JP2004358211A - Surgical x-ray tv apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a surgical X-ray TV apparatus which is operable for a long period of time by suppressing the temperature elevation of an X-ray tube device by improving efficiency in heat conduction. <P>SOLUTION: Both ends of a heat radiating pipe 39 which is added to a C arm 9, are communicated and connected into a housing 19, and an insulating oil within the housing 19 is circulated in the heat radiating pipe 39 by a circulating pump 41. Therefore, heat of the insulating oil to which heat from a cooling fin 33 of a fixed anode type X-ray tube 21 is transmitted, can be efficiently transmitted to the C arm 9 wherein heat capacity is greater than that of the X-ray tube device 13. As a result, heat conduction from the housing 19 to the C arm 9 can be made highly efficient to suppress the temperature elevation of the X-ray tube device 13, thereby operating the surgical X-ray TV apparatus for a long period of time is realized. <P>COPYRIGHT: (C)2005,JPO&NCIPI

Description

  The present invention relates to a surgical X-ray TV apparatus for supporting an imaging means such as an image intensifier or an X-ray flat panel detector and an X-ray tube apparatus so as to perform fluoroscopic imaging at the time of surgery. The present invention relates to a heat radiation technique for an X-ray tube device having a fixed anode type X-ray tube built in a housing.

  X-ray tube apparatuses are roughly classified into a rotary anode type and a fixed anode type. The rotating anode type is widely used mainly in an apparatus that involves X-ray imaging because it can withstand a large instantaneous load. On the other hand, the fixed anode type has a relatively small instantaneous load, but has been used for a relatively long time. This fixed anode type is used, for example, in a surgical X-ray TV apparatus for performing fluoroscopic imaging during an operation.

  2. Description of the Related Art An X-ray tube apparatus provided with a fixed anode type X-ray tube, which is called a monotank type which is compact for surgical use, has, for example, the following configuration (for example, see Patent Document 1).

  In this apparatus, a fixed anode type X-ray tube having a cathode (filament) and a fixed anode (target) disposed opposite to each other in a glass bulb in a high vacuum state, a high voltage transformer for applying a high voltage, and , A filament transformer for feeding the filament and the like are accommodated in one housing filled with insulating oil.

  Thermions generated at the cathode (filament) are accelerated by the high voltage and collide with the fixed anode to generate X-rays. At this time, 99% or more of the energy supplied to the fixed anode type X-ray tube is converted to heat. In order to release this heat to the outside, a cooling fin is attached to one end of the fixed anode led out of the glass bulb. Heat generated at the fixed anode is transmitted to the insulating oil via the cooling fins, and further transmitted to the housing by convection of the insulating oil. The heat transmitted into the housing is released from the housing to the outside air or transmitted to an arm that connects and supports the housing.

  As described above, natural heat radiation is performed without using a cooling fan or the like because a surgical X-ray TV device is used during surgery. That is, when the cooling is performed by the cooling fan, dust is wound up, which is inappropriate in a surgical operating room requiring a clean environment.

An air-cooling fin to increase the surface area may be attached to the outside of the housing without using a fan.However, in the case of a surgical use, maintenance such as wiping blood or the like after surgery is complicated. It is not realistic because it becomes.
JP-A-5-242992

However, the conventional example having such a configuration has the following problem.
That is, in the conventional apparatus, the X-ray intensity may be increased (increase the load on the X-ray tube apparatus) in order to improve the image quality of the fluoroscopic image, depending on the size of the fluoroscopic target region and the like. The conventional X-ray tube apparatus has a problem in that heat generated under a large load cannot be quickly released due to convection of insulating oil and natural heat radiation through the housing and the arm.

  By the way, in the conventional X-ray tube device, when the temperature of the insulating oil rises too much, the insulating oil expands and the internal pressure of the housing becomes excessively high, which is dangerous.

  Therefore, a thermal switch is provided in the housing, and a safety mechanism is provided for stopping the operation of the X-ray tube device when the temperature of the insulating oil reaches a predetermined value (for example, 60 or 70 ° C.). Has been. For this reason, if the temperature of the insulating oil in the housing rises sharply, the above-mentioned safety mechanism is activated and the X-ray is stopped, so that the operation cannot be performed for a long period of time, which hinders diagnosis and surgery. Sometimes.

  The present invention has been made in view of such circumstances, and by increasing the efficiency of heat conduction from a housing to an arm, it is possible to suppress an increase in the temperature of an X-ray tube device and operate for a long time. It is an object of the present invention to provide a surgical X-ray TV device.

The present invention has the following configuration to achieve such an object.
That is, according to the first aspect of the present invention, the first aspect of the present invention provides an X-ray tube apparatus having a fixed anode type X-ray tube in a housing filled with insulating oil, and an imaging means opposed to each other. A surgical X-ray TV device having an arm that is connected to the housing, the both ends of which are connected to each other in the housing, the insulating oil in the housing can be circulated, and the heat-radiating pipe attached to the arm; And a circulating pump for circulating the insulating oil inside the radiating pipe.

  [Operation and Effect] Both ends of the heat radiating pipe are connected to each other in the housing, and the circulating pump circulates the insulating oil in the housing through the heat radiating pipe. Since the heat radiating pipe is attached to the arm, the heat of the insulating oil to which the heat from the fixed anode type X-ray tube is transmitted can be efficiently transferred to the arm having a larger heat capacity than the X-ray tube device. Can be transmitted. Therefore, the efficiency of heat conduction from the housing to the arm can be increased, so that the temperature rise of the X-ray tube device can be suppressed, and the operation can be performed for a long time.

  According to a second aspect of the present invention, there is provided an X-ray tube apparatus having a fixed anode type X-ray tube in a housing filled with insulating oil, and a surgical X-ray apparatus having an arm for supporting an imaging means in opposition. In the linear TV device, a Peltier element mounted with the heat absorbing surface facing the housing side, a radiator mounted on the heat radiating surface of the Peltier element, mounted on the radiator, and capable of circulating a refrigerant and attached to the arm. And a circulation pump for circulating a refrigerant in the heat dissipation pipe.

  [Operation and Effect] The heat of the insulating oil in the housing is absorbed by the heat absorbing surface of the Peltier element and transmitted to the radiator attached to the heat releasing surface. The heat transmitted to the radiator is transmitted to the refrigerant via the heat-dissipating pipe, and finally transmitted to the arm having a large heat capacity by the circulation pump. Therefore, the efficiency of heat conduction from the housing to the arm can be increased, so that the temperature rise of the X-ray tube device can be suppressed, and the operation can be performed for a long time.

  Preferably, the heat radiating pipe is attached to the arm with an aluminum foil tape.

  (Operation / Effect) The X-ray tube device may be detached from the arm during maintenance such as replacement of the X-ray tube. In this case, the heat radiation pipe can be easily removed from the arm by peeling off the aluminum foil tape, and maintenance work can be easily performed.

  In addition, as the aluminum foil tape, for example, a material used for attaching a heat exchange pipe for heat exchange of a refrigerator to a refrigerator body, which has a high thermal conductivity and a sufficient adhesive force, can be used. The aluminum foil tape referred to here is one in which an adhesive material is adhered to one surface of a tape material made of aluminum.

  Further, it is preferable that a concave portion corresponding to the outer shape of the heat radiating pipe is formed in the arm (claim 4).

  (Operation / Effect) Since the heat dissipation pipe is in close contact with the housing by the concave portion and the contact area increases, heat can be efficiently transmitted.

  Instead of providing a concave portion on the arm, the cross-sectional shape of the heat-radiating pipe may be made flat or rectangular so as to increase the degree of adhesion to the arm.

  According to this invention, both ends of the heat radiating pipe attached to the arm are connected to the inside of the housing, and the insulating oil in the housing is circulated to the heat radiating pipe by the circulation pump. The heat of the insulating oil to which the heat has been transmitted can be efficiently transmitted to the arm having a larger heat capacity than the X-ray tube device. Therefore, the efficiency of heat conduction from the housing to the arm can be increased, so that the temperature rise of the X-ray tube device can be suppressed, and the operation can be performed for a long time.

An embodiment of the present invention will be described below with reference to the drawings.
1 to 3 relate to an embodiment of the present invention. FIG. 1 is a perspective view showing a schematic configuration of a surgical X-ray TV apparatus according to the first embodiment, and FIG. 2 is a longitudinal sectional view of the X-ray tube apparatus. FIG. 3 is a view showing a manner in which the heat radiating pipe is attached.

  The surgical X-ray TV apparatus 1 according to the first embodiment includes a bed 3 on which a subject is placed and a base unit 5. The bed 3 is fixed or semi-fixed on the floor. The base unit 5 is arranged on the side of the bed 3, has a built-in power supply device, a control unit, and the like, and is configured to be movable on the floor.

  The base unit 5 has a support 7 having an axis of rotation about a vertical axis at the top. A base end of a support arm 11 that holds the C-arm 9 at the distal end is attached to an upper portion of the support 7. The support arm 11 holds the C-arm 9 at its distal end so as to be rotatable in a direction indicated by a two-dot chain line in the figure.

  An X-ray tube device 13 is attached to one end of the C-arm 9, and an imaging unit 15 is attached to a facing position. The imaging unit 15 has a function of visualizing transmitted X-rays such as an image intensifier and an X-ray flat panel detector.

  The upper side of the X-ray tube device 13 and the side surface on the side of the C-arm 9 and about half the length of the arc of the C-arm 9 are covered with a resin cover 17 in consideration of maintainability and the like. For the sake of simplicity, only a part is shown by a two-dot chain line).

Please refer to FIG.
The X-ray tube apparatus 13 is a so-called monotank type which is compact for surgical use. The housing 19 is filled with insulating oil, and includes a fixed anode X-ray tube 21, a high-pressure transformer 23, and a filament transformer 25.

  The fixed anode type X-ray tube 21 includes a glass bulb 27 having a high vacuum inside, a cathode (filament) 29 to which a high voltage is applied from a filament transformer 25, and a fixed anode (filament) connected to a high voltage transformer 23. Target) 31. The fixed anode 31 includes cooling fins 33 that are led out of the glass bulb 27 from its rear end.

  When the high voltage transformer 23 and the filament transformer 25 operate according to the tube voltage and tube current desired by the photographer, the thermoelectrons generated at the cathode 29 are accelerated by the high voltage and fixed as shown by the dotted line in the figure. An X-ray is generated in the direction shown by the two-dot chain line in the figure by colliding with the tip inclined surface of the anode 31. The generated X-rays are emitted to the imaging unit 15 side via a radiation unit 20 provided upright on the upper surface of the housing 19. At this time, 99% or more of the energy supplied to the X-ray tube device 13 changes to heat. This heat is released from the cooling fins 33 and transmitted to the housing 19 by the convection of the insulating oil, or to the C-arm 9 connected to the housing 19, and is released to the surroundings.

  A suction hole 35 is formed on one side of the housing 19 on the side of the C-arm 9, and a return hole 37 is formed on the back side of the housing 19 (although it is not visible due to the relationship shown in the drawing), away from the suction hole 35. Have been. Both ends of the heat radiating pipe 39 are connected to the suction port 35 and the return hole 37. The heat dissipating pipe 39 is preferably made of a material having a high thermal conductivity, for example, aluminum.

  A circulation pump 41 is attached near the suction port 35. The circulation pump 41 takes in the insulating oil in the housing 19 from the suction hole 35 and circulates the heat through the heat radiating pipe 39, and circulates the insulating oil passing through the heat radiating pipe 39 into the housing 19 through the return hole 37. Function.

  The heat radiating pipe 39 passes through the circulation pump 41 from the suction hole 35 and is attached to one side surface (the front side surface in FIG. 1) of the C arm 9, and makes a U-turn at a position about half the arc length of the C arm 9. Is folded back. Further, it is attached so as to return to the same surface of the C-arm 9, passes through the upper surface of the C-arm 9 in front of the housing 19, and is connected to the return hole 37 of the housing 19 via the opposite side surface.

  The reason why the heat radiating pipe 39 is folded back at a position about half the length of the arc of the C-arm 9 is that the heat is transmitted to the C-arm 9 with respect to the imaging unit 15 at a position facing the X-ray tube device 13. This is to prevent adverse effects of heat.

  As shown in FIG. 3, a concave portion 43 is formed on the side surface of the C-arm 9 according to the outer shape of the heat radiating pipe 39. The heat radiating pipe 39 is attached so as to fit into the concave portion 43, and is adhered and fixed to the C arm 9 with an aluminum foil tape 45 from above.

  Since the resin cover 17 is attached to the C-arm 9 as described above, the heat-dissipating pipe 39 and the aluminum foil tape 45 are protected from being seen from the outside and from being stained. (See FIGS. 1 and 2).

  As described above, both ends of the heat radiating pipe 39 attached to the C-arm 9 are connected to the inside of the housing 19, and the insulating oil in the housing 19 is circulated through the heat radiating pipe 39 by the circulating pump 41, whereby a fixed anode type is provided. The heat of the insulating oil to which the heat from the cooling fins 33 of the X-ray tube 21 has been transmitted can be efficiently transmitted to the C-arm 9 having a larger heat capacity than the X-ray tube device 13. Therefore, the efficiency of heat conduction from the housing 19 to the C-arm 9 can be increased, so that the temperature rise of the X-ray tube device 13 can be suppressed, and the operation can be performed for a long time.

  Further, in the apparatus of the present embodiment, the heat radiation pipe 39 is attached to the C-arm 9 with the aluminum foil tape 45. Therefore, at the time of maintenance, the cover 17 is removed and the aluminum foil tape 45 is peeled off. Can be easily removed from the C-arm 9, and the operation can be easily performed.

  In order to facilitate removal of the heat radiation pipe 39 from the housing 19, it is preferable that the heat radiation pipe 39 be attached to a connection portion between the suction port 35 and the return hole 37 and the heat radiation pipe 39 via a detachable connector (joint).

  The heat dissipating pipe 39 may be attached by attaching with the aluminum foil tape 45 as in the above-described embodiment, or may be attached in the following manner.

Please refer to FIG.
FIG. 4 is a diagram showing another mounting mode of the heat radiating pipe.

  In this example, an adhesive P is applied and fixed to the side surface of the heat radiating pipe 39 and the surface of the C arm 9. The adhesive P is preferably one having excellent heat conductivity and strength at the time of fixing, for example, solder. Since the adhesive P covers the arc-shaped outer peripheral surface of the heat radiating pipe 39 and the surface of the C-arm 9 as shown in FIG. 4, the contact area between them can be increased, and the thermal conductivity can be increased.

  Further, the heat radiating pipe 39 does not need to have a circular cross section as described above, and may have the following shape.

Here, reference is made to FIG.
FIG. 5 is a diagram showing a cross-sectional shape of the heat dissipation pipe.

  The heat-dissipating pipe 39A has an elliptical cross-section. A concave portion 43A is formed on the surface of the C-arm 9 so as to match the outer shape of the heat radiating pipe 39A. The heat dissipation pipe 39A has its long axis side along the C arm 9 surface. Therefore, the contact area increases, and heat can be more efficiently dissipated.

Next, a second embodiment of the present invention will be described with reference to FIGS.
FIG. 6 is a side view showing a main part of the surgical X-ray TV device according to the second embodiment, and FIG. 7 is a plan view thereof. In addition, about the structure similar to Example 1, the same code | symbol is attached | subjected and detailed description is abbreviate | omitted.

  On the upper side of the housing 19, two Peltier elements 51 are arranged side by side. The heat absorbing surface is directed to the housing 19 side, and a radiator 53 is attached to the heat radiating surface. The Peltier element 51 is provided at the upper part of the side surface of the housing 19 because the fixed anode type X-ray tube 21 is disposed in the vicinity of the Peltier element 51 (see FIG. 2). Therefore, it is a part requiring cooling. Further, as the Peltier element 51, for example, a general-purpose product (about 4 × 4 cm) used for cooling a CPU of a computer is preferable because it is easily available and advantageous in cost. It should be noted that a DC power source (not shown) required for operation is connected to the Peltier element.

  The radiator 53 has a size enough to cover the two Peltier elements 51 and is made of a material having a large heat capacity. A hollow portion having a “U” shape when viewed from the side is provided therein, and a heat radiating pipe 39 is inserted therein. The refrigerant can be circulated through the heat-dissipating pipe 39, and the refrigerant is circulated by a circulation pump 41 attached to the side surface of the housing 19. As in the first embodiment, a part of the heat-dissipating pipe 39 is attached to the vicinity of the center of the C-arm 9.

  With such a configuration, the heat of the insulating oil in the housing 19 is absorbed by the heat absorbing surface of the Peltier device and transmitted to the radiator 53 attached to the heat releasing surface. The heat transmitted to the radiator 53 is transmitted to the refrigerant via the heat radiating pipe 39, and finally transmitted to the C-arm 9 having a large heat capacity by the circulation pump 41. That is, the heat of the insulating oil to which the heat from the cooling fins 33 of the fixed anode X-ray tube 21 has been transmitted can be efficiently transmitted to the C-arm 9 having a larger heat capacity than the X-ray tube device 13. it can. Therefore, the efficiency of heat conduction from the housing 19 to the C-arm 9 can be increased, so that the temperature rise of the X-ray tube device 13 can be suppressed, and the operation can be performed for a long time.

  Note that the present invention is not limited to the configuration of each of the embodiments described above, and can be modified as follows.

  (1) The heat dissipating pipe 39 may be provided not only on the front side of the C arm 9 but also on the back side as shown in FIG.

  (2) The heat radiating pipe 39 extends along the C-arm 9 in a substantially arc shape until it is turned back to make a U-turn. However, it may be arranged in a small zigzag shape or along a large arc shape.

  (3) The surgical X-ray TV apparatus 1 according to each of the above embodiments employs a form in which the X-ray tube apparatus 13 and the imaging unit 15 are supported by the C-arm 9 so as to face each other. The present invention is not limited to the device supported by 9, and can be applied to, for example, the surgical X-ray TV device 1 including various arms such as a U-shaped arm.

  (4) Instead of arranging two Peltier elements 51 side by side, only one large element may be provided. Further, the Peltier element 51 may be provided not on the side surface of the housing 19 but on the upper surface thereof. Further, a heat pipe may be employed as the heat radiation pipe.

1 is a perspective view illustrating a schematic configuration of a surgical X-ray TV device according to a first embodiment. It is a longitudinal section of an X-ray tube device. It is a figure which shows the attachment aspect of a radiation pipe. It is a figure showing other attachment modes of a pipe for heat dissipation. It is a figure which shows the cross-sectional shape of a pipe for heat dissipation. FIG. 7 is a side view showing a main part of a surgical X-ray TV device according to a second embodiment. FIG. 7 is a plan view of FIG. 6.

Explanation of reference numerals

DESCRIPTION OF SYMBOLS 1 ... Surgical X-ray TV apparatus 3 ... Bed 9 ... C arm 13 ... X-ray tube apparatus 15 ... Imaging part 17 ... Cover 19 ... Housing 21 ... Fixed anode type X-ray tube 23 ... High voltage transformer 25 ... Filament transformer 27 ... Glass bulb 29… Cathode 31… Fixed anode 35… Suction hole 37… Return hole 39… Heat dissipation pipe 41… Circulation pump 43… Concave 45… Aluminum foil tape 51… Peltier element 53… Radiator

Claims (4)

  In an X-ray tube apparatus having a fixed anode type X-ray tube in a housing filled with insulating oil, and a surgical X-ray TV apparatus having an arm for supporting an imaging unit in opposition, both ends are provided in the housing. The apparatus is provided with a heat-dissipating pipe connected to the arm and connected to the arm, and a circulation pump for circulating the insulating oil in the housing to the heat-dissipating pipe. A surgical X-ray TV apparatus characterized by the above-mentioned.   In an X-ray tube apparatus having a fixed anode type X-ray tube in a housing filled with insulating oil, and a surgical X-ray TV apparatus having an arm for supporting an imaging means in opposition, a heat absorbing surface is provided on the housing side. A radiator attached to the radiator, a radiator attached to the radiator, a radiator attached to the radiator, a radiator pipe circulating a refrigerant, and attached to the arm, and a radiator pipe inside the radiator pipe. And a circulation pump for circulating the refrigerant.   3. The surgical X-ray TV apparatus according to claim 1, wherein the heat radiating pipe is attached to the arm with an aluminum foil tape. The surgical X-ray TV apparatus according to any one of claims 1 to 3, wherein a concave portion is formed in the arm according to an outer shape of the heat radiating pipe. .

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