Radiation tomographic imaging apparatus, data transfer control method, and data transfer control program

Abstract

To efficiently execute data transfer while suppressing cost increase in a radiation tomographic imaging apparatus having an extended axial field of view.SOLUTION: A radiation tomographic imaging apparatus comprises: a first detector ring in which a plurality of first detectors that detect radiation are arranged in a circular shape with a long axis direction of a top plate on which a subject is placed as a central axis; a second detector ring in which a plurality of second detectors that detect radiation are arranged in the circular shape and which is disposed adjacent to the first detector ring; a first transfer unit that transfers to a console first data generated on the basis of outputs from the plurality of first detectors and second data generated on the basis of outputs from the plurality of second detectors; a second transfer unit that transfers the second data to the first transfer unit; and a control unit that controls transfer of the second data by the second transfer unit on the basis of a drug used in a scan on the subject using radiation and / or on an imaging site of the subject in the scan.SELECTED DRAWING: Figure 2

Description

[Technical Field]

[0001] The present embodiment relates to a radiation tomography apparatus, a data transfer control method, and a data transfer control program. [Background technology]

[0002] Conventionally, radiation tomography systems, such as positron emission tomography (PET) systems, single photon emission computed tomography (SPECT) systems, and X-ray computed tomography (CT) systems, have typically consisted of a single gantry. In recent years, radiation tomography systems with a longitudinal axis field of view have been studied in order to increase radiation sensitivity.

[0003] As radiation detectors become longer in axis, data acquisition systems (hereinafter referred to as DAS) become larger in scale. This increases the length and number of cables connecting the console in the radiation tomography imaging device to the hub board for data transfer. The increased length and number of cables increases manufacturing costs and maintenance burdens. This requires redesigning the data acquisition system for each gantry, but there are concerns that the redesign will also increase costs.

[0004] For example, when a high-dose scan of an area such as the heart is performed using a PET device with a long-axis field of view, the PET device must use a high-speed field programmable gate array (FPGA) to process the enormous amount of data. However, the use of a high-speed FPGA increases the manufacturing cost of the DAS. On the other hand, when a low-dose scan such as a whole-body scan is performed using a PET device with a long-axis field of view, the high-speed FPGA transmits data containing many empty packets, which prevents the use of high-performance data transmission specifications. [Prior art documents] [Patent documents]

[0005] [Patent Document 1] Japanese Patent Publication No. 2020-110575 Summary of the Invention [Problem to be solved by the invention]

[0006] The problem to be solved by the present invention is to efficiently transfer data in a radiation tomography imaging apparatus with a longitudinal field of view while suppressing increases in cost. However, the problem to be solved by the embodiments disclosed in this specification and the drawings is not limited to the above problem. Problems corresponding to the effects of each configuration shown in the embodiments described below can also be positioned as other problems. [Means for solving the problem]

[0007] The radiation tomography apparatus according to this embodiment includes a first detector ring, a second detector ring, a first transfer unit, a second transfer unit, and a controller. The first detector ring includes a plurality of first detectors arranged in a circular ring shape with the longitudinal direction of a tabletop on which a subject is placed as a central axis, and the first detector ring includes a plurality of second detectors arranged in the circular ring shape, and the second detector ring is disposed adjacent to the first detector ring. The first transfer unit transfers first data generated based on outputs from the plurality of first detectors and second data generated based on outputs from the plurality of second detectors to a console. The second transfer unit transfers the second data to the first transfer unit. The controller controls the transfer of the second data by the second transfer unit based on a drug used in a scan of the subject using the radiation and / or an imaging region of the subject in the scan. [Brief explanation of the drawings]

[0008] [Figure 1] FIG. 1 is a diagram showing an example of the configuration of a PET apparatus according to an embodiment. [Figure 2] FIG. 2 is a flowchart showing an example of a procedure for a data transfer control process according to the embodiment. [Figure 3] FIG. 3 is a diagram showing an example of PET imaging of the heart of a subject according to the embodiment. [Figure 4] FIG. 4 is a diagram showing an example of PET imaging of the whole body of a subject according to the embodiment. [Figure 5] FIG. 5 is a diagram showing an example of transfer of second data and transfer of first data according to the embodiment. DETAILED DESCRIPTION OF THE INVENTION

[0009] The radiation tomography imaging apparatus, the data transfer control method, and the data transfer control program will be described in detail below with reference to the drawings. In the following embodiments, parts with the same reference numerals perform similar operations, and redundant description will be omitted as appropriate. Note that the radiation tomography imaging apparatus, the data transfer control method, and the data transfer control program according to the present application are not limited to the following embodiments.

[0010] The radiation tomography imaging apparatus according to this embodiment has an imaging mechanism for performing, for example, PET (Positional Emission Tomography) imaging. Examples of such radiation tomography imaging apparatus include a PET apparatus having only a PET imaging function, a PET-CT apparatus having a PET imaging mechanism and an X-ray CT (Computed Tomography) imaging mechanism, and a PET-MR apparatus having a PET imaging mechanism and an MR (Magnetic Resonance) imaging mechanism.

[0011] Furthermore, the radiation tomography apparatus according to this embodiment may have an imaging mechanism for performing SPECT (Single Photon Emission CT) imaging. Examples of such nuclear medicine diagnostic apparatuses include a SPECT apparatus having only a SPECT imaging mechanism, a SPECT-CT apparatus having a SPECT imaging mechanism and a CT imaging mechanism, and a SPECT-MR apparatus having a SPECT imaging mechanism and an MR imaging mechanism.

[0012] Furthermore, the radiation tomography imaging apparatus according to this embodiment may be, for example, a stationary / rotate-type (fourth generation CT) X-ray computed tomography imaging apparatus in which a large number of X-ray detection elements arranged in a ring shape are fixed and only the X-ray generation unit rotates around the subject.

[0013] The radiation tomography apparatus according to this embodiment can be applied to any of the above types of apparatus, but for the sake of specificity, the following description will be given assuming that it is a PET apparatus.

[0014] (Embodiment) FIG. 1 is a diagram showing an example of the configuration of a PET device 1 according to an embodiment. As shown in FIG. 1, the PET device 1 includes a PET gantry 10, a bed 50, and a console 70. Typically, the PET gantry 10 and the bed 50 are installed in a common examination room. The console 70 is installed in a control room adjacent to the examination room. The PET gantry 10 is an imaging device for performing PET imaging (PET scan) on a subject P. The bed 50 movably supports a tabletop 53 on which the subject P to be imaged is placed. The console 70 is a computer that controls the PET gantry 10, the CT gantry 30, the bed 50, etc.

[0015] As shown in FIG. 1, the PET gantry 10 includes an existing PET imaging mechanism (hereinafter referred to as the first PET imaging mechanism) 10A and an expanded PET imaging mechanism (hereinafter referred to as the second PET imaging mechanism) 10B. The first PET imaging mechanism 10A includes, for example, a first detector ring 11A, a first signal processing circuit 13A, and a first processing circuit 15A. Although FIG. 1 illustrates the first PET imaging mechanism 10A and the second PET imaging mechanism 10B as being included in the same housing (PET gantry 10), this embodiment is not limited to this. For example, the first PET imaging mechanism 10A and the second PET imaging mechanism 10B may be mounted in different housings.

[0016] The first detector ring 11A is configured by arranging a plurality of first detectors 17A in a circular ring shape with the longitudinal direction of the tabletop 53 on which the subject P is placed as the central axis Z. The first detector ring 11A is a detector that detects radiation, and in the PET device 1, corresponds to a gamma ray detector that detects gamma rays. An image field of view (FOV) is set at the opening of the first detector ring 11A. The subject P is positioned so that the imaging region of the subject P is included in the image field of view (also referred to as the imaging field of view). A drug labeled with a positron-emitting nuclide is administered to the subject P. Positrons emitted from the positron-emitting nuclide annihilate with surrounding electrons. This annihilation generates pairs of annihilation gamma rays. The first detector ring 11A is used, for example, when the heart of the subject P is to be imaged.

[0017] The drug administered to the subject P is, for example, a drug for scanning the heart of the subject P (hereinafter referred to as a cardiac scan drug) or a drug for scanning the whole body of the subject P (hereinafter referred to as a whole body scan drug). The count rate of the cardiac scan drug is about 10 times that of the whole body scan drug. Known cardiac scan drugs and whole body scan drugs can be used, so their description will be omitted. The imaging region of the subject P is the heart of the subject P or the whole body of the subject P. The name of the drug and / or the name of the imaging region is written in an examination order transmitted from a Radiology Information System (RIS) to the PET device 1 via a network, for example. The name of the drug and / or the name of the imaging region may be input by a user via the input interface 76.

[0018] The first detector 17A detects pair annihilation gamma rays emitted from inside the body of the subject P. The first detector 17A generates an electrical signal corresponding to the amount of light of the detected pair annihilation gamma rays. For example, the first detector 17A has multiple scintillators and multiple photomultiplier tubes. The scintillators receive pair annihilation gamma rays originating from radioactive isotopes in the subject P and generate scintillation light. The multiple scintillators correspond to multiple detection elements that detect gamma rays. That is, the first detector 17A has multiple detection elements. The photomultiplier tubes generate an electrical signal corresponding to the amount of light of the scintillation light. The generated electrical signal is supplied to the first signal processing circuit 13A. Note that the first detector 17A may be realized by a Depth Of Interaction (DOI) detector capable of distinguishing a position of interaction.

[0019] The first signal processing circuit 13A generates single-event data based on the electrical signal output from the first detector 17A. Specifically, the first signal processing circuit 13A performs, for example, detection time measurement processing, position calculation processing, and energy calculation processing on the electrical signal. The first signal processing circuit 13A is realized by an application specific integrated circuit (ASIC), a field programmable gate array (FPGA), another complex programmable logic device (CPLD), or a simple programmable logic device (SPLD) configured to be able to execute the detection time measurement processing, position calculation processing, and energy calculation processing.

[0020] The first signal processing circuit 13A measures the time of detection of gamma rays by the first detector 17A through detection time measurement processing. Specifically, the first signal processing circuit 13A monitors the peak value of the electrical signal from the first detector 17A and measures the time when the peak value exceeds a preset threshold as the detection time. In other words, the first signal processing circuit 13A electrically detects pair annihilation gamma rays by detecting that the peak value has exceeded the threshold. The first signal processing circuit 13A calculates the incident position of the pair annihilation gamma rays based on the electrical signal from the first detector 17A through position calculation processing. The incident position of the pair annihilation gamma rays corresponds to the position coordinates of the scintillator onto which the pair annihilation gamma rays are incident. The first signal processing circuit 13A calculates the energy value of the detected pair annihilation gamma rays based on the electrical signal from the first detector 17A through energy calculation processing.

[0021] The first signal processing circuit 13A associates detection time data, position coordinate data, and energy value data related to a single event. A combination of energy value data, position coordinate data, and detection time data related to a single event is called single event data. The first signal processing circuit 13A generates single event data one after another each time a pair annihilation gamma ray is detected. The first signal processing circuit 13A outputs the generated single event data to the first processing circuit 15A.

[0022] The first processing circuit 15A has a first coincidence counting function 151A, a first integrating function 153A, and a first transfer function 155A. The first processing circuit 15A is realized using hardware resources such as an ASIC, FPGA, CPLD, or SPLD. Note that the first processing circuit 15A is not limited to an ASIC, FPGA, CPLD, or SPLD, and may be realized using various processors and memories. The first processing circuit 15A that realizes the first coincidence counting function 151A, the first integrating function 153A, and the first transfer function 155A corresponds to the first coincidence counting unit, the first integrating unit, and the first transfer unit, respectively. Furthermore, the first processing circuit 15A that realizes the first coincidence counting function 151A, the first integrating function 153A, and the first transfer function 155A may be realized using different circuits, such as the first coincidence counting circuit, the first integrating circuit, and the first transfer circuit. The first signal processing circuit 13A and the first processing circuit 15A may be integrated and referred to as a first DAS (Data Acquisition System). The first processing circuit 15A may be provided for each predetermined angle range. In this case, the first processing circuit 15A functions as a relay hub for data integration.

[0023] The first coincidence counting function 151A performs coincidence counting processing on the single event data from the first signal processing circuit 13A. In the coincidence counting processing, the first coincidence counting function 151A repeatedly identifies single event data relating to two single events that fall within a predetermined time frame from the repeatedly supplied single event data. This pair of single events is presumed to be derived from pair annihilation gamma rays generated from the same pair annihilation point. The pair of single events is collectively called a coincidence counting event.

[0024] The line connecting the pair of first detectors 17A (more specifically, scintillators) that detected this pair of annihilation gamma rays is called the LOR (Line Of Response). Event data related to the pair of events that make up the LOR is called coincidence event data. Hereinafter, when there is no particular distinction between coincidence event data and single event data, they will be collectively referred to as PET event data. Furthermore, the PET event data generated by the first PET imaging mechanism 10A will be referred to as first data.

[0025] Although the first signal processing circuit 13A and the first coincidence function 151A are included in the first PET imaging mechanism 10A in the above configuration, this embodiment is not limited to this. For example, both the first signal processing circuit 13A and the first coincidence function 151A, or only the first coincidence function 151A, may be included in the console 70. In this case, the electrical signal or single-event data output from the first detector 17A corresponds to the first data. Furthermore, one first coincidence function 151A may be provided for each of the first signal processing circuits 13A included in the first PET imaging mechanism 10A, or the first signal processing circuits 13A included in the first PET imaging mechanism 10A may be divided into multiple groups, and one first coincidence function 151A may be provided for each group. The groups may be divided, for example, into groups corresponding to the multiple first detectors 17A included in a predetermined angular range relative to the central axis Z.

[0026] For the sake of concreteness, the following description will be given assuming that the specified angle range is four angle ranges, with 0° being directly above the vertical direction of the central axis Z, and the first range is from 0° to 90°, the second range is from 90° to 180°, the third range is from 180° to 270°, and the fourth range is from 270° to 360°.

[0027] The first integrating function 153A integrates multiple pieces of first data based on outputs from multiple first detectors 17A that are included in a predetermined angle range with respect to the central axis Z, out of the multiple first detectors 17A. Specifically, the first integrating function 153A integrates PET event data included in a first range to generate first data corresponding to the first range. The first integrating function 153A also integrates PET event data included in a second range to generate first data corresponding to the second range. The first integrating function 153A also integrates PET event data included in a third range to generate first data corresponding to the third range. The first integrating function 153A also integrates PET event data included in a fourth range to generate first data corresponding to the fourth range.

[0028] The first transfer function 155A transfers first data generated based on outputs from the plurality of first detectors 17A and second data generated based on outputs from the plurality of second detectors 17B to the console 70. For example, the first transfer function 155A transfers the integrated first data and the integrated second data to the console 70 for each angle range. The second data and the integrated second data will be described later. Note that the data transfer rate by the first transfer function 155A (hereinafter referred to as the first transfer rate) may be faster than the data transfer rate by the second transfer function 155B (hereinafter referred to as the second transfer rate), which will be described later.

[0029] The second PET imaging mechanism 10B has a second detector ring 11B, a second signal processing circuit 13B, and a second processing circuit 15B. The various functions and configurations of the second PET imaging mechanism 10B are generally the same as those of the first PET imaging mechanism 10A, but will be explained as appropriate below.

[0030] The second detector ring 11B has a plurality of second detectors 17B arranged on a circumference around the central axis Z. The second detectors 17B correspond to gamma ray detectors that detect gamma rays. An image field of view (FOV) is set at the opening of the second detector ring 11B. The second detector ring 11B is used, for example, when the entire body of the subject P is to be imaged.

[0031] The second detector 17B detects pair annihilation gamma rays emitted from inside the body of the subject P. The second detector 17B generates an electrical signal according to the light intensity of the detected pair annihilation gamma rays. For example, the second detector 17B has a plurality of scintillators and a plurality of photomultiplier tubes. The plurality of scintillators correspond to a plurality of detection elements that detect gamma rays. In other words, the second detector 17B has a plurality of detection elements. The electrical signal generated by the photomultiplier tube according to the light intensity of the scintillation light is supplied to the second signal processing circuit 13B. Note that the second detector 17B may be realized by a DOI detector.

[0032] The second signal processing circuit 13B generates single event data based on the electrical signal output from the second detector 17B. Specifically, the second signal processing circuit 13B performs, for example, detection time measurement processing, position calculation processing, and energy calculation processing on the electrical signal. The second signal processing circuit 13B is realized by an ASIC, FPGA, CPLD, or SPLD configured to be able to execute the detection time measurement processing, position calculation processing, and energy calculation processing.

[0033] The second signal processing circuit 13B measures the time of detection of gamma rays by the second detector 17B through a detection time measurement process. Specifically, the second signal processing circuit 13B monitors the peak value of the electrical signal from the second detector 17B and measures the time when the peak value exceeds a preset threshold as the detection time. In other words, the second signal processing circuit 13B electrically detects pair annihilation gamma rays by detecting that the peak value has exceeded the threshold. The second signal processing circuit 13B calculates the incident position of the pair annihilation gamma rays based on the electrical signal from the second detector 17B through a position calculation process. The second signal processing circuit 13B calculates the energy value of the detected pair annihilation gamma rays based on the electrical signal from the second detector 17B through an energy calculation process.

[0034] The second signal processing circuit 13B generates single event data by associating the detection time data, position coordinate data, and energy value data related to the single event. The second signal processing circuit 13B generates single event data one after another every time a pair annihilation gamma ray is detected, and outputs the generated single event data to the second processing circuit 15B.

[0035] The second processing circuit 15B has a second coincidence function 151B, a second integrating function 153B, and a second transfer function 155B. The second processing circuit 15B is realized using hardware resources such as an ASIC, FPGA, CPLD, or SPLD. The second processing circuit 15B may be realized using various processors and memories, without being limited to an ASIC, FPGA, CPLD, or SPLD. The second processing circuit 15B that realizes the second coincidence function 151B, the second integrating function 153B, and the second transfer function 155B corresponds to a second coincidence unit, a second integrating unit, and a second transfer unit, respectively. The second processing circuit 15B that realizes the second coincidence function 151B, the second integrating function 153B, and the second transfer function 155B may also be realized using different circuits, such as a second coincidence circuit, a second integrating circuit, and a second transfer circuit. The second signal processing circuit 13B and the second processing circuit 15B may be integrated and referred to as a second DAS. The second processing circuit 15B may be provided for each predetermined angle range. In this case, the second processing circuit 15B functions as a relay hub for data integration.

[0036] The second coincidence function 151B performs coincidence processing on the single event data from the second signal processing circuit 13B. In the coincidence processing, the second coincidence function 151B repeatedly identifies single event data relating to two single events that fall within a predetermined time frame from the repeatedly supplied single event data. The line connecting the pair of second detectors 17B (more specifically, scintillators) that detected the pair annihilation gamma rays is the LOR. The PET event data (coincidence event data and single event data) generated by the second PET imaging mechanism 10B is called second data.

[0037] Although the second signal processing circuit 13B and the second coincidence function 151B are included in the second PET imaging mechanism 10B in the above configuration, this embodiment is not limited thereto. For example, both the second signal processing circuit 13B and the second coincidence function 151B, or only the second coincidence function 151B, may be included in the console 70. In this case, the electrical signal or single-event data output from the second detector 17B corresponds to the second data. Furthermore, one second coincidence function 151B may be provided for each of the second signal processing circuits 13B included in the second PET imaging mechanism 10B, or the second signal processing circuits 13B included in the second PET imaging mechanism 10B may be divided into multiple groups, and one second coincidence function 151B may be provided for each group. The groups may be divided, for example, into groups corresponding to the multiple second detectors 17B included in a predetermined angular range relative to the central axis Z. For the sake of specificity, the following description will be given assuming that the predetermined angle ranges are the four angle ranges (first range, second range, third range, and fourth range) as described above.

[0038] The second integrating function 153B integrates multiple pieces of second data based on outputs from multiple second detectors 17B that are included in a predetermined angle range with respect to the central axis Z, among the multiple second detectors 17B. Specifically, the second integrating function 153B integrates PET event data included in a first range to generate second data corresponding to the first range. The second integrating function 153B also integrates PET event data included in the second range to generate second data corresponding to the second range. The second integrating function 153B also integrates PET event data included in a third range to generate second data corresponding to the third range. The second integrating function 153B also integrates PET event data included in a fourth range to generate second data corresponding to the fourth range.

[0039] The second transfer function 155B transfers the second data generated based on the outputs from the plurality of second detectors 17B to the first transfer function 155A in the first processing circuit 15A. For example, the second transfer function 155B is controlled by a control function 731 (described later) to transfer the second data based on the agent used in a scan of the subject P using radiation and / or the region of the subject P being imaged in the scan. Control of the transfer of the second data will be described later. When the second data is transferred to the first transfer function 155A, the first transfer function 155A transfers the first data and the second data to the console 70.

[0040] Specifically, the second transfer function 155B transfers the second data integrated for each of the four angle ranges to the first transfer function 155A for each angle range under the control of the control function 731. At this time, the first transfer function 155A transfers the first data and the second data to the console 70 for each angle range. Note that the second transfer rate may be slower or faster than the first transfer rate. Also, the second transfer rate may be the same as (approximately the same as) the first transfer rate. For the sake of specificity, the following description will be given assuming that the second transfer rate is slower than the first transfer rate.

[0041] If the sum of the data amount per unit time of the first data and the data amount per unit time of the second data exceeds the maximum value of the first transfer rate, the second transfer function 155B stores the second data in memory. Specifically, the second transfer function 155B receives information on the data amount per unit time of the first data from the first transfer function 155A. At this time, the second transfer function 155B uses the information on the data amount per unit time of the first data to calculate the sum of the data amount per unit time of the first data and the data amount per unit time of the second data. Next, the second transfer function 155B compares the calculated sum with the maximum value of the first transfer rate and determines whether the calculated sum exceeds the maximum value of the first transfer rate.

[0042] If the calculated sum exceeds the maximum value of the first transfer rate, the second transfer function 155B stores the second data in the second processing circuit 15B or in a memory associated with the second transfer function 155B. If the calculated sum does not exceed the maximum value of the first transfer rate, the second transfer function 155B transfers the second data to the first transfer function 155A.

[0043] Furthermore, when second data is stored in the memory associated with the second processing circuit 15B or the second transfer function 155B, the second transfer function 155B uses information on the amount of first data generated per unit time to calculate the sum of the maximum value of the second transfer rate and the amount of first data generated per unit time. The second transfer function 155B then compares the calculated sum with the maximum value of the first transfer rate to determine whether the calculated sum exceeds the maximum value of the first transfer rate. If the calculated sum exceeds the maximum value of the first transfer rate, the second transfer function 155B stores the second data in memory, for example, for data that exceeds the amount of data that can be transferred at the first transfer rate. That is, if the amount of data transferred to the console 70 by the first transfer function 155A (the total amount of the first data and the second data (hereinafter referred to as the first total data amount)) exceeds the maximum value of the first transfer rate, the second transfer function 155B limits the transfer of the second data to the first transfer function 155A.

[0044] The first integration function 153A, the second integration function 153B, the first transfer function 155A, and the second transfer function 155B may be electrically connected for each angular range. For example, four first processing circuits 15A that realize the first integration function 153A and the first transfer function 155A are installed in the first PET imaging mechanism 10A, corresponding to the four angular ranges. Furthermore, four second processing circuits 15B that realize the second integration function 153B and the second transfer function 155B are installed in the second PET imaging mechanism 10B, corresponding to the four angular ranges. In this case, the four first processing circuits 15A and the four second processing circuits 15B are electrically connected, respectively, corresponding to the four angular ranges.

[0045] 1, a subject P to be scanned is placed on a bed 50, and the bed 50 moves the placed subject P. The bed 50 includes a base 51, a support frame 52, a top board 53, and a bed driving device .

[0046] The base 51 is placed on the floor. The base 51 is a housing that supports the support frame 52 so that it can move in a direction perpendicular to the floor (Y-axis direction). The support frame 52 is a frame that is provided on the upper part of the base 51. The support frame 52 supports the top plate 53 so that it can slide along the central axis Z. The top plate 53 is a flexible plate on which the subject P is placed.

[0047] The bed drive device 54 is housed in the housing of the bed 50. The bed drive device 54 is a motor or actuator that generates power to move the support frame 52 on which the subject P is placed and the tabletop 53. The bed drive device 54 operates under control of the console 70 or the like. The bed 50 is positioned so that the long axis of the tabletop 53 is parallel to the central axis Z of the opening of the PET gantry 10.

[0048] 1, the console 70 includes a PET data memory 71, a processing circuit 73, a display 74, a memory 75, and an input interface 76. For example, data communication between the PET data memory 71, the processing circuit 73, the display 74, the memory 75, and the input interface 76 is performed via a bus.

[0049] The PET data memory 71 is a storage device that stores single event data and coincidence event data transmitted from the PET gantry 10. That is, the PET data memory 71 stores first data and second data. The PET data memory 71 is a storage device such as an HDD (Hard Disk Drive), an SSD (Solid State Drive), or an integrated circuit storage device.

[0050] The processing circuitry 73 includes, as hardware resources, processors such as a CPU, MPU, and GPU (Graphics Processing Unit), and memories such as ROM and RAM. The processing circuitry 73 executes various programs read from the memory to implement a control function 731, a reconstruction processing function 733, an image processing function 735, and a display processing function 737. That is, the processing circuitry 73 corresponds to a processor that implements the function corresponding to each program by reading and executing the program from the memory. In other words, the processing circuitry 73 after reading each program has the function corresponding to the read program. The control function 731, the reconstruction processing function 733, the image processing function 735, and the display processing function 737 may be implemented by the processing circuitry 73 on a single board, or may be distributed and implemented by the processing circuits 73 on multiple boards. The processing circuits 73 that implement the control function 731, the reconstruction processing function 733, the image processing function 735, and the display processing function 737 correspond to a control unit, a reconstruction processing unit, an image processing unit, and a display processing unit, respectively.

[0051] The processing circuitry 73 controls the PET gantry 10 and the bed 50 using a control function 731 to perform PET imaging. The PET imaging according to this embodiment is a scan in which the imaging region of the subject P is moved to the FOV in accordance with the imaging region and / or drug related to the scan of the subject P to collect ET event data. The processing circuitry 73 is also capable of performing a positioning scan using the PET gantry 10 (hereinafter referred to as a PET positioning scan). For the PET positioning scan, the processing circuitry 73 synchronously controls the PET gantry 10 and the bed 50.

[0052] The processing circuitry 73 controls the transfer of the second data by the second transfer function 155B based on the agent used in the scan of the subject P using radiation and / or the imaging region of the subject P in the scan, using the control function 731. For example, when the scan of the subject P is performed on the heart of the subject P, the control function 731 controls the second transfer function 155B to limit the transfer of the second data to the first transfer function 155A.

[0053] Specifically, when a user inputs via the input interface 76 that the imaging region of the subject P is the heart and / or that the name of the drug used during the scan is a cardiac scan drug, the control function 731 controls the second transfer function 155B to restrict the transfer of the second data to the first transfer function 155A. Note that the control function 731 may identify that the imaging region of the subject P is the heart and / or the name of the cardiac scan drug from the examination order for the subject P transmitted from the RIS to the PET device 1 via the network by using a known language analysis process or the like.

[0054] Furthermore, when a scan of the subject P is performed on the whole body of the subject P, the control function 731 controls the second transfer function 155B to transfer the second data to the first transfer function 155A. Specifically, when a user inputs via the input interface 76 that the imaging region of the subject P is the whole body and / or that the name of the drug used during the scan is a whole-body scan drug, the control function 731 controls the second transfer function 155B to transfer the second data to the first transfer function 155A. Note that the control function 731 may identify that the imaging region of the subject P is the whole body and / or the name of the whole-body scan drug from the examination order for the subject P transmitted from the RIS to the PET device 1 via the network by using a known language analysis process or the like.

[0055] The processing circuitry 73 reconstructs a PET image showing the distribution of positron-emitting nuclides administered to the subject P using the reconstruction processing function 733 based on the coincidence event data. Specifically, the PET image is reconstructed using the first data and the second data. The reconstruction processing function 733 may reconstruct a first PET image based on the first data and a second PET image based on the second data. In this case, the reconstruction processing function 733 combines the first PET image and the second PET image to generate a PET image corresponding to the imaging region. The reconstruction processing function 733 may also generate a positioning image for PET based on the PET event data. Known methods such as iterative reconstruction and FBP can be used as appropriate for reconstructing the PET image, so a description thereof will be omitted.

[0056] The processing circuitry 73 performs various image processing on the PET image using the image processing function 735. For example, the image processing function 735 performs three-dimensional image processing such as volume rendering, surface volume rendering, pixel value projection processing, MPR (Multi-Planer Reconstruction) processing, and CPR (Curved MPR) processing on the PET image to generate a display image.

[0057] The processing circuitry 73 displays various information on the display 74 using the display processing function 737. For example, the display processing function 737 causes the display 74 to display the PET image reconstructed by the reconstruction processing function 733 and / or the PET image on which image processing has been performed by the image processing function 735. Furthermore, the display processing function 737 causes the display 74 to display a setting screen related to PET imaging prior to the execution of PET imaging.

[0058] The display 74 displays various information under the control of the processing circuit 73. As the display 74, for example, a CRT (Cathode Ray Tube) display, a liquid crystal display (LCD), an organic electroluminescence display (OLED), a light emitting diode (LED) display, a plasma display, or any other display known in the art can be appropriately used. The display 74 may be a desktop type, or may be configured as a tablet terminal or the like capable of wireless communication with the console 70.

[0059] The memory 75 is a storage device such as an HDD, SSD, or integrated circuit storage device that stores various information. The memory 75 may also be a drive or the like that reads and writes various information from and to a portable storage medium such as a CD (Compact Disc)-ROM drive, a DVD (Digital Versatile Disc) drive, or a flash memory. The memory 75 stores, for example, various data related to the execution of the control function 731, the reconstruction processing function 733, the image processing function 735, and the display processing function 737. The memory 75 stores upsampling data based on first data and second data collected by executing a PET scan on the subject P. The memory 75 stores various programs related to the execution of the control function 731, the reconstruction processing function 733, the image processing function 735, and the display processing function 737.

[0060] The input interface 76 accepts various input operations from the user, converts the accepted input operations into electrical signals, and outputs the electrical signals to the processing circuitry 73. For example, the input interface 76 may be, for example, a mouse, keyboard, trackball, switch, button, joystick, touchpad, touch panel display, or the like. Note that, in this embodiment, the input interface 76 is not limited to a device equipped with physical operation components such as a mouse, keyboard, trackball, switch, button, joystick, touchpad, or touch panel display. For example, an electrical signal processing circuit that receives an electrical signal corresponding to an input operation from an external input device provided separately from the device and outputs the electrical signal to the processing circuitry 73 is also included as an example of the input interface 76. The input interface 76 may also be configured as a tablet terminal or the like that is capable of wireless communication with the console 70.

[0061] The above has described the overall configuration of the PET device 1. Below, a description will be given of the process for controlling the transfer of PET event data during execution of PET imaging (hereinafter referred to as data transfer control process).

[0062] 2 is a flowchart showing an example of the procedure of the data transfer control process. To specifically explain the data transfer control process, it is assumed that the first data and the second data are integrated in the four angle ranges as described above.

[0063] (Step S201) The names of the imaging region and / or the medication are set by a user instruction via the input interface 76 or by analysis of the examination order. As a result, the names of the imaging region and / or the medication are input to the processing circuitry 73. Also, in this step, various imaging conditions for PET imaging of the subject P are input and set. At this time, the processing circuitry 73 then controls the transfer of the second data by the second transfer function 155B using the control function 731 based on the set medication and / or imaging region.

[0064] (Step S202) The processing circuitry 73 starts PET imaging of the subject P using the imaging conditions set by the control function 731. For example, prior to PET imaging, the control function 731 determines a position on the PET gantry 10 where the imaging region can be imaged (hereinafter referred to as the imaging position) based on the set imaging region. Next, the control function 731 controls the bed driving device 54 in response to a user instruction via the input interface 76 to move the tabletop 53 on which the subject P is placed to the imaging position. As a result, the tabletop 53 on which the subject P is placed moves to the imaging position. Next, the set drug is injected into the subject P.

[0065] (Step S203) If the imaging region is the heart (YES in step S203), the process proceeds to step S206. If the imaging region is not the heart (NO in step S203), that is, if the imaging region is the whole body, the process proceeds to step S204.

[0066] FIG. 3 is a diagram showing an example of PET imaging of the heart H of a subject P. As shown in FIG. 3, prior to PET imaging, the heart H of the subject P is placed in the imaging field of view of the first detector ring 11A. As shown in FIG. 3, administration of a drug to the subject P causes gamma rays GR to be emitted from the heart H of the subject P. The gamma rays GR emitted from the heart H are mainly detected by the first detector 17A in the first detector ring 11A. At this time, the gamma rays GR emitted from the heart H may also be detected by the second detector 17B in the second detector ring 11B. The count rate related to the detection of gamma rays GR by the first detector 17A is higher than the count rate related to the detection of gamma rays GR by a drug used in a whole-body scan of the subject P. In FIG. 3, the count rate is represented by the density of gamma rays GR.

[0067] FIG. 4 illustrates an example of PET imaging of the whole body of a subject P. As shown in FIG. 4, prior to PET imaging, the whole body of the subject P is positioned in the field of view of the first and second detector rings 11A and 11B. As shown in FIG. 4, gamma rays GR are emitted from the whole body of the subject P due to administration of a drug to the subject P. The gamma rays GR emitted from the whole body of the subject P are detected by the first detector 17A in the first detector ring 11A and the second detector 17B in the second detector ring 11B. In FIG. 4, the count rate is indicated by the density of the gamma rays GR. The count rate related to the detection of the gamma rays GR by the first detector 17A and the second detector 17B is lower than the count rate related to the detection of the gamma rays GR by the drug used in the cardiac scan of the subject P shown in FIG. 4. As shown in FIG. 4, 22nd data generated by the detection of the gamma rays GR by the second detector 17B is transferred to the first processing circuit 15A for the first detector ring 11A. An arrow DT in FIG. 4 indicates an example of the transfer of the second data.

[0068] (Step S204) The second transfer function 155B acquires (receives) information on the amount of first data generated per unit time from the first processing circuit 15A. Next, the second transfer function 155B calculates the sum of the maximum value of the second transfer rate and the amount of first data generated per unit time (total first data amount). The total first data amount corresponds to the total amount of data that needs to be transferred from the first transfer function 155A to the console 70 when the maximum amount of second data is transferred from the second transfer function 155B.

[0069] (Step S205) The second transfer function 155B compares the first total data amount with the maximum value of the first transfer speed. If the first total data amount exceeds the maximum value of the first transfer speed (Yes in step S205), the process proceeds to step S206. If the first total data amount does not exceed the maximum value of the first transfer speed (No in step S205), that is, if the first total data amount is equal to or less than the maximum value of the first transfer speed, the process proceeds to step S207.

[0070] (Step S206) The second processing circuit 15B restricts the transfer of the second data by the second transfer function 155B and transfers the second data to the first processing circuit 15A. The restriction of the second data and the transfer of the second data are performed for each of the four angle ranges. Specifically, if the imaging region is the heart H or the drug used for PET imaging is a cardiac scan drug, the second transfer function 155B stops the transfer of the second data to the first processing circuit 15A.

[0071] Furthermore, if the imaging region is the whole-body heart or the drug used in PET imaging is a cardiac scan drug, the second transfer function 155B limits the amount of second data to be transferred so that the total amount of first data does not exceed the maximum value of the first transfer rate, and transfers the limited amount of second data to the first processing circuit 15A. Note that the second transfer function 155B may temporarily store the amount of second data corresponding to the difference between the total amount of first data and the maximum value of the first transfer rate, or the second data itself, in a memory in the second processing circuit 15B or a memory associated with the second transfer function 155B. The transfer of the second data with the limit and the storage of the second data in the memory are performed for each of the four angle ranges.

[0072] (Step S207) The second processing circuit 15B transfers the second data to the first processing circuit 15A without any restrictions by the second transfer function 155B. At this time, the transfer of the second data is performed for each of the four angle ranges.

[0073] (Step S208) The first transfer function 155A transfers the second data and the first data to the console 70. If the second data has not been transferred from the second transfer function 155B, the first transfer function 155A transfers the first data to the console 70. At this time, the processing circuit 73 causes the control function 731 to store the first data and the second data in the PET data memory 71. At this time, the first data and the second data indicate information related to the detection position, so that the PET event data can be identified at the transfer destination console 70.

[0074] (Step S209) If the PET imaging has not ended (NO in step S209), the processes from step S203 onward are repeated. If the PET imaging has ended (YES in step S209), the data transfer control process ends. The processes from step S203 to step S209 may be performed each time a gamma ray GR is detected, for example, each time the first data and second data are generated (each event), or may be repeated at predetermined time intervals.

[0075] Fig. 5 is a diagram showing an example of the transfer of second data and the transfer of first data. The graph on the right side of Fig. 5 shows an example of the data transfer size (second transfer rate) of the second data relative to the size (packet length) of the second data for one event detected by the second detector 17B. The graph on the left side of Fig. 5 shows an example of the data transfer size (first transfer rate) of the first data relative to the size (packet length) of the first data and the size of the second data for one event detected by the first detector 17A.

[0076] As shown in Fig. 5, the sum of the data amounts of the first data and the second data (total first data amount) is smaller than the maximum value of the first transfer rate. Therefore, the process of step S207 is executed. That is, the second transfer function 155B transfers the second data shown in Fig. 5 to the first processing circuit 15 (first transfer function 155A). As shown in Fig. 5, in a whole-body scan, the first transfer function 155A transfers the first data and the second data to the console 70, and therefore the data communication capacity of the first transfer function 155A is effectively utilized.

[0077] From the above, the radiation tomography imaging apparatus of the embodiment has a first detector ring 11A configured by arranging a plurality of first detectors 17A that detect radiation in a ring shape with the long axis direction of the tabletop 53 on which the subject P is placed as the central axis Z, and a second detector ring 11B configured by arranging a plurality of second detectors 17B that detect radiation in the ring shape and arranged adjacent to the first detector ring 11A, and has a first transfer unit 155A that transfers first data generated based on outputs from the plurality of first detectors 17A and second data generated based on outputs from the plurality of second detectors 17B to the console 70, and a second transfer unit 155B that transfers the second data to the first transfer unit 155A, and controls the transfer of the second data by the second transfer unit 155B based on the drug used in the scan of the subject P using radiation and / or the imaging region of the subject P in the scan.

[0078] Furthermore, the radiation tomography imaging apparatus of the embodiment integrates a plurality of first data based on outputs from a plurality of first detectors 17A that fall within a predetermined angular range relative to the central axis Z, integrates a plurality of second data based on outputs from a plurality of second detectors 17B that fall within a predetermined angular range, transfers the integrated first data and the integrated second data to the console 70 for each angular range, transfers the integrated second data to the first integration function 153A for each angular range, and the first integration function 153A, the second integration function 153B, the first transfer function 155A, and the second transfer function 155B are electrically connected for each angular range.

[0079] For example, the radiation tomography apparatus according to the embodiment limits the transfer of the second data when a scan is performed on the heart H of the subject P, and transfers the second data to the first transfer unit 155A when a scan is performed on the whole body of the subject P. In addition, in the radiation tomography apparatus according to the embodiment, the first data transfer rate by the first transfer unit 155A is faster than the second data transfer rate by the second transfer unit 155B. In addition, the radiation tomography apparatus according to the embodiment stores the second data in memory when the sum of the data amount per unit time of the first data and the data amount per unit time of the second data exceeds the maximum value of the first transfer rate.

[0080] For these reasons, according to the radiation tomography imaging apparatus of the embodiment, by electrically connecting the second DAS in the second PET imaging mechanism 10B, which is extended along the longitudinal direction of the tabletop 53 relative to the existing PET imaging mechanism (first PET imaging mechanism 10A), and the first DAS in the first PET imaging mechanism 10A, for example, according to the angle range, data transfer can be performed without changing the existing DAS configuration even when the radiation detectors are extended. As a result, according to the radiation tomography imaging apparatus of the embodiment, scanning in the longitudinal axis field of view can be achieved using the existing DAS configuration, so there is no need to redesign the data acquisition system, and the length and number of cables related to data transfer can be minimized, thereby reducing increases in manufacturing costs and maintenance burdens.

[0081] Furthermore, the radiation tomography imaging apparatus according to the embodiment can control the transfer of the second data in accordance with the imaging region or drug of the subject P. As a result, the radiation tomography imaging apparatus according to the embodiment can efficiently utilize communication resources in accordance with the scan target, as shown in Fig. 5, for example, thereby reducing the number of cables required for data transfer and the number of empty packets, thereby achieving efficient data communication.

[0082] As described above, the radiation tomography imaging apparatus according to the embodiment can efficiently transfer data related to scanning in a longitudinal axis field of view while reducing increases in manufacturing costs and maintenance burdens.

[0083] (First Modification) In the embodiment, the first data and the second data are generated by integrating the PET event data for each predetermined angle range, and then integrated for each predetermined angle range. However, in this modification, the PET event data is not integrated. That is, in this modification, data transfer is performed for the first data and the second data for each pair of first detectors and each pair of second detectors. Therefore, in this modification, the first integration function 153A and the second integration function 153B are unnecessary.

[0084] Therefore, in the radiation tomography apparatus according to the first modification of the embodiment, the first transfer function 155A for the first detectors 17A and the second detectors 17B that are located in the same direction relative to the central axis Z and the second transfer function 155B for the second detectors that are located in the same direction are electrically connected by a transfer line that transfers second data. Other configurations are similar to those of the embodiment, and therefore descriptions thereof will be omitted. Furthermore, the data transfer control process and effects of this modification are similar to those of the embodiment, except for the data integration, and therefore descriptions thereof will be omitted.

[0085] (Second Modification) In contrast to the embodiment and the first modified example, this modified example further includes, in addition to the existing PET imaging mechanism (first PET imaging mechanism) 10A and second PET imaging mechanism 10B, a PET imaging mechanism (hereinafter referred to as a third PET imaging mechanism) that is further expanded from the existing first PET imaging mechanism 10A. The third PET imaging mechanism has a third detector ring, a third signal processing circuit, and a third processing circuit. The various functions and configurations of the third PET imaging mechanism are the same as those of the second PET imaging mechanism 10B. The first PET imaging mechanism 10A, the second PET imaging mechanism 10B, and the third PET imaging mechanism are daisy-chain connected, i.e., connected like beads, for data transfer. Below, the processing and functions that differ between this modified example and the embodiment will be described.

[0086] The first processing circuit 15A transfers the first data, the second data, and the third data generated based on the outputs of the plurality of third detectors to the console 70 via the first transfer function 155A. For example, the first transfer function 155A transfers the integrated first data, the integrated second data, and the integrated third data to the console 70 for each angle range. The third data and the integrated third data will be described later. Note that the first transfer rate may be faster than the second transfer rate and the data transfer rate by a third transfer function described later (hereinafter referred to as the third transfer rate).

[0087] The second processing circuit 15B transfers the second data and the third data to the first transfer function 155A in the first processing circuit 15A via the second transfer function 155B. For example, the second transfer function 155B is controlled by the control function 731 to transfer the second data and the third data based on the agent used in the scan of the subject P using radiation and / or the region of the subject P being imaged in the scan. The control of the transfer of the second data and the third data will be described later. Once the second data and the third data have been transferred to the first transfer function 155A, the first transfer function 155A transfers the first data, the second data, and the third data to the console 70.

[0088] Specifically, the second transfer function 155B transfers the second data integrated for each of the four angle ranges and the third data integrated for each of the four angle ranges to the first transfer function 155A for each angle range under the control of the control function 731. At this time, the first transfer function 155A transfers the first data, second data, and third data for each angle range to the console 70. The second transfer speed is, for example, the same as (approximately the same as) the third transfer speed.

[0089] If the sum of the data amount per unit time of the first data, the data amount per unit time of the second data, and the data amount per unit time of the second data exceeds the maximum value of the first transfer rate, the second transfer function 155B stores the second data and / or the third data in the memory of the second processing circuit 15B. Specifically, the second transfer function 155B receives information on the data amount per unit time of the first data from the first transfer function 155A. In addition, the second transfer function 155B receives the third data from the third transfer function. At this time, the second transfer function 155B uses the information on the data amount per unit time of the first data and the third data to calculate the sum of the data amount per unit time of the first data, the data amount per unit time of the second data, and the data amount per unit time of the third data. Next, the second transfer function 155B compares the calculated sum with the maximum value of the first transfer rate and determines whether the calculated sum exceeds the maximum value of the first transfer rate.

[0090] If the calculated sum exceeds the maximum value of the first transfer rate, the second transfer function 155B stores the second data and / or the third data in memory associated with the second processing circuit 15B or the second transfer function 155B. If the calculated sum does not exceed the maximum value of the first transfer rate, the second transfer function 155B transfers the second data and the third data to the first transfer function 155A.

[0091] If the second data and / or the third data is stored in the memory associated with the second processing circuit 15B or the second transfer function 155B, the second transfer function 155B uses information on the amount of first data generated per unit time to calculate the sum of the maximum value of the second transfer rate and the amount of first data generated per unit time. Then, the second transfer function 155B compares the calculated sum with the maximum value of the first transfer rate and determines whether the calculated sum exceeds the maximum value of the first transfer rate.

[0092] If the calculated sum exceeds the maximum value of the first transfer rate, the second transfer function 155B stores in memory, for example, the second data and / or the third data, for data that exceeds the amount of data that can be transferred at the first transfer rate. In other words, if the amount of data transferred to the console 70 by the first transfer function 155A (the total amount of the first data, the second data, and the third data (hereinafter referred to as the total data amount)) exceeds the maximum value of the first transfer rate, the second transfer function 155B limits the transfer of the second data and the third data to the first transfer function 155A.

[0093] The third PET imaging mechanism has a third detector ring, a third signal processing circuit, and a third processing circuit. The third detector ring has a plurality of third detectors arranged on a circumference around the central axis Z. The third detector corresponds to a gamma ray detector that detects gamma rays. An image field of view (FOV) is set at the opening of the third detector ring.

[0094] The third detector detects pair annihilation gamma rays emitted from inside the body of the subject P. The third detector generates an electrical signal according to the light intensity of the detected pair annihilation gamma rays. For example, the third detector has multiple detection elements (multiple scintillators and multiple photomultiplier tubes). The electrical signal generated by the photomultiplier tube according to the light intensity of the scintillation light is supplied to a third signal processing circuit. Note that the third detector may be realized by a DOI detector.

[0095] The third signal processing circuit generates single event data by performing, for example, detection time measurement processing, position calculation processing, and energy calculation processing on the electrical signal output from the third detector. The third signal processing circuit is realized by an ASIC, FPGA, CPLD, or SPLD configured to be able to execute the detection time measurement processing, position calculation processing, and energy calculation processing. The third signal processing circuit monitors the peak value of the electrical signal from the third detector through the detection time measurement processing, measures the time when the peak value exceeds a predetermined threshold as the detection time, and electrically detects pair annihilation gamma rays. The third signal processing circuit calculates the incident position of the pair annihilation gamma rays based on the electrical signal from the third detector through the position calculation processing. The third signal processing circuit calculates the energy value of the detected pair annihilation gamma rays based on the electrical signal from the third detector through the energy calculation processing.

[0096] The third signal processing circuit generates single event data by associating data on the detection time, data on the position coordinates, and data on the energy value related to the single event. The third signal processing circuit generates single event data one after another every time a pair annihilation gamma ray is detected, and outputs the generated single event data to the third processing circuit.

[0097] The third processing circuit has a third coincidence counting function, a third integration function, and a third transfer function. The third processing circuit is realized using hardware resources such as an ASIC, FPGA, CPLD, or SPLD. The third processing circuit may be realized using various processors and memories, without being limited to an ASIC, FPGA, CPLD, or SPLD. The third processing circuit that realizes the third coincidence counting function, the third integration function, and the third transfer function corresponds to a third coincidence counting unit, a third integration unit, and a third transfer unit, respectively. The third processing circuit that realizes the third coincidence counting function, the third integration function, and the third transfer function may be realized by different circuits, such as a third coincidence counting circuit, a third integration circuit, and a third transfer circuit. The third signal processing circuit and the third processing circuit may be integrated and referred to as a third DAS. The third processing circuit may be provided for each predetermined angle range. In this case, the third processing circuit functions as a data integration relay hub.

[0098] The third coincidence function performs coincidence processing on the single event data from the third signal processing circuit. In the coincidence processing, the third coincidence function repeatedly identifies single event data relating to two single events that fall within a predetermined time frame from the repeatedly supplied single event data. The line connecting the pair of third detectors (more specifically, scintillators) that detected the pair annihilation gamma rays is the LOR. The PET event data (coincidence event data and single event data) generated by the third PET imaging mechanism is called the third data.

[0099] Although the third signal processing circuit and the third coincidence counting function are included in the third PET imaging mechanism in the above configuration, this embodiment is not limited thereto. For example, both the third signal processing circuit and the third coincidence counting function, or only the third coincidence counting function, may be included in the console 70. In this case, the electrical signal or single-event data output from the third detector corresponds to the third data. Furthermore, one third coincidence counting function may be provided for each of the multiple third signal processing circuits included in the third PET imaging mechanism, or the multiple third signal processing circuits included in the third PET imaging mechanism may be divided into multiple groups, and one third coincidence counting function may be provided for each group. The groups may be divided, for example, into groups corresponding to the multiple third detectors included in a predetermined angular range relative to the central axis Z. For the sake of concreteness, the following description will be given assuming that the predetermined angular range is one of the four angular ranges (first range, second range, third range, and fourth range) as described above.

[0100] The third integration function integrates multiple pieces of third data based on outputs from multiple third detectors that are included in a predetermined angle range with respect to the central axis Z, among the multiple third detectors. Specifically, the third integration function integrates PET event data included in a first range to generate third data corresponding to the first range. Furthermore, the third integration function integrates PET event data included in a second range to generate third data corresponding to the second range. Furthermore, the third integration function integrates PET event data included in the third range to generate third data corresponding to the third range. Furthermore, the third integration function integrates PET event data included in a fourth range to generate third data corresponding to the fourth range.

[0101] The third transfer function transfers the third data generated based on outputs from the multiple third detectors to the second transfer function 155B in the second processing circuit 15B. For example, the third transfer function is controlled by the control function 731 to transfer the third data based on the agent used in a scan of the subject P using radiation and / or the region of the subject P being imaged in the scan. Control of the transfer of the third data will be described later. When the third data is transferred to the second transfer function 155B, the second transfer function 155B transfers the second data and the third data to the console 70.

[0102] Specifically, the third transfer function transfers the third data integrated for each of the four angle ranges to the second transfer function 155B for each angle range under the control of the control function 731. At this time, the second transfer function 155B transfers the second data and the third data for each angle range to the console 70. Note that the third transfer speed may be the same as (approximately the same as) the second transfer speed, or may be faster than the second transfer speed.

[0103] If the sum of the data amount per unit time of the second data and the data amount per unit time of the third data exceeds the maximum value of the second transfer rate, the third transfer function stores the third data in memory. Specifically, the third transfer function receives information on the data amount per unit time of the second data from the second transfer function 155B. At this time, the third transfer function calculates the sum of the data amount per unit time of the second data and the data amount per unit time of the third data using the information on the data amount per unit time of the second data. Next, the third transfer function compares the calculated sum with the maximum value of the second transfer rate and determines whether the calculated sum exceeds the maximum value of the second transfer rate.

[0104] If the calculated sum exceeds the maximum value of the second transfer rate, the third transfer function stores the third data in a third processing circuit or memory associated with the third transfer function. If the calculated sum does not exceed the maximum value of the second transfer rate, the third transfer function transfers the third data to second transfer function 155B.

[0105] Furthermore, when the third data is stored in the memory associated with the third processing circuit or the third transfer function, the third transfer function uses information about the amount of second data generated per unit time to calculate the sum of the maximum value of the third transfer rate and the amount of second data generated per unit time. The third transfer function then compares the calculated sum with the maximum value of the second transfer rate and determines whether the calculated sum exceeds the maximum value of the second transfer rate. If the calculated sum exceeds the maximum value of the second transfer rate, the third transfer function stores the third data in memory, for example, for data that exceeds the amount of data that can be transferred at the second transfer rate. That is, if the amount of data transferred by the second transfer function 155B to the first transfer function 155A (the total amount of the second data and the third data (hereinafter referred to as the second total data amount)) exceeds the maximum value of the second transfer rate, the third transfer function limits the transfer of the third data to the second transfer function 155B.

[0106] The first integrating function 153A, the second integrating function 153B, the third integrating function, the first forwarding function 155A, the second forwarding function 155B, and the third forwarding function are electrically connected (daisy chain) for each angle range. For example, the first processing circuit 15A, the second processing circuit 15B, and the third processing circuit are electrically connected corresponding to the four angle ranges, respectively.

[0107] The processing circuitry 73 further controls, via the control function 731, the transfer of the third data by the third transfer function based on the drug used in the scan of the subject P using radiation and / or the imaging region of the subject P in the scan. For example, when the scan of the subject P is performed on the heart H of the subject P, the control function 731 controls the third transfer function to restrict the transfer of the third data to the second transfer function 155B. Specifically, when a user instructs via the input interface 76 that the imaging region of the subject P is the heart H and / or the name of the drug used in the scan is a cardiac scan drug, the control function 731 controls the third transfer function to restrict the transfer of the third data to the second transfer function 155B.

[0108] Furthermore, when a scan of the subject P is performed on the whole body of the subject P, the control function 731 controls the third transfer function to transfer the third data to the second transfer function 155B. Specifically, when a user instructs via the input interface 76 to input that the imaging region of the subject P is the whole body and / or that the name of the drug used during the scan is a whole-body scan drug, the control function 731 controls the third transfer function to transfer the third data to the second transfer function 155B.

[0109] The data transfer process in this modification is the same as the flowchart of the data transfer process shown in Fig. 2, but with the addition of processing content executed by the control function 731, first transfer function 155A, second transfer function 155B, third integration function, and third transfer function. The processing related to the transfer of the third data corresponds to the processing added in a nested structure to the data transfer process shown in Fig. 2. For these reasons, to avoid redundant explanation, the explanation of the data transfer process in this modification will be omitted.

[0110] From the above, the radiation tomography imaging apparatus according to the second modified embodiment is configured by arranging third detectors that detect radiation in a circular pattern, and further includes a third detector ring arranged adjacent to the second detector ring 11B, and a third transfer function that transfers third data generated based on the output from the third detector to the second transfer function 155B, the second transfer function 155B transfers the second data and the third data to the first transfer function 155A, and the first transfer function 155A transfers the first data, the second data, and the third data to the console 70, and controls the transfer of the third data by the third transfer function based on the drug and / or the imaging site, and the first detector 17A, the second detector 17B, and the third detector that are positioned in the same direction relative to the central axis are electrically connected by a daisy chain for the transfer of the third data.

[0111] According to the radiation tomography apparatus of the second modified embodiment, it is possible to further expand the longitudinal axis field of view of the existing PET imaging mechanism (first PET imaging mechanism 10A) at low cost along the longitudinal axis direction of the tabletop 53. Other effects are the same as those of the embodiment, and therefore description thereof will be omitted.

[0112] When the technical idea of ​​this embodiment is realized in a data transfer control method, the data transfer control method transfers, to the console 70, first data generated based on outputs from a plurality of first detectors 17A arranged in an annular shape with the central axis Z in the longitudinal direction of the tabletop 53 on which the subject P is placed, and second data generated based on outputs from a plurality of second detectors 17B that detect radiation and are adjacent to the plurality of first detectors 17A along the longitudinal axis, and controls the transfer of the second data by the second transfer unit 155B to the first transfer unit 155A prior to the transfer of the second data to the console 70, based on the agent used in the scan of the subject P using radiation and / or the region of the subject P being imaged in the scan. The processing procedures and effects of the data transfer control method are similar to those of the embodiment, and therefore description thereof will be omitted.

[0113] When the technical idea of ​​this embodiment is realized by a data transfer control program, the data transfer control program causes a computer to transfer first data generated based on output from a plurality of first detectors 17A arranged in a ring shape with the longitudinal direction of the tabletop 53 on which the subject P is placed as the central axis Z, and second data generated based on output from a plurality of second detectors 17B that detect radiation adjacent to the plurality of first detectors 17A along the longitudinal direction and detect radiation, to the console 70 by the first transfer unit 155A, and prior to transferring the second data to the console 70, transfer the second data to the first transfer unit 155A by the second transfer unit 155B, and control the transfer of the second data to the first transfer unit 155A by the second transfer unit 155B based on the drug used in the scan of the subject P using radiation and / or the imaging area of ​​the subject P in the scan.

[0114] For example, the data transfer control process can be realized by installing a data transfer control program in a computer in the console 70 of the radiation tomography apparatus and expanding the installed data transfer control program in the memory of the computer in the console 70. In this case, the program that can cause the computer to execute the method can also be stored and distributed on a storage medium such as a magnetic disk (such as a hard disk), an optical disk (such as a CD-ROM or DVD), or a semiconductor memory. The processing procedures and effects of the data transfer control process are the same as those in the embodiment, so a description thereof will be omitted.

[0115] According to at least one of the embodiments and modifications described above, in a radiation tomography imaging apparatus with a longitudinal axis field of view, it is possible to suppress an increase in cost and to efficiently transfer data.

[0116] Although several embodiments of the present invention have been described, these embodiments are presented as examples and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, substitutions, and modifications can be made without departing from the spirit of the invention. These embodiments and their modifications are included within the scope and spirit of the invention, as well as within the scope of the invention described in the claims and their equivalents. [Explanation of symbols]

[0117] 1 PET device 10 PET gantry 10A 1st PET imaging mechanism 10B Second PET imaging mechanism 11A First detector ring 11B Second detector ring 13A First signal processing circuit 13B Second signal processing circuit 15A 1st processing circuit 15B Second processing circuit 17A First detector 17B Second detector 50 berths 51 Foundation 52 Support frame 53 Top plate 54 Bed drive unit 70 Console 71 PET data memory 73 Processing Circuit 74 Display 75 memory 76 Input Interface 151A 1st coincidence function 151B Second coincidence function 153A First Integrated Function 153B Second Integrated Function 155A First Transfer Function 155B Second Transfer Function 731 Control Functions 733 Reconstruction Processing Function 735 Image Processing Function 737 Display Processing Function

Claims

1. a first detector ring configured by arranging a plurality of first detectors for detecting radiation in an annular shape with a central axis in the longitudinal direction of a tabletop on which the subject is placed; a second detector ring configured by arranging a plurality of second detectors in the annular shape to detect the radiation and disposed adjacent to the first detector ring; a first transfer unit that transfers first data generated based on outputs from the plurality of first detectors and second data generated based on outputs from the plurality of second detectors to a console; a second transfer unit that transfers the second data to the first transfer unit; a control unit that controls the transfer of the second data by the second transfer unit based on a drug used in a scan of the subject using the radiation and / or an imaging region of the subject in the scan; A radiation tomography imaging device having the same.

2. When the scan is performed on a heart of the subject, the second transfer unit restricts transfer of the second data; When the scan is performed on the whole body of the subject, the second transfer unit transfers the second data to the first transfer unit. The radiation tomography apparatus according to claim 1 .

3. a first transfer rate of data by the first transfer unit is faster than a second transfer rate of data by the second transfer unit; The radiation tomography apparatus according to claim 1 .

4. when a sum of a data amount per unit time of the first data and a data amount per unit time of the second data exceeds a maximum value of the first transfer speed, the second transfer unit stores the second data in a memory; The radiation tomography apparatus according to claim 3 .

5. a first transfer unit for a first detector located in the same direction with respect to the central axis among the plurality of first detectors and the plurality of second detectors, and a second transfer unit for a second detector located in the same direction are electrically connected by a transfer line that transfers the second data; The radiation tomography apparatus according to claim 1 .

6. a first integration unit that integrates a plurality of the first data based on outputs from a plurality of first detectors included in a predetermined angle range with respect to the central axis among the plurality of first detectors; a second integration unit that integrates a plurality of second data based on outputs from a plurality of second detectors included in the predetermined angle range among the plurality of second detectors; the first transfer unit transfers the integrated first data and the integrated second data to the console for each of the angle ranges; the second transfer unit transfers the integrated second data to the first integration unit for each of the angle ranges; the first integrated section, the second integrated section, the first transfer section, and the second transfer section are electrically connected for each of the angle ranges. The radiation tomography apparatus according to any one of claims 1 to 5.

7. a third detector ring configured by arranging third detectors that detect the radiation in the annular shape and disposed adjacent to the second detector ring; a third transfer unit that transfers third data generated based on an output from the third detector to the second transfer unit, the second transfer unit transfers the second data and the third data to the first transfer unit; the first transfer unit transfers the first data, the second data, and the third data to the console; the control unit controls the transfer of the third data by the third transfer unit based on the drug and / or the imaging site; the first detector, the second detector, and the third detector, which are positioned in the same direction with respect to the central axis, are electrically connected by a daisy chain for the transfer of the third data. The radiation tomography apparatus according to any one of claims 1 to 5.

8. the first detector ring is configured to image a heart of the subject; the second detector ring is configured to image the entire body of the subject excluding the heart; The radiation tomography apparatus according to any one of claims 1 to 5.

9. the agent is an agent related to a cardiac scan of the subject or an agent related to a whole-body scan of the subject, The imaging site is the heart or the whole body. The radiation tomography apparatus according to any one of claims 1 to 5.

10. a first transfer unit transferring to a console first data generated based on outputs from a plurality of first detectors arranged in an annular shape with a central axis in the longitudinal direction of a tabletop on which the subject is placed, and second data generated based on outputs from a plurality of second detectors that detect radiation and are adjacent to the plurality of first detectors along the longitudinal direction, the second data being second data; a second transfer unit transfers the second data to the first transfer unit prior to the transfer of the second data to the console; controlling the transfer of the second data by the second transfer unit to the first transfer unit based on a drug used in a scan of the subject using the radiation and / or an imaging region of the subject in the scan; A data transfer control method comprising:

11. On the computer, a first transfer unit transferring to a console first data generated based on outputs from a plurality of first detectors arranged in an annular shape with a central axis in the longitudinal direction of a tabletop on which the subject is placed, and second data generated based on outputs from a plurality of second detectors that detect radiation and are adjacent to the plurality of first detectors along the longitudinal direction, the second data being second data; a second transfer unit transfers the second data to the first transfer unit prior to the transfer of the second data to the console; controlling the transfer of the second data by the second transfer unit to the first transfer unit based on a drug used in a scan of the subject using the radiation and / or an imaging region of the subject in the scan; A data transfer control program that realizes this.

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