JP5202742B2 - Radiation imaging apparatus, control method therefor, and program - Google Patents

Description

The present invention relates to a radiation imaging apparatus configured to include a radiation detector that detects radiation transmitted through a subject as an image signal, and an electrical component that processes the image signal, a control method thereof, and a program. . In the description of the present specification, an example is shown in which X-rays are applied as radiation. However, the present invention is not limited to this, and examples of radiation include α rays, β rays, and γ rays. And

  Conventionally, for example, in the field of industrial non-destructive inspection and medical diagnosis, X-ray imaging apparatuses using X-rays, which are a kind of radiation, have been widely used. In this X-ray imaging apparatus, for example, an X-ray generation unit and an imaging unit with a built-in X-ray detector are arranged facing each other on opposite sides of the subject at the center, and the X-ray generation unit X-rays from the X-ray generation unit The image information (image signal) is obtained by detecting X-rays transmitted through the subject with an X-ray detector.

  In recent years, with the development of digital technology, the progress of digital X-ray detectors using various imaging devices that convert detected X-rays into electrical signals has been remarkable. An X-ray imaging apparatus equipped with this digital X-ray detector has begun to be introduced into many facilities in place of an imaging apparatus that performs analog imaging by a conventional film / screen method using a phosphor and a photosensitive film. .

  A flat panel detector (flat panel), which is a typical X-ray detector that handles digital signals, generally includes a fluorescent substance that converts X-rays into visible light, and pixels that are composed of photoelectric conversion elements and switching elements in two columns and rows. It is configured by combining photoelectric conversion panels arranged in a three-dimensional array. The X-rays incident on the X-ray detector are converted into electric charges in each pixel through visible light from the phosphor, and the electric charges (electrical signals) are read out from the respective pixels and output as image signals.

  In recent years, with the widespread use of digital X-ray detectors, demands for technical issues such as miniaturization of X-ray imaging apparatuses, improvement of image quality of captured images, and stability of images have become more severe. And as a point that must be considered in realizing these, there is heat generation of electrical parts used in the apparatus and indispensable for digitization, and a heat dissipation means for efficiently radiating this heat generation is required. That is. In this case, heat radiation is an important issue not only for ensuring the normal operation and durability of the heat generating electrical components, but also for preventing changes in the characteristics of the X-ray detector due to temperature rise inside the X-ray imaging apparatus. .

  For example, a fan motor is used as one of the most effective heat dissipation methods in electronic equipment with a housing structure, and forced air is used to cool the inside by introducing external air while discharging the hot air inside the housing. There is an air-cooled heat dissipation method. However, according to this method, it is unavoidable that foreign matter enters the inside of the housing during operation, and light from outside also enters by providing a vent in a part of the exterior member for ventilation. It becomes easy to do.

  The X-ray detector can output an image signal with less noise by detecting only light in which X-rays are converted by a phosphor. Therefore, in the X-ray imaging apparatus, it is not preferable that extraneous light from the outside penetrates to the vicinity of the X-ray detector. In addition, a casing made of an exterior member generally has an important role as a shield for electromagnetic noise, and if there is an opening such as a vent in the casing, a path through which electromagnetic noise enters is created. There is a risk that the driving of the internal electric circuit may be hindered. For these reasons, it is not desirable that an opening is present in the exterior member of the operating X-ray imaging apparatus.

  In order to deal with such a problem, for example, Patent Document 1 below proposes a technique in which a shutter that opens and closes a vent is provided inside the vent and a fan is provided inside the shutter. In an X-ray imaging apparatus that performs still image imaging in which only a very short time is actually taken during the operation period of the X-ray imaging apparatus, it is sufficiently effective to use the means of Patent Document 1 or the like. However, when external air is introduced into the X-ray imaging apparatus, intrusion of moisture, dust and the like is unavoidable at the same time. Moisture and dust that has entered the inside may accelerate the deterioration of the phosphor and semiconductor elements of the X-ray detector, or the accumulated dust may interfere with the heat dissipation of the electrical components, and may be a source of ignition. There is also a risk of becoming.

  In addition, providing an air filter made of a porous synthetic resin material at the vent for introducing outside air is one of the countermeasures against dust, but it is less effective in preventing moisture intrusion, and cleaning and replacement of the air filter It is inconvenient because it requires maintenance work.

On the other hand, an X-ray imaging apparatus as shown in FIG. 12 has also been proposed.
FIG. 12 is a schematic diagram illustrating a conventional example and illustrating an example of a schematic configuration of an imaging unit in the X-ray imaging apparatus. Specifically, the imaging unit 1200 in FIG. 12 includes a substantially sealed casing (box) including an X-ray detector 1201 and an electrical component 1204 and the like, and an exterior member outside the casing. A fan motor 1213 for ventilation is provided inside an exterior.

  X-rays emitted from an X-ray generator (not shown) are incident on the X-ray detector 1201 in the direction of the arrow, and the X-ray detector 1201 converts the incident X-rays into electrical signals (image signals). To do. The image signal is input from the X-ray detector 1201 through the flexible cable 1202 to the signal processing board 1203. A plurality of electrical components 1204 are mounted on the signal processing board 1203, and these electrical components 1204 work to apply various processes to the image signal from the X-ray detector 1201, and also X-rays It performs various functions for driving the detector 1201.

  The electrical component 1204 is a main heat source in the photographing unit 1200, and a heat conduction sheet 1205, a heat conduction member 1206, and a heat radiation frame 1207 are provided as heat radiation means for avoiding concentration of generated heat. And constitutes a heat transfer path.

  The heat conductive sheet 1205 is formed of, for example, an elastic sheet made of silicone rubber, and transfers heat of the electric component 1204 to the heat conductive member 1206. The heat conducting member 1206 is made of a material having high heat conductivity such as copper or aluminum, and efficiently transfers heat to the heat radiating frame 1207. When the amount of heat generated is large, a special heat conduction tool such as a heat pipe or a graphite material may be used as the heat conduction member 1206. The heat dissipating frame 1207 is a member for releasing the heat conducted by the heat conducting member 1206 and the heat transmitted by air convection and radiation to the outside while widely diffusing, and the frame of the housing structure. A part is also used.

  The detector frame 1208 holds the X-ray detector 1201, the signal processing board 1203, and the like via a member (not shown) while containing the X-ray detector 1201 and the signal processing board 1203. The detector frame 1208 is made of, for example, a metal having electrical conductivity such as iron, stainless steel, and aluminum. The detector frame 1208 protects the X-ray detector 1201 and the electrical component 1204 included from external electrical noise, It also has a role to prevent release.

  The X-ray transmission unit cover 1209 protects the X-ray detector 1201 while transmitting X-rays so as not to deteriorate. For the X-ray transmission portion cover 1209, a carbon plate or a thin aluminum plate, which is a material having a high X-ray transmittance, is used. Here, the heat dissipation frame 1207, the detector frame 1208, and the X-ray transmission part cover 1209 are combined to form a housing structure, and the space including the X-ray detector 1201, the signal processing board 1203, and the electric component 1204 is substantially sealed. It is configured. Therefore, external light does not reach the photosensitive portion of the X-ray detector 1201, and it is possible to prevent moisture and dust from entering the vicinity of the X-ray detector 1201 and the signal processing board 1203. Further, the shielding effect against electrical noise intrusion and electromagnetic wave emission is enhanced.

  The exterior cover 1210 is a member that is outside the detector frame 1208 and forms the appearance of the imaging unit 1200. The exterior cover 1210 supports the detector frame 1208 by connection by a not-shown part, and is supported from the outside by a mechanism not shown. The exterior cover 1210 is provided with vent holes 1211 and 1212, and the vent motor 1213 is provided with a fan motor 1213 at a close position. The fan motor 1213 blows air so that the air in the photographing unit 1200 is discharged from the vent 1211. The vent 1212 is for taking in air outside the photographing unit 1200 into the inside.

  The heat inside the casing is transferred to the air coming in contact from the outer surface of the casing while being diffused at the portion of the heat dissipation frame 1207. The air flows in the direction B indicated by the arrow by the fan motor 1213, passes through the vent 1211, and is discharged out of the photographing unit 1200.

  The exterior cover 1210 has vent holes 1211 and 1212, and external light, moisture, dust, and the like may enter the photographing unit 1200. However, the X-ray detector 1201 and the signal processing board 1203 can be prevented from entering even inside the detector frame 1208.

  In the example shown in FIG. 12, the configuration of ventilation air cooling by the fan motor 1213 is shown. However, in the case of low power consumption, the configuration not including the fan motor 1213, that is, the X-ray imaging apparatus configured by heat radiation by natural air cooling is also configured. it can.

JP-A-10-177224

  However, even the conventional X-ray imaging apparatus having the above-described configuration has caused the following problems.

  With the recent development of signal processing technology and signal transmission technology, an environment for handling image signals at a high frame rate has been established. As a field of use of digital X-ray detectors, until now it was mainly used for X-ray imaging devices that only acquire still images. Opportunities for use in imaging apparatuses that perform CT imaging that handles three-dimensional image information are also increasing.

  If high-speed moving image shooting is performed, the frequency of driving electrical components per unit time increases, which inevitably increases power consumption and heat generation. Although X-ray detector heat generation was not problematic for low-frequency driving in still image shooting, it has a significant effect on the characteristics of the X-ray detector itself in cases such as when continuous driving for moving image shooting continues for a long time. It may become a level that affects.

  In addition, if the heat generation of the electric component 1204 mounted on the signal processing board 1203 causes a distribution of the amount of heat generation in the plane of the signal processing board 1203, the X-ray detector 1201 in the same space is also affected. Effect. As a result, temperature unevenness between the high temperature portion and the low temperature portion occurs in the panel surface of the X-ray detector 1201, and the detection characteristics vary from portion to portion, degrading the quality of the output image. Further, immediately after the energization at the time of starting the X-ray imaging apparatus, the temperature of the X-ray detector is low, but the temperature becomes high due to the influence of heat generation while the drive is continuously performed. However, there is a problem that the detection characteristics of the X-ray detector change and lacks stability.

  The present invention has been made in view of such problems, and improves the cooling effect of the electric parts that generate heat, even when performing moving image shooting that continues for a long time, and the radiation detector. The purpose is to provide a mechanism to achieve stable performance maintenance.

The radiation imaging apparatus of the present invention is a radiation imaging apparatus configured to include a radiation detector that detects, as an image signal, radiation that has passed through a subject, and an electrical component that processes the image signal. And a housing for storing the electrical component therein, a blower unit that is provided in the housing and sends air on the electrical component side to the radiation detector side, and when the subject is continuously photographed, Control means for terminating the operation of the blowing means when the temperature in the vicinity of the radiation detector exceeds a predetermined temperature .
The method of controlling a radiation imaging apparatus according to the present invention is provided in a housing that stores therein a radiation detector that detects radiation transmitted through a subject as an image signal and an electrical component that processes the image signal. A method for controlling a radiography apparatus including a blowing unit that sends air on the side to the radiation detector side, wherein when the subject is continuously imaged, a temperature in the vicinity of the radiation detector is a predetermined value. A step of terminating the operation of the blowing means when the temperature is exceeded ;
The program of the present invention is for causing a computer to execute the steps of the method for controlling the radiation imaging apparatus.

  According to the present invention, it is possible to improve the cooling effect of the electric parts that generate heat, and to maintain stable performance of the radiation detector, even when performing moving image shooting that continues for a long time.

It is a schematic diagram which shows an example of schematic structure of the X-ray imaging apparatus (radiography apparatus) which concerns on the 1st Embodiment of this invention. In the X-ray imaging apparatus (radiation imaging apparatus) according to the first embodiment of the present invention, it is a schematic diagram illustrating an example of a control relationship of a control unit with respect to an imaging unit. It is a characteristic view which shows an example of the temperature change inside the imaging | photography part shown in FIG.1 and FIG.2. It is a characteristic view which shows an example of the temperature change inside the imaging | photography part shown in FIG.1 and FIG.2. It is a flowchart which shows an example of the process sequence in the control method of the X-ray imaging apparatus (radiography apparatus) which concerns on the 1st Embodiment of this invention. It is a characteristic view which shows an example of the temperature change inside the imaging part of the X-ray imaging apparatus (radiation imaging apparatus) which concerns on the 1st Embodiment of this invention. It is a schematic diagram which shows an example of the control relationship with respect to the imaging | photography part of a control part in the X-ray imaging apparatus (radiography apparatus) which concerns on the 2nd Embodiment of this invention. It is a flowchart which shows an example of the process sequence in the control method of the X-ray imaging apparatus (radiography apparatus) which concerns on the 2nd Embodiment of this invention. It is a schematic diagram which shows an example of the control relationship with respect to the imaging part of a control part in the X-ray imaging apparatus (radiography apparatus) which concerns on the 3rd Embodiment of this invention. It is a flowchart which shows an example of the process sequence in the control method of the X-ray imaging apparatus (radiography apparatus) which concerns on the 3rd Embodiment of this invention. FIG. 9 is a schematic diagram illustrating an example of a fan motor and an operation state of the fan motor for each condition of a temperature value T1 and a temperature value T2 during continuous shooting according to the third embodiment of the present invention. It is a schematic diagram which shows a prior art example and shows an example of schematic structure of the imaging | photography part in an X-ray imaging device.

  Hereinafter, embodiments (embodiments) for carrying out the present invention will be described with reference to the drawings.

(First embodiment)
First, a first embodiment of the present invention will be described.
FIG. 1 is a schematic diagram illustrating an example of a schematic configuration of an X-ray imaging apparatus (radiation imaging apparatus) according to the first embodiment of the present invention. Here, in FIG. 1, the same code | symbol is attached | subjected about the structure similar to the structure shown in FIG.

  As shown in FIG. 1, the X-ray imaging apparatus (radiation imaging apparatus) 100 includes an X-ray generation unit (radiation generation unit) 110, an imaging unit 120, and a control unit 130.

  The X-ray generation unit 110 generates and irradiates the subject 200 with X-rays (radiation) 111 based on the control of the control unit 130. Then, the X-ray (radiation) 112 transmitted through the subject 200 is input to the imaging unit 120 (specifically, the X-ray detector 1201). That is, in the X-ray imaging apparatus 100, the X-ray generation unit 110 and the imaging unit 120 incorporating the X-ray detector 1201 are arranged facing each other on opposite sides of the subject 200 placed in the center.

  The imaging unit 120 includes an X-ray detector 1201, a flexible cable 1202, a signal processing board 1203, an electrical component 1204, a heat conduction sheet 1205, a heat conduction member 1206, a heat dissipation frame 1207, a detector frame 1208, and an X-ray transmission part cover 1209. Have. Furthermore, the photographing unit 120 includes an exterior cover 1210, vent holes 1211 and 1212, a fan motor 1213, a heat insulating member 1220, and fan motors 1230-1 and 1230-2.

  The X-ray detector (radiation detector) 1201 is irradiated with the X-ray 112 irradiated from the X-ray generator 110 and transmitted through the subject 200 in the direction of the arrow, and the X-ray detector 1201 receives the incident X-ray. Convert to electrical signal (image signal). The X-ray detector 1201 inputs this image signal to the signal processing board 1203 via the flexible cable 1202. A plurality of electrical components 1204 are mounted on the signal processing board 1203, and these electrical components 1204 perform various processes on the image signal from the X-ray detector 1201, and the X-ray detector 1201. It performs various functions for driving.

  The electrical component 1204 is a main heat source in the photographing unit 120, and a heat conduction sheet 1205, a heat conduction member 1206, and a heat radiation frame 1207 are provided as heat radiation means for avoiding concentration of generated heat. And constitutes a heat transfer path.

  The heat conductive sheet 1205 is formed of, for example, an elastic sheet made of silicone rubber, and transfers heat of the electric component 1204 to the heat conductive member 1206. The heat conducting member 1206 is made of a material having high heat conductivity such as copper or aluminum, and efficiently transfers heat to the heat radiating frame 1207. When the amount of heat generated is large, a special heat conduction tool such as a heat pipe or a graphite material may be used as the heat conduction member 1206. The heat dissipating frame 1207 is a member for releasing the heat conducted by the heat conducting member 1206 and the heat transmitted by air convection and radiation to the outside while widely diffusing, and the frame of the housing structure. A part is also used.

  In addition, the heat dissipating frame 1207 in the present embodiment is preferably made of a metal typified by aluminum having a high thermal conductivity because of demands for both strength and thermal diffusivity. Furthermore, in order to efficiently transfer heat by thermal radiation, a process (such as anodizing or painting) for increasing the thermal emissivity of the member surface may be added to the heat dissipating frame 1207. In addition, in order to efficiently exchange heat with air, a device for partially increasing the surface area (roughening the surface, providing a large number of fins, etc.) is added to the heat dissipating frame 1207. There is also.

  The detector frame 1208 holds the X-ray detector 1201, the signal processing board 1203, and the like via a member (not shown) while containing the X-ray detector 1201 and the signal processing board 1203. The detector frame 1208 is made of, for example, a metal having electrical conductivity such as iron, stainless steel, and aluminum. The detector frame 1208 protects the X-ray detector 1201 and the electrical component 1204 included from external electrical noise, It also has a role to prevent release.

  The X-ray transmission unit cover 1209 protects the X-ray detector 1201 while transmitting X-rays so as not to deteriorate. For the X-ray transmission portion cover 1209, a carbon plate or a thin aluminum plate, which is a material having a high X-ray transmittance, is used. Here, the heat dissipating frame 1207, the detector frame 1208, and the X-ray transmission portion cover 1209 are combined to form a housing structure (first housing structure). The X-ray detector 1201, the signal processing board 1203, and the electrical components The space including 1204 is stored in a substantially sealed manner. Therefore, external light does not reach the photosensitive portion of the X-ray detector 1201, and it is possible to prevent moisture and dust from entering the vicinity of the X-ray detector 1201 and the signal processing board 1203. Further, the shielding effect against electrical noise intrusion and electromagnetic wave emission is enhanced.

  The exterior cover 1210 is outside the casing (first casing) that includes the detector frame 1208, and encloses the casing, and forms an exterior of the imaging unit 120 (second casing). Body). The exterior cover 1210 supports the detector frame 1208 by connection by a not-shown part, and is supported from the outside by a mechanism not shown. The exterior cover 1210 is provided with vent holes 1211 and 1212, and the vent motor 1213 is provided with a fan motor 1213 at a close position. The fan motor 1213 blows air so as to exhaust the air in the photographing unit 120 from the vent hole 1211, and constitutes a cooling means for lowering the temperature inside the photographing unit 120 (particularly, inside the housing). The vent 1212 is for taking in air outside the photographing unit 120 into the inside.

  The heat inside the casing (first casing) is transmitted to the air coming in contact from the outer surface of the casing while being diffused in the portion of the heat dissipating frame 1207. The air flows in the direction B indicated by the arrow by the fan motor 1213, passes through the vent 1211, and is discharged out of the photographing unit 120.

  The heat insulating member 1220 is a member having a heat insulating effect for making it difficult for the heat of the electric component 1204 mounted on the signal processing board 1203 to be transmitted to the X-ray detector 1201, and is a member having low thermal conductivity. For example, the heat insulating member 1220 is configured by a porous resin member, a bag-like member enclosing a fiber, a box structure having a sealed air layer, or the like. For example, if the inside of the sealed space of the box structure can be brought close to a vacuum, heat transfer by convection is suppressed, so that the heat insulating effect by the heat insulating member 1220 is further increased. In addition, even when complete sealing is difficult, the heat insulating effect by the heat insulating member 1220 can be obtained as long as the space has a small number of openings so that convection hardly occurs.

  For example, even when the surface material of the box structure is made of a metal material such as stainless steel having a low thermal emissivity, heat transfer due to radiation can be suppressed, and the heat insulating effect by the heat insulating member 1220 is enhanced. As described above, by providing the heat insulating member 1220 between the X-ray detector 1201 and the signal processing board 1203, the temperature and the temperature of the X-ray detector 1201 are affected so as to affect the characteristics and durability even during continuous imaging. Can be prevented. In addition, the influence of the heat generation distribution on the signal processing board 1203 on the temperature distribution in the panel surface of the X-ray detector 1201 is reduced, and deterioration of the quality of the output image can be prevented.

  The fan motor 1230 is provided inside the detector frame 1208, that is, inside the casing (first casing), and has a role of agitating the air inside the casing to reduce temperature variation inside the casing. Air stirring means. In the example illustrated in FIG. 1, an example in which two fan motors 1230-1 and 1230-2 are configured as the fan motor 1230 is illustrated. In other words, in the present embodiment, since the fan motor 1230 is provided inside the photographing unit 120 where there is a considerable demand for downsizing, the fan motor 1230 needs to have a small diameter and a small amount of air flow. The fan motor is provided.

  In this way, by providing the fan motor 1230 that stirs the air inside the housing, convection heat dissipation is promoted, contributing to cooling of the highly heat-generating electrical component 1204, and reducing the risk of abnormal operation and deterioration. it can. In addition, the influence of the heat generation distribution on the signal processing board 1203 on the temperature distribution in the panel surface of the X-ray detector 1201 is also reduced, and quality deterioration of the output image can be prevented.

  However, in the case of the X-ray imaging apparatus 100 that continuously performs high-speed moving image capturing, the amount of heat generated by the electrical component 1204 may increase as heat dissipation by stirring the air inside the housing by the fan motor 1230 becomes insufficient. A device for cooling from the frame 1207 side is also required.

At this time, as a device for improving the heat dissipation that can be applied to the heat dissipating frame 1207, there is the following method as described above.
"Made of metal, such as aluminum with high thermal conductivity", "Adding a treatment that increases the thermal emissivity of the surface of the member (such as anodizing or coating)", "Ingenuity to partially increase the surface area ( It is conceivable to roughen the surface or provide a large number of fins).

  In addition, forced ventilation and air cooling by the fan motor 1213 is effective. In addition to this, for example, by using a cooling means such as a heat sink, a Peltier element, or a liquid cooling unit made of copper or aluminum, the heat radiation frame 1207 is deprived of heat. Cooling is also effective. When using cooling means such as an air cooling fan motor, Peltier element, liquid cooling unit, etc., there are many inconveniences because it requires electric power, and costs, noise, and risk of failure increase. Even if a cooling means using conduction or heat radiation is adopted, there is a great merit.

  For example, when using heat conduction, a member having high heat conductivity is provided as a cooling means so as to be connected to both the heat dissipation frame 1207 and the exterior cover 1210. Examples of the member having high thermal conductivity include a structure made of copper or aluminum, a heat pipe, a graphite sheet, and the like, and heat exchange between the heat dissipation frame 1207 and the exterior cover 1210 is promoted by this member. Therefore, it is effective as a cooling means.

  Further, for example, in the case of using thermal radiation, a casing configured to include a heat dissipating frame 1207, a detector frame 1208, and an X-ray transmitting portion cover 1209, or an exterior configured to include an exterior cover 1210. Devise to increase the thermal emissivity of the wall surface of the member. Specifically, alumite treatment for an aluminum material, painting with a paint having a high thermal emissivity, application of a surface of a thermal radiation sheet, use of a material coated with a thermal radiation film, etc. are effective as cooling means.

  In this way, by configuring the photographing unit 120, the cooling effect of the electric component 1204 that generates high heat can be improved even when performing moving image photographing that continues for a long time. Furthermore, the characteristic variation due to the temperature unevenness in the panel surface of the X-ray detector 1201 can be suppressed, and the stable performance of the X-ray detector 1201 can be maintained.

The control unit 130 controls the overall operation of the X-ray imaging apparatus 100.
Here, the control unit 130 is formed by a general computer, for example, and has a hardware configuration such as a CPU, RAM, ROM, external memory, input device, display unit, communication interface, and the like. . At this time, the CPU controls the entire X-ray imaging apparatus 100 using, for example, a program or data stored in the ROM or the external memory. The RAM includes an area for temporarily storing programs and data loaded from, for example, a ROM or an external memory, and also includes a work area required for the CPU to perform various processes. The ROM generally stores, for example, a computer BIOS and setting data. Further, the external memory stores, for example, an operating system (OS), a program executed by the CPU, and information necessary for processing of the control unit 130. The input device is operated, for example, when an operator gives various instructions to the X-ray imaging apparatus 100, and inputs the instructions to the CPU or the like. Moreover, a display part displays various information and an image based on control of CPU, for example. The communication interface controls transmission / reception of various information and data performed between the control unit 130 and the external device.

  FIG. 2 is a schematic diagram illustrating an example of a control relationship of the control unit 130 with respect to the imaging unit 120 in the X-ray imaging apparatus (radiation imaging apparatus) according to the first embodiment of the present invention. Here, in FIG. 2, the same code | symbol is attached | subjected about the structure similar to the structure shown in FIG.

  As shown in FIG. 2, the fan motor 1213 and the fan motor 1230 are connected to the control unit 130 in a controllable manner, and the control unit 130 is operated and stopped by power control for the fan motor 1213 and the fan motor 1230. Switching control is performed. For example, the control unit 130 performs control to stop any or all of the fan motor 1213 and the fan motor 1230 in a situation where the photographing frequency is low, for example, a situation where continuous moving image photographing is not performed. By doing so, energy consumption can be suppressed in a situation where there is little adverse effect of heat generation.

  The control unit 130 is configured to be able to control the operations of the signal processing board 1203 and the X-ray detector 1201 via the signal processing board 1203 connected to the X-ray detector 1201. For example, the control unit 130 is configured to acquire an image signal detected by the X-ray detector 1201 as image data via the signal processing board 1203.

  FIG. 3 is a characteristic diagram illustrating an example of a temperature change inside the photographing unit 120 illustrated in FIGS. 1 and 2. Specifically, FIG. 3 shows two locations of the X-ray detector 1201 and the air in the vicinity of the signal processing board 1203 when continuous imaging is performed permanently with the fan motor 1230 stopped under the control of the control unit 130. The temperature change is shown.

  Here, the environmental temperature is constant, the vertical axis is the temperature change ΔT, and the horizontal axis is the elapsed time t. In addition, as shown in FIG. 3, the X-ray detector 1201 has an output characteristic that deteriorates when the semiconductor element or phosphor used in the X-ray detector 1201 becomes high temperature, and also affects durability. An allowable temperature rise value is set. Since the allowable temperature rise value of the X-ray detector 1201 is lower than that of general electric parts, consideration must be given to the temperature rise.

  In the case of the example shown in FIG. 3, the rise in the temperature of the air near the signal processing board 1203 rises quickly due to heat generation of the electric component 1204, and the temperature rise of the X-ray detector 1201 is slow compared to that, and rises slowly over time. . This is because the heat generation amount of the signal processing board 1203 is much larger than that of the X-ray detector 1201, and the heat transfer path from the electric component 1204 of the signal processing board 1203 to the X-ray detector 1201 is long. This is because the thermal resistance is large. Here, paying attention to the temperature change of the X-ray detector 1201 shown in FIG. 3, there is a difference after continuous operation over a sufficiently long time from the start of driving. There may be a temperature difference at which the characteristic change of the vessel 1201 can sufficiently occur. Further, the temperature of the air in the vicinity of the signal processing board 1203 is suppressed to a level at which there is no problem by devising various types of heat dissipation for the electric component 1204 of the heat generation source.

  FIG. 4 is a characteristic diagram illustrating an example of a temperature change inside the photographing unit 120 illustrated in FIGS. 1 and 2. Specifically, FIG. 4 shows the air in the vicinity of the X-ray detector 1201 and the signal processing board 1203 when the continuous imaging is performed in a state where the fan motor 1230 is operated permanently under the control of the control unit 130. The temperature change of two places is shown. Here, the environmental temperature is constant, the vertical axis is the temperature change ΔT, and the horizontal axis is the elapsed time t.

  In the example shown in FIG. 4, the heat of the air in the vicinity of the signal processing board 1203 is diffused and the temperature rise is moderate as compared with the example shown in FIG. 3, and the air is sent by stirring the air by the fan motor 1230. Since the warm air transmits heat, the temperature of the X-ray detector 1201 rises early. Further, since the air is agitated by the fan motor 1230 even after a sufficient time has elapsed, the temperature of the X-ray detector 1201 rises more than the case shown in FIG. It becomes an obstacle to satisfy the temperature rise value. If this happens, another means must be added to promote heat dissipation, which may increase costs and cause other problems.

  Therefore, the control unit 130 of the X-ray imaging apparatus 100 according to the present embodiment performs control in the flowchart shown in FIG.

  FIG. 5 is a flowchart illustrating an example of a processing procedure in the control method of the X-ray imaging apparatus (radiation imaging apparatus) according to the first embodiment of the present invention. In the processing shown in FIG. 5, it is assumed that the fan motor 1213 has been operating from the beginning.

  First, for example, when an operator inputs an instruction to start continuous imaging from the input device, in step S101, the control unit 130 controls the X-ray generation unit 110 and the imaging unit 120 to start continuous imaging start processing. I do.

  When the continuous shooting is started, subsequently, in step S102, the control unit 130 starts time measurement with a built-in clock at the same time, and updates the elapsed time t as needed with the elapsed time from the start of continuous shooting as t. Perform the process.

  Subsequently, in step S103, the control unit 130 determines whether or not the current elapsed time t exceeds a preset predetermined time tA. Here, the predetermined time tA set in advance is, for example, a temperature increase inside the imaging unit 120 (particularly an allowable temperature increase of the X-ray detector 1201) depending on the configuration of the X-ray imaging apparatus and the environment in which it is used. It is a value determined in consideration. Thus, in the present embodiment, a predetermined time tA is obtained in advance from the results of experiments and simulations, including providing a table according to the environment, and this is stored in advance in the external memory of the control unit 130. Keep it.

  As a result of the determination in step S103, if the current elapsed time t exceeds a preset predetermined time tA, the process proceeds to step S104.

  In step S104, the control unit 130 performs stop control to stop the fan motor 1230.

  On the other hand, as a result of the determination in step S103, if the current elapsed time t does not exceed the preset predetermined time tA, the process proceeds to step S105.

  In step S105, the control unit 130 performs operation execution control for operating the fan motor 1230.

When the process of step S104 or S105 ends, the process proceeds to step S106.
In step S106, the control unit 130 determines whether an imaging end signal is input from the input device by the operator, for example.

  If the result of determination in step S106 is that a shooting end signal has not been input, processing returns to step S103, and processing from step S103 onward is performed again.

On the other hand, as a result of the determination in step S106, if a photographing end signal is input, the process proceeds to step S107.
In step S107, the control unit 130 controls the X-ray generation unit 110 and the imaging unit 120 to perform imaging end processing. Thereafter, the process of the flowchart shown in FIG. 5 ends.

  By performing the above-described control by the control unit 130 in the present embodiment, for example, the temperature characteristic shown in FIG. 6 is obtained.

  FIG. 6 is a characteristic diagram showing an example of a temperature change inside the imaging unit 120 of the X-ray imaging apparatus (radiation imaging apparatus) according to the first embodiment of the present invention. Specifically, FIG. 6 shows the control of the X-ray detector 1201 and the signal processing board 1203 in the case where the operation of the fan motor 1230 is controlled by the control of the control unit 130 shown in FIG. The temperature change of two places of air is shown. Here, the environmental temperature is constant, the vertical axis is the temperature change ΔT, and the horizontal axis is the elapsed time t.

  In FIG. 6, the fan motor 1230 is stopped at a predetermined time tA indicated by a vertical dotted line. Here, since the fan motor 1230 is operating during the period from the elapsed time t <predetermined time tA, the inside of the photographing unit 120 shows a temperature change similar to the characteristic diagram shown in FIG. At this time, the heat of the air in the vicinity of the signal processing board 1203 is diffused so that the temperature rises gently, and the temperature of the X-ray detector 1201 rises early.

  Thereafter, when the elapsed time t> predetermined time tA, the fan motor 1230 stops, so that the heat diffusion of the air near the signal processing board 1203 and the temperature rise of the X-ray detector 1201 due to the hot air stop, It converges to the same temperature value as the characteristic diagram shown in FIG.

  Comparing the characteristic diagram shown in FIG. 6 with the characteristic diagrams shown in FIGS. 4 and 3, the temperature change in FIG. 6 adopting the control in this embodiment is early from the start of photographing due to the internal stirring action of the fan motor 1230. At the timing, the temperature of the X-ray detector 1201 rises. When continuous imaging is performed continuously, after the X-ray detector 1201 reaches a sufficiently high temperature, the warm air heated by the signal processing board 1203 due to the stop of the fan motor 1230 is not sent. The temperature rise of the X-ray detector 1201 is suppressed. Then, the temperature of the X-ray detector 1201 is thermally saturated at a stage where it does not become as high as the situation shown in FIG. By the control in this embodiment, the time from the start of imaging until the temperature of the X-ray detector 1201 becomes nearly constant can be shortened, and the influence of the characteristic change of the X-ray detector 1201 due to the temperature change can be suppressed. It is also possible to avoid excessively raising the temperature of the X-ray detector 1201 beyond the allowable temperature rise value.

  Note that it is also possible to obtain the same effect by controlling the fan motor 1213 to stop at the time until the stop timing of the fan motor 1230 shown in FIG. It is effective for. Due to the absence of the fan motor 1213, the cooling of the electrical component 1204 is not promoted, and the degree of increase in the air temperature in the vicinity of the signal processing board 1203 becomes more rapid. Also, heat is transmitted to the X-ray detector 1201 side by the action of the internal stirring of the fan motor 1230, and the time until the temperature of the X-ray detector 1201 becomes nearly constant becomes faster. Therefore, further improvement can be achieved in terms of suppressing the influence of the characteristic change of the X-ray detector 1201 due to the temperature change. Also, when a means other than the fan motor 1213 is used as the cooling means, the X-ray detector 1201 can be used as long as it is possible to increase or decrease the action of the cooling means as in the case of the operation execution / stop control of the fan motor 1213. This is effective in speeding up the time until the temperature of the liquid becomes nearly constant.

  According to the X-ray imaging apparatus of the present embodiment, the cooling effect of the electrical component 1204 that generates a high amount of heat can be improved even when moving images are captured that last for a long time. Furthermore, the dispersion | variation in the characteristic by the temperature change on the time axis in the X-ray detector 1201 can be suppressed, and the stable performance of the X-ray detector 1201 can be maintained.

(Second Embodiment)
Next, a second embodiment of the present invention will be described.
In the second embodiment, the configuration is almost the same as that of the X-ray imaging apparatus 100 shown in FIG. 1, but the internal configuration of the imaging unit is slightly different from that of the first embodiment. In the following, the second embodiment will be described with a focus on differences from the first embodiment.

  FIG. 7 is a schematic diagram illustrating an example of a control relationship of the control unit 130 with respect to the imaging unit 220 in the X-ray imaging apparatus (radiation imaging apparatus) according to the second embodiment of the present invention. Here, in FIG. 7, the same reference numerals are given to the same components as those shown in FIG. 2 (or FIG. 1).

  2 is different from the configuration shown in FIG. 2 in that the imaging unit 220 in the second embodiment has a first temperature detection element 2210 added in the vicinity of the X-ray detector 1201 with respect to the imaging unit 120 shown in FIG. It is a point provided. The temperature information detected by the first temperature detection element 2210 is transmitted as an electrical signal to the control unit 130, and the control unit 130 is configured to be able to recognize a temperature value near the X-ray detector 1201. ing.

  And in the control part 130 of the X-ray imaging apparatus which concerns on this embodiment, it is made to perform control in the flowchart shown in FIG.

  FIG. 8 is a flowchart illustrating an example of a processing procedure in the control method of the X-ray imaging apparatus (radiation imaging apparatus) according to the second embodiment of the present invention. In the process shown in FIG. 8, it is assumed that the fan motor 1213 has been operating from the beginning.

  First, for example, when an instruction to start continuous imaging is input from the input device by the operator, in step S201, the control unit 130 controls the X-ray generation unit 110 and the imaging unit 220 to start continuous imaging. I do.

  When the continuous shooting is started, subsequently, in step S202, the control unit 130 starts monitoring the temperature by the first temperature detection element 2210 at the same time, and sets the temperature value by the first temperature detection element 2210 as T1. , Update processing is performed as needed.

  Subsequently, in step S203, the control unit 130 determines whether or not the current temperature value T1 of the first temperature detection element 2210 exceeds a predetermined temperature value TA set in advance. Here, the predetermined temperature value TA set in advance is, for example, a value determined in consideration of the temperature increase inside the imaging unit 120 (particularly the allowable temperature increase of the X-ray detector 1201). In the present embodiment, for example, a predetermined temperature value TA is set with a margin for the allowable temperature increase of the X-ray detector 1201 and stored in advance in an external memory of the control unit 130.

  As a result of the determination in step S203, when the current temperature value T1 of the first temperature detection element 2210 exceeds a predetermined temperature value TA set in advance, the process proceeds to step S204.

  In step S204, the control unit 130 performs stop control for stopping the fan motor 1230.

  On the other hand, as a result of the determination in step S203, if the current temperature value T1 of the first temperature detection element 2210 does not exceed the predetermined temperature value TA set in advance, the process proceeds to step S205.

  In step S205, the control unit 130 performs operation execution control for operating the fan motor 1230.

When the process of step S204 or S205 ends, the process proceeds to step S206.
In step S206, the control unit 130 determines whether an imaging end signal is input from the input device by the operator, for example.

  If the result of determination in step S206 is that a shooting end signal has not been input, processing returns to step S203, and processing from step S203 onward is performed again.

  On the other hand, if the result of determination in step S206 is that a shooting end signal has been input, processing proceeds to step S207.

  In step S207, the control unit 130 controls the X-ray generation unit 110 and the imaging unit 220 to perform imaging end processing. Thereafter, the process of the flowchart shown in FIG. 8 ends.

  By performing the above-described control by the control unit 130 in the present embodiment, for example, the temperature characteristics shown in FIG. 6 can be obtained as in the first embodiment. That is, the time from the start of imaging until the temperature of the X-ray detector 1201 becomes nearly constant can be shortened, and the influence of the characteristic change of the X-ray detector 1201 due to the temperature change can be suppressed. It is also possible to avoid excessively raising the temperature of the X-ray detector 1201 beyond the allowable temperature rise value.

  As described in the first embodiment, the fan motor 1213 is stopped until the stop timing of the fan motor 1230 in FIG. 6, and the operation start control is performed at substantially the same timing as the stop of the fan motor 1230. This is effective for obtaining the same effect. Further, as described in the first embodiment, the same effect as in the present embodiment can be obtained even when means other than the fan motor 1213 is used as the cooling means.

  By the way, in the first embodiment, the predetermined time tA to be set in advance needs to be determined according to the configuration of the X-ray imaging apparatus and the environment in which it is used, and a table corresponding to the environment must be provided. It was not necessary, or the results of experiments and simulations were necessary. On the other hand, in the second embodiment, since the predetermined temperature value TA is set from the allowable temperature of the X-ray detector 1201, a table, experiment, or simulation result corresponding to the environment is not necessary, and the fan motor 1230 It is possible to reduce the error in the stop timing.

  According to the X-ray imaging apparatus of the present embodiment, the cooling effect of the electrical component 1204 that generates a high amount of heat can be improved even when moving images are captured that last for a long time. Furthermore, the dispersion | variation in the characteristic by the temperature change on the time axis in the X-ray detector 1201 can be suppressed, and the stable performance of the X-ray detector 1201 can be maintained.

(Third embodiment)
Next, a third embodiment of the present invention will be described.
In the third embodiment, the configuration is almost the same as that of the X-ray imaging apparatus 100 shown in FIG. 1, but the internal configuration of the imaging unit is slightly different from the first embodiment (or the second embodiment). In the following, the third embodiment will be described with a focus on differences from the first embodiment (or the second embodiment).

  FIG. 9 is a schematic diagram illustrating an example of a control relationship of the control unit 130 with respect to the imaging unit 320 in the X-ray imaging apparatus (radiation imaging apparatus) according to the third embodiment of the present invention. Here, in FIG. 9, the same components as those shown in FIG. 2 (or FIG. 7) are denoted by the same reference numerals.

  The imaging unit 320 according to the third embodiment is different from the imaging unit 120 illustrated in FIG. 2 in that the first temperature detection element 2210 is provided in the vicinity of the X-ray detector 1201 as in the second embodiment. Yes. Furthermore, the imaging unit 320 in the third embodiment is provided with a second temperature detection element 3210 added in the vicinity of the signal processing board 1203 (that is, in the vicinity of the electric component 1204). The temperature information detected by the first temperature detection element 2210 and the second temperature detection element 3210 is transmitted to the control unit 130 as an electrical signal, and the control unit 130 includes the X-ray detector 1201 and the signal processing board 1203. It is possible to recognize a temperature value in the vicinity of.

  And in the control part 130 of the X-ray imaging apparatus which concerns on this embodiment, it is made to perform control in the flowchart shown in FIG.

  FIG. 10 is a flowchart illustrating an example of a processing procedure in the control method of the X-ray imaging apparatus (radiation imaging apparatus) according to the third embodiment of the present invention.

  First, for example, when an instruction to start continuous imaging is input from the input device by the operator, in step S301, the control unit 130 controls the X-ray generation unit 110 and the imaging unit 320 to start continuous imaging. I do.

  When the continuous shooting is started, subsequently, in step S302, the control unit 130 starts monitoring the temperature by the first temperature detection element 2210 and the second temperature detection element 3210 at the same time. Then, the control unit 130 performs a process of updating the temperature value by the first temperature detection element 2210 as T1 and the temperature value by the second temperature detection element 3210 as T2, as needed.

  Subsequently, in step S303, the control unit 130 determines whether or not the current temperature value T1 of the first temperature detection element 2210 exceeds a predetermined temperature value TA (predetermined first temperature) set in advance. Judging.

  As a result of the determination in step S303, when the current temperature value T1 of the first temperature detection element 2210 exceeds a predetermined temperature value TA set in advance, the process proceeds to step S304.

  In step S304, the control unit 130 performs stop control for stopping the fan motor 1230 and performs operation execution control for operating the fan motor 1213.

  On the other hand, as a result of the determination in step S303, if the current temperature value T1 of the first temperature detection element 2210 does not exceed the predetermined temperature value TA set in advance, the process proceeds to step S305.

  In step S305, the control unit 130 performs operation execution control for operating the fan motor 1230.

  Subsequently, in step S306, the control unit 130 determines whether or not the current temperature value T2 of the second temperature detection element 3210 exceeds a predetermined temperature value TB (predetermined second temperature) set in advance. Judging.

  As a result of the determination in step S306, if the current temperature value T2 of the second temperature detection element 2210 exceeds a predetermined temperature value TB set in advance, the process proceeds to step S307.

  In step S307, the control unit 130 performs operation execution control for operating the fan motor 1213.

  On the other hand, as a result of the determination in step S306, if the current temperature value T2 of the second temperature detection element 3210 does not exceed the predetermined temperature value TB set in advance, the process proceeds to step S308.

  In step S308, the control unit 130 performs stop control to stop the fan motor 1213.

  When the process of step S304, S307, or S308 ends, the process proceeds to step S309.

  In step S309, the control unit 130 determines whether an imaging end signal is input from the input device by the operator, for example.

  If the result of determination in step S309 is that a shooting end signal has not been input, processing returns to step S303, and processing from step S303 onward is performed again.

  On the other hand, as a result of the determination in step S309, if a photographing end signal is input, the process proceeds to step S310.

  In step S310, the control unit 130 controls the X-ray generation unit 110 and the imaging unit 320 to perform imaging end processing. Thereafter, the process of the flowchart shown in FIG. 10 ends.

  The predetermined temperature values TA and TB set in advance are values determined from allowable temperature values of the X-ray detector 1201 and the electric component 1204, respectively. These values are set with a margin for the allowable temperature (allowable temperature rise), and are stored in advance in the external memory of the control unit 130. The allowable temperature (allowable temperature rise value) of the X-ray detector 1201 in which the change in characteristics greatly affects the performance is generally set lower than the allowable temperature of the normal electrical component 1204. In addition, the heat generation amount of the signal processing board 1203 in which many electric components 1204 that perform signal processing at high speed are often mounted is larger than the heat generation amount of the X-ray detector 1201, and the temperature value T2 is the temperature value T1. Tend to be higher. From these, the predetermined temperature value TB is almost always set higher than the predetermined temperature value TA.

  FIG. 11 shows a third embodiment of the present invention, and is a schematic diagram showing an example of operating conditions of the fan motor 1213 and the fan motor 1230 for each condition of the temperature value T1 and the temperature value T2 during continuous shooting. In FIG. 11, ON indicates the operating state of the fan motor, and OFF indicates the stopped state of the fan motor.

  When T1> TA, the control unit 130 performs control to turn on the fan motor 1213 and turn off the fan motor 1230 regardless of the value of T2. In this case, the fan motor 1230 is stopped to suppress air agitation so that heat generated in the signal processing board 1203 does not flow as much as possible to the X-ray detector 1201. Then, the fan motor 1213 is operated to promote heat dissipation of the signal processing board 1203. By making this state, further temperature rise of the X-ray detector 1201 is suppressed.

  When T1> TA is not satisfied and T2> TB, the control unit 130 performs control to turn on the fan motor 1213 and turn on the fan motor 1230. In this case, the fan motor 1213 is operated to promote heat dissipation of the signal processing board 1203 in order to avoid the electrical component 1204 from being kept in a high temperature state. At the same time, the fan motor 1230 is operated to raise the temperature of the X-ray detector 1201 and approach the stable state, and the air is stirred to distribute a part of the heat of the signal processing board 1203 to the X-ray detector 1201.

  When T1> TA is not satisfied and T2> TB is not satisfied, the control unit 130 performs control to turn off the fan motor 1213 and turn on the fan motor 1230. This state corresponds to a state immediately after energization of the X-ray imaging apparatus or an initial state of continuous imaging. In this case, in order to raise the temperature of the X-ray detector 1201 and bring it close to a stable state, the fan motor 1230 is operated to stir the air, and a part of the heat of the signal processing board 1203 is distributed to the X-ray detector 1201. However, the temperature near the signal processing board 1203 is also low, and the heat distributed to the X-ray detector 1201 becomes insufficient. Therefore, the fan motor 1213 is stopped in order to suppress heat dissipation of the signal processing board 1203. By doing so, the temperature of the X-ray detector 1201 can be raised more quickly and a stable state can be realized.

  In addition, as described in the first embodiment, even when a means other than the fan motor 1213 is used as the cooling means, the same effect in the present embodiment can be obtained as long as the control of the action of the cooling means is possible. Can be obtained. Further, regarding the flowchart shown in FIG. 10, the same effect as in the present embodiment can be obtained even if control other than the flowchart shown in FIG. 10 is performed as long as the control realizes the driving situation shown in FIG. 11. .

  According to the X-ray imaging apparatus of the present embodiment, the cooling effect of the electrical component 1204 that generates a high amount of heat can be improved even when moving images are captured that last for a long time. Furthermore, the dispersion | variation in the characteristic by the temperature change on the time axis in the X-ray detector 1201 can be suppressed, and the stable performance of the X-ray detector 1201 can be maintained.

(Other embodiments of the present invention)
The functions of the control unit 130 of the X-ray imaging apparatus according to each embodiment of the present invention described above and the steps of FIGS. 5, 8 and 10 showing the control method are performed by the CPU of the computer in its external memory or the like. This can be realized by executing a stored program. This program and a computer-readable recording medium such as an external memory storing the program are included in the present invention.

  In addition, the present invention can be implemented as, for example, a system, apparatus, method, program, storage medium, or the like. Specifically, the present invention may be applied to a system including a plurality of devices. You may apply to the apparatus which consists of one apparatus.

  In the present invention, a software program (in the embodiment, a program corresponding to the flowcharts shown in FIGS. 5, 8, and 10) that realizes the functions of the above-described embodiments is directly or remotely transmitted to the system or apparatus. Includes supplies. The present invention also includes a case where the system or the computer of the apparatus is achieved by reading and executing the supplied program code.

  Accordingly, since the functions of the present invention are implemented by computer, the program code installed in the computer also implements the present invention. In other words, the present invention includes a computer program itself for realizing the functional processing of the present invention.

  In that case, as long as it has the function of a program, it may be in the form of object code, a program executed by an interpreter, script data supplied to the OS, and the like.

  Examples of the recording medium for supplying the program include a flexible disk, hard disk, optical disk, magneto-optical disk, MO, CD-ROM, CD-R, and CD-RW. In addition, there are magnetic tape, nonvolatile memory card, ROM, DVD (DVD-ROM, DVD-R), and the like.

  As another program supply method, a browser on a client computer is used to connect to an Internet home page. The computer program itself of the present invention or a compressed file including an automatic installation function can be downloaded from the homepage by downloading it to a recording medium such as a hard disk.

  It can also be realized by dividing the program code constituting the program of the present invention into a plurality of files and downloading each file from a different homepage. That is, a WWW server that allows a plurality of users to download a program file for realizing the functional processing of the present invention on a computer is also included in the present invention.

  In addition, the program of the present invention is encrypted, stored in a storage medium such as a CD-ROM, distributed to users, and key information for decryption is downloaded from a homepage via the Internet to users who have cleared predetermined conditions. Let It is also possible to execute the encrypted program by using the downloaded key information and install the program on a computer.

  Further, the functions of the respective embodiments described above are realized by the computer executing the read program. In addition, based on the instructions of the program, the OS running on the computer performs part or all of the actual processing, and the functions of the above-described embodiments can also be realized by the processing.

  Further, the program read from the recording medium is written in a memory provided in a function expansion board inserted into the computer or a function expansion unit connected to the computer. Thereafter, based on the instructions of the program, the CPU provided in the function expansion board or function expansion unit performs part or all of the actual processing, and the functions of the above-described embodiments are also realized by the processing.

  Note that each of the above-described embodiments is merely a specific example for carrying out the present invention, and the technical scope of the present invention should not be construed as being limited thereto. . That is, the present invention can be implemented in various forms without departing from the technical idea or the main features thereof.

DESCRIPTION OF SYMBOLS 100: X-ray imaging apparatus (radiography apparatus), 110: X-ray generation part (radiation generation part), 120: Imaging part, 1201: X-ray detector, 1202: Flexible cable, 1203: Signal processing board, 1204: Electricity Components: 1205: Thermal conductive sheet, 1206: Thermal conductive member, 1207: Heat dissipation frame, 1208: Detector frame, 1209: X-ray transmission part cover, 1210: Exterior cover, 1211, 1212: Vent, 1213: Fan motor, 1220: Thermal insulation member, 1230: Fan motor, 130: Control unit

Claims (16)

A radiation imaging apparatus configured to include a radiation detector that detects radiation transmitted through a subject as an image signal, and an electrical component that processes the image signal,
A housing for storing the radiation detector and the electrical component therein;
Blower means provided in the housing and for sending air on the electrical component side to the radiation detector side;
Control means for terminating the operation of the blowing means when the temperature in the vicinity of the radiation detector exceeds a predetermined temperature when continuously photographing the subject;
A radiation imaging apparatus comprising: A cooling means provided on the outside of the housing for cooling the housing;
2. The control unit according to claim 1, wherein when the temperature of the vicinity of the radiation detector exceeds a predetermined temperature during continuous imaging of the subject, the control unit starts operation of the cooling unit. Radiography equipment.   The control means ends the operation of the air blowing means and starts the operation of the cooling means when the temperature in the vicinity of the radiation detector exceeds the predetermined temperature while continuously photographing the subject. The radiographic apparatus according to claim 2, wherein: A judgment means for judging whether or not a temperature in the vicinity of the radiation detector exceeds the predetermined temperature;
The radiation imaging apparatus according to claim 2, wherein the control unit controls the operation of the blowing unit and the operation of the cooling unit according to a determination result of the determination unit. First temperature detecting means for detecting a temperature in the vicinity of the radiation detector;
Second temperature detecting means for detecting a temperature in the vicinity of the electrical component;
Further comprising
The control means ends the operation of the air blowing means and starts the operation of the cooling means when the temperature detected by the first temperature detection means exceeds the first temperature which is the predetermined temperature, When the temperature detected by the first temperature detection means is equal to or lower than the first temperature and the temperature detected by the second temperature detection means exceeds the second temperature, the operation of the blower means is started. The radiation imaging apparatus according to claim 2, wherein the operation of the cooling unit is started.   The radiographic apparatus according to claim 2, wherein the control unit starts the operation of the cooling unit when the operation of the air blowing unit is finished. An exterior member formed to cover the outside of the housing;
A heat dissipating means that is part of the housing and radiates the air on the electrical component side to the outside of the housing;
Further comprising
The said cooling means sends the air heated by the said heat radiating means to the outer side of the said exterior member through the vent provided in the said exterior member, The said any one of Claims 2 thru | or 6 characterized by the above-mentioned. Radiography equipment. The radiation imaging apparatus according to claim 7 , wherein the cooling unit is a fan motor provided in the vent. The radiation imaging apparatus according to any one of claims 1 to 8, characterized in that the continuous shooting a moving picture. The blowing means, the radiation imaging apparatus according to any one of claims 1 to 9, characterized in that the fan motor provided in the vicinity of the electrical component. A radiation detector that detects radiation that has passed through the subject as an image signal and an electrical component that processes the image signal are provided in a housing, and air on the electrical component side is sent to the radiation detector side. A method for controlling a radiographic apparatus including a blowing means,
A method of controlling a radiographic apparatus, comprising: a step of ending the operation of the blowing unit when a temperature in the vicinity of the radiation detector exceeds a predetermined temperature during continuous imaging of the subject. When the subject is continuously photographed, if the temperature in the vicinity of the radiation detector exceeds a predetermined temperature, operation of a cooling unit provided on the outside of the housing for cooling the housing is started. The method for controlling a radiation imaging apparatus according to claim 11 , further comprising a step of: When continuously photographing the subject, if the temperature in the vicinity of the radiation detector exceeds the predetermined temperature, the operation of the blowing unit is terminated and the operation of the cooling unit is started. The method of controlling a radiation imaging apparatus according to claim 12 . The radiation imaging apparatus further includes first temperature detecting means for detecting a temperature in the vicinity of the radiation detector, and second temperature detecting means for detecting a temperature in the vicinity of the electrical component. ,
When the temperature detected by the first temperature detection means exceeds the first temperature which is the predetermined temperature, the operation of the blower means is terminated and the operation of the cooling means is started, and the first temperature detection When the temperature detected by the means is equal to or lower than the first temperature and the temperature detected by the second temperature detection means exceeds the second temperature, the operation of the blowing means is started and the cooling means 14. The method of controlling a radiation imaging apparatus according to claim 12 or 13 , wherein the operation is started. The method of the radiation imaging apparatus according to any one of claims 12 to 14, characterized in that to start the operation of said cooling means when it is completed to operation of said blowing means. The program for making a computer perform the process of the control method of the radiography apparatus of any one of Claims 11 thru | or 15 .

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