JP2004154236A - Surgical x-ray tv device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a surgical X-ray TV device of which the motion extending for a long time is possible by suppressing a temperature rise of an X-ray tube device by making the thermal conductivity highly efficient. <P>SOLUTION: Both ends of a heat pipe 37 are attached to a housing 19 and a C-arm 9, and thus, the heat of the housing 19 can be efficiently transmitted to the C-arm 9 of which the thermal capacity is larger than the X-ray tube device, through the heat pipe 37. Therefore, the thermal conductivity from the housing 19 to the C-arm 9 can be made highly efficient, and the temperature rising of the X-ray tube device can be suppressed, and the motion extending for a long time can be performed. <P>COPYRIGHT: (C)2004,JPO

Description

[0001]
TECHNICAL FIELD OF THE INVENTION
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.
[0002]
[Prior art]
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.
[0003]
An X-ray tube apparatus provided with a fixed anode type X-ray tube, which is called a monotank type compact for surgical use, has, for example, the following configuration (Japanese Patent Application Laid-Open No. Hei 5-242992).
[0004]
A fixed anode type X-ray tube having a cathode (filament) and a fixed anode (target) opposed to each other in a glass bulb in a high vacuum state, a high voltage transformer for applying a high voltage, and a filament power supply Are housed in one housing filled with insulating oil.
[0005]
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.
[0006]
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.
[0007]
It is also conceivable to attach cooling fins to the housing without using a fan, but this is also not practical in the case of surgical use because maintenance for wiping blood or the like after surgery becomes complicated.
[0008]
[Problems to be solved by the invention]
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 that heat generated under a large load cannot be quickly released due to the convection of insulating oil and natural heat radiation through the housing and the arm.
[0009]
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.
[0010]
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.). Have 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.
[0011]
The present invention has been made in view of the above circumstances, and a surgical X-ray capable of operating for a long time by suppressing the temperature rise of the X-ray tube device by increasing the efficiency of heat conduction. It is intended to provide a TV device.
[0012]
[Means for Solving the Problems]
The present invention has the following configuration to achieve such an object.
[0013]
That is, according to the first aspect of the present invention, there is provided a surgical X-ray apparatus including a fixed anode type X-ray tube in a housing filled with insulating oil, and a surgical X-ray including an arm for supporting an imaging unit in opposition. In the linear TV device, both ends of a heat pipe are attached to the housing and the arm.
[0014]
(Action / Effect)
Attach both ends of a heat pipe having a thermal conductivity 100 times or more that of copper to the housing and the arm. Thereby, the heat of the housing to which the heat from the fixed anode type X-ray tube has been transmitted can be efficiently transmitted through the heat pipe 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.
[0015]
Further, in the surgical X-ray TV device according to claim 1, the surgical X-ray TV device according to claim 1, further comprising a connecting member having a recess along an outer shape of the heat pipe, wherein the heat pipe is It is preferable to be attached via the connecting member (claim 2).
[0016]
(Action / Effect)
Since the heat pipe generally has a circular cross section, the contact area with the housing or the arm is small. Therefore, by attaching the heat pipe via a connecting member having a concave portion along the outer shape of the heat pipe, the contact area can be increased, so that heat can be efficiently transmitted.
[0017]
Note that the space between the arc portion of the heat pipe and the connection member may be filled with a heat conductive material (for example, a solder material) without providing the concave portion.
[0018]
Further, in the surgical X-ray TV apparatus according to claim 2, it is preferable that the connection member is attached via an elastic or viscous heat radiation material (claim 3).
[0019]
(Action / Effect)
Since the housing, the arm, and the connecting member are all made of metal, even if they come into contact with each other, the degree of adhesion is low due to the intervening air layer. Therefore, by interposing a heat transfer material having a high heat conductivity, it is possible to further increase the heat conductivity while improving the adhesion.
[0020]
Examples of the heat transfer material include a heat dissipation sheet (elastic sheet) and a heat dissipation paste (viscous paste).
[0021]
BEST MODE FOR CARRYING OUT THE INVENTION
An embodiment of the present invention will be described below with reference to the drawings.
1 to 4 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 embodiment, and FIG. 2 is a longitudinal sectional view of an X-ray tube apparatus. FIG. 3 is an external perspective view of the heat transfer section, and FIG. 4 is an exploded perspective view showing a heat pipe mounting structure.
[0022]
The surgical X-ray TV apparatus 1 according to the 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.
[0023]
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.
[0024]
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.
[0025]
The upper part of the X-ray tube device 13 and a part of the tip of the C-arm 9 on the X-ray tube device 13 side are covered with a resin cover 17 in consideration of maintainability and the like.
[0026]
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-voltage transformer 23, and a transformer 25 for filament.
[0027]
The fixed anode 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 (target) connected to the high voltage transformer 23. ) 31 is provided. The fixed anode 31 includes cooling fins 33 that are led out of the glass bulb 27 from its rear end.
[0028]
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.
[0029]
Please refer to FIG.
A heat transfer section 35 is attached to the upper side surface of the housing 19 and the tip of the C-arm 9. Although not shown, a heat transfer section 35 is also attached to a side surface opposite to the housing 19 in FIG.
[0030]
The heat transfer section 35 is configured and attached as shown in FIG.
[0031]
The heat pipe 37 has a generally elongated rod shape and is generally used. In this example, three heat pipes 37 are used. At both ends of the heat pipe 37, rectangular connection members 39 are fixed by an adhesive P. As the adhesive, one having excellent heat conductivity and strength at the time of fixing is preferable. For example, solder can be used. Since the adhesive P fills the arc-shaped outer peripheral surface of the heat pipe 37 and the surface of the connection member 39, the contact area between the connection material 39 and the heat pipe 37 can be increased, and the heat conductivity can be increased.
[0032]
A screw hole 41 is formed in the connection member 39, and the connection member 39 is attached to the housing 19 and the C-arm 9 by an attachment screw 43. At this time, it is preferable that the heat transfer material 44 be sandwiched between the connection member 39 and the housing 19 and the C-arm 9.
[0033]
Examples of the heat transfer material 44 include a paper-like heat transfer sheet having elasticity and a viscous paste applied between the CPU package and a cooling unit attached to the upper surface thereof. Since the housing 19, the C-arm 9, and the connecting member 39 are all made of metal, even if they come into contact with each other, the degree of adhesion is low due to the intervening air layer. Therefore, the heat conductivity of the heat transfer portion 35 can be further increased by increasing the adhesiveness between the heat transfer material 44 and the heat transfer material 44 having a high heat conductivity.
[0034]
The connection member 39 of the heat transfer unit 35 on the side of the X-ray tube device 13 is preferably mounted on the side surface of the housing 19 at a position close to the cooling fin 33 from the viewpoint of heat radiation efficiency.
[0035]
In the surgical X-ray TV apparatus 1 configured as described above, since both ends of the heat pipe 37 having a thermal conductivity 100 times or more that of copper are attached to the housing 19 and the C-arm 9, the heat of the housing 19 is transferred to the X-ray tube. The heat can be efficiently transmitted to the C-arm 9 having a larger heat capacity than the device 13 through the heat pipe 37.
[0036]
Incidentally, if the temperature of the insulating oil is too high, the insulating oil expands and the internal pressure of the housing 19 is excessively increased, which is dangerous. Therefore, the X-ray tube device 13 has a thermal switch (not shown) provided in the housing 19. ) Detects the temperature of the insulating oil, and has a safety mechanism for stopping the operation of the X-ray tube device 13 when the temperature reaches a predetermined value (for example, 60 or 70 ° C.). For this reason, if the temperature of the insulating oil in the housing 19 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. May come.
[0037]
However, according to the apparatus of this embodiment, since the heat is efficiently transmitted from the housing 19 to the C-arm 9 by the heat pipe 37, the efficiency is increased, so that the temperature rise of the X-ray tube apparatus 13 can be suppressed. it can. Therefore, it is possible to prevent the temperature from rising to such an extent that the above-mentioned safety mechanism operates, and it is possible to operate the surgical X-ray TV apparatus 1 for a long time.
[0038]
Preferably, the connecting member 39 is configured as shown in FIG.
[0039]
That is, the concave portion 45 corresponding to the outer peripheral surface shape of the heat pipe 37 is provided on the mounting member side of the heat pipe 37 in the connecting member 39. FIG. 5 shows an example in which the outer peripheral surface of the heat pipe 37 has a circular shape. However, when the outer peripheral surface (longitudinal section) has a rectangular shape, a shape corresponding to the rectangular shape may be used.
[0040]
Further, in the above-described example, the heat pipe 37 in the shape of an elongated rod has been described as an example, but a special heat pipe 37A having a shape as shown in FIG. 6 may be employed.
[0041]
That is, this heat pipe 37A is one in which a single zigzag tube 47 is formed in a plate-shaped housing 49 and is formed from one end side to the other end side of the housing 49 (the meandering thin tube heat pipe). Also called a pipe). Screw holes 41A are provided at both ends of the housing 49. In the case of such a special type of heat pipe 37A, since the heat pipe 37A has a simple structure, it can be easily attached to the side surfaces of the housing 19 and the C-arm 9.
[0042]
The present invention is not limited to the above-described embodiment, but can be modified as follows.
[0043]
(1) In the above embodiment, three heat pipes 37 are provided in the heat transfer unit 35, but four or more heat pipes may be provided in order to further increase the heat radiation. Conversely, if there is room for heat dissipation, two or less heat pipes may be used.
[0044]
(2) The heat pipe 37 may be directly attached to the X-ray tube device 19 and the C-arm 9 without being attached via the connecting member 39.
[0045]
(3) If the connection member 39 and the X-ray tube device 19 and the C-arm 9 have sufficiently high thermal conductivity, the heat transfer material 44 need not be used.
[0046]
(4) In the above embodiment, since the cover 17 is attached to the X-ray tube device 13, the heat transfer portion 35 is attached only to the side surface of the X-ray tube device 13, but the heat transfer portion 35 is attached to other portions. The heating section 35 may be further attached. For example, it is attached across the rear surface of the housing 19 (the right front side in FIG. 3) and the lower surface of the C-arm 9 (the surface not shown in FIG. 3).
[0047]
(5) The surgical X-ray TV apparatus 1 according to the above-described embodiment 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 the device, and can be applied to, for example, the surgical X-ray TV device 1 including various arms such as a U-shaped arm.
[0048]
【The invention's effect】
As is clear from the above description, according to the present invention, since both ends of the heat pipe are attached to the housing and the arm, the heat of the housing can be efficiently passed through the heat pipe to the arm having a larger heat capacity than the X-ray tube device. Can be transmitted to. 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.
[Brief description of the drawings]
FIG. 1 is a perspective view showing a schematic configuration of a surgical X-ray TV apparatus according to an embodiment.
FIG. 2 is a longitudinal sectional view of the X-ray tube device.
FIG. 3 is an external perspective view of a heat transfer unit.
FIG. 4 is an exploded perspective view showing a mounting structure of the heat pipe.
FIG. 5 is a longitudinal sectional view showing a preferred example of a mounting member.
FIG. 6 is a plan view showing a modification of the heat pipe.
[Explanation of symbols]
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 X-ray tube 23 ... High voltage transformer 25 ... Filament transformer 27 ... Glass Bulb 29 ... Cathode 31 ... Fixed anode 35 ... Heat transfer part 37 ... Heat pipe 39 ... Connection member 39
P: adhesive 44: heat transfer material 45: recess

Claims (3)

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, the housing and the arm A surgical X-ray TV apparatus, wherein both ends of a heat pipe are attached. The surgical X-ray TV apparatus according to claim 1, further comprising a connecting member having a recess along the outer shape of the heat pipe, wherein the heat pipe is attached via the connecting member. Surgical X-ray TV device. The surgical X-ray TV apparatus according to claim 2, wherein the connecting member is attached via an elastic or viscous heat transfer material.

Images