JP5972554B2 - Nuclear medicine diagnostic equipment - Google Patents

Description

  Embodiments described herein relate generally to a nuclear medicine diagnostic apparatus.

  For example, the nuclear medicine diagnosis apparatus collects PET as follows (see, for example, Patent Document 1). First, a drug labeled with a radioisotope that emits positron is administered to a subject. The nuclear medicine diagnostic apparatus repeatedly detects gamma rays emitted from the subject using a plurality of photodetectors arranged in a ring shape around the subject. Then, the gamma ray detection time is used as a time stamp, and two gamma rays detected within a predetermined time frame are identified. The two identified gamma rays are presumed to have been generated from the same pair annihilation point. The nuclear medicine diagnostic apparatus estimates that there is a pair annihilation point on a line (LOR: line of response) connecting a pair of simultaneously measured detectors. Thus, identification of two gamma rays generated from the same pair annihilation point is called simultaneous measurement (coincidence). The nuclear medicine diagnostic apparatus generates PET image data based on an output signal from a photodetector relating to LOR.

  In a conventional nuclear medicine diagnosis apparatus, when an IC board provided in a data collection system detects the possibility of failure due to temperature, the entire apparatus is turned off to prevent the IC board from failing.

JP 2003-279852 A

  However, in the above method, when the IC board is likely to break down due to temperature, the entire apparatus is turned off, and the user cannot continue the examination in the clinical field.

  The objective is to improve throughput by allowing the device to operate as continuously as possible.

Nuclear medicine diagnosis apparatus according to this embodiment is provided adjacent each a plurality of gamma ray detectors for detecting gamma rays emitted from the radiation the position elements is administered to the subject, the plurality of gamma ray detectors, A plurality of data collection systems in which analog-digital circuits are formed, a power supply unit for supplying power to each of the plurality of data collection systems, and a plurality of cooling fans for cooling each of the plurality of data collection systems A plurality of cooling fan units, a first comparison unit that compares a rotation speed of each of the plurality of cooling fans with a first threshold value, and a rotation speed of the cooling fan that exceeds the first threshold value among the plurality of cooling fans. a second comparator for comparing the second threshold value, the case where a plurality of cooling fans each rotational speed exceeds the first threshold value, the plurality of data The control power supply unit with respect to the collection system, respectively in order to to continue power supply, the is a plurality of cooling fans each rotational speed is equal to or less than the first threshold value, if greater than the second threshold value, a warning signal Generating an output control signal for generating the power, and controlling the power supply unit to continue power supply to each of the plurality of data collection systems, and controlling at least one of the plurality of cooling fans. A first control unit that controls the cooling fan unit to increase the rotation speed of the cooling fan whose rotation speed is less than or equal to the second threshold when the rotation speed is less than or equal to the second threshold.

It is a block diagram which shows the structure of PET-CT which concerns on this embodiment. It is the block diagram which showed the structure of PET stand 2 in FIG. 1A in detail. It is a figure which shows the detail of the gamma ray detector 21 in FIG. 1B. It is the figure which showed in detail the relationship between the data collection system unit 22, the gamma-ray detector 21, the system control part 11, IC board 75, and the electric power supply part 40 in PET apparatus in FIG. 1B. It is the figure which showed the structure of the data collection system unit 22 in PET apparatus in FIG. 3 in detail. It is the figure which showed typically the structure of the cooling fan 84 and the cooling fan unit 841. FIG. It is the figure which showed the flow of the degeneracy mode which starts from the cooling fan rotational speed detection about each cooling fan 843 which exists in the same data collection system unit 22 in the PET apparatus based on this embodiment. It is the figure which showed the flow of the degeneracy mode which starts from the thermal radiation temperature detection for every cooling fan 843 which exists in the same data collection system unit 22 in the PET apparatus based on this embodiment. It is the figure which showed the flow of the degeneration mode which starts from the ambient temperature detection of IC board 75 which exists in the same data collection system unit 22 in the PET apparatus based on this embodiment. It is the figure which showed typically the detail of the image correction described in FIG.

  Hereinafter, the nuclear medicine diagnosis apparatus according to the present embodiment will be described with reference to the drawings. In the following description, components having substantially the same function and configuration are denoted by the same reference numerals, and redundant description will be given only when necessary. Note that the nuclear medicine diagnostic apparatus according to this embodiment is any one of a gamma camera, SPECT, and PET. In the following description, a PET-CT apparatus having PET will be described.

  FIG. 1A is a block diagram showing the overall configuration of a PET-CT apparatus according to the present invention. A PET-CT apparatus 100 has a CT gantry 1 having an imaging unit that performs tomographic imaging of a subject P with X-rays, and administers a radiopharmaceutical to the subject P, and images a positron emitted from the body of the subject P. Accordingly, the PET gantry 2 having an imaging unit that performs tomography of the subject P, the top plate 59 on which the subject P is placed, the bed 5 that supports the top plate 59 and moves the top plate 59, and the CT gantry 1 includes a high voltage generation unit 92 that generates a high voltage necessary for X-ray irradiation, and an X-ray control unit 91.

  The PET-CT apparatus 100 includes a mechanism unit 4 that tilts the CT gantry 1, moves the PET gantry 2, moves the bed 5, or moves the top plate 59, and the detectors of the CT gantry 1 and the PET gantry 2. An image generation unit 6 that performs processing of detected and collected data and a display unit 9 that displays image data processed by the image generation unit 6 are provided.

  Further, the PET-CT apparatus 100 includes a bed position detection unit 7 for positioning the bed 5 when the subject P is set to a desired imaging region by imaging with the CT platform 1 or the PET platform 2, and the PET platform 2. And a PET position detecting unit 8 for performing positioning.

  The PET-CT apparatus 100 controls the operation unit 10 that selects and inputs various conditions such as subject information, imaging conditions, and display conditions, and inputs various commands, and the units of the PET-CT apparatus 100. And a system control unit 11 for controlling.

  The CT gantry 1 includes a substantially cylindrical CT opening 14 into which the subject P of the top plate 59 is sent in the center, an X-ray tube 15 that irradiates the subject P with X-rays, and an X through the subject P. An X-ray detector 12 that is disposed opposite to the X-ray tube 15 and detects X-rays transmitted through the subject P and converts them into an electric signal, and an electric signal output from the X-ray detector 12 is collected and processed. A data acquisition system 13 and an X-ray tube 15, an X-ray detector 14, and a rotating ring (not shown) that rotatably supports the data acquisition system unit 13 are provided on the outer periphery of the CT opening 14 of the CT mount 1. . The CT gantry 1 is held by a holding unit (not shown) so as to be tiltable about a horizontal axis passing through the center of the rotary ring and parallel to the rotary ring surface.

  On the other hand, the PET mount 2 is administered with a substantially cylindrical PET opening 23 into which the subject P on the top plate 59 is sent in the center, and a radioisotope arranged in a ring shape on the outer periphery of the PET opening 23. A positron emitted from the body of the subject P is converted into an optical signal, the converted optical signal is converted into an electrical signal, and the electrical signal output from the gamma ray detector 21 is processed. And a data collection system 94.

  The mechanism unit 4 includes a CT gantry tilt mechanism 41 that tilts the CT gantry 1, a top plate moving mechanism 42 that horizontally moves the couchtop 59 in the vertical direction and the longitudinal direction of the couchtop 59, and the PET gantry 2 as the body of the subject P. A PET frame moving mechanism 43 that moves in the axial direction, a bed moving mechanism 44 that moves the bed 5 toward the opening of the CT frame 1 and the PET frame 2 for imaging by the CT frame 1 or the PET frame 2, and a CT frame tilt A mechanism 41, a top plate moving mechanism 42, a PET gantry moving mechanism 43, a couch moving mechanism 44, and a gantry / top / bed mechanism control unit 45 that controls the power supply unit 40 shown in FIG. 1B are provided. .

  The high voltage generation unit 92 includes a high voltage generation unit 92 that generates a high voltage applied between the anode and the cathode in order to accelerate thermionic electrons generated from the cathode of the X-ray tube 15, and the system control unit 11. And an X-ray control unit 91 that controls X-ray irradiation conditions such as tube current, tube voltage, and irradiation time in the high voltage generation unit 92 in accordance with the instruction signal.

  The image generation unit 6 processes the data sent from the CT gantry 1 to generate CT image data, and processes the data sent from the PET gantry 2 to generate PET image data. A PET image processing unit 62 that performs the composition processing by superimposing the CT image data generated by the CT image processing unit 61 on the PET image data generated by the PET image processing unit 62 and generates PET-CT image data 63.

  The couch position detector 7, when performing imaging with the CT gantry 1, has a CT imaging couch position detector 71 for detecting the couch 5 that moves from the PET gantry imaging position to the CT imaging position, and imaging with the PET gantry 2. When performing the above, there is provided a PET imaging couch position detector 72 for detecting the couch 5 that moves from the CT imaging position to the PET gantry imaging position.

  The PET position detector 8 includes a PET gantry imaging position detector 81 for detecting the PET gantry 2 that moves from the PET gantry stand-by position of the PET gantry 2 to the PET gantry imaging position, and a CT gantry. 1 is provided with a PET gantry standby position detector 82 for detecting the PET gantry 2 that moves from the PET gantry imaging position to the PET gantry standby position of the PET gantry 2 in the case of imaging by 1.

  Then, the signals detected by the bed position detector 7 and the PET position detector 8 are sent to a gantry / top / bed mechanism control unit 45 configured by a servo amplifier and the like, and the gantry / top / bed mechanism control unit. 45 is provided with a monitor such as a liquid crystal display or a CRT for displaying the driving motors of the bed moving mechanism 44 and the PET gantry moving mechanism 43 based on these signals.

  The display unit 9 displays the PET image reconstructed by the reconstruction unit 57 on the display device. As a display device, a CRT display, a liquid crystal display, an organic EL display, a plasma display, or the like can be used as appropriate.

  The operation unit 10 is an interface provided with an input device such as a keyboard, a trackball joystick, a mouse, a display panel, and various switches, and includes age, sex, physique, examination site, examination method, past diagnosis history, etc. Various imaging conditions such as subject information are set and various commands are input.

  The system control unit 11 functions as the center of the PET-CT apparatus. The system control unit 11 includes a memory, a CPU, and the like. For example, a dedicated program is developed in its own memory, and each part is controlled according to the dedicated program to perform PET collection and PET image reconstruction processing. After temporarily storing information such as command signals and imaging conditions supplied from the operation unit 10, generation and display of CT image data, PET image data, or PET / CT image data based on these information, and control relating to the moving mechanism And on / off of power supply to the power supply unit 40 shown in FIG.

  FIG. 1B is a block diagram showing more specifically the relationship among the PET gantry 2, the PET image processing unit 62, and the system control unit 11 in FIG. 1A. As shown in FIG. 1B, the PET includes a PET gantry 2 and a PET image processing unit 62. The PET mount 2 has a detector block 30 inside the casing.

  A top plate 59 on which the subject P can be placed is inserted into the opening of the rotating ring provided with the gamma ray detector 21. The rotating ring provided with the gamma ray detector 21 has a plurality of detector blocks 30 arranged circumferentially around the long axis of the top plate. Typically, a plurality of rotating rings including the gamma detector 21 are arranged along the long axis of the top plate.

  FIG. 2 is a diagram showing a detailed structure of the detector block 30. In FIG. 2 (also in FIG. 1), only one detector block 30 is shown for simplicity, but more detector blocks 30 can be mounted inside the actual housing.

  Each detector block 30 is equipped with a gamma ray detector 21 and a front end circuit 35 as shown in FIG.

  The gamma ray detector 21 detects gamma rays and generates an electrical signal corresponding to the intensity of the detected gamma rays. Specifically, the gamma ray detector 21 detects gamma rays emitted from within the subject, and generates an analog electrical signal corresponding to the intensity of the detected gamma rays. The gamma ray detector 21 detects a laser pulse incident from a laser pulse generator (not shown), and generates an analog electrical signal corresponding to the intensity of the detected laser pulse.

  Specifically, each gamma ray detector 21 is joined to a plurality of scintillators (crystals) 331, a light guide 333, and a photomultiplier tube 335 as shown in FIG.

  Each scintillator 331 is made of a scintillator crystal formed in a rectangular parallelepiped shape. The scintillator crystal is a substance that generates fluorescence when gamma rays are incident. As the scintillator crystal, for example, NaI (sodium iodide), BGO (bismuth acid germanate), LSO (a product obtained by adding a certain amount of cerium to lutetium silicate) and the like are used. A single detector block 30 has a plurality of scintillators 331 arranged in a two-dimensional manner.

  The energy calculation unit 351 in FIG. 1B generates an electrical signal (energy signal) having an intensity corresponding to the energy value of the light incident on the gamma ray detector 21 based on the electrical signal from the photomultiplier tube 335.

  The photomultiplier tube 335 is optically joined to the light guide 333 so that the photocathode faces the light guide 333 side. A front end circuit 35 is joined to the surface of the photomultiplier tube 335 opposite to the photocathode. The photomultiplier tube 335 receives fluorescence from the scintillator 331 via the light guide 333, amplifies the received fluorescence, and generates a pulsed electric signal corresponding to the amount of the amplified fluorescence. The photomultiplier tube 335 receives the laser pulse incident on the light guide 333, amplifies the received laser pulse, and generates a pulsed electric signal corresponding to the amount of the amplified laser pulse. Thus, the photomultiplier tube 335 functions as an electric signal generator. The generated electric pulse is supplied to the front end circuit 35. Instead of the photomultiplier tube 335, a photodiode that functions as an electric signal generator may be provided.

  The front end circuit 35 has functions of an energy calculation unit 351, a position calculation unit 353, and a detection time measurement unit 355 shown in FIG. 1B.

  The position calculation unit 353 generates an electric signal (position signal) having an intensity corresponding to the position coordinate where the light is incident based on the electric signal from the photomultiplier tube 335. Typically, the position coordinates are the position coordinates of the scintillator 331 where the light is generated. The gamma rays are actually incident on the scintillator 331. Therefore, the gamma ray calculated by the position calculation unit 353 does not actually enter the scintillator 331. Therefore, it can be said that the position coordinates of the laser pulse calculated by the position calculation unit 353 are fictitious position coordinates. The generated position signal is supplied to the detection time list storage unit 51 of the PET image processing unit 62.

  The PET image processing unit 62 includes a detection time list storage unit 51, an output value estimation unit 53, a simultaneous measurement unit 55, and a reconstruction unit 57.

  The detection time list storage unit 51 stores detection time list data. The detection time list is a list in which at least event data and detection time data are associated with each event. On the detection time list, the detection time of the gamma ray event is used as a time stamp. One detection time list may be generated for all the photomultiplier tubes 335 or may be generated for each detector block 30.

  The output value estimation unit 53 estimates the output value of the failed IC board 75 using the plurality of IC boards 75 other than the failed IC board 75 when the failed IC board 75 exists. A detailed output estimation method in the output value estimation unit 53 will be described later.

  The simultaneous measurement unit 55 performs simultaneous measurement of gamma ray events using relative time. Specifically, the simultaneous measurement unit 55 repeatedly identifies two gamma ray events that fall within a predetermined time frame from the relative time list, and repeatedly identifies event data related to the two gamma ray events. Two identified gamma events are presumed to originate from a pair of gamma rays generated from the same pair annihilation point. A line connecting a pair of gamma ray detectors 21 that has detected a pair of gamma rays is called LOR (line of interest). By repeatedly performing simultaneous measurement, event data relating to LOR is identified.

  The reconstruction unit 57 reconstructs PET image data representing the concentration distribution of the radioisotope in the subject.

  FIG. 3 is a diagram showing the structure of the data collection system 94 in the PET apparatus shown in FIG. 1A in more detail. The data collection system 94 includes a plurality of data collection system units 22. Each data collection system unit 22 includes a plurality of IC substrates 75 and a plurality of temperature sensors disposed around the plurality of IC substrates 75 and corresponding to the plurality of IC substrates 75, respectively. Although FIG. 3 shows that four data collection system units 22 are arranged in an arc shape, the number is not limited to four. Similarly, although it is described that four IC substrates 75 are arranged in one data collection system unit 22, the number is not limited to four. The power supply unit 40 supplies power independently to each of the data collection system units 22 via the power supply line 90. The power supply unit 40 includes a configuration necessary for individually stopping power supply to the power supply line 90. Around the IC substrate 75, a temperature sensor 95 for detecting the heat radiation temperature from each IC substrate 75 is arranged for each IC substrate 75. In FIG. 3, as an example, the temperature sensor 95 is illustrated as being disposed above the IC substrate 75. The system control unit 11 controls the power supply unit 40 so as to stop power supply to the data collection system unit 22 that satisfies a certain condition (described later). Since the IC board 75 may break down as the temperature of the board itself rises, the cooling fan 843 for releasing the heat inside the data collection system unit 22, the rotation speed comparison unit 46, And a temperature comparison unit 47.

  FIG. 4A is a diagram showing the structure in the data collection system unit 22 in the PET apparatus according to the present embodiment in FIG. 3 in more detail. A temperature comparison unit 47 that compares whether the temperature discharged from the inside of the data collection system unit 22 to the outside exceeds a threshold value, a rotation speed comparison unit 46 that compares the rotation speed of the cooling fan 843 with the threshold value, and cooling A fan unit 84 is provided.

  FIG. 4B is a diagram showing the cooling fan unit 84 in FIG. 4A in more detail. The cooling fan unit 84 includes a cooling fan 843 and a cooling fan unit 841.

  The flow of FIGS. 5 to 7 will be described below. The control in each of FIGS. 5 to 7 is called a degenerate mode because the operation state of the apparatus is changed according to the degree of deterioration of the state in the data collection system unit 22.

  FIG. 5 is a diagram showing a flow of the degenerate mode starting from the detection of the cooling fan rotation speed for each of the cooling fans 843 existing in the same data collection system unit 22 according to the present embodiment. That is, FIG. 5 is a flow showing control only within one data collection system unit 22. First, the rotation speed comparison unit 46 compares whether or not the rotation speed of the cooling fan 843 is higher than a certain threshold value (here, the first threshold value) (S11). When the rotation speed of the cooling fan 843 exceeds the first threshold value, the heat released from the data collection system unit 22 to the outside is sufficient, and thus the cooling fan 843 having a rotation speed exceeding the first threshold value is provided. The power supply to each data collection system unit 22 is continued. When the rotation speed of the cooling fan 843 is equal to or lower than the first threshold value, the rotation speed comparison unit 46 again compares the rotation speed of the cooling fan 843 with a second threshold value that is a numerical value lower than the first threshold value (S12). ). When the rotation speed of the cooling fan 843 exceeds the second threshold value, the system control unit 11 generates an output control signal for generating a warning signal and supplies power to each of the plurality of data collection system units 22. In order to continue the operation, the power supply unit 40 is controlled. When the rotation speed of the cooling fan 843 is equal to or lower than the second threshold value, the system control unit 11 has a rotation speed other than the cooling fan 843 that exists in the same data collection system unit 22 and has a rotation speed equal to or lower than the second threshold value. The rotation speed is increased for at least one cooling fan 843 (S13). Next, the temperature comparison unit 47 compares whether or not the heat radiation temperature from the cooling fan 843 existing in the same data collection system unit 22 is higher than the third threshold (S14). When the heat dissipation temperature from the cooling fan 843 is equal to or lower than the third threshold value, the data collection system unit 22 includes an output control signal for generating a warning signal and the cooling fan 843 having a heat dissipation temperature equal to or lower than the third threshold value. The system control unit 11 controls the power supply unit 40 in order to continue the power supply. When the heat radiation temperature from the cooling fan 843 is higher than the third threshold value, an output control signal for generating a warning signal is generated, and the data collection system unit 22 provided with the cooling fan 843 having a heat radiation temperature higher than the third threshold value is provided. On the other hand, the system controller 11 controls the power supply line 90 so as to stop the power supply (S15). The operation of the apparatus is continued using the data collection system unit 22 to which power supply continues.

  FIG. 6 is a diagram showing a flow of the degeneration mode starting from the detection of the heat radiation temperature for each cooling fan 843 existing in the same data collection system unit 22 in the PET apparatus according to the present embodiment. That is, FIG. 6 is a flow showing the control only within one data collection system unit 22. Further, FIG. 6 is a flow relating to temperature detection of one specific cooling fan 843 provided in one data collection system unit 22. First, the temperature comparison unit 47 compares the heat radiation temperature from the cooling fan 843 with the first threshold (S21). When the heat radiation temperature from the cooling fan 843 is equal to or lower than the first threshold, the system control unit 11 supplies the power supply unit to each of the data collection system units 22 provided with the IC substrate 75 having the heat radiation temperature equal to or lower than the first threshold. The system control unit 11 controls the power supply unit 40 so that 40 transmits power. When the heat radiation temperature from the cooling fan 843 exceeds the first threshold, the rotation speed of the cooling fan 843 is increased (S22). Thereafter, in the same manner, the temperature comparison unit 47 compares the heat radiation temperature from the cooling fan 843 with the first threshold value (S23). When the heat dissipation temperature from the cooling fan 843 is equal to or lower than the first threshold, the system control unit 11 supplies power to each of the data collection system units 22 provided with the IC substrate 75 having the heat dissipation temperature equal to or lower than the first threshold. The system control unit 11 controls the power supply unit 40 to do this. When the heat dissipation temperature from the cooling fan 843 is higher than the first threshold, the system control unit 11 stops the power supply to each of the data collection system units 22 having the cooling fan 843 whose heat dissipation temperature is equal to or higher than the first threshold. The power supply unit 40 is controlled via the power supply line 90 (S24). The operation of the apparatus is continued using a plurality of data collection system units 22 other than the data collection system unit 22 from which power supply is stopped.

  FIG. 7 is a diagram showing a flow of the degeneration mode starting from the detection of the ambient temperature of the IC board 75 existing in the same data collection system unit 22 according to the present embodiment. That is, FIG. 7 is a flow showing control only within one data collection system unit 22. Further, the flow of FIG. 7 is a flow for all the IC boards 75 provided in one specific data collection system unit 22. First, for a plurality of IC substrates 75 in the same data collection system unit 22, the temperature comparison unit 47 compares the ambient temperature of each IC substrate 75 with a first threshold value (S31). When there is no IC board 75 whose heat dissipation temperature exceeds the first threshold in the same data collection system unit 22, the system control unit 11 determines that the data collection system unit does not include any IC board 75 whose heat dissipation temperature exceeds the first threshold. The power supply unit 40 is controlled so as to continue supplying power to each of the two. When there is one IC board 75 having a heat radiation temperature exceeding the first threshold in the same data collection system unit 22, an output control signal for generating a warning signal is generated and the output value estimation unit 32 will be described later. Image correction processing is performed, and the operation of the apparatus is continued (S32). When two or more IC boards 75 having a heat dissipation temperature exceeding the first threshold exist in the same data collection system unit 22, a warning signal is generated and two IC boards 75 having a heat dissipation temperature exceeding the first threshold are generated. The power supply is stopped for each of the data collection system units 22 having the above (S33). The operation of the apparatus is continued using a plurality of data collection system units 22 other than the data collection system unit 22 from which power supply is stopped.

  Further, the apparatus may be operated by combining flowcharts (degenerate mode operation) as shown in FIGS.

FIG. 8 shows an image correction method when there is one IC substrate 75 whose heat dissipation temperature exceeds the first threshold. Hereinafter, it is assumed that the gamma ray detector 21 (D ₁ ) in FIG. 8 is in an unusable state. Gamma ray detector 21 _{(D 1)} is present at both ends of the two gamma ray detectors 21 and _{(D 3} and _{D 5),} gamma detectors 21 _{(D 1)} of the present across two gamma ray detectors 21 _{(D 3} And D ₅ ), based on the output values of the two gamma ray detectors 21 (D ₄ and D ₆ ) existing at the position opposite to D ₅ ), the output value estimation unit 32 determines the output value of the gamma ray detector 21 (D ₁ ). presume. The gamma rays emitted from the radiation consent element administered to the subject are detected by the gamma ray detector 21 facing the annihilation radiation generation point. Due to the energy conservation law, the sum of the radiation energies detected by the opposing gamma ray detectors 21 (for example, D ₃ and D ₄ ) is constant. Further, it is detected by the two gamma ray detectors 21 (D ₃ and D ₅ ) adjacent to the gamma ray detector 21 (D ₁ ) and the two gamma ray detectors 21 (D ₄ and D ₆ ) existing at opposite positions. Gamma rays are estimated to have the same origin. Furthermore, the output of the pair ((D ₃ and D ₄ ) and (D ₅ and D ₆ )) of two gamma ray detectors 21 adjacent to the gamma ray detector 21 (D ₁ ) is the gamma ray detector 21 (D ₁ and D ₂ ), it is considered that the output is similar to that of the output of the gamma ray detector 21 (D ₁ ) if the output of the gamma ray detector 21 (D ₂ ) is known. Therefore, image correction can be performed based on the estimated output value of the gamma ray detector 21 (D ₁ ).

  As described above, according to the present invention, the nuclear medicine diagnostic apparatus that can improve the throughput while reducing the burden on the user by performing the control according to the deterioration state in the data collection system unit 22 in the PET apparatus. Can be realized.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These novel embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the scope of the invention. These embodiments and modifications thereof are included in the scope and gist of the invention, and are included in the invention described in the claims and the equivalents thereof.

  P ... Subject, 1 ... CT frame, 2 ... PET frame, 4 ... Mechanical unit, 5 ... Bed, 6 ... Image generating unit, 7 ... Bed position detector, 8 ... PET position detector, 9 ... Display unit, 10 DESCRIPTION OF SYMBOLS ... Operation part, 11 ... System control part, 12 ... X-ray detector, 13 ... Data acquisition system in CT apparatus, 14 ... CT opening part, 15 ... X-ray tube, 21 ... Gamma-ray detector, 22 ... Data in PET apparatus Collection system unit, 23 ... PET aperture, 30 ... detector block, 32 ... output value estimation unit, 331 ... scintillator, 333 ... light guide, 335 ... photomultiplier tube, 35 ... front end circuit, 351 ... energy calculation unit 353: Position calculation unit, 355 ... Detection time measurement unit, 40 ... Electric power supply unit, 41 ... CT mount tilt mechanism, 42 ... Top plate moving mechanism, 43 ... PET mount moving mechanism, 44 ... Sleeper mover 45 ... Standing / top / bed mechanism control unit, 46 ... rotational speed comparison unit, 47 ... temperature comparison unit, 51 ... detection time list storage unit, 53 ... output value estimation unit, 55 ... simultaneous measurement unit, 57 ... re- Configuration unit 59 ... top plate 61 ... CT image processing unit 62 ... PET image processing unit 63 ... Image processing unit 71 ... CT imaging couch position detector 72 ... PET imaging couch position detector 75 ... IC substrate 81. PET frame imaging position detector 82 82 PET frame stand-by position detector 84 84 cooling fan unit 841 cooling fan unit 843 cooling fan 90 power supply line 91 X-ray control unit , 92... High voltage generator, 94... Data collection system in PET apparatus, 95... Temperature sensor, 100.

Claims (5)

A plurality of gamma ray detectors for detecting gamma rays emitted from the radiation the position elements is administered to the subject,
A plurality of data acquisition systems provided adjacent to each of the plurality of gamma ray detectors and formed with analog-digital circuits;
A power supply unit for supplying power to each of the plurality of data collection systems;
A plurality of cooling fan units having a plurality of cooling fans for cooling each of the plurality of data collection systems;
A first rotation speed comparison unit that compares the rotation speed of each of the plurality of cooling fans with a first threshold;
A second rotation speed comparison unit that compares the rotation speed of the cooling fan that exceeds the first threshold value with the second threshold value among the plurality of cooling fans;
When the rotation speed of each of the plurality of cooling fans exceeds the first threshold, the power supply unit is controlled to continue supplying power to each of the plurality of data collection systems;
When the rotation speed of each of the plurality of cooling fans is equal to or lower than the first threshold value and exceeds the second threshold value, an output control signal for generating a warning signal is generated, and for each of the plurality of data collection systems And controlling the power supply unit to continue power supply,
When the rotational speed of at least one of the plurality of cooling fans is less than or equal to the second threshold value, the cooling fan unit increases the rotational speed of the cooling fan whose rotational speed is less than or equal to the second threshold value. A control unit for controlling
A nuclear medicine diagnostic apparatus. A plurality of heat-dissipating temperature detectors that are provided in each of the plurality of data collection systems and detect heat-dissipating temperatures from the cooling fans;
A temperature comparison unit that compares the heat radiation temperature from each of the plurality of cooling fans with a third threshold;
The control unit controls the power supply unit to stop power supply to the data collection system to which the heat dissipation temperature detection unit that detects the heat dissipation temperature exceeding the third threshold is attached,
Output control for generating a warning signal and controlling the power supply unit in order to continue power supply to the data collection system to which the heat dissipation temperature detection unit that detects the heat dissipation temperature below the third threshold is attached 2. The nuclear medicine diagnosis apparatus according to claim 1, wherein a signal is generated. A plurality of gamma ray detectors for detecting a plurality of gamma rays emitted from a radioisotope administered to a subject;
A plurality of data acquisition systems provided adjacent to the plurality of gamma ray detectors and formed with analog-digital circuits;
A power supply unit for supplying power to each of the plurality of data collection systems;
A plurality of cooling fan units having a plurality of cooling fans for cooling each of the plurality of data collection systems;
A plurality of data collection systems, each of the plurality of data collection systems, a third comparison unit for comparing the heat radiation temperature from each of the plurality of cooling fans with a first threshold;
A controller that controls each of the plurality of cooling fan units to increase the rotational speed of each of the plurality of cooling fans when the heat dissipation temperature exceeds the first threshold;
Equipped with,
The third comparison unit increases the cooling fan rotation speed by the control unit, and then compares the heat radiation temperature with the first threshold value.
The control unit generates an output control signal for generating a warning signal when it is determined that the heat dissipation temperature exceeds the first threshold value, and exceeds the first threshold value among the plurality of data collection systems. Controlling the power supply unit to stop power supply to the data collection system that releases the heat dissipation temperature;
When it is determined that the heat radiation temperature is equal to or lower than the first threshold, the power supply unit is controlled to continue supplying power to each of the plurality of data collection circuits.
Nuclear medicine diagnostic equipment. A plurality of gamma ray detectors for detecting gamma rays emitted from radioisotopes administered to the subject;
A plurality of data collection systems provided adjacent to the plurality of gamma ray detectors and formed with analog-digital conversion circuits;
A plurality of IC boards respectively corresponding to the plurality of gamma ray detectors and provided in each of the plurality of data collection systems;
A power supply unit for supplying power to each of the plurality of data collection systems;
A temperature sensor installed in the plurality of data collection systems to detect the temperature around each of the plurality of IC substrates;
Based on the output value of the temperature sensor, a temperature comparison unit that compares the heat radiation temperature from each of the plurality of IC substrates with a first threshold;
In order to stop power supply to a data collection system having two or more IC substrates exceeding the first threshold when there are two or more IC substrates exceeding the first threshold among the plurality of IC substrates. Controlling the power supply unit;
When there is one IC board that exceeds the first threshold among the plurality of IC boards, an output control signal for generating a warning signal is generated and power is supplied to each of the plurality of data collection systems. Controlling the power supply unit to continue
A nuclear medicine diagnostic apparatus comprising: a control unit that controls the power supply unit in order to continue power supply to each of the plurality of data collection systems when there is no IC substrate that exceeds the first threshold. A plurality of gamma ray detectors for detecting a plurality of gamma rays emitted from a radioisotope administered to a subject;
When there is one IC substrate that exceeds the first threshold among the plurality of IC substrates, two second detectors adjacent to the first detector corresponding to one IC substrate that exceeds the first threshold; The output of the first detector using a method of estimating the output value of the first detector using the two second detectors and two third detectors located across the annihilation radiation generation point The nuclear medicine diagnosis apparatus according to claim 4, further comprising: an output value estimation unit that estimates

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