JP7140500B2 - X-ray CT device and detector module - Google Patents

Description

Embodiments of the present invention relate to X-ray CT apparatus and detector modules.

2. Description of the Related Art Conventionally, an X-ray CT (Computed Tomography) apparatus that uses X-rays to image the inside of a subject is known. An X-ray CT apparatus includes an X-ray detector for detecting X-rays that have passed through a subject. The X-ray detector rotates around an imaging space in which the subject is placed, and generates detection data indicating the X-ray intensity distribution based on the X-rays that have passed through the subject at each rotational position (view). Output. An X-ray CT apparatus collects detection data for a full or half circumference and reconstructs CT image data.

X-ray detectors have various electronic components that process signals based on detected X-rays. Since these electronic components generate heat in the process of signal processing, the X-ray detector has a heat exhaust mechanism for exhausting the generated heat (exhaust heat). For example, in an X-ray detector, heat exchange is performed by thermally connecting a heat sink to an electronic component serving as a heat source and sending air (outside air) to the heat sink using a fan.

Japanese Patent Application Laid-Open No. 2001-309912

A problem to be solved by the present invention is to provide an X-ray CT apparatus and a detector module capable of efficiently exhausting heat.

An X-ray CT apparatus according to an embodiment includes an X-ray tube, an X-ray detector, and a rotating frame. X-ray tubes generate X-rays. An X-ray detector detects the X-rays. A rotating frame rotatably supports the X-ray tube and the X-ray detector. The X-ray detector includes an electronic component, a heat transfer member, and a heat pipe. Electronic components process signals based on the detected X-rays. The heat transfer member is in contact with the electronic component and transfers heat generated from the electronic component. The heat pipe contains a volatile working fluid. A heat receiving portion of the heat pipe is provided inside the heat transfer member. The heat radiating portion of the heat pipe is provided at a position closer to the center of rotation of the rotating frame than the heat receiving portion.

FIG. 1 is a diagram showing an example of the configuration of an X-ray CT apparatus according to the first embodiment. FIG. 2 is a diagram illustrating an example of the configuration of the X-ray detector according to the first embodiment; FIG. 3 is a diagram illustrating an example of the configuration of the X-ray detector according to the first embodiment; 4A is a diagram illustrating an example of the configuration of an X-ray detector according to the first embodiment; FIG. 4B is a diagram illustrating an example of the configuration of the X-ray detector according to the first embodiment; FIG. 4C is a diagram illustrating an example of the configuration of the X-ray detector according to the first embodiment; FIG. FIG. 5 is a diagram for explaining the effects of the X-ray CT apparatus according to the first embodiment. FIG. 6 is a diagram illustrating an example of the configuration of an X-ray detector according to a modification of the first embodiment; FIG. 7 is a diagram showing an example of the configuration of an X-ray detector according to the second embodiment. FIG. 8 is a diagram showing an example of the configuration of an X-ray detector according to another embodiment. FIG. 9 is a diagram showing an example configuration of an X-ray detector according to another embodiment. FIG. 10 is a diagram showing an example configuration of an X-ray detector according to another embodiment. FIG. 11 is a diagram showing an example of the configuration of an X-ray detector according to another embodiment. FIG. 12 is a diagram showing an example configuration of an X-ray detector according to another embodiment.

An X-ray CT apparatus and a detector module according to embodiments will be described below with reference to the drawings. In addition, embodiment is not restricted to the following embodiments. In addition, the contents described in one embodiment are in principle similarly applied to other embodiments.

(First embodiment)
FIG. 1 is a diagram showing an example of the configuration of an X-ray CT apparatus 1 according to the first embodiment. As shown in FIG. 1, the X-ray CT apparatus 1 according to the first embodiment has a gantry device 10, a bed device 20, and a console device 30. As shown in FIG. The gantry device 10, the bed device 20, and the console device 30 are communicably connected to each other. In FIG. 1, a plurality of gantry devices 10 are shown for convenience of explanation, but basically the X-ray CT apparatus 1 is provided with one gantry device 10. As shown in FIG.

In this embodiment, the longitudinal direction of the rotational axis of the rotating frame 12 or the top board 23 of the bed device 20 in the non-tilt state is defined as the "Z-axis direction". Further, an axial direction perpendicular to the Z-axis direction and horizontal to the floor surface is defined as an “X-axis direction”. Further, the axial direction perpendicular to the Z-axis direction and perpendicular to the floor surface is defined as the “Y-axis direction”.

The gantry device 10 is a device that irradiates a subject P (patient) with X-rays, detects the X-rays that have passed through the subject P, and outputs the X-rays to the console device 30 . The gantry device 10 has an X-ray tube 11 , a rotating frame 12 , an X-ray high voltage device 13 , a control device 14 , a wedge 15 , a collimator 16 and an X-ray detector 40 .

The X-ray tube 11 is a vacuum tube that emits thermal electrons from a cathode (filament) toward an anode (target) by applying a high voltage from an X-ray high voltage device 13 . The X-ray tube 11 generates X-rays by colliding thermal electrons with an anode.

The rotating frame 12 is an annular frame that supports the X-ray tube 11 and the X-ray detector 40 so as to face each other and rotates the X-ray tube 11 and the X-ray detector 40 by the control device 14 . In addition to the X-ray tube 11 and the X-ray detector 40, the rotating frame 12 further includes an X-ray high-voltage device 13 and a control board 17 to support them. The detection data generated by the control board 17 is provided to the non-rotating portion (e.g., fixed frame) of the gantry 10 by optical communication from a transmitter having a light emitting diode (LED) provided on the rotating frame 12. It is sent to a receiver with a photodiode and forwarded to the console device 30 . Note that the method of transmitting the detection data from the rotating frame 12 to the non-rotating portion of the gantry 10 is not limited to the optical communication described above, and any method of non-contact data transmission may be employed.

The X-ray high-voltage device 13 has an electric circuit such as a transformer and a rectifier, and has a high-voltage generator function to generate a high voltage to be applied to the X-ray tube 11. and an X-ray control device for controlling an output voltage according to the X-ray output. The high voltage generator may be of a transformer type or an inverter type. The X-ray high-voltage device 13 may be provided on the rotating frame 12 or may be provided on the fixed frame (not shown) side of the gantry device 10 . Note that the fixed frame is a frame that rotatably supports the rotating frame 12 .

The control device 14 has a processing circuit having a CPU (Central Processing Unit) and the like, and drive mechanisms such as motors and actuators. The control device 14 has a function of receiving an input signal from an input interface attached to the console device 30 or the gantry device 10 and controlling the operations of the gantry device 10 and the bed device 20 . For example, the control device 14 receives an input signal and performs control to rotate the rotating frame 12 , control to tilt the gantry device 10 , and control to operate the bed device 20 and the tabletop 23 . The control for tilting the gantry device 10 is performed by the control device 14 based on tilt angle (tilt angle) information input through an input interface attached to the gantry device 10. This is achieved by rotating the Note that the control device 14 may be provided in the gantry device 10 or may be provided in the console device 30 .

Wedge 15 is a filter for adjusting the dose of X-rays emitted from X-ray tube 11 . Specifically, the wedge 15 transmits and attenuates the X-rays emitted from the X-ray tube 11 so that the X-rays emitted from the X-ray tube 11 to the subject P have a predetermined distribution. It is a filter that For example, the wedge 15 is a filter made of aluminum so as to have a predetermined target angle and a predetermined thickness. The wedge 15 is also called a wedge filter or a bow-tie filter.

The collimator 16 is a lead plate or the like for narrowing down the irradiation range of the X-rays transmitted through the wedge 15 . The collimator 16 is formed in a slit shape by combining a plurality of lead plates or the like. Note that the collimator 16 may also be called an X-ray diaphragm or a pre-collimator.

The X-ray detector 40 detects X-rays emitted from the X-ray tube 11 and passed through the subject P. FIG. The X-ray detector 40 has, for example, a plurality of X-ray detection element arrays in which a plurality of X-ray detection elements are arranged in the channel direction along one circular arc centering on the focal point of the X-ray tube 11 . The X-ray detector 40 has, for example, a structure in which a plurality of X-ray detection element arrays each having a plurality of X-ray detection elements arranged in the channel direction are arranged in the slice direction (also referred to as the row direction or row direction).

Also, the X-ray detector 40 is, for example, an indirect conversion type detector having a collimator unit, a scintillator array, and a plurality of photodiodes. The collimator unit is arranged on the surface of the scintillator array on the X-ray incident side and has an X-ray shielding plate having a function of absorbing scattered X-rays. The scintillator array has a plurality of scintillators, and each scintillator has a scintillator crystal that outputs light in an amount corresponding to the amount of incident X-rays. The multiple photodiodes output electrical signals (analog signals) corresponding to the light from the scintillator. The collimator unit, scintillator array, and photodiode will be described in detail later.

Note that the X-ray detector 40 may be a direct conversion detector having a semiconductor element that converts incident X-rays into analog signals. Moreover, the photodiode may be configured by an optical sensor such as a photomultiplier tube (PMT).

FIG. 2 is a diagram showing an example of the configuration of the X-ray detector 40 according to the first embodiment. For example, as shown in FIG. 2, the X-ray detector 40 has a collimator unit 41 and multiple detector modules 50 . In FIG. 2, the X-ray irradiation range is indicated by a dashed line 11A, and the X-ray irradiation direction is indicated by a dashed arrow. In the following description, the circumferential direction around the X-ray tube 11 is called the channel direction, and the direction along the Z-axis, which is the rotation axis of the rotating frame 12, is called the slice direction.

The collimator unit 41 is configured, for example, by attaching a plurality of X-ray shielding plates along the X-ray irradiation direction to a support member formed in an arc shape along the channel direction. The collimator unit 41 is formed in a substantially arc shape centering on the X-ray tube 11 and is arranged on the front side of each detector module 50 in the X-ray irradiation direction. Remove lines.

A plurality of detector modules 50 are arranged side by side along the channel direction on the outer peripheral side of the collimator unit 41 . Although FIG. 2 shows an example in which a plurality of detector modules 50 are arranged one-dimensionally along the channel direction, the embodiment is not limited to this. For example, the detector modules 50 may be arranged two-dimensionally along the channel direction and the slice direction. Note that the collimator unit 41 may also be called a grid or a post-collimator.

The detector module 50 has a scintillator array and photodiodes, and converts incident X-rays into analog signals. Here, the X-rays incident on the scintillator array are converted into light (scintillation light) for each scintillator block separated by a grid-like reflective material. The light converted for each scintillator block is then converted into an analog signal for each photodiode corresponding to each scintillator block. That is, the scintillator blocks and photodiodes corresponding to the regions separated by the reflector function as one X-ray detection element. The configuration of the detector module 50 according to the first embodiment will be detailed later.

Note that the configuration shown in FIG. 2 is merely an example, and is not limited to the contents of the illustration. For example, the X-ray detector 40 includes a light shielding container (light shielding container 60 to be described later). This light-tight container accommodates, for example, the collimator unit 41 and the detector module 50 .

Returning to the description of FIG. The control board 17 controls readout of signals from a plurality of X-ray detection elements arranged in the channel direction and the slice direction to generate detection data indicating the intensity distribution of X-rays. For example, the control board 17 generates detection data by performing various signal processing such as amplification processing on analog signals read from each X-ray detection element. Detection data generated by the control board 17 is transferred to the console device 30 . The control board 17 is installed on the rotating frame 12 by a support member (not shown). Note that the control board 17 may be installed not only on the rotating frame 12 but also on the gantry device 10 or the console device 30, for example.

The bed device 20 is a device for placing and moving a subject P to be scanned, and includes a base 21 , a bed driving device 22 , a top plate 23 and a support frame 24 . The base 21 is a housing that supports the support frame 24 so as to be vertically movable. The bed driving device 22 is a motor or actuator that moves the table 23 on which the subject P is placed in the longitudinal direction of the table 23 . A top plate 23 provided on the upper surface of the support frame 24 is a plate on which the subject P is placed. Note that the bed drive device 22 may move the support frame 24 in the longitudinal direction of the top plate 23 in addition to the top plate 23 .

The console device 30 is a device that receives an operator's operation of the X-ray CT apparatus 1 and reconstructs CT image data using detection data collected by the gantry device 10 . The console device 30 has a memory 31, a display 32, an input interface 33, and a processing circuit 34, as shown in FIG. Memory 31, display 32, input interface 33, and processing circuitry 34 are communicatively connected to each other. Although the console device 30 is described as being separate from the gantry device 10 , the console device 30 or a part of each component of the console device 30 may be included in the gantry device 10 .

The memory 31 is implemented by, for example, a RAM (Random Access Memory), a semiconductor memory device such as a flash memory, a hard disk, an optical disk, or the like. The memory 31 stores projection data and CT image data, for example.

The display 32 displays various information. For example, the display 32 outputs a medical image (CT image) generated by the processing circuit 34, a GUI (Graphical User Interface) for accepting various operations from the operator, and the like. For example, the display 32 is a liquid crystal display or a CRT (Cathode Ray Tube) display. Also, the display 32 may be provided on the gantry device 10 . The display 32 may be of a desktop type, or may be configured by a tablet terminal or the like capable of wireless communication with the main body of the console device 30 .

The input interface 33 receives various input operations from the operator, converts the received input operations into electrical signals, and outputs the electrical signals to the processing circuit 34 . For example, the input interface 33 allows the operator to input acquisition conditions for acquiring projection data, reconstruction conditions for reconstructing CT image data, image processing conditions for generating post-processed images from CT images, and the like. accept. For example, the input interface 33 is implemented by a mouse, keyboard, trackball, switch, button, joystick, and the like. Also, the input interface 33 may be provided in the gantry device 10 . Also, the input interface 33 may be composed of a tablet terminal or the like capable of wireless communication with the main body of the console device 30 .

A processing circuit 34 controls the operation of the entire X-ray CT apparatus 1 . For example, processing circuitry 34 performs system control functions 341 , preprocessing functions 342 , reconstruction processing functions 343 , and image processing functions 344 .

The system control function 341 controls various functions of the processing circuit 34 based on input operations received from the operator via the input interface 33 . For example, the system control function 341 controls CT scans performed in the X-ray CT apparatus 1 . Also, the system control function 341 controls generation and display of CT image data in the console device 30 by controlling a preprocessing function 342 , a reconstruction processing function 343 , and an image processing function 344 .

The preprocessing function 342 generates data by performing preprocessing such as logarithmic conversion processing, offset correction processing, inter-channel sensitivity correction processing, and beam hardening correction on the detection data output from the control board 17 . Data before preprocessing (detection data) and data after preprocessing may be collectively referred to as projection data.

The reconstruction processing function 343 performs reconstruction processing using the filtered back projection method, the iterative reconstruction method, or the like on the projection data generated by the preprocessing function 342 to obtain CT image data (reconstructed image data).

The image processing function 344 converts the CT image data generated by the reconstruction processing function 343 into tomographic image data of an arbitrary cross section or three-dimensional Convert to image data.

By the way, in general, heat is exhausted from an X-ray detector by thermally connecting a heat sink to a portion serving as a heat source and sending air (outside air) to the heat sink using a fan. An A/D (Analog to Digital) converter is known as a main heat source in an X-ray detector. An A/D converter (Analog to Digital Converter: ADC) is an electronic component that converts an analog signal output from a photodiode into a digital signal, and is usually installed outside the light shielding container. For example, the A/D converter is installed on a dedicated substrate (ADC substrate) provided outside the light shielding container.

When the A/D converter is installed outside the light shielding container, a signal line (flexible cable or the like) is run from the photodiode inside the light shielding container to the outside and connected to the A/D converter. From the viewpoint of noise elimination, it is required to shorten the length of the signal line through which the analog signal is transmitted. has structural limitations. Therefore, in order to further reduce noise, an "ADC substrate-integrated PD module" has been developed in which an A/D converter and a photodiode are mounted on the same substrate.

However, when an ADC substrate-integrated PD module is mounted, it is conceivable that the heat exhaust mechanism described above may not be able to perform sufficient heat exchange. This is because the ADC substrate-integrated PD module is accommodated (sealed) in a light-shielding container together with the scintillator array in order to eliminate the influence of ambient light (any light other than scintillation light). In other words, since the ADC substrate-integrated PD module generates heat in the light shielding container, it is considered that sufficient heat exchange cannot be performed without a heat exhaust mechanism for discharging the generated heat to the outside of the light shielding container.

Therefore, the X-ray CT apparatus 1 according to the first embodiment includes an X-ray detector 40 having a heat pipe that operates by centrifugal force due to rotation of the rotating frame 12 in order to efficiently exhaust heat. The configuration of the X-ray CT apparatus 1 according to the first embodiment will be described below.

In this embodiment, the case where the X-ray detector 40 includes an ADC board-integrated PD module will be described, but the embodiment is not limited to this. For example, the embodiments are applicable even when the A/D converter is provided at any position as a separate body from the photodiode. Also, the embodiment can discharge not only the heat of the A/D converter, but also the heat from any component that generates heat. That is, the embodiment can exhaust heat from the unit rotated by the rotating frame 12 together with the X-ray detector 40 . Examples of units rotated by the rotating frame 12 include a power supply unit that supplies power to the X-ray detector 40 and the control board 17 .

In addition, in this embodiment, connecting two (or three or more) members in a state in which heat can be conducted is referred to as “thermal connection”. Typically, thermal connection refers to bonding (connecting) two members with a heat-conducting adhesive, but even if the two members are simply brought into contact with each other, heat can be conducted between them. If it is in such a state, it is described as “thermally connected”.

3, 4A, 4B, and 4C are diagrams showing an example of the configuration of the X-ray detector 40 according to the first embodiment. FIG. 3 illustrates the internal configuration of one of the plurality of detector modules 50 provided in the X-ray detector 40. As shown in FIG. Also, FIG. 4A shows a cross-sectional view of the X-ray detector 40 passing through the X-ray irradiation direction and the slice direction. Also, FIG. 4B shows a cross-sectional view of the X-ray detector 40 passing through the X-ray irradiation direction and the channel direction. Also, FIG. 4C shows a schematic diagram showing only the heat pipe 70 of FIGS. 4A and 4B. In addition, in FIGS. 3, 4A, and 4B, the X-ray irradiation direction is indicated by a dashed arrow. 3, 4A, 4B, and 4C, the upper side corresponds to the side closer to the rotation center of the rotating frame 12, and the lower side corresponds to the side farther from the rotation center. In other words, the upper side in the drawing corresponds to the side closer to the X-ray tube 11 , and the lower side in the drawing corresponds to the side farther from the X-ray tube 11 .

As shown in FIGS. 3, 4A, and 4B, the detector module 50 has, for example, a scintillator array 51, an ADC substrate integrated PD module 52, and a positioning plate 53. FIG.

The scintillator array 51 is, for example, a member in which a plurality of rectangular parallelepiped scintillator blocks are arranged in the channel direction and the slice direction, and a grid-like reflector is formed between the scintillator blocks. The scintillator array 51 is stacked on the ADC substrate integrated PD module 52 . The scintillator array 51 generates light (scintillation light) according to the energy and intensity of the X-rays incident through the collimator unit 41 . The top surface of the scintillator array 51 (the surface closest to the collimator unit 41) corresponds to the X-ray incident surface.

The ADC board-integrated PD module 52 is an electronic component in which an A/D converter and a photodiode are mounted on the same board. The ADC board-integrated PD module 52 has the same number of photodiodes as the number of scintillator blocks. Each photodiode generates an analog signal corresponding to light generated for each scintillator block (that is, for each X-ray detection element). The A/D converter converts the analog signal read out from the photodiode for each X-ray detection element into a digital signal and outputs the digital signal to the control board 17 . The ADC board-integrated PD module 52 is an example of an electronic component that processes signals based on detected X-rays. Further, as the ADC board-integrated PD module 52, any conventional ADC board-integrated PD module can be applied.

In the ADC board-integrated PD module 52, if the A/D converter can convert an analog signal for each X-ray detection element into a digital signal, the arrangement position and number of arrangements with respect to the photodiodes can be set arbitrarily. be. However, the A/D converter is preferably arranged at a position that does not block the light generated for each scintillator block.

The positioning plate 53 is a support member that holds the positional relationship of the collimator unit 41 , the scintillator array 51 , and the ADC board-integrated PD module 52 . For example, the positioning plate 53 is attached to the collimator unit 41 by positioning pins 54 and 55 while supporting the scintillator array 51 and the ADC substrate integrated PD module 52 . The positioning plate 53 is made of aluminum, for example. Note that the positioning pins 54 and 55 are rod-shaped members for fixing the positional relationship between the collimator unit 41 and the positioning plate 53 .

Here, the positioning plate 53 is thermally connected to the ADC board-integrated PD module 52 . For example, when the A/D converter is exposed on the lower surface of the PD module 52 integrated with the ADC board (the surface in contact with the positioning plate 53), the positioning plate 53 contacts the PD module 52 integrated with the ADC board. Thermally connected. Further, for example, when the A/D converter is not exposed on the lower surface of the ADC board-integrated PD module 52, the A/D converter and the positioning plate 53 are thermally connected via a heat-conducting member. be. That is, the positioning plate 53 is an example of a heat transfer member that contacts the electronic component and transfers heat generated from the electronic component.

The light shielding container 60 is a container (closed container) that accommodates the collimator unit 41 and the plurality of detector modules 50 . That is, the light shielding container 60 accommodates the collimator unit 41 , the scintillator array 51 , the ADC substrate integrated PD module 52 , and the positioning plate 53 . The light-shielding container 60 accommodates the scintillator array 51 and the ADC substrate-integrated PD module 52, thereby making it possible to convert light generated by the scintillator array 51 into an analog signal without being affected by ambient light.

The collimator unit 41 has an X-ray shielding plate 41A and a support member 41B. The X-ray shielding plate 41A is configured by arranging a plurality of plate members made of metal such as tungsten or molybdenum in the channel direction. Each plate member is arranged in a direction parallel to the X-ray irradiation direction. The support member 41B is a support member that is formed in an arc shape along the channel direction and supports the X-ray shielding plate 41A. For example, the support members 41B are arranged on both sides of the X-ray shielding plate 41A in the slice direction and fixed to the side walls of the light shielding container 60. As shown in FIG. The side walls are members that form walls on both ends of the light shielding container 60 in the slice direction. Note that the X-ray shielding plate 41A is not limited to the case where a plurality of plate members are arranged in parallel, and may be arranged in a grid pattern.

The heat pipes 70, 71 are formed by a container containing a volatile working fluid. As for the material of the container constituting the heat pipes 70 and 71 and the type of the working fluid, any material may be applied as long as it is applicable to exhaust heat from electronic components. In the following description, the heat pipe 71 is basically the same as the heat pipe 70 except that it is arranged symmetrically with the heat pipe 70 in FIG. 4A. omitted.

In the example shown in FIGS. 4A and 4B, one end of the heat pipe 70 is provided inside the positioning plate 53 . Here, the heat pipe 70 and the positioning plate 53 are thermally connected to each other. At the portion thermally connected to the positioning plate 53 , the working fluid volatilizes under the influence of heat transferred from the positioning plate 53 . That is, as shown in FIG. 4C, the portion of the heat pipe 70 that is thermally connected to the positioning plate 53 functions as a heat receiving portion 70A.

For example, the heat receiving portion 70A of the heat pipe 70 is inserted into the positioning plate 53 from the end of the positioning plate 53 in the slice direction. The heat receiving portion 70A is arranged substantially along the slice direction inside the positioning plate 53 . Specifically, the heat receiving portion 70A is inclined so that the portion closer to the insertion position into the positioning plate 53 is positioned closer to the rotation center of the rotating frame 12, and the portion farther from the insertion position is positioned farther from the rotation center. placed.

Also, the other end of the heat pipe 70 is thermally connected to the light shielding container 60 . Specifically, the portion of the heat pipe 70 protruding outside the positioning plate 53 is bent in a direction parallel to the X-ray irradiation direction and thermally connected to the inner surface of the side wall of the light shielding container 60 . A fin 61 for heat radiation is installed on the outer surface of the side wall of the light shielding container 60 . That is, in the portion of the heat pipe 70 that is thermally connected to the light-shielding container 60 , the volatilized working fluid condenses due to the function of the heat radiation fins 61 . That is, as shown in FIG. 4C, the portion of the heat pipe 70 that is thermally connected to the light shielding container 60 functions as a heat radiating portion 70B. However, the side wall of the light shielding container 60 is preferably made of a heat conductive material. The side walls of the light shielding container 60 are plate members that form both end walls of the light shielding container 60 in the slice direction.

For example, the heat radiating portion 70B of the heat pipe 70 is arranged so as to pass through the support member 41B of the collimator unit 41 (see FIGS. 4A and 4B). For example, the support member 41B has grooves formed in a direction parallel to the X-ray irradiation direction. The heat radiating portion 70B is arranged along the groove formed in the support member 41B. The heat radiating portion 70B arranged along the groove of the support member 41B is thermally connected to the inner surface of the side wall of the light shielding container 60. As shown in FIG. The light shielding container 60 has fins 61 for heat dissipation on the outer surface of the side wall. For example, the heat radiation fins 61 are installed in a range (or a range covering the thermally connected part) of the outer surface of the side wall of the light shielding container 60 corresponding to the part where the heat radiation part 70B of the heat pipe 70 is thermally connected. be done. The fins 62 are heat radiation fins for condensing the working fluid in the heat pipes 71 .

Here, the reason why the heat pipes 70 and 71 are bent is to operate the working fluid by the centrifugal force generated by the rotation of the rotating frame 12 . In the example shown in FIG. 4A, the heat receiving portions of the heat pipes 70 and 71 are arranged inside the positioning plate 53 in a substantially V shape. Specifically, the heat-receiving portions of the two heat pipes 70 and 71 are arranged so as to be close to the center of rotation near both ends in the slicing direction of the positioning plate 53 and far from the center of rotation near the center in the slicing direction. be. As a result, the heat receiving portions of the heat pipes 70 and 71 are piped in a substantially V shape that is inclined upward from near the center toward near the ends. The heat pipes 70 and 71 extend along the X-ray irradiation direction outside the positioning plate 53 and are piped so as to penetrate the support member 41B of the collimator unit 41 .

With such piping, the heat pipes 70 and 71 bypass the scintillator array 51 located closer to the center of rotation of the rotating frame 12 than the ADC substrate-integrated PD module 52, which is a heat source, outside the light shielding container 60. heat can be dissipated to Further, even if the gantry 10 is tilted, in at least one of the heat pipes 70 and 71, the heat radiating portion is positioned closer to the center of rotation than the heat receiving portion, so cooling can be performed.

Although the configuration of one detector module 50 has been described in FIG. 3, each detector module 50 mounted on the X-ray detector 40 has the same configuration. That is, in the X-ray detector 40, a plurality of detector modules 50 are arranged in one direction (for example, channel direction).

Moreover, the configurations shown in FIGS. 3, 4A, 4B, and 4C are merely examples, and the contents of the drawings are not limited. For example, the dimensions of each illustrated member are not limited to those illustrated, and can be changed as appropriate within a range that does not affect the functions described above.

4A and 4B, the case where the light-shielding container 60 accommodates the collimator unit 41, the scintillator array 51, the ADC substrate-integrated PD module 52, and the positioning plate 53 has been described, but the embodiment is limited to this. not something. In other words, the light-shielding container 60 only needs to accommodate at least the ADC substrate integrated PD module 52 (A/D converter), the positioning plate 53, and the heat pipes 70 and 71, and can also accommodate other members. is.

Moreover, although FIG. 4B describes the case where the heat pipe is arranged at one place in the channel direction, the present invention is not limited to this. That is, the heat pipes may be arranged at multiple locations in the channel direction.

As described above, the X-ray CT apparatus 1 according to the first embodiment includes the X-ray tube 11, the X-ray detector 40, and the rotating frame 12. The X-ray tube 11 generates X-rays. The X-ray detector 40 detects X-rays. The rotating frame 12 rotatably supports the X-ray tube 11 and the X-ray detector 40 . The X-ray detector 40 includes an ADC board integrated PD module 52 , a positioning plate 53 , and heat pipes 70 and 71 . The ADC board-integrated PD module 52 processes signals based on detected X-rays. The positioning plate 53 is in contact with the ADC board-integrated PD module 52 and conducts heat generated from the ADC board-integrated PD module 52 . Heat pipes 70 and 71 contain a volatile working fluid. Heat receiving portions of the heat pipes 70 and 71 are provided inside the positioning plate 53 . The heat radiating portions of the heat pipes 70 and 71 are provided at positions closer to the rotation center of the rotating frame 12 than the heat receiving portions. Thereby, the X-ray CT apparatus 1 having the X-ray detector 40 can exhaust heat efficiently.

FIG. 5 is a diagram for explaining the effects of the X-ray CT apparatus 1 according to the first embodiment. As shown in FIG. 5, since the X-ray detector 40 is rotated by the rotating frame 12, centrifugal force is applied to the X-ray detector 40. As shown in FIG. Here, as shown in the left diagram of FIG. 5, when the X-ray detector 40 passes below the gantry device 10, a centrifugal force is applied downward in the diagram. At this time, since the heat receiving portion 70A is positioned below the heat radiating portion 70B, the working fluid condensed in the heat radiating portion 70B is sent to the heat receiving portion 70A by centrifugal force. Then, the vaporized working fluid with low density is sent to the heat radiating section 70B.

On the other hand, as shown in the right diagram of FIG. 5, when the X-ray detector 40 passes above the gantry 10, centrifugal force is applied upward in the diagram. At this time, since the heat receiving portion 70A is positioned above the heat radiating portion 70B, the working fluid condensed at the heat radiating portion 70B is sent to the heat receiving portion 70A by centrifugal force. Then, the vaporized working fluid with low density is sent to the heat radiating section 70B.

Although FIG. 5 illustrates only the case where the X-ray detector 40 is positioned below or above the gantry 10, centrifugal force is It takes in the direction away from the center of rotation. Moreover, even if the X-ray detector 40 exists at any position on the rotation orbit, the heat radiation part 70B is provided at a position closer to the center of rotation than the heat receiving part 70A. Therefore, the working fluid condensed in the heat radiating portion 70B is sent to the heat receiving portion 70A by centrifugal force regardless of the position of the X-ray detector 40 on the rotation track. Therefore, heat pipes 70 and 71 can be operated by centrifugal force due to rotation of rotating frame 12 . As a result, the X-ray CT apparatus 1 including the X-ray detector 40 can constantly exhaust heat regardless of the rotational position and tilt angle of the X-ray detector 40 .

Also, the heat pipes 70 and 71 can discharge the heat generated inside the light shielding container 60 to the outside of the light shielding container 60 . Therefore, the X-ray CT apparatus 1 including the X-ray detector 40 can perform sufficient heat exchange even when the ADC board-integrated PD module 52 is mounted.

At least part of the heat pipes 70 and 71 extends along the normal direction to the rotation track of the rotating frame 12 . This normal direction corresponds to the irradiation direction of X-rays, and corresponds to the direction in which the centrifugal force generated by the rotation of the rotating frame 12 is applied. Therefore, the X-ray CT apparatus 1 including the X-ray detector 40 can efficiently utilize the centrifugal force to operate the heat pipe.

Further, the heat pipes 70 and 71 radiate heat through heat radiation fins 61 and 62 provided on the outer surface of the side wall of the light shielding container 60 . Therefore, the X-ray CT apparatus 1 including the X-ray detector 40 is expected to exhaust heat sufficiently even if the X-ray detector 40 is not provided with a cooling fan. In other words, the X-ray detector 40 does not have to have a fan for cooling.

Also, for example, the heat radiating portions of the heat pipes 70 and 71 are arranged along grooves formed in the support member 41B. As a result, the heat pipes 70 and 71 can be provided with a large area for thermal connection with the side wall of the light shielding container 60, so that heat can be efficiently dissipated.

Further, the heat radiation portions of the heat pipes 70 and 71 are provided at positions closer to the center of rotation of the rotation frame 12 than the ADC substrate-integrated PD module 52 serving as a heat source. Therefore, the X-ray CT apparatus 1 including the X-ray detector 40 can efficiently utilize the centrifugal force to operate the heat pipe.

In addition, the cooling fan is weak against rotation by the rotating frame 12 due to its nature, and may break down. However, since the X-ray CT apparatus 1 including the X-ray detector 40 does not need to include a fan for cooling the X-ray detector 40, it is possible to reduce causes of failure. As a result, the X-ray CT apparatus 1 including the X-ray detector 40 can improve maintainability.

Further, the X-ray CT apparatus 1 including the X-ray detector 40 can discharge heat generated inside the light shielding container 60 to the outside of the light shielding container 60 . Therefore, in addition to the electronic components that serve as heat sources, various substrates exposed to the outside air and on which dust tends to accumulate can be accommodated in the light shielding container 60, so that the accumulation of dust can be reduced. Become.

In the first embodiment, the heat dissipating portions of the heat pipes 70 and 71 extend in the normal direction (direction parallel to the X-ray irradiation direction). direction. However, in order to efficiently use the centrifugal force to send the condensed working fluid to the heat receiving part, it is preferable that the angle of inclination with respect to the normal direction is small.

(Modification of the first embodiment)
In the above embodiment, the heat pipes 70 and 71 are directly thermally connected to the inner surface of the side wall of the light shielding container 60, but the embodiment is not limited to this. For example, the heat pipe may be indirectly thermally connected to the inner surface of the side wall of the light shielding container 60 .

FIG. 6 is a diagram showing an example configuration of an X-ray detector 40 according to a modification of the first embodiment. FIG. 6 shows a cross-sectional view of the X-ray detector 40 along the X-ray irradiation direction and the slice direction. In addition, in FIG. 6, the X-ray irradiation direction is indicated by a dashed arrow. Also, in FIG. 6, the description will focus on the points that are different from FIG. 4A, and the same components as in FIG. 4A will be assigned the same reference numerals as in FIG. 4A, and the description will be omitted. In addition, although FIG. 6 illustrates only the configuration on one side in the slice direction, the configuration on the opposite side is the same.

As shown in FIG. 6 , the X-ray detector 40 according to the modified example of the first embodiment includes heat pipes 72 . The heat pipe 72 is provided inside the light shielding container 60 in the same manner as the heat pipe 70 shown in FIG. 4A. A heat receiving portion of the heat pipe 72 is provided inside the positioning plate 53 .

Here, the heat radiating portion of the heat pipe 72 is thermally connected to the inner surface of the side wall of the light shielding container 60 via a heat transfer member placed between the inner surface of the side wall of the light shielding container 60 . In the example shown in FIG. 6, the heat radiating portion of the heat pipe 72 is thermally connected to the inner surface of the side wall of the light shielding container 60 via the support member 41B of the collimator unit 41. In the example shown in FIG.

The support member 41B according to the modified example of the first embodiment is made of, for example, a highly thermally conductive material such as aluminum. A hole (or groove) having a diameter equal to or larger than the outer diameter of the heat pipe 72 is formed in the support member 41B in a direction parallel to the X-ray irradiation direction. The heat pipe 72 is inserted into the hole of the support member 41B and thermally connected to the inner surface of the hole. The support member 41B is thermally connected to the inner surface of the side wall of the light shielding container 60. As shown in FIG. On the outer surface of the side wall of the light-shielding container 60, heat radiation fins 63 are provided in a range corresponding to a portion where the heat pipe 72 and the hole of the support member 41B are thermally connected (or a range covering the thermally connected portion). is installed. As a result, the volatilized working fluid is condensed in the portion where the heat pipe 72 and the hole of the support member 41B are thermally connected due to the function of the fins 63 for heat radiation. That is, the portion of the heat pipe 72 that is thermally connected to the hole functions as a heat radiating portion.

Thus, the heat pipe 72 according to the modification of the first embodiment is indirectly thermally connected to the inner surface of the side wall of the light shielding container 60 . Thereby, the X-ray detector 40 according to the modification of the first embodiment can exhaust heat efficiently.

Also, the heat pipe 72 fixes the position between the collimator unit 41 and the positioning plate 53 . In other words, the heat pipe 72 functions as a positioning pin that fixes the position between the collimator unit 41 and the positioning plate 53 . Thereby, the X-ray detector 40 according to the modification of the first embodiment can reduce the number of positioning pins.

Note that the configuration shown in FIG. 6 is merely an example, and is not limited to the contents of the illustration. For example, in FIG. 6, the case of indirect thermal connection via the support member 41B has been described, but the present invention is not limited to this. For example, the heat pipe 72 may be indirectly thermally connected to the inner surface of the side wall of the light shielding container 60 via a heat transfer member provided separately from the support member 41B.

Also, for example, FIG. 6 illustrates the case where the entire support member 41B is made of a material with high thermal conductivity, but the present invention is not limited to this. For example, the portion of the support member 41B between the heat radiating portion of the heat pipe 72 and the side wall of the light shielding container 60 may be made of a material with high thermal conductivity.

(Second embodiment)
In the first embodiment, the case where the heat radiating portion of the heat pipe is provided inside the light shielding container 60 has been described, but the embodiment is not limited to this. For example, the heat radiating portion of the heat pipe may be provided outside the light shielding container 60 .

FIG. 7 is a diagram showing an example of the configuration of the X-ray detector 40 according to the second embodiment. FIG. 7 shows a cross-sectional view of the X-ray detector 40 along the X-ray irradiation direction and the slice direction. In addition, in FIG. 7, the X-ray irradiation direction is indicated by a dashed arrow. 7A and 7B, the description will focus on the points that are different from those in FIG. 4A, and the same components as in FIG. 4A will be assigned the same reference numerals as in FIG. 4A, and descriptions thereof will be omitted. Also, although FIG. 7 illustrates only one side configuration in the slice direction, the configuration on the opposite side is the same.

As shown in FIG. 7, the X-ray detector 40 has a heat pipe 73 . The heat receiving portion of the heat pipe 73 is provided inside the positioning plate 53 inside the light shielding container 60, like the heat receiving portion 70A of the heat pipe 70 shown in FIG. 4A.

Here, the heat radiating portion of the heat pipe 73 is provided outside the light shielding container 60 . In the example shown in FIG. 7 , the heat dissipation portion of the heat pipe 73 is thermally connected to the heat dissipation fins 64 outside the light shielding container 60 . In this case, it is preferable to provide a positioning pin 54 to fix the position between the collimator unit 41 and the positioning plate 53 .

A hole having a diameter equal to or larger than the outer diameter of the heat pipe 73 is formed in the side wall of the light shielding container 60 according to the second embodiment. The heat pipe 73 protrudes outside the light shielding container 60 through a hole in the light shielding container 60 . The heat pipe 73 and the hole of the light-shielding container 60 are bonded with a light-shielding sealing material. A portion of the heat pipe 73 protruding outside the light shielding container 60 is bent in a direction parallel to the X-ray irradiation direction and thermally connected to the fins 64 for heat dissipation. As a result, the volatilized working fluid is condensed by the function of the fins 64 in the portion of the heat pipe 73 that is thermally connected to the fins 64 . That is, the portion of the heat pipe 73 that is thermally connected to the fins 64 functions as a heat radiating portion.

Thus, in the X-ray detector 40 according to the second embodiment, the light shielding container 60 accommodates at least the ADC substrate integrated PD module 52 , the positioning plate 53 and the heat receiving portions of the heat pipes 73 . Also, the light shielding container 60 has a hole through which the heat pipe 73 is passed. This hole is a hole that penetrates the side wall of the light shielding container 60 . Also, the heat radiation portion of the heat pipe 73 is provided outside the light shielding container 60 . This allows the X-ray detector 40 to efficiently exhaust heat outside the light shielding container 60 . Therefore, the X-ray detector 40 can discharge the heat generated inside the light shielding container 60 to the outside of the light shielding container 60 .

In addition, in FIG. 7, although the case where heat is dissipated using the fins 64 installed outside the light shielding container 60 is illustrated, the embodiment is not limited to this. For example, the heat dissipation portion of the heat pipe 73 may be thermally connected to the inner surface of the housing of the X-ray detector 40 . Since the housing of the X-ray detector 40 has a large contact area with the air, a heat dissipation effect is expected. Furthermore, the outer surface of the housing of the X-ray detector 40 may be provided with fins for heat radiation. That is, the heat radiating portion of the heat pipe is thermally connected to at least one of the housing of the X-ray detector 40 and the heat radiating fins 64 .

(Other embodiments)
Various different forms may be implemented in addition to the embodiments described above.

(Improved thermal conductivity of positioning plate 53)
In the above-described embodiment, the positioning plate 53 made of aluminum transfers heat to the heat receiving portion 70A. It is possible.

FIG. 8 is a diagram showing an example of the configuration of an X-ray detector 40 according to another embodiment. FIG. 8 shows a cross-sectional view of the X-ray detector 40 along the X-ray irradiation direction and the slice direction. In addition, in FIG. 8, the X-ray irradiation direction is indicated by a dashed arrow. 8A and 8B, the description will focus on the points that are different from those in FIG. 4A, and the same components as those in FIG. 4A will be assigned the same reference numerals as those in FIG. 4A, and their description will be omitted.

As shown in FIG. 8, the positioning plate 53 has, for example, a member 53A made of copper in addition to a member made of aluminum. Copper is a material with higher thermal conductivity than aluminum. In other words, the positioning plate 53 has a first member with thermal conductivity and a second member with higher thermal conductivity than the first member. Thereby, the X-ray detector 40 can improve thermal conductivity.

The member 53A may be provided at only one position on the positioning plate 53, or may be provided at a plurality of positions. However, the member 53A is preferably provided for each electronic component that serves as a heat source.

(Variations regarding the shape of the heat pipe)
Moreover, the shape of the heat pipe illustrated in the above embodiment is merely an example, and other shapes can be realized.

9, 10, and 11 are diagrams showing an example of the configuration of an X-ray detector 40 according to another embodiment. 9, 10, and 11 show cross-sectional views of the X-ray detector 40 passing through the X-ray irradiation direction and the slice direction. In addition, in FIGS. 9, 10, and 11, the X-ray irradiation direction is indicated by a dashed arrow. 9, 10, and 11 will be described with a focus on the points that are different from FIG. 4A, and the same components as in FIG. 4A will be assigned the same reference numerals as in FIG. 4A, and their description will be omitted.

As shown in FIG. 9, the X-ray detector 40 may have heat pipes 74 and 75 . The heat pipes 74 and 75 are curved and extended inside the positioning plate 53 . That is, the heat pipe is not limited to being laid in a bent state, and may be laid in a curved state.

The X-ray detector 40 may also include a heat pipe 76, as shown in FIG. The heat pipe 76 has a shape (substantially V-shaped) such that the heat pipe 70 and the heat pipe 71 are connected near the central portion in the slice direction of the positioning plate 53 .

Also, as shown in FIG. 11, the X-ray detector 40 may include a heat pipe 77 . A heat radiating portion of the heat pipe 77 is formed on one side of the collimator unit 41 in the slice direction. The heat receiving portion of the heat pipe 77 is formed along the slice direction of the positioning plate 53, and is provided closer to the center of rotation as it is closer to the heat radiating portion, and farther from the center of rotation as it is farther from the heat radiating portion.

(When an A/D converter is provided outside the light shielding container 60)
Also, for example, the embodiments are applicable to a case where an A/D converter is provided outside the light shielding container 60 .

FIG. 12 is a diagram showing an example configuration of an X-ray detector 40 according to another embodiment. FIG. 12 shows a cross-sectional view of the X-ray detector 40 along the X-ray irradiation direction and the slice direction. In addition, in FIG. 12, the X-ray irradiation direction is indicated by a dashed arrow. Also, in FIG. 12, the points different from FIG. 4A will be mainly described, and the same components as in FIG. 4A will be assigned the same reference numerals as in FIG. 4A, and description thereof will be omitted.

As shown in FIG. 12 , the X-ray detector 40 includes a substrate 90 and heat pipes 73 . The substrate 90 is a substrate that is provided outside the light shielding container 60 and has an A/D converter. Also, the heat pipe 73 is provided outside the light shielding container 60 .

Here, the heat receiving portion of the heat pipe 78 is thermally connected to the substrate 80 . Specifically, the heat receiving portion of the heat pipe 78 is preferably directly thermally connected to the A/D converter provided on the substrate 80 . Also, the heat radiating portion of the heat pipe 78 is provided at a position closer to the center of rotation of the rotating frame 12 than the heat receiving portion, and is thermally connected to the heat radiating fins 82 .

Thereby, the X-ray detector 40 can be applied even when an A/D converter is provided outside the light shielding container 60 . In this case, the light shielding container 60 accommodates a photodiode 65 instead of the ADC substrate integrated PD module 52 .

(Rotational position control of the X-ray detector 40 when the gantry is stopped)
Further, when stopping the gantry 10 , the X-ray CT apparatus 1 stops with the X-ray detector 40 moved below the rotating frame 12 .

For example, when the processing circuit 34 of the X-ray CT apparatus 1 receives an instruction from the operator to end imaging, the processing circuit 34 rotates the rotating frame 12 until the X-ray detector 40 is positioned below the rotating frame 12 . Then, the gantry device 10 is stopped. In this case, the heat radiating portion of the heat pipe is located above the heat receiving portion (upper in the direction of gravity). Therefore, the working fluid condensed in the heat radiating portion moves to the heat receiving portion due to gravity. As a result, even if residual heat remains inside the X-ray detector 40 even though the gantry 10 has stopped, the heat pipe can be activated by gravity.

(multi-console)
Although the console device 30 has been described as performing multiple functions with a single console, the multiple functions may be performed by separate consoles. For example, the functions of the processing circuit 34 such as the preprocessing function 342 and the reconstruction processing function 343 may be distributed.

(integrated server)
The processing circuit 34 is not limited to being included in the console device 30, and may be included in an integrated server that collectively processes detection data acquired by a plurality of medical image diagnostic apparatuses.

(Main body of post-processing)
Post-processing may be performed on either the console 30 or an external workstation. Alternatively, both the console 30 and the work station may be processed at the same time.

(full scan/half scan)
Reconstruction of a CT image requires projection data for 360° around the circumference of the subject, and projection data for 180°+fan angle for the half-scan method. This embodiment can be applied to any reconstruction method. In the following, for the sake of simplicity, a reconstruction (full-scan reconstruction) method for reconstruction using projection data for 360 degrees around the object will be used.

(single tube/multiple tubes)
The above-described embodiments can be applied to both a single-tube type X-ray CT apparatus and a so-called multi-tube type X-ray CT apparatus in which a plurality of pairs of X-ray tubes and detectors are mounted on a rotating ring. is.

(Application to other medical image diagnostic apparatuses)
The above-described embodiments are applicable not only to the X-ray CT apparatus but also to other medical image diagnostic apparatuses. For example, the heat pipe described above is mounted on a rotating body in a medical image diagnostic apparatus (nuclear medicine diagnostic apparatus, dental CT apparatus, etc.) having a configuration in which equipment such as a radiation detector is rotated using a rotating frame. Thus, it is possible to efficiently discharge the heat generated inside the rotating body.

(Destination to save projection data/reconstructed image data)
The storage of projection data and reconstructed image data is not limited to the case where the memory 31 of the console device 30 stores the data. , the projection data and the reconstructed image data may be stored in response to the storage request.

According to at least one embodiment described above, heat can be efficiently exhausted.

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

1 X-ray CT apparatus 11 X-ray tube 12 Rotating frame 40 X-ray detector 70, 71 Heat pipe

Claims (14)

an X-ray tube for generating X-rays;
an X-ray detector that detects the X-ray;
a rotating frame that rotatably supports the X-ray tube and the X-ray detector,
The X-ray detector is
a scintillator array that generates light in response to the incident X-rays;
an electronic component for processing the light-based signal;
a heat transfer member that is in contact with the electronic component and holds the positional relationship between the scintillator array and the electronic component, the heat transfer member transferring heat generated from the electronic component;
a heat pipe containing a volatile working fluid;
The heat receiving portion of the heat pipe is provided inside the heat transfer member,
the heat radiating portion of the heat pipe is provided at a position closer to the center of rotation of the rotating frame than the heat receiving portion ;
The heat transfer member has a first member having thermal conductivity and a second member having higher thermal conductivity than the first member,
the second member is in contact with the heat receiving portion and the electronic component;
X-ray CT equipment. The heat pipe is arranged in a bent or curved state between the heat receiving part and the heat dissipating part so that the working fluid is actuated by centrifugal force generated by the rotation of the rotating frame.
The X-ray CT apparatus according to claim 1. at least part of the heat pipe extends along a direction normal to the rotation orbit of the rotating frame;
3. The X-ray CT apparatus according to claim 1 or 2. The X-ray detector does not have a fan for cooling,
The X-ray CT apparatus according to any one of claims 1-3. The heat radiation part is provided at a position closer to the center of rotation of the rotating frame than the electronic component.
The X-ray CT apparatus according to any one of claims 1-4. The heat receiving portion of the heat pipe is arranged to be close to the center of rotation near both ends in the slicing direction of the heat transfer member, and to be far from the center of rotation near the center of the heat transfer member in the slice direction. piped in a substantially V shape inside the thermal member;
The X-ray CT apparatus according to any one of claims 1-5. further comprising a light-shielding container housing at least the electronic component, the heat transfer member, and the heat pipe;
The heat radiation part is thermally connected to the inner surface of the side wall of the light shielding container,
The X-ray CT apparatus according to any one of claims 1-6 . The light-shielding container includes heat-dissipating fins on the outer surface of the side wall to which the heat-dissipating portion is thermally connected.
The X-ray CT apparatus according to claim 7 . the heat pipe fixes a position between the collimator unit and the heat transfer member;
The X-ray CT apparatus according to claim 7 or 8 . further comprising a light shielding container housing at least the electronic component, the heat transfer member, and the heat receiving portion of the heat pipe;
The light shielding container has a hole through which the heat pipe passes,
The heat radiation part is provided outside the light shielding container,
The X-ray CT apparatus according to any one of claims 1-6 . The heat dissipation part is thermally connected to at least one of heat dissipation fins and a housing of the X-ray detector outside the light shielding container,
The X-ray CT apparatus according to claim 10 . The electronic component is an A/D converter-integrated PDA, which is a PDA (Photodiode Array) incorporating an A/D (Analog to Digital) converter.
The X-ray CT apparatus according to any one of claims 1-11 . a scintillator array that generates light in response to incident X-rays;
an electronic component for processing the light-based signal;
a heat transfer member that is in contact with the electronic component and holds the positional relationship between the scintillator array and the electronic component, the heat transfer member transferring heat generated from the electronic component;
a heat pipe containing a volatile working fluid;
The heat receiving portion of the heat pipe is provided inside the heat transfer member,
the heat radiating portion of the heat pipe is provided at a position closer to the X-ray incident surface than the heat receiving portion ;
The heat transfer member has a first member having thermal conductivity and a second member having higher thermal conductivity than the first member,
the second member is in contact with the heat receiving portion and the electronic component;
detector module. an X-ray tube for generating X-rays;
an X-ray detector that detects the X-ray;
a rotating frame that rotatably supports the X-ray tube and the X-ray detector,
The X-ray detector is
an electronic component that is an A/D converter-integrated PDA that processes signals based on the detected X-rays and that is a PDA (Photodiode Array) incorporating an A/D (Analog to Digital) converter ;
a heat pipe containing a volatile working fluid;
a light shielding container that houses at least the electronic component and the heat receiving part of the heat pipe;
the heat receiving portion of the heat pipe is thermally connected to the electronic component,
The heat radiating portion of the heat pipe is provided at a position closer to the rotation center of the rotating frame than the heat receiving portion, and discharges heat to the outside of the light shielding container.
X-ray CT equipment.

Images