par le détecteur (70) en un signal électrique ; un dispositif de comptage (40) qui compte le signal électrique converti par le convertisseur photoélectrique (30) et délivre une valeur de comptage du signal électrique ; un dispositif de calcul (50) qui calcule, sur la base de la valeur de comptage du signal électrique, au moins un résultat de calcul de la dose de rayonnement et un débit de dose ; et un dispositif d'affichage (60) qui affiche le résultat de calcul. Le détecteur (70) comprend : un capteur (10) configuré à partir d'un matériau radioluminescent qui génère des photons correspondant à la dose de rayonnement du rayonnement incident ; un dispositif de dispersion (100) qui disperse les photons générés par le capteur (10) ; et une fibre optique (20) qui transmet les photons au convertisseur photoélectrique (30) à travers un orifice d'entrée de la fibre optique (20).
PCT/JP2022/004405 2021-04-23 2022-02-04 Détecteur et dispositif de surveillance de rayonnement WO2022224541A1 (fr)

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JP2021073504A JP2022167602A (ja) 2021-04-23 2021-04-23 検出器及び放射線モニタ

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Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2003098259A (ja) * 2001-09-27 2003-04-03 Nihon Medi Physics Co Ltd 放射線検出器
US20150153462A1 (en) * 2012-06-21 2015-06-04 Siemens Aktiengesellschaft Scintillator Plate
JP2019039812A (ja) * 2017-08-25 2019-03-14 東京電力ホールディングス株式会社 シンチレータ

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2003098259A (ja) * 2001-09-27 2003-04-03 Nihon Medi Physics Co Ltd 放射線検出器
US20150153462A1 (en) * 2012-06-21 2015-06-04 Siemens Aktiengesellschaft Scintillator Plate
JP2019039812A (ja) * 2017-08-25 2019-03-14 東京電力ホールディングス株式会社 シンチレータ

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