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WO2017038133A1 - Détecteur de rayonnement et module détecteur - Google Patents

Détecteur de rayonnement et module détecteur Download PDF

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Publication number
WO2017038133A1
WO2017038133A1 PCT/JP2016/059501 JP2016059501W WO2017038133A1 WO 2017038133 A1 WO2017038133 A1 WO 2017038133A1 JP 2016059501 W JP2016059501 W JP 2016059501W WO 2017038133 A1 WO2017038133 A1 WO 2017038133A1
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WIPO (PCT)
Prior art keywords
light receiving
microcell
receiving element
scintillator
light
Prior art date
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Ceased
Application number
PCT/JP2016/059501
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English (en)
Japanese (ja)
Inventor
淳一 大井
倫明 津田
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Shimadzu Corp
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Shimadzu Corp
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Priority to JP2017537565A priority Critical patent/JP6508343B2/ja
Publication of WO2017038133A1 publication Critical patent/WO2017038133A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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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
    • G01T1/16—Measuring radiation intensity
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • 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

Definitions

  • the present invention relates to a radiation detector and a detector module used in a nuclear medicine diagnostic apparatus such as a positron emission tomography apparatus (PET apparatus).
  • a nuclear medicine diagnostic apparatus such as a positron emission tomography apparatus (PET apparatus).
  • PET apparatus nuclear medicine diagnosis using positron emission tomography
  • PET apparatus is an apparatus that generates a radiographic image showing a distribution of a radiopharmaceutical labeled with a positron emission nuclide in a subject.
  • the PET apparatus includes a plurality of radiation detectors arranged so as to surround the subject in a ring shape.
  • the radiopharmaceutical administered to the subject is accumulated at the site of interest, and positrons are released from the accumulated drug.
  • the emitted positron causes pair annihilation with the electron, and generates a pair of ⁇ rays having diametrically opposite momentum.
  • a pair of gamma rays are emitted in opposite directions, and each gamma ray is detected simultaneously by the radiation detector.
  • the position of the radiopharmaceutical is calculated based on the detected ⁇ -ray information, and a radiographic image showing the distribution of the radiopharmaceutical in the region of interest is provided by the PET apparatus.
  • the radiation detector includes a scintillator that absorbs radiation and converts it into light, and a photodetector that uses SiPM (Silicon Photo Multiplier) or the like.
  • SiPM has a configuration in which a large number of APDs (Avalanche Photo Diode) are disposed as light receiving elements (photoelectric conversion elements), and is hardly affected by a magnetic field. For this reason, SiPM can be used as a photodetector for PET-MR in which a magnetic resonance tomography apparatus (MR apparatus) suitable for anatomical diagnosis and a PET apparatus suitable for physiological function diagnosis are combined (for example, patents). Reference 1).
  • MR apparatus magnetic resonance tomography apparatus
  • the conventional radiation detector 101 is configured by optically joining a scintillator 103 and a SiPM 105 as a photodetector.
  • the scintillator 103 interacts with ⁇ rays and generates a large number of photons (photons).
  • the SiPM 105 receives photons generated from the scintillator 103 and converts them into electrical signals.
  • a large number of radiation detectors 101 are arranged in a one-dimensional matrix or a two-dimensional matrix to constitute a detector module 101a.
  • the SiPM 105 has a large number of microcells 107 arranged in a two-dimensional matrix.
  • each microcell 107 is provided with an APD 109 that is a photoelectric conversion element and a quenching resistor 111. That is, when a photon is incident on the APD 109, the photon is converted into an electric signal and output from the SiPM 105 as a ⁇ -ray detection signal.
  • a region where the APD 109 is provided is a light receiving region 107a.
  • Each of the radiation detectors 101 includes a power source 121, a preamplifier 113, a comparator 115, and a shaping amplifier 117, as shown in FIGS. 11 (a) and 11 (b).
  • the power supply 121 applies a bias voltage V required for outputting a ⁇ -ray detection signal to each of the microcells 107 provided in the photodetector 105.
  • the preamplifier 113 is provided downstream of the SiPM 105 and amplifies an output signal from the SiPM 105 and converts it into a voltage.
  • the comparator 115 and the shaping amplifier 117 are connected to the preamplifier 113, respectively. One of the amplified and converted output signals is input to the comparator 115, and the other output signal is input to the shaping amplifier 117.
  • the comparator 115 derives information on the time when the ⁇ -ray is detected as timing information based on the input output signal. That is, an electrical signal indicating timing information is output based on the time when the photon detection amount in the microcell 107 exceeds a predetermined threshold value set in advance.
  • the shaping amplifier 117 further amplifies and shapes the input output signal to obtain a pulse having a wave height proportional to the energy of the incident ⁇ -ray. Based on the pulse height obtained by the shaping amplifier 117, information on the detected energy level of the ⁇ -ray is output as energy information.
  • the configuration is such that the output signal is transmitted to the comparator 115 and the shaping amplifier 117, respectively, and in each of the radiation detectors 101, the time information (timing information) when the ⁇ -rays are detected and the energy information of the detected ⁇ -rays.
  • timing information for example, refer nonpatent literatures 1 and 2.
  • the radiation detector 101 is often used for a TOF type (detection time difference: Time Of Flight) PET apparatus. For this reason, in the radiation detector 101, there is an increasing demand for further improving the resolution of timing information (timing resolution).
  • the pulse height of the signal output from the SiPM 105 does not change depending on the number of photons incident on one microcell 107. Therefore, in order to maintain the linearity between the number of photons incident on the SiPM 105 and the pulse wave height output from the SiPM 105, it is necessary to increase the number of microcells 107 provided in the SiPM 105. That is, by increasing the number of microcells 107, it is possible to avoid a plurality of photons from entering the same microcell 107 at the same time, so that the linearity between the number of incident photons and the output can be suitably maintained. As a result, the energy resolution in the radiation detector 101 can be improved.
  • the pitch of the microcells 107 is reduced in the conventional radiation detector 101 to increase the number of microcells 107 per unit area, there is a concern that the timing resolution is lowered. That is, in each of the microcells 107, the peripheral edge 107b of the light receiving region 107a is provided with a partition wall, so that the peripheral edge 107b of the microcell 107 becomes a photon insensitive part. Then, as the number of microcells 107 provided in the SiPM 105 increases, the area of the light receiving region 107a decreases on the light detection surface (xy plane) of the SiPM 105, so that the photon detection efficiency (PDE) of the SiPM 105 decreases.
  • PDE photon detection efficiency
  • the fluctuation of the time from when the photon is generated in the scintillator 103 until the photon reaches the microcell 107 and the photon detection amount exceeds a predetermined threshold is important. Therefore, when the photon detection efficiency of the SiPM 105 is lowered, the time resolution until the photon detection amount exceeds the predetermined threshold value is increased, so that the timing resolution of the radiation detector 101 is lowered.
  • the number of microcells 107 per unit area decreases. To do. In this case, since the probability that two or more photons simultaneously enter the same microcell 107 increases, the linearity between the number of incident photons and the output deteriorates. As a result, the energy resolution in the radiation detector 101 is lowered.
  • the present invention has been made in view of such circumstances, and can be used for a PET apparatus such as a TOF-PET apparatus.
  • the radiation detector and the detector have high energy resolution and high timing resolution.
  • the purpose is to provide modules.
  • the present invention has the following configuration. That is, the radiation detector according to the present invention includes at least one scintillator that detects incident radiation and emits light, and includes a first light receiving element and a second light receiving element that convert light emitted from the scintillator into an electrical signal.
  • Each of which is arranged in a matrix and is optically coupled to the scintillator, and a time for which the radiation is incident on the scintillator based on an electrical signal converted by the first light receiving element
  • a timing information acquisition circuit that acquires timing information that is information
  • an energy information acquisition circuit that acquires energy information that is information related to the energy of the radiation incident on the scintillator based on the electrical signal converted by the second light receiving element
  • Each of the scintillators includes at least one first light receiving element. And it is characterized in that at least one respectively optically coupled to the second light receiving element.
  • the light detection means includes the first light receiving element and the second light receiving element that convert the light emitted from the scintillator into an electric signal.
  • the timing information acquisition circuit acquires timing information based on the electrical signal of the first light receiving element, and the energy information acquisition circuit acquires energy information based on the electrical signal of the second light receiving element.
  • Each of the scintillators is optically coupled to each of at least one first light receiving element and at least one second light receiving element. That is, after the radiation incident on the scintillator is converted into light, a part of the radiation becomes timing information via the first light receiving element, and the remaining part becomes energy information via the second light receiving element.
  • a first light receiving element that is a light receiving element for timing information income and a second light receiving element that is a light receiving element for acquiring energy information are provided separately.
  • the present invention may take the following configurations. That is, in the radiation detector according to the present invention, at least one scintillator that detects incident radiation and emits light, and a first light receiving element that converts light emitted from the scintillator into an electrical signal are arranged in a matrix.
  • At least one first light detecting means optically coupled to the scintillator, and second light receiving elements for converting the light emitted from the scintillator into an electric signal, arranged in a matrix, and the scintillator Timing information for acquiring timing information, which is information related to the time when the radiation is incident on the scintillator, based on an electrical signal converted by the first light receiving element and at least one second light detection unit optically coupled The radiation incident on the scintillator based on the acquisition circuit and the electrical signal converted by the second light receiving element
  • An energy information acquisition circuit for acquiring energy information that is information relating to the energy of each of the scintillators, wherein each of the scintillators is optically coupled to each of at least one of the first light receiving elements and at least one of the second light receiving elements. It is characterized by
  • the first light detecting means includes the first light receiving element
  • the second light detecting means includes the second light receiving element.
  • the timing information acquisition circuit acquires timing information based on the electrical signal of the first light receiving element
  • the energy information acquisition circuit acquires energy information based on the electrical signal of the second light receiving element.
  • Each of the scintillators is optically coupled to each of at least one first light receiving element and at least one second light receiving element. That is, after the radiation incident on the scintillator is converted into light, a part of the radiation becomes timing information via the first light receiving element, and the remaining part becomes energy information via the second light receiving element.
  • a first light receiving element that is a light receiving element for timing information income and a second light receiving element that is a light receiving element for acquiring energy information are provided separately.
  • the first light detecting means including the first light receiving element and the second light detecting means including the second light receiving element have different configurations. For this reason, the existing light detection means having a specification that improves the timing resolution is used as the first light detection means, and the existing light detection means that has another specification that improves the energy resolution is the second light detection. Each can be used as a means. That is, since it is not necessary to newly manufacture a light detection means including the first light receiving element and the second light receiving element, the radiation detector according to the present invention can be manufactured more easily.
  • a first bias voltage supply power source that applies a first bias voltage to the first light receiving element, and a first bias voltage that is lower than the first bias voltage for the second light receiving element. It is preferable to provide a second bias voltage supply power source that applies
  • the first bias voltage supply power supply applies the first bias voltage to the first light receiving element.
  • the second bias voltage supply power supply applies a second bias voltage lower than the first bias voltage to the second light receiving element.
  • a first bias voltage which is a relatively high voltage is applied to the first light receiving element.
  • a second bias voltage lower than the first bias voltage is applied to the second light receiving element.
  • the bias voltage is lowered, the energy resolution obtained from the light receiving element is improved. Therefore, higher-resolution energy information can be acquired based on the electrical signal output from the second light receiving element for acquiring energy information.
  • the area of the light receiving region per unit area of the first light receiving element is larger than the area of the light receiving region per unit area of the second light receiving element.
  • the area of the light receiving region per unit area of the first light receiving element is larger than the area of the light receiving region per unit area of the second light receiving element. Configured. By increasing the area of the light receiving region per unit area, the timing resolution acquired from the light receiving element is improved. Therefore, higher-resolution timing information can be acquired based on the electrical signal output from the first light receiving element for acquiring timing information.
  • the area of the second light receiving element on the light detecting surface of the light detecting means is 2% to 40% of the area of the first light receiving element on the light detecting surface of the light detecting means. Is preferred.
  • the area of the second light receiving element on the light detecting surface of the light detecting means is 2% to the area of the first light receiving element on the light detecting surface of the light detecting means. 40%.
  • the timing resolution acquired using the first light receiving element is suitably improved while maintaining the energy resolution acquired using the second light receiving element. Therefore, more accurate information can be acquired about the radiation incident on the radiation detector.
  • a detector module in which a plurality of radiation detectors according to the present invention are arranged in a one-dimensional direction or a two-dimensional direction.
  • a detector module has the effect of the radiation detector according to the present invention, and it is possible to preferably improve both the timing resolution and the energy resolution. Therefore, by applying such a detector module to various PET apparatuses, particularly TOF-PET, both energy resolution and timing resolution can be improved.
  • a more appropriate diagnosis can be performed by acquiring a radiographic image that more accurately displays the distribution of the radiopharmaceutical.
  • the light detection means includes the first light receiving element and the second light receiving element that convert light emitted from the scintillator into an electric signal.
  • the timing information acquisition circuit acquires timing information based on the electrical signal of the first light receiving element, and the energy information acquisition circuit acquires energy information based on the electrical signal of the second light receiving element.
  • Each of the scintillators is optically coupled to each of at least one first light receiving element and at least one second light receiving element. That is, after the radiation incident on the scintillator is converted into light, a part of the radiation becomes timing information via the first light receiving element, and the remaining part becomes energy information via the second light receiving element.
  • a first light receiving element that is a light receiving element for timing information income and a second light receiving element that is a light receiving element for acquiring energy information are provided separately.
  • FIG. 1 is a diagram illustrating an overall configuration of a radiation detector according to Embodiment 1.
  • FIG. (A) is an overhead view showing the overall configuration of the radiation detector
  • (b) is an overhead view showing the overall configuration of a detector module configured by arranging the radiation detectors in a matrix
  • FIG. 2 is a longitudinal sectional view showing an overall configuration of a PET apparatus configured using a detector module.
  • 1 is a diagram illustrating a configuration of a photodetector according to Embodiment 1.
  • FIG. (A) is a top view which shows the structure of a photodetector
  • (b) is a figure which shows the structure of a microcell.
  • FIG. 3 is a plan view illustrating an example of an arrangement pattern of microcells for the radiation detector according to the first embodiment.
  • A is a diagram showing a pattern in which microcells 15b are arranged in a one-dimensional direction
  • (b) is a diagram showing a pattern in which microcells 15b are densely arranged in a two-dimensional matrix
  • (c) is a diagram. It is a figure which shows the pattern which the microcell 15a and the microcell 15b disperse
  • FIG. 10 is a plan view showing an example of an arrangement pattern of microcells for the radiation detector according to the second embodiment.
  • (A) is a diagram showing a pattern in which microcells 15b are arranged in a one-dimensional direction
  • (b) is a diagram showing a pattern in which microcells 15b are densely arranged in a two-dimensional matrix
  • (c) is a diagram. It is a figure which shows the pattern which the microcell 15a and the microcell 15b disperse
  • FIG. (A) is a bird's-eye view showing a configuration in which the same bias voltage is applied to each microcell
  • (b) is a circuit diagram showing a configuration in which the same bias voltage is applied to each microcell.
  • FIG. 6 is a diagram illustrating a configuration of a radiation detector according to a third embodiment.
  • FIG. (A) is a bird's-eye view showing the overall configuration of the radiation detector
  • (b) is a diagram showing an example of an array pattern in which the pitch length of the microcell 15a is the same as the pitch length of the microcell 15b
  • c) is a diagram showing an example of an arrangement pattern in which the pitch length of the microcells 15a is longer than the pitch length of the microcells 15b. It is a figure which shows the structure which changes a specification with respect to each microcell about the radiation detector which concerns on Example 3.
  • FIG. (A) is a bird's-eye view showing a configuration in which a different bias voltage is applied to each microcell
  • (b) is a circuit diagram showing a configuration in which a different bias voltage is applied to each microcell.
  • FIG. 4 is a plan view showing an example of an arrangement pattern of microcells. It is a figure which shows the whole structure of the radiation detector which concerns on a prior art example.
  • A) is an overhead view showing the overall configuration of the radiation detector
  • (b) is an overhead view showing the overall configuration of a detector module configured by arranging the radiation detectors in a matrix
  • FIG. 4 is a plan view showing a configuration of a photodetector in which microcells are arranged
  • 4D is a diagram showing a configuration of microcells. It is a figure which shows the structure of the radiation detector which concerns on a prior art example.
  • (A) is a bird's-eye view showing a configuration for applying a bias voltage to each microcell
  • (b) is a circuit diagram showing a configuration for applying a bias voltage to each microcell.
  • Embodiment 1 of the present invention will be described below with reference to the drawings.
  • the radiation detector 1 is configured by optically joining a scintillator 3 and a photodetector 5.
  • the scintillator 3 is composed of LYSO, LFS, or the like, and generates a large number of photons by interaction with incident ⁇ rays.
  • the photodetector 5 detects photons generated from the scintillator 3 and converts them into electrical signals.
  • the light detector 5 corresponds to the light detecting means in the present invention.
  • An example of the photodetector 5 is SiPM configured by arranging light receiving elements in a matrix.
  • the first embodiment will be described using SiPM as the photodetector 5.
  • a detector module 2 is configured by arranging a large number of radiation detectors 1 on a substrate 6 in a one-dimensional direction or a two-dimensional direction.
  • the configuration of the PET apparatus 7 including the radiation detector 1 according to the first embodiment is as shown in FIG. That is, the PET apparatus 7 includes a gantry 11 provided with an introduction hole 9 for introducing a subject.
  • a housing 13 is provided inside the gantry 11. Inside the housing 13, the detector modules 2 are arranged in a ring shape so as to surround the introduction hole 9.
  • Each of the radiation detectors 1 and the housing 13 are connected by a connection base 14.
  • the direction from the center Mo of the introduction hole 9 toward the detection surface (xy plane) of the detector module 2 is the incident direction of ⁇ rays.
  • the number of detector modules 2 arranged in a ring shape in FIG. 1C is eight, the number of detector modules 2 forming the ring structure may be changed as appropriate.
  • the PET device 7 to which the radiation detector 1 is applied various types of PET devices such as TOF-PET and PET-MR can be used in addition to a normal PET device.
  • the SiPM used as the photodetector 5 has a large number of microcells 15 arranged in a two-dimensional matrix.
  • Each microcell 15 includes an APD 17 and a quenching resistor 19 as shown in FIG.
  • the APD 17 is a photoelectric conversion element that converts light into electrical information.
  • the APD 17 detects photons incident on the microcell 15 and converts them into electrical signals.
  • the microcell 15 corresponds to the light receiving element in the present invention.
  • a region where the APD 17 occupies and can detect photons is a light receiving region F.
  • a partition wall made of a photon insensitive material is provided on the peripheral edge of the light receiving region F.
  • a region where such a partition is provided is defined as a dead region N.
  • the radiation detector 1 is a microcell 15 that acquires information (timing information) about the time when ⁇ rays are incident on one scintillator 3, and a micro that acquires information (energy information) about the energy of the incident ⁇ rays.
  • the cell 15 is separated from the cell 15.
  • the detection surface of the photodetector 5 is arranged so that microcells 15a used for acquiring timing information and microcells 15b used for acquiring energy information coexist.
  • the microcell 15a distinguishes the light receiving area F by indicating the light receiving area F by halftone dots
  • the microcell 15b distinguishes the light receiving area F by hatching.
  • Each of the microcells 15a corresponds to a first light receiving element in the present invention
  • each of the microcells 15b corresponds to a second light receiving element in the present invention.
  • the arrangement pattern of the microcells 15a and 15b on the detection surface of the photodetector 5 is not limited to the pattern shown in FIG. That is, as shown in FIG. 3B, the microcells 15a may be densely arranged at an appropriate position such as the central region of the photodetector 5. Further, as shown in FIG. 3C, a configuration may be adopted in which each of the microcells 15a and each of the microcells 15b is dispersed over the entire photon detection surface of the photodetector 5.
  • the total area of the microcells 15b is preferably 2% to 40%, more preferably 3% to 30% of the total area of the microcells 15a.
  • the most preferable example is about 10%.
  • the total area of the microcells 15b is about 10% of the total area of the microcells 15a.
  • the radiation detector 1 further includes a first power source 21, a second power source 23, a first preamplifier 25, a second preamplifier 27, a comparator 29, and the like. And a shaping amplifier 31.
  • the first power supply 21 and the second power supply 23 are voltage supply power supplies for applying a bias voltage.
  • the first power supply 21 applies a bias voltage V1 to each of the microcells 15a.
  • the first power supply 23 applies a bias voltage V2 to each of the microcells 15b.
  • the height of the bias voltage V1 is adjusted to be higher than the height of the bias voltage V2.
  • the first power supply 21 corresponds to the first bias voltage supply power supply in the present invention.
  • the second power source 23 corresponds to the second bias voltage supply power source in the present invention.
  • the bias voltage V1 corresponds to the first bias voltage in the present invention.
  • the bias voltage V2 corresponds to the second bias voltage in the present invention.
  • the first preamplifier 25 is connected to the microcell 15a and amplifies the output signal from the microcell 15a and converts it into a voltage.
  • the second preamplifier 27 is connected to each of the microcells 15b, and amplifies the signal output from each of the microcells 15b and converts it into a voltage.
  • the comparator 29 is connected to the first preamplifier 25 and outputs timing information based on the output signal amplified and converted by the first preamplifier 25. That is, the timing information is output from the comparator 29 based on the time when the photon detection amount in the microcell 15a exceeds the predetermined threshold.
  • the first preamplifier 25 and the comparator 29 correspond to the timing information acquisition circuit in the present invention.
  • the shaping amplifier 31 is connected to the second preamplifier 27, and outputs energy information based on the output signal amplified and converted by the second preamplifier 27. That is, by further amplifying and shaping the output signal of the second preamplifier 27, a pulse having a wave height proportional to the energy of photons incident on the microcell 15b is obtained. Based on the pulse height of the pulse acquired by the shaping amplifier 31, information relating to the energy level of the ⁇ rays incident on the scintillator 3 is output from the shaping amplifier 31 as energy information.
  • the second preamplifier 27 and the shaping amplifier 31 correspond to the energy information acquisition circuit in the present invention.
  • Each of the timing information and energy information obtained for one scintillator 3 is transmitted to a coincidence circuit (not shown). That is, timing information and energy information in each scintillator 3 provided in each detector module 2 is transmitted to the coincidence circuit. Further, the position information of the scintillator 3 that outputs timing information and energy information is also transmitted to the coincidence circuit.
  • the coincidence circuit detects position information of ⁇ -ray electron pairs generated by the pair annihilation of the same positrons based on timing information, energy information, and position information related to all scintillators 3 provided in the PET apparatus 7. . Then, based on the position information of the ⁇ -ray electron pair, a radiographic image that displays the distribution of the radiopharmaceutical is generated.
  • the radiation detector 1 includes the microcell 15a used for outputting the timing information and the microcell 15b used for outputting the energy information. Therefore, different standards (specifications) can be set for each of the microcells 15a and each of the microcells 15b.
  • the microcell 15a can be set to a predetermined specification that improves the timing resolution
  • the microcell 15b can be set to another specification that improves the energy resolution.
  • the radiation detector 1 is configured to improve both timing resolution and energy resolution by setting bias voltages to be applied to different heights. That is, among the plurality of microcells 15 optically coupled to one scintillator 3, a bias voltage V ⁇ b> 1 that is a relatively high voltage is applied to each of the microcells 15 a used for acquiring timing information by the first power supply 21. The On the other hand, a bias voltage V2, which is a relatively low voltage, is applied to each of the microcells 15b used for acquiring energy information by the second power source 23.
  • the photon detection efficiency PDE
  • the timing resolution acquired by the microcell 15a is improved by applying the high bias voltage V1 to the microcell 15a.
  • the microcell 15a is a microcell used exclusively for obtaining timing information in the scintillator 3. Therefore, even if the PDE in the microcell 15a increases, the energy resolution in the scintillator 3 does not decrease. Therefore, by applying the high bias voltage V1 to the microcell 15a, the scintillator 3 can enjoy only the advantageous effect of improving the timing resolution.
  • the photon detection efficiency is lowered, so that the probability that two or more photons are simultaneously detected in the same microcell can be reduced. Therefore, by applying the low bias voltage V2 to the microcell 15b, the energy resolution obtained by the microcell 15b is improved.
  • the microcell 15b is a microcell used exclusively in the scintillator 3 for acquiring energy information. Therefore, even if the PDE in the microcell 15b decreases, the timing resolution in the scintillator 3 does not decrease. Therefore, by applying the relatively low bias voltage V2 to the microcell 15b, the scintillator 3 can enjoy only the advantageous effect of improving the energy resolution.
  • the specification is set such that the PDE is relatively high for the timing information acquisition microcell 15a, and the PDE is relatively low for the energy information acquisition microcell 15b.
  • the energy resolution can be improved while improving the timing resolution by changing the height of the bias voltage (supply voltage) between the microcell 15a and the microcell 15b.
  • the scintillator 3 and the photodetector 5 are optically coupled on a one-to-one basis.
  • the photodetector 5 is provided with a microcell 15a used for acquiring timing information and a microcell 15b used for acquiring energy information.
  • each of the microcells 107 is transmitted in parallel to the comparator 115 and the shaping amplifier 117. Timing information is acquired based on the output of the comparator 115, and energy information is acquired based on the output of the shaping amplifier 117. That is, each of the microcells 107 provided in the photodetector 105 is used for both acquisition of timing information and acquisition of energy information.
  • the conventional radiation detector 101 it is difficult for the conventional radiation detector 101 to achieve both high timing resolution and high energy resolution. That is, if the bias voltage V applied to all the microcells 107 is increased in order to improve the accuracy of timing information, the photon detection efficiency (PDE) increases. As a result, the probability that the same microcell 107 detects two or more photons at the same time increases, so the accuracy of energy information decreases. On the other hand, if the bias voltage V applied to all the microcells 107 is lowered in order to improve the accuracy of energy information, the photon detection efficiency is lowered. As a result, the fluctuation of the time when the photon detection amount exceeds the predetermined threshold increases, and the accuracy of the timing information decreases.
  • a part of the plurality of microcells 15 provided in the photodetector 5 is a microcell 15a used exclusively for obtaining timing information.
  • the other part is a microcell 15b used exclusively for obtaining energy information.
  • one or more microcells 15 a dedicated for timing information acquisition and one or more microcells 15 b dedicated for energy information acquisition are optically coupled to one scintillator 3.
  • a first power supply 21 for applying a relatively high bias voltage V1 is connected to the microcell 15a, and a second power supply 23 for applying a relatively low bias voltage V2 is connected to the microcell 15b. . Therefore, the radiation detector 1 can apply bias voltages having different heights to each of the microcell 15a and the microcell 15b.
  • the accuracy of timing information can be improved while avoiding a decrease in energy resolution.
  • the low bias voltage V2 to the microcell 15b dedicated to energy information acquisition, the accuracy of the energy information can be improved while avoiding a decrease in timing resolution. As a result, both the timing resolution and the energy resolution in the radiation detector 1 can be improved.
  • Lu-based scintillator 3 In recent years, lutetium-based (Lu-based) materials such as LYSO and LFS are used as the scintillator 3. Such a Lu-based scintillator has a light emission amount approximately 10 times larger than that of a bismuth-based scintillator such as BGO that has been used conventionally. As a result of examination by the inventor, there was no difference in energy resolution between the Lu-based scintillator and the bismuth-based scintillator, which was about 15%, although the light emission amount was greatly different.
  • the timing resolution can be improved while maintaining the energy resolution of the radiation detector. It becomes.
  • the effects of the present invention can be suitably achieved when the microcell 15b contributing to the acquisition of energy information is about 2% to 40% of the microcell 15a contributing to the acquisition of timing information. found.
  • the timing information and the energy information about the ⁇ rays incident on the scintillator 3 are obtained by the configuration in which one or more microcells 15 a and one or more microcells 15 b are optically coupled to one scintillator 3. , Both can improve accuracy. Then, by using the radiation detector 1 including the scintillator 3 and the photodetector 5, it is possible to realize the PET apparatus 7 that achieves both high timing resolution and high energy resolution for ⁇ rays. As a result, a more accurate radiographic image can be acquired for the distribution of the radiopharmaceutical, so that a more accurate diagnosis can be performed on the subject M.
  • TOF-PET TOF type PET apparatus
  • the overall configuration of the radiation detector 1A according to the second embodiment is common to the configuration of the radiation detector 1 according to the second embodiment. That is, the radiation detector 1A has a configuration in which one photodetector 5A is optically coupled to one scintillator 3 as in the radiation detector 1 (see FIG. 1A).
  • the photodetector 5 according to the first embodiment the area of the light receiving region F in each microcell 15 is the same.
  • the photodetector 5A according to the second embodiment is different from the first embodiment in that the light receiving region F in each of the microcells 15a is wider than the light receiving region F in each of the microcells 15b. That is, as shown in FIG. 5A, the photodetector 5A is configured such that the pitch length T1 of the microcell 15a is longer than the pitch length T2 of the microcell 15b.
  • the area occupied by the insensitive area N (partition wall) formed between the adjacent light receiving areas F is reduced.
  • the area of the light receiving region F per unit area in one microcell 15a is larger than the area of the light receiving region F per unit area in one microcell 15b.
  • the specification of the microcell 15a used for acquiring timing information and the specification of the microcell 15b used for acquiring energy information are made different.
  • the specification of the microcell 15a and the specification of the microcell 15b are made different by changing the area of the light receiving region F per unit area.
  • the microcell 15a dedicated to timing information acquisition has a relatively large area of the light receiving region F per unit area, so that the photon detection efficiency is higher. As a result, timing information with higher resolution can be acquired based on the output of the microcell 15a.
  • the microcell 15b dedicated to energy information acquisition has a relatively small area of the light receiving region F per unit area, so that the photon detection efficiency is lower, but the linearity between the number of incident photons and the output is suitably maintained. As a result, energy information with higher resolution can be acquired based on the output of the microcell 15b.
  • the pitch length T2 of the microcells 15b relatively short, the number of microcells 15b (number of pixels) per unit area increases. By increasing the number of pixels, it is possible to more reliably avoid a situation in which the same microcell 15b simultaneously detects two or more photons, so that the energy resolution can be further improved.
  • the microcell 15a is set to be relatively wide while the microcell 15b is set to be relatively narrow with respect to the area of the light receiving region F per unit area in the microcell 15. .
  • this configuration improves the accuracy of energy information for the microcell 15b while setting the microcell 15a to a predetermined specification that improves the accuracy of timing information. Can be set to different specifications.
  • the arrangement pattern of the microcells 15a and 15b can be changed as appropriate in the second embodiment as in the first embodiment. That is, the arrangement of the microcells 15a may be set densely as shown in FIG. 5B, or may be dispersed as shown in FIG. 5C. Further, the shape of the light receiving region F is not limited to a rectangle, and the shape of the light receiving region F may be appropriately changed to a hook shape or the like as in the microcell 15b shown in FIG.
  • the specification of the microcell 15a and the specification of the microcell 15b are set to different specifications by changing the area of the light receiving region per unit area. Therefore, as shown in FIGS. 6A and 6B, even if the same bias voltage V is applied from the single power source 22 to each of the microcell 15a and the microcell 15b, the timing resolution And energy resolution can be improved. Therefore, it is not necessary to prepare a plurality of power sources for each radiation detector. In addition, since it is not necessary to change the circuit so that each of the microcells 15a and each of the microcells 15b is connected to a separate power source, the manufacturing cost of the radiation detector that exhibits the effect of the present invention can be reduced. Can be further reduced.
  • the radiation detector 1A according to the second embodiment is not limited to the structure shown in FIG. 6, and may have a structure including the first power source 21 and the second power source as shown in FIG. That is, while changing the area of the light receiving region of the microcell 15, the first power supply 21 applies a high bias voltage V1 to the microcell 15a, and the first power supply 21 applies the high voltage bias voltage V1 to the microcell 15a. It may be a configuration. In this case, since the microcell 15a has a large light receiving area and a high bias voltage, the timing resolution can be further improved by a synergistic effect. On the other hand, since the micro cell 15b has a small light receiving area and a low bias voltage, the energy resolution can be further improved by a synergistic effect.
  • the radiation detector 1 is configured by optically coupling one photodetector 5 to one scintillator 3.
  • the radiation detector 1B according to the third embodiment has a configuration in which a plurality of photodetectors 5 are optically coupled to one scintillator 3, as shown in FIG.
  • the detector module 2 is configured by arranging the radiation detectors 1B in a one-dimensional matrix or a two-dimensional matrix.
  • Example 3 it is assumed that two photodetectors 5 are optically coupled to one scintillator 3.
  • one of the two photodetectors 5 is a photodetector 5L, and the other is a photodetector 5R.
  • the photodetector 5L has microcells 15a used for obtaining timing information arranged in a matrix
  • the photodetector 5R has microcells 15b used for obtaining energy information arranged in a matrix.
  • the light detector 5L corresponds to the first light detection means in the present invention
  • the light detector 5R corresponds to the second light detection means in the present invention.
  • the radiation detector 1B includes a first power source 21 and a second power source 23 as in the first embodiment.
  • the first power supply 21 applies a relatively high bias voltage V1 to each of the microcells 15a
  • the second power supply 23 applies a relatively low bias voltage V2 to each of the microcells 15b.
  • the timing resolution is improved.
  • the microcell 15a is set to a predetermined specification that is advantageous for acquiring timing information, while the microcell 15b is another specification that is advantageous for acquiring energy information. Can be set to Therefore, it is possible to improve both the timing resolution and energy resolution obtained for each of the radiation detectors 1B.
  • a plurality of photodetectors 5 are optically coupled to one scintillator 3, and either one of the microcells 15a or 15b is arranged in a matrix in each photodetector 5. It is arranged.
  • one of the first power source 21 and the second power source 23 is connected to each photodetector 5. That is, since it is not necessary to connect a plurality of power supplies to one photodetector 5, circuit design becomes relatively easy.
  • each photodetector 5 either one of the microcell 15a or the microcell 15b is arranged in a matrix. Therefore, the existing photodetector that is advantageous for acquiring timing information is used as the photodetector 5L, and the existing photodetector that is advantageous for acquiring energy information is the photodetector.
  • Each can be used as 5R. That is, since it is not necessary to newly manufacture a photodetector having both the microcell 15a and the microcell 15b, the radiation detector according to the present invention can be more easily manufactured.
  • the present invention is not limited to the above embodiment, and can be modified as follows.
  • the gain is set high, the photon detection efficiency is set high, the number of pixels is set low, the crosstalk probability is set low, or the dark count is set low, the timing resolution is improved while the energy resolution is lowered.
  • the gain is set low, the photon detection efficiency is set low, the number of pixels is increased, the crosstalk probability is set high, or the dark count is set high, the energy resolution is improved while the timing resolution is lowered.
  • a microcell 15a with a relatively high gain is used as the microcell 15a dedicated to timing information acquisition
  • a microcell 15b with a relatively low gain is used as the microcell 15b dedicated to energy information acquisition.
  • timing information with improved resolution can be acquired based on the output of the microcell 15a having a high gain among the microcell groups optically coupled to the same scintillator 3.
  • energy information with improved resolution can be acquired based on the output of the microcell 15b having a low gain.
  • the configuration in which one or more photodetectors 5 are optically coupled to one scintillator 3 has been described as an example.
  • the radiation detector 1 ⁇ / b> C may be configured by optically coupling the scintillator 3 to one photodetector 5.
  • the detector module 2C constituted by the radiation detector 1C has a configuration as shown in FIG. 9B.
  • the radiation detector 1C according to the modified example according to (2) has a configuration in which four scintillators 3a to 3d are optically coupled to one photodetector 5.
  • At least one microcell 15a used for acquiring timing information and at least one microcell 15b used for acquiring energy information are optically coupled to each scintillator 3. That is, in the photodetector 5, the areas where the scintillators 3a to 3d are optically coupled are Pa to Pd, respectively (see FIG. 9B).
  • the microcells 15 in each of the regions Pa to Pd one or more microcells 15a (see FIG. 9B, halftone dots) and one or more microcells 15b (see FIG. 9B, hatched lines) are included. It only has to be done.
  • the microcell 15a is set to a specification that is advantageous for obtaining timing information, and is set to another specification that is advantageous for obtaining energy information.
  • the specification of the microcell 15a and the specification of the microcell 15b are differentiated by applying the bias voltage V1 to the photodetector 5L and applying the bias voltage V2 to the photodetector 5R.
  • the pitch length T1 of the microcell 15a provided in the photodetector 5L is made longer than the pitch length T2 of the microcell 15b provided in the photodetector 5R. May be.
  • the pitch length By changing the pitch length, the area of the light receiving region F per unit area in the microcell 15a becomes wider than the area of the light receiving region F per unit area in the microcell 15b.
  • the specification of the microcell 15a and the specification of the microcell 15b can be differentiated by applying the configuration in which the area of the light receiving region per unit area is changed.
  • the pitch length of the microcell is changed for each photodetector 5. That is, by using, as an example, SiPM having specifications with a relatively long pitch length of microcells as the photodetector 5L, and using SiPM with specifications having a relatively short pitch length of microcells as the photodetector 5R. 2 can be realized. In this case, since the resolution of both timing information and energy information can be improved by combining existing SiPM and the like, it is relatively easy to manufacture the radiation detector according to the present invention.
  • each photodetector optically coupled to one scintillator 3 may be changed for each photodetector optically coupled to one scintillator 3. If at least one microcell 15a and at least one microcell 15b are optically coupled to one scintillator 3, each of the photodetector 5L and the photodetector 5R has a microcell 15a and a microcell 15b. May be mixed.
  • the scintillator 3 and the photodetector 5 are directly coupled to each other, but the present invention is not limited to this. That is, the light guide which transmits light between the scintillator 3 and the photodetector 5 may be provided, and the scintillator 3 and the photodetector 5 may be indirectly optically coupled.

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Abstract

L'invention concerne une microcellule (15) dans un détecteur optique (5) qui est constituée d'une microcellule (15a) et d'une microcellule (15b). La microcellule (15a) est utilisée pour l'acquisition d'informations de base de temps et la microcellule (15b) est utilisé pour l'acquisition d'informations d'énergie. Chaque scintillateur (3) est relié optiquement à au moins une microcellule (15a) et au moins une microcellule (15b). Grâce à la fourniture de microcellules séparées pour l'acquisition d'informations d'énergie et l'acquisition d'informations de base de temps, il est possible de régler la microcellule (15a) selon une spécification pour l'acquisition d'informations de base de temps et de régler la microcellule (15b) selon une autre spécification pour l'acquisition d'informations d'énergie. Par conséquent, il devient possible d'améliorer la résolution d'énergie tout en améliorant la résolution de base de temps dans un détecteur de rayonnement.
PCT/JP2016/059501 2015-09-04 2016-03-24 Détecteur de rayonnement et module détecteur Ceased WO2017038133A1 (fr)

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CN109425869A (zh) * 2017-08-30 2019-03-05 赫克斯冈技术中心 具有扫描功能和接收器的可设定接收范围的测量装置
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WO2018235810A1 (fr) * 2017-06-23 2018-12-27 浜松ホトニクス株式会社 Détecteur optique et dispositif de détection optique
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CN109425869A (zh) * 2017-08-30 2019-03-05 赫克斯冈技术中心 具有扫描功能和接收器的可设定接收范围的测量装置
CN109425869B (zh) * 2017-08-30 2023-05-30 赫克斯冈技术中心 具有扫描功能和接收器的可设定接收范围的测量装置
JP2022525255A (ja) * 2018-05-28 2022-05-11 ウニベルシタ デ バルセローナ ＳｉＰＭにおける光クロストーク効果の低減
JP7414306B2 (ja) 2018-05-28 2024-01-16 ウニベルシタ デ バルセローナ ＳｉＰＭにおける光クロストーク効果の低減
JP2020038185A (ja) * 2018-08-31 2020-03-12 キヤノンメディカルシステムズ株式会社 フォトンカウンティング検出器およびｘ線ｃｔ装置
JP7246975B2 (ja) 2018-08-31 2023-03-28 キヤノンメディカルシステムズ株式会社 フォトンカウンティング検出器およびｘ線ｃｔ装置
RU2837644C1 (ru) * 2024-12-05 2025-04-03 Российская Федерация, от имени которой выступает Государственная корпорация по атомной энергии "Росатом" (Госкорпорация "Росатом") Сцинтилляционный детектор

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