JPH0713305U - Medical X-ray device, irradiation tube and medical position display device - Google Patents

Abstract

(57) [Summary] [Purpose] X regardless of positioning distance and angle.
The center of the line-radiation cone should always be visible with good visibility on the illuminated surface of the patient. [Structure] A plurality of visible optical means 23 and 24 are provided outside the X-ray emission cone in the irradiation cylinder 1 at intervals in the circumferential direction,
Each visible optical means generates visible light on a plane including the X-ray axis, thereby illuminating a + -shaped optical pattern on the irradiated surface of the patient to linearly image the X-ray emission center. Can be displayed on the illuminated surface as the intersection position of.

Description

[Detailed description of the device]

[0001]

[Industrial applications]

 The present invention relates to a medical X-ray apparatus and an irradiation tube, a dental X-ray apparatus such as an intraoral radiography apparatus called dental, and an irradiation tube used in the dental X-ray apparatus, for example. Regarding

The present invention also relates to a medical position display device which is preferably used for displaying the position of irradiation of invisible electromagnetic waves such as X-rays, infrared rays and ultraviolet rays used for medical examination.

[0003]

2. Description of the Related Art A dental X-ray apparatus for intraoral radiography is legally allowed to irradiate X-rays in an area exceeding the size of the radiographic film placed in the oral cavity. It is the only X-ray device. Irradiation exceeding the film diagonal at the end of the irradiation cylinder is recognized by various standards, in contrast to the normal film size of 30 × 40 mm in length × width (film diagonal of 50 mm). This is not allowed with other X-ray equipment.

To explain the reason, the dental X-ray apparatus for intraoral radiography does not always use the apparatus and the film with a certain dimension, unlike other X-ray machines, but rather the angle depending on the desired site for radiography. Coupled with the fact that the film position is not directly visible to the operator because the distance is changed and the film is inserted into the patient's oral cavity, the radiation cone of X-rays, that is, the irradiation field is located inside the film. This is because there is a tendency to make a so-called corn-cutting shooting error without entering. If a corn cut occurs, it will be necessary to retake an image, resulting in an increase in the patient's exposure dose. This is because, in order to reduce this risk, it is necessary to irradiate X-rays over a large area over the film size. In this way, with a dental X-ray device for intraoral radiography, even if the exposed area is set to be slightly larger than the film size, the total amount of patient exposure can be reduced compared to multiple X-ray exposure. become.

Even with a dental X-ray apparatus in which it is permitted to irradiate X-rays in an area exceeding the size of the film to be photographed, from the viewpoint of reducing the patient exposure dose, it is necessary to reduce the number of photographing times. At the same time, it is desirable to reduce the exposure dose and exposure area, and for that purpose it is necessary to improve the positioning and reproducibility of positioning of the X-ray equipment. The positioning reproducibility is the positioning reproducibility of the X-ray irradiation field and the positioning reproducibility such as the irradiation angle. Such reproducibility is compared with pre-operative and post-operative follow-up observation of the patient's treatment. Is important when doing. In the prior art, there is a structure in which a scale is displayed so that the operator can know the irradiation angle of the X-ray irradiator, but such a structure is not sufficient to improve reproducibility. In order to improve such reproducibility, attempts have conventionally been made to position by visible light.

A typical prior art is disclosed in Japanese Utility Model Laid-Open No. 55-51280. In this prior art, a visible optical system for displaying a visible spot light at the X-ray irradiation position of the irradiation target can be freely put in and taken out at a position coaxial with the X-ray irradiation axis of the irradiation cylinder and a retracted position outside the irradiation area. Composed.

In such a prior art, it is necessary to mechanically retract the visible optical system to the retracted position after positioning with the spot light, and therefore the positioning that has been performed may be misaligned due to the retracting operation.

Further, in this prior art, the position where the spot light is focused, that is, the position where the diameter of the spot light is the minimum is a certain point in the optical axis direction, and the diameter of the spot light spreads before and after that point. . In addition, when the irradiation target is irradiated with spot light at a relatively shallow angle for positioning, that is, when the irradiation is performed obliquely instead of from the front of the irradiation target, the diameter of the spot light irradiated is, for example, It is difficult to know the optical axis, that is, the X-ray axis line accurately because the spot light shape is distorted due to the oval shape or the unevenness of the object to be illuminated, the face shape, and the skin.

Another prior art is Japanese Utility Model Laid-Open No. 55-166213. In this prior art, a cylindrical photoconductive structure similar to an X-ray emission cone is provided, and by this, the contour of the X-ray irradiation field is illuminated so as to be drawn with visible light.

The problem with this prior art is that the center of the field is difficult to see.

[0011] Still another prior art is the Japanese Utility Model Laid-Open No. Sho 58-1405. In this prior art, a visible spot is projected from three points spaced in the circumferential direction of the irradiation tube toward a certain point on the X-ray axis. Illuminate the light.

In this prior art, there is a problem that a plurality of irradiation spot lights appear before and after the one point of the X-ray axis. Therefore, even in this prior art, the center of the irradiation field is difficult to see.

[0013]

[Problems to be solved by the device]

 An object of the present invention is to provide a medical X-ray device, an irradiation tube, and a medical position capable of accurately knowing the center of the irradiation field when irradiating the irradiation position of invisible electromagnetic waves such as X-rays, infrared rays, and ultraviolet rays. It is to provide a display device.

[0014]

[Means for Solving the Problems]

 The present invention relates to a medical X-ray device in which a radiation cone of X-rays emitted from an X-ray generator is regulated by an irradiation cylinder, wherein the irradiation cylinder is provided with a plurality of visible optical elements that are circumferentially spaced outside the radiation cone. Is provided, and each visible optical means is a medical X-ray device characterized by generating planar visible light including an X-ray axis.

In the present invention, the X-ray generation unit is equipped with an irradiation tube that regulates the radiation cone of X-rays from the X-ray generation section, and the irradiation tube emits visible light to the X-ray irradiation target. It has a visible light means for illuminating and displaying the X-ray irradiation position, and at least one of the irradiation cylinder and the X-ray generator is provided on the outer periphery of the irradiation cylinder and has a surface shape for controlling on / off of the visible optical means. A medical X-ray apparatus having a switch.

The X-ray generator of the present invention is attached to the arm so as to be angularly displaceable around a rotation axis intersecting the X-ray axis, and the planar switch is arranged so that the X-ray axis direction is relative to the rotation axis. It is characterized in that it is arranged on one or both sides of the direction.

Further, at least the tip of the irradiation tube of the present invention is made of a translucent material.

Further, the present invention is characterized in that the tube tip of the irradiation tube is detachable.

Further, the present invention is characterized in that the irradiation cylinder is attached to the X-ray generation unit so as to be angularly displaceable around the X-ray axis.

Further, the present invention provides a cylindrical body for guiding a radiation cone of X-rays, and a plurality of visible optical means provided on the cylindrical body outside the radiation cone and arranged at intervals in the circumferential direction of the cylindrical body. And each visible optical means is characterized in that it generates planar visible light including the axis of the X-ray.

The present invention also includes a cylindrical body that draws an X-ray radiation cone, and visible optical means that is provided on the cylindrical body and that illuminates the X-ray irradiation target with visible light to display the X-ray irradiation position. It is characterized in that it is provided on the outer periphery of the cylindrical body and is provided with a planar switch for controlling on / off of the visible optical means.

Further, the present invention is characterized in that at least the tip of the tubular body is made of a translucent material.

Further, the present invention is characterized in that a battery for supplying electric power to the visible optical means is built in the cylindrical body, and the irradiation cylinder is attachable to and detachable from the X-ray generator.

Further, according to the present invention, a cylinder tip is detachably provided at a cylinder base end of a cylinder for guiding an X-ray radiation cone, and a support projecting forward from an end of the cylinder base end on the irradiation target side is provided. The support piece is fixed so that the tip of the cylinder is attached to the end of the base end of the cylinder, and the protruding length of the support piece is the focal point of the X-ray tube and the irradiation surface of the irradiated body. The irradiation tube is characterized in that an allowable distance SSD between and is selected to be a value that is secured.

Furthermore, the present invention provides a cylindrical body having a hollow portion that allows invisible electromagnetic waves to pass therethrough, and a plurality of visible optical elements that are provided in the cylindrical body so as to surround the hollow portion of the cylindrical body and be spaced apart in the circumferential direction. Each of the visible optical means generates a visible light in a plane including the axis of the invisible electromagnetic wave, and is a medical position display device.

Further, the present invention is characterized in that each visible optical means includes a light source for generating visible light, and a lens for concentrating the visible light from the light source in a planar shape.

Further, the present invention is characterized in that the planar visible light intersects with the axis of the invisible electromagnetic wave as an intersection.

Further, the present invention is characterized in that planar visible light directly intersects with an axis of the invisible electromagnetic wave as an intersection.

Further, according to the present invention, an operation switch for turning on / off each light source is provided on the outer periphery of the cylindrical body, and when the operation switch is turned on, each light source is turned on for a predetermined time. It is characterized by

Further, the present invention is characterized in that each light source is a light emitting diode.

[0031]

[Action]

 According to the invention, a plurality of visible light means are arranged on the tube body of the irradiation tube at intervals in the circumferential direction outside the radiation cone of the X-rays, and each of these visible light means has an axis line of the X-ray. Generates planar visible light that contains. Therefore, the planar visible light from each of the plurality of visible optical means intersects in a straight line on the X-ray axis. Therefore, regardless of the distance to the surface of the irradiated object in the X-ray axis direction, and even on an irradiated object with irregular asperities such as the surface of the skin of the face, the intersection of visible light is relative to the irradiated object. It is accurately displayed on the surface of the irradiated object regardless of the X-ray irradiation angle. Further, even if the intersection of visible light is not on the skin, the position of the intersection can be easily estimated by rotating the fan-shaped beam of visible light around the X-ray axis. Further, according to the present invention, a switch for controlling on / off of each visible optical means is a planar switch, and the planar switch is positioned on the outer periphery of at least one of the irradiation cylinder and the X-ray generation unit. Sometimes it is necessary to provide a wide area, including the part that the operator naturally touches, so that when the operator holds and operates the irradiation tube and the X-ray generation part by hand, the planar switch can be easily operated. It is possible to operate without turning on and off the visible light.

As described above, since it is possible to easily turn on / off the visible optical means by the planar switch, when the fan-shaped visible light beam crosses the patient's eye depending on the imaging site, the operator needs to adjust the position at the time of positioning. The visible optical means can be turned on only for a minimum period of time, and it can be turned off during the time after the positioning until the end of X-ray imaging, so that the pain caused by the patient's glare can be alleviated as much as possible. Especially when the patient is sensitive to light, the visible light beam enters the eye during radiography, causing the patient to move, resulting in a misalignment of the patient's position. The present invention solves this problem although it may result in blurring of the image.

This planar switch is arranged on one side or both sides in the X-ray axial direction with respect to the rotation axis of the X-ray generation section by the arm that instructs the X-ray generation section, and thus operates the X-ray generation section. At this time, the planar switch can be easily operated. The pivot axis intersects the X-ray axis and may be, for example, a horizontal axis.

Furthermore, according to the present invention, at least the tip of the irradiation tube is made of a light-transmissive material, so that the axis of the X-ray emission cone is aligned with the tip of the tube tip as close as possible to the irradiated surface of the patient. The crossing points, eg the + -shaped light image, which is the pointing optical pattern, can be observed in close proximity, thus limiting the exposed area and allowing more precise positioning. If the barrel tip is light-shielding, even if the visible light pattern that indicates the axis of the X-ray emission cone is illuminated, the tip of the barrel tip will be visible when approaching the irradiated surface of the patient. When the gap between the tip of the tube tip and the irradiated surface of the patient becomes small, the visible light pattern cannot be observed only from a very shallow angle with respect to the irradiated surface. It becomes very difficult to recognize the crossing optical pattern, that is, the pointing point at the center of the X-ray emission cone, and to clearly recognize the center of the X-ray emission cone due to the visible light pattern, the X-ray emission In order to observe from a shallow angle with respect to the axis of the cone, that is, from a position close to that axis, it is necessary to increase the distance between the tip of the barrel tip and the irradiated surface of the patient, and as a result, X-rays Circle from the focus of the X-ray tube The problem is that the exposed area of the patient expands because it spreads out like a circle, and it causes a decrease in the dose on the X-ray receiving surface of the film and X-ray detection sensor, so it is necessary to lengthen the imaging time. Therefore, there arises a problem that the total amount of radiation dose to the patient increases. In the present invention, such a problem is solved by making at least the tip of the irradiation tube from a transparent material.

Further, according to the present invention, the tube tip of the irradiation tube can be attached and detached, whereby the tube tip can be exchanged for each patient and the risk of nosocomial infection such as virus can be prevented. In this case, the barrel tip may be made of a material that can be repeatedly sterilized, or may be made of a material that is discarded.

Further, according to the present invention, an X-ray limiting diaphragm made of a material that blocks or attenuates X-rays such as lead material and antimony is incorporated in such a removable barrel tip to reduce the radiation dose to the patient. You may be able to do.

Further, according to the present invention, the irradiation cylinder is attached to the X-ray generation unit so as to be angularly displaceable around the X-ray axis. Therefore, the visible light pattern that intersects the axis of the X-ray emission cone, that is, the beam of the fan-shaped plane that indicates the center of the irradiation field, is the intersection point of the visible light depending on the angular displacement of the irradiation cylinder. It becomes possible to perform angular displacement while maintaining the condition that coincides with. Therefore, in actual clinical practice, the operator can match the linear optical pattern formed by the fan-shaped plane beam of visible light with the imaging reference line most suitable for the imaging site, thus dramatically improving the image reproducibility. be able to. The imaging reference line is, for example, the anatomically significant tooth axis line and occlusal plane, and between the two points on any face that the operator has arranged to obtain reproducibility during subsequent imaging. It may be a line connecting the lines, or may be, for example, a horizontal line of the ear or a hearing line or a nose line. Furthermore, when the patient is sensitive to light, the visible light pattern can be displaced from the patient's eyes by the angular displacement of the irradiation tube, which can relieve the patient's pain as described above.

Further, according to the present invention, the battery for supplying the electric power to the visible optical means is housed in the irradiation tube, and the irradiation tube can be attached to and detached from the X-ray generation unit, so that it has already been delivered to the clinic. This irradiation tube can be attached to an already delivered X-ray device and used.

Further, according to the present invention, the tube body of the irradiation tube is composed of a tube body base end portion and a tube tip detachable from the tube body base end portion, and the tube body base end portion is covered with The support piece protruding toward the irradiation body is fixed so that the tip of the tube can be attached to the end of the cylinder base end using this support piece. The length projecting forward is selected so that an allowable distance SSD (Sorce-Skin Distance) between the X-ray tube focal point and the irradiation surface of the irradiation object is secured. Therefore, even if X-rays are irradiated without mounting the tip of the cylinder on the base end of the cylinder, at least the allowable distance SSD is secured. This distance SSD is from the X-ray tube focus allowed to the output tube voltage of the X-ray device to the exposed skin surface in various X-ray standards such as IEC Publication 407 Radiation Protection in Medical X-ray Equipment 10kV to 400kV. The minimum value of the distance is specified, and X-ray irradiation from a distance below this is not permitted, and the present invention can avoid such a danger.

Furthermore, according to the present invention, a tubular body having a hollow portion for transmitting invisible electromagnetic waves such as X-rays, ultraviolet rays, infrared rays, and laser light, and a circumferential space surrounding the hollow portion. And a plurality of visible optical means are provided, and each visible optical means generates visible light in a plane including the axis of an invisible electromagnetic wave passing through the hollow portion. With such planar visible light, the irradiation position of the invisible electromagnetic wave can be displayed on the irradiation surface.

Further, according to the present invention, each visible optical means includes a light source and a lens for concentrating the visible light from the light source in a planar shape, and with such a configuration, the visible light beam in the direction perpendicular to the optical axis is formed. It is possible to accurately display the irradiation position of the invisible electromagnetic wave by irradiating the visible light beam with substantially the same size over a predetermined width in the optical axis direction while reducing the enlargement of the window. Therefore, even if the irradiated position is not a uniform circle such as the face, distortion of the visible light shape due to unevenness of the irradiated surface can be reduced, and the irradiation position of the invisible electromagnetic wave can be accurately determined by the operator. It becomes possible to show in.

Further, according to the present invention, the visible light emitted by each visible optical means intersects with the axis of the invisible electromagnetic wave as an intersection, so that the irradiation position of the invisible electromagnetic wave can be displayed more accurately. Is possible.

Further, according to the present invention, the visible light emitted by each visible optical means is made orthogonal to each other with the axis line of the invisible electromagnetic wave as the intersection point, so that the position of the axis line of the invisible electromagnetic wave on the irradiation surface is The operator can grasp the irradiation field as a point symmetry with respect to the intersection point of the visible light beam, which enables the irradiation position of the invisible electromagnetic wave to be displayed more accurately.

Further, according to the present invention, since the operation switch is provided on the outer periphery of the cylindrical body and the light source is turned on for a predetermined time when the operation switch is turned on, the operator turns off the operation switch. This eliminates the need for operation, simplifies the operation, eliminates wasteful power consumption of each light source, and makes it possible to set the invisible electromagnetic wave irradiation position easily and accurately in a short time.

Further, according to the present invention, since each light source is composed of a light emitting diode, the configuration is extremely simple and the present invention can be implemented inexpensively as compared with the case of using a semiconductor laser oscillator or the like. Therefore, the manufacturing cost can be reduced.

[0046]

【Example】

 FIG. 1 is a cross-sectional view showing an irradiation tube 1 and an X-ray generator 2 to which the irradiation tube 1 is attached according to an embodiment of the present invention. FIG. 2 is a front view of the irradiation tube 1 as seen from the right side in FIG. is there. The X-rays generated from the X-ray generation part 2 are made into a radiation cone and guided by the irradiation cylinder 1.

FIG. 3 is a perspective view showing the whole of a dental X-ray apparatus 3 for intraoral radiography, which is so-called dental, including the irradiation tube 1 and the X-ray generator 2. The X-ray apparatus main body 4 has arms 7, 8 and 9 which can be angularly displaced around a vertical axis on a support 6 which is erected on a base 5, and which is used in the oral cavity of a patient seated on a seat plate 10 of the support 6. A film or an X-ray detection sensor is put in and an X-ray is emitted from the X-ray generator 2 from outside the oral cavity to perform imaging. The X-ray apparatus of the present invention may be of a stationary type as shown in FIG. 3, but may be of a suspended type, a wall mounted type or a movable type with wheels mounted on the base 5. Good.

Referring again to FIG. 1, in the X-ray generation unit 2, the X-ray tube 11 is housed in the case 12, and the case 12 is filled with insulating oil or the like. The case 12 is fixedly mounted in the housing 13, and the mounting member 14 is fixed to the X-ray opening 63 of the case 12. A diaphragm 15 made of a material such as a lead material is fixed in the mounting member 14, whereby X-rays from a focal point F of the X-ray tube 11 are formed into an irradiation cone 16 which is It is guided in the irradiation tube 1 and is irradiated to the irradiation surface such as the skin surface of the patient, which is the irradiation object on the right side of FIG.

The irradiation cylinder 1 basically has an irradiation cylinder body 17 and a cylinder tip 18. The irradiation cylinder main body 17 has a cylindrical body base end portion 19 attached to the housing 13, and a cylinder tip 18 is detachably mounted by a support piece 20 on an irradiation target side end portion 19a of the cylindrical body base end portion 19. Be worn. The tubular body base end portion 19 and the tubular tip 18 form a tubular body 21.

Inside the tube base end portion 19 of the irradiation tube body 17, outside the X-ray emission cone 16, a plurality of visible portions are provided at circumferential intervals around the X-ray axis 22 as shown in FIG. Optical means 23, 24 are provided. In this embodiment, two visible optical means 23 and 24 are provided at intervals of 90 degrees in the circumferential direction. The one visible optical means 23 generates planar visible light 25 including the X-ray axis 22 on the irradiation target side. The other visible optical means 24 emits planar visible light 26 including the X-ray axis 22. Therefore, these planar visible lights 25 and 26 are orthogonal to each other on the X-ray axis 22. The intersection of the planar visible lights 25 and 26 always exists on the X-ray axis 22. As a result, when these visible lights 25 and 26 are illuminated on the surface of the irradiated body, the intersecting position thereof represents the X-ray axis 22. Therefore, the operator is required to position the X-ray generator 2. In working, regardless of the allowable distance SSD between the focal point F of the X-ray tube 11 and the irradiated skin surface of the patient, which is the irradiated surface of the irradiated object, and the angle between the irradiated surface and the X-ray axis 22. However, the visibility can always be made good and the X-ray axis 22 and hence the center of the irradiation field can be well grasped, and as a result, the positioning performance can be dramatically improved as described above. The irradiation tube main body 17 is configured to include a tube base end portion 19, visible light means 23 and 24, a battery 31, a planar switch 32, a drive circuit 33, a lid 35 and the like. The axis line 22 of the X-ray coincides with the axis line of the irradiation cylinder 1.

FIG. 4 is a cross-sectional view of the visible optical means 23, and another visible optical means 24 also has the same structure as the visible optical means 23. The visible light laser diode 27 generates visible light having a wavelength of, for example, 650 to 830 nm, and the visible light is subjected to focusing by the plano-convex lens 28 and further by a cylindrical lens 29 arranged in front of it. It is converted into a plane-shaped visible light 25 that is fan-shaped. The laser diode 27 and the lenses 28 and 29 are housed in the cylindrical case 30 and integrated, and housed in the cylindrical base end portion 19.

FIG. 5 shows an electrical configuration related to the laser diode 27. The laser diode provided in the visible optical means 24 is indicated by reference numeral 27a. Electric power from the battery 31 is supplied to the drive circuit 33 via the planar switch 32, and the laser diodes 27 and 27a are driven by this. The battery 31 is provided in the storage recess 34 shown in FIG. 2 of the cylindrical base end portion 19 and is closed by a lid 35 so as to be openable and closable. Further, the drive circuit 33 is housed in the case 30 of the visible optical means 23.

FIG. 6 is a cross-sectional view of visible optical means 23 used in place of the configuration of FIG. 4 described above. The visible optical means 23 shown in FIG. 6 has an incandescent sphere 36, and this incandescent sphere 36 has a linear filament 37. The axis of the linear filament 37 corresponds to the plane of the planar visible light 25, and the upper and lower straight lines in FIG. 6 including the axis of the filament 37 pass through the X-ray axis 22. The incandescent bulb 36 is also powered by the battery 31 via the planar switch 32. A lens 38 for focusing is arranged in front of the incandescent bulb 36. The lens 38 may be a combination of two plano-convex lenses as shown in FIG. 6, or may be two convex lenses. The incandescent bulb 36 and the lens 38 are housed in a cylindrical case 39. To be done. The other visible optical means 24 may also have a configuration similar to that shown in FIG.

Further, as another embodiment of the present invention, the visible optical means 23, 24 include a light source for generating visible light, a lens, and a light shield having slits for forming the planar visible light 25, 26. It may be realized by a combination with a sex diaphragm, or may have another configuration.

Since the battery 31 and the drive circuit 33 are housed in the tube base end portion 19 of the irradiation tube 1 and the irradiation tube can be removably attached to the X-ray generator 2 with the bolt 56, It can be easily attached to the already delivered X-ray device. As another embodiment of the present invention, the battery 31 or other power source may be connected from the low voltage circuit of the X-ray generator 2, for example.

FIG. 7 is a view showing in simplified form the planar visible light 25, 26 generated from the visible optical means 23, 24 of the irradiation cylinder 1. The visible lights 25 and 26 are flat as described above, and thus, when illuminated on the surface of the illuminated object, draw a thin linear optical pattern. In this embodiment, two fan-shaped beams of visible light 25 and 26 are generated at positions 90 degrees apart from each other in the circumferential direction of the cylindrical base end portion 19, so that a plurality of positions pa, along the X-ray axis 22 are set. The surface-like optical patterns of the irradiated object in pb and pc are as shown in FIG. 8 (1), FIG. 8 (2) and FIG. 8 (3), and such a + -shaped optical pattern is formed at the end of the barrel tip 18. In front of the portion 40 (on the right side in FIG. 7), the intersection of the visible lights 25 and 26 always indicates the center of the X-ray emission cone 16 regardless of the irradiation position and angle. As another embodiment of the present invention, in addition to the + -shaped visible optical pattern, a larger number of fan-shaped visible light beams are generated, and the intersections of these planar visible lights are set to the X-ray axis 22. You may make it match.

As shown in FIGS. 1 and 2, the planar switch has a tape shape or a sheet shape, and surrounds the tube base end portion 19 of the irradiation tube body 17 over the entire circumference in the circumferential direction. Composed. With this, the operator can easily perform the positioning without being distracted by the operation of the planar switch 32 by the operator's finger when the operator positions the imaged portion in actual clinical practice. Although the planar switch 32 is arranged in a part along the axis of the irradiation tube main body 17 in this embodiment, the area of the planar switch 32 is natural when the operator positions it as another embodiment of the present invention. It is preferable to arrange them so as to cover as wide a range as possible including the area to be touched, and it is also possible to cover the entire outer peripheral surface of the irradiation cylinder main body 17 with the planar switch 32. .

The reason why the planar switch 32 is operated to control the on / off of the visible optical means 23 and 24 in this manner is that the visible light 25 and 26 may cross the patient's eyes depending on the imaging site. This is because, in such a case, the visible light is radiated for a moment so that the positioning is finished in a very short time, so that the patient's glare can be reduced as much as possible. Further, by providing the planar switch on the irradiation tube and / or the rear part of the X-ray generation unit, the planar switch can be operated with the position of the operator's hand when positioning the X-ray generation unit with respect to the irradiation target. I have to. As another embodiment of the present invention, the planar switch 32 may be omitted and the visible optical means 23 and 24 may be continuously turned on.

In the above-described embodiment, the planar switch 32 is interposed between the battery 31 and the drive circuit 33 to control the power on / off, but as another embodiment of the present invention. Alternatively, a control signal for performing on / off control may be applied to a processing circuit such as a microcomputer, and the driving circuit 33 may be controlled by this processing circuit to control the laser diodes 27, 27a. The planar switch 32 only needs to have a configuration capable of generating an electric signal by touching or pressing the human body, and can be realized by a pressure sensitive sheet, a membrane switch, or the like, or a metal plate. Etc., and other configurations may be used.

FIG. 9 is a perspective view of another embodiment of the present invention. The planar switch 32 is provided in the X-ray generation unit 2 as described above, and the planar switch 32 can be operated by the operator's hand 41 while performing the positioning operation of the X-ray generation unit 2. However, it is also possible to further provide the planar switch 42 on the X-ray generator 2 so that the hand 41a can be used for positioning and performing a switch operation. The X-ray generation unit 2 is attached to the arm 9 so as to be angularly displaceable around a horizontal rotation axis 43 that intersects the X-ray axis 22 vertically. In this embodiment, the rotation axis 43 passes through the X-ray axis 22. The planar switches 32 and 42 are arranged on both sides in the direction of the X-ray axis 22 with respect to the rotation axis 43, for example, at the rear of the irradiation tube 1 and the X-ray generator 2, respectively, to improve operability. Further, the planar switch 32 may be attached to only one of the irradiation tube 1 and the rear part of the X-ray generator 2.

The cylinder tip 18 is for ensuring a distance when the focal point F of the X-ray tube 11 and the end portion 40 of the cylinder tip 18 contact the exposed surface of the patient as a value equal to or greater than the allowable distance SSD. And may be a transparent material such as transparent glass, lead glass, acrylic resin, vinyl chloride, or the like. As a result, the end portion 40 of the barrel tip 18 is brought into a state where it is as close as possible to, for example, the exposed surface of the patient, which is the irradiated surface, and a + -shaped visible light pattern is formed as shown in FIG. It is possible to observe from the outside of the X-ray, so that the X-ray exposure center can be accurately known, and therefore accurate positioning is possible, and the exposure area can be X-rayed within the range where the allowable distance SSD is secured. It is possible to make the exposed area that spreads in a conical shape as small as possible by bringing it as close as possible to the wire tube 11. The cylindrical base end portion 19 may also be made of a light-transmitting material like the cylindrical tip 18, but may be made of a light-shielding material.

FIG. 10 is a simplified cross-sectional view showing a configuration of a support piece 20 that is made detachable from the barrel base end portion 19 of the barrel tip 18 and supports the detachable barrel tip 18. A plurality of support pieces 20 (four pieces in this embodiment) are provided at equal intervals in the circumferential direction, and the base end portions 44 thereof are embedded in the cylindrical body base end portion 19 and are made of a resilient material having elasticity. It consists of materials such as piano wire. The tip portion 45 of the support piece 20 is bent outward in the radial direction, so that the tip end portion 45 of the support piece 20 is elastically attached to a frustoconical locking surface 46 that extends radially outward in the vicinity of the end portion 40 of the barrel tip 18. The cylinder tip 18 is prevented from being disengaged from the fitting portion 47 of the end portion 19a of the cylinder body base end portion 19 by this.

The support piece 20 projects forward from the end 19 a of the tubular body proximal end 19 on the irradiation target 48 side in the natural state shown in FIG. 11 in which the tubular tip 18 is separated from the tubular body proximal end 19. The protruding length L1 to the tip portion 45 is a value at which an allowable distance SSD between the focal point F of the X-ray tube 11 and the irradiation surface 48 of the irradiation target is secured, that is, the allowable distance SSD. The above values are selected. Therefore, even when the tube tip 18 is forgotten to be attached and X-ray imaging is performed, the tip end portion 45 of the support piece 20 contacts the irradiation surface 48, and the allowable distance SSD is secured. If the barrel tip 18 is screwed into the barrel base end 19 and mounted, such a support piece 20 is not provided. Therefore, if the barrel tip 18 is forgotten to be mounted, the barrel base end 19 is not attached. The end portion 19a of the above contacts the surface 48 to be irradiated, so that the permissible distance SSD is not secured and the X-ray is exposed in a state where the X-ray intensity is high. The present invention solves this problem.

FIG. 12 is a sectional view showing a cylinder tip 49 of another embodiment which can be used in place of the cylinder tip 18 described above. When the tube tip 49 is detachable from the tube base end portion 19 and replaced, when using a film which is widely used at present with a length x width of 30 x 40 mm (film diagonal of 50 mm), it is necessary to carry out the above-mentioned procedure. For this purpose, it is necessary to use a tube tip 18 with a relatively large inner diameter, while a smaller film with a length x width of 22 x 30 mm (diagonal film 37.2 mm) is used when photographing children. At this time, if the above-mentioned barrel tip 18 is used, the irradiation field exceeds a small film size, resulting in giving unnecessary exposure dose to a pediatric patient. In order to solve this problem, as shown in FIG. 12, a barrel tip 49 in which a secondary diaphragm 50 made of a material such as lead material or antimony is fixed to a barrel tip body 51 is used. Such a barrel tip 49 is prepared separately from the barrel tip 18 described above and can be replaced with the barrel base end portion 19 with one touch, so to speak, by using this barrel tip 49, the irradiation field 52 by the barrel tip 18 described above. A relatively small irradiation field 53 can be achieved, which can contribute to the reduction of the exposure dose. In this FIG. 12, a structure for ensuring the allowable distance SSD may be provided similarly to the support piece 20.

FIG. 13 is a bottom view of a part of the irradiation cylinder 1 and the X-ray generator 2. The tubular body proximal end portion 19 that constitutes the tubular body 21 of the irradiation tubular body 17 is fitted to the portion 54 near the X-ray generation portion 2 with the attachment member 14 of the X-ray generation portion 2, and the end portion of the housing 13 55 (see FIG. 1 described above) is fitted, the shaft portion 57 of the bolt 56 is gently inserted through the elongated hole 58 formed in the circumferential direction of the cylindrical portion 54, and the elongated hole similar to the elongated hole 58. The shaft 57 is inserted into the mounting member 14 of the X-ray generation unit 2 and fixed thereto. The shaft portion 57 also passes through a bolt insertion hole 60 formed in the end portion 55 of the housing 13 of the X-ray generation portion 2 and having a circular cross section perpendicular to the axis. The head portion 61 of the bolt 56 partially covers the elongated hole 58 of the tubular portion 54. As a result, the cylindrical base end portion 19 is prevented from moving in the direction of the X-ray axis 22 and can be angularly displaced around the axis 22 along the circumferential length of the elongated hole 58. The length L2 of the long hole 58 along the circumferential direction may be, for example, a value that exceeds the circumferential angle of the visible optical means 23 1 and 24, which is 90 degrees in this embodiment.

As described above, the visible optical means 23 and 24 are provided at the tube base end portion 19 of the irradiation tube main body 17, and therefore, the intersections of the planar visible lights 25 and 26 that display the center of the irradiation field. Can rotate the planar visible light 25, 26 in a state of being coincident with the X-ray axis 22. Therefore, in actual clinical practice, the operator can match the linear light pattern with the imaging reference line that is most suitable for the imaging site, thereby dramatically improving the image reproducibility. Also, when the patient is hypersensitive to light, the visible light 25 or 26 can be displaced from the patient's eyes by angularly displacing the tubular base end portion 19 so that the patient does not feel dazzled. The patient's pain can be relieved.

FIG. 14 is a cross-sectional view showing a cylinder 101 of another embodiment of the present invention and an X-ray generator 2 to which the cylinder 101 is detachably mounted, and FIG. 15 is a right side of the cylinder 101 in FIG. It is the sectional view seen from the direction. The X-ray generation unit 2 is similar to that of the embodiment shown in FIGS. 1 to 13, and therefore corresponding parts are designated by the same reference numerals. At the end 55 of the housing 13 of the X-ray generator 2, the medical position display device 103 of this embodiment is attached. This medical position display device 103 basically encloses a tubular body 101 fixed to the end portion 55 by a bolt 61 and a hollow portion 104 defining the irradiation cone 16 in the tubular body 101, and surrounds the tubular body 101 in the circumferential direction. And a plurality of (4 in this embodiment) visible optical means 105 provided at intervals. The visible optical means 105 is configured to include a light emitting diode (abbreviated as LED) as a light source and a cylindrical lens 107, and the light from the light emitting diode 106 is converted into an invisible electromagnetic wave from the X-ray tube 11 by the cylindrical lens 107. It is condensed in a plane including the optical axis of the X-ray. Such visible optical means 105 are provided at intervals of 90 degrees in the circumferential direction.

The tubular body 101 is attached to the housing 13 and has an attachment member 108 to which the diaphragm 15 is fixed, and a first tubular portion 109 which is exterior to the attachment member 108 and is fitted to the end portion 55. The second tubular portion 110 is coaxially fixed to the first tubular portion 109, and the light-transmitting tubular tip 111 is provided coaxially with the second tubular portion 110. The first and second tubular portions 109 and 110 are made of a synthetic resin such as vinyl chloride, and the barrel tip 111 is made of a transparent synthetic resin such as acrylic.

Storage holes 113 for accommodating the respective visible optical means 105 are formed in the first cylinder portion 109 at intervals of 90 degrees in the circumferential direction, and the inside of each storage hole 113 and the light emitting diode 116 are arranged in the second cylinder portion 110. It is fixed to the outer peripheral surface of the truncated cone-shaped portion 115 by a substantially L-shaped mounting piece 116 and a screw 117. A straight cylindrical sleeve 118 made of lead and having a thickness of, for example, about 0.5 mm is mounted on the inner peripheral surface of the truncated cone portion 115 to define the X-ray irradiation cone 16.

A control means 119 and an operation switch 120 connected to a wiring board of the control means 119 are provided on the outer periphery of the second tubular portion 110. The control means 119 and the operation switch 120 are , Is covered with an outer cover body 123 together with the battery 121 that supplies electric power to each light emitting diode 116. A through hole 124 is formed in the outer cover body 123, and the outer cover body 123 is covered with a flexible sheet body 125 called a flash sheet so as to surround the through hole 124. By pressing the sheet body 125 from the outside, the operation piece 126 of the operation switch 120 can be indirectly pressed to change the switching mode. In the present embodiment, each light emitting diode 106 is configured to light up for a predetermined time of, for example, 10 seconds only when the operation switch 120 is pressed. Such a delay time is set by the control means 119.

FIG. 16 is a diagram showing an arrangement state of each cylindrical lens 107, and FIG. 17A is a simplified sectional view taken along the section line AA of FIG. The cylindrical lenses 107 are arranged at intervals of 90 degrees on a virtual circle C centered on the optical axis m of the X-ray. Cylindrical lenses 107a and 107b symmetrically arranged with respect to a virtual plane including the optical axis m will be described. One of the cylindrical lenses 107a shapes the light source light into a fan-shaped beam indicated by reference numeral 126, and the other cylindrical lens 107a. Lens 107b is shaped into a fan-shaped beam as indicated by reference numeral 127. Each of the beams 126 and 127 can form a thin linear light pattern having substantially the same width B on the irradiation surfaces Pa, Pb, and Pc spaced apart in the optical axis direction. FIG. 17B shows the optical pattern at each position Pa, Pb, Pc along the optical axis m of the X-ray. At the positions of Pa, Pb, and Pc, the optical pattern has an intersection point Q on the optical axis m of the X-ray, has a constant cross-shaped size, and has substantially the same size as the X-ray irradiation area. Therefore, when positioning the X-ray irradiation position, there is no risk that the light pattern will extend even if the distance to the irradiated surface changes slightly, and this light pattern has a surface of almost the same size as the actual X-ray irradiation area. Since the area will be illuminated, inconveniences such as cone cutting can be eliminated.

In the above description, the cylindrical lenses 107a and 107b that are adjacent to each other in the horizontal direction have been described, but the same applies to the cylindrical lenses 107c and 107d that are adjacent to each other in the vertical direction.

FIG. 18 is a simplified block diagram showing the electrical configuration of the control means 119. The control means 119 has a timer circuit 128 in which a predetermined time, for example, 10 seconds is set, and when the operation switch 120 is turned on at time t1 as shown in FIG. As shown in (2), the power from the battery 121 is applied to the line 129 only for the time W = 10 sec to cause the light emitting diode 106 to emit light. When the time W ends at the time t2, the power supply to the line 129 is cut off, so that the light emitting diodes 106 are turned off.

The present invention can be suitably implemented not only for displaying X-rays but also for displaying the position of irradiation with other invisible electromagnetic waves such as infrared rays, ultraviolet rays, and laser light.

As another embodiment of the present invention, the visible light irradiation pattern is not limited to the cross shape shown in FIG. 20 (1), but may be an X shape as shown in FIG. 20 (2). Of course, as shown in FIG. 20 (3), the two light patterns 129 and 130 may intersect at an angle other than a right angle. In addition, the present invention is designed to position the X-ray irradiation position on the occlusal plane of the patient during panorama radiography called panorama by setting the light pattern on the irradiated surface as a horizontal line "-" extending in the horizontal direction. Can be implemented. Furthermore, by using a vertical line “│” that extends in the vertical direction, it is possible to accurately irradiate the affected part, which is long in the vertical direction, with infrared rays or ultraviolet rays for treatment.

The present invention can be widely implemented not only for dentistry but also for medical use.

[0077]

[Effect of device]

 As described above, according to the present invention, the plurality of visible optical means are arranged outside the radiation cone of the X-rays, and each of the visible optical means generates the planar visible light including the axis of the X-rays. By doing so, during irradiation of X-rays, the axis of the X-rays, and hence the center of the radiation cone, can always be known on the irradiated surface, and therefore the X-ray emission can be positioned accurately.

Further, according to the present invention, as described above, each visible optical means generates planar visible light including the X-ray axis, and each visible optical means has a plurality of circumferentially spaced intervals. , The optical pattern illuminated on the surface to be illuminated is, for example, a + shape, and the intersection of two or more of the linear lines is the axis of the X-ray. Accurately know the position of the + -shaped intersection of visible light, even if the surface is displaced in the X-ray axis direction or if the irradiated surface is at an angle other than perpendicular to the X-ray axis. Therefore, it is possible to clearly know the X-ray emission cone, that is, the center of the irradiation field. Thus, according to the present invention, it becomes possible to always display the X-ray axis line with good visibility regardless of the positioning distance and the angle. This can significantly improve the positioning performance. This prevents mispositioning of the image, which causes a so-called cone cut, which is a deviation between the irradiation field due to the X-ray emission cone and the film or the X-ray detection sensor, thereby reducing the risk of re-imaging, and Since the positioning accuracy can be improved as described above, the irradiation cone of X-rays can be narrowed, the irradiation field can be reduced, and the exposure dose of the patient can be dramatically reduced.

Further, according to the present invention, in the state where the visible light pattern is illuminated on the illuminated surface, a thin linear optical pattern, for example, a + shape, is drawn, and therefore, the positioning accuracy can be improved. By doing so, the positioning reproducibility can be improved and the diagnostic value can be increased.

Further, according to the present invention, by providing a planar switch on the outer circumference of at least one of the irradiation or the X-ray generation unit, it is possible to perform positioning operation of the X-ray generation unit or the irradiation cylinder of the X-ray apparatus. Since the planar switch is inevitably arranged in a wide area on the touched part, the operator can position the visible optical means without being distracted by the operation of turning on / off the visible optical means. In addition, it is possible to prevent the misalignment of the positioning performed when the light is turned off after the positioning. Moreover, it is possible to easily turn on the light only at the time of positioning operation, and thus even a patient who is sensitive to light can be prevented from causing unnecessary pain to the patient due to glare or the like.

Further, according to the present invention, at least the tip of the irradiation tube is made of a light-transmissive material, so that even when the tip of the tube tip is close to the irradiated surface such as the skin, the X-ray Since the center of the irradiation field can be seen from an angle close to the axis of the X-ray, the positioning performance can be further improved, and the desired irradiation position can be set accurately in this way. Can be made smaller.

Further, according to the present invention, the tip of the tube can be detached, and the tip of the tube can be replaced for each patient to reduce the risk of nosocomial infection. By changing the diaphragm, it is possible to irradiate X-rays in a minimum irradiation field according to the film size used, and thus it is possible to further reduce the X-ray exposure dose of the patient.

Further, according to the present invention, the irradiation tube is attached to the X-ray generation unit so as to be capable of angular displacement around the axis of the X-ray, and therefore the irradiation tube together with the visible light beam can be rotated in the circumferential direction. As a result, the visible light beam can be completely escaped from the patient's field of view, and the patient's pain such as visible light entering the patient's eyes and feeling glare can be reduced. Furthermore, a plurality of linear visible lights can be aligned with the tooth axis and the occlusal plane, which are the imaging reference lines, and thus reproducibility can be improved.

Further, according to the present invention, the cylindrical body for guiding the X-ray radiation cone of the irradiation cylinder is constituted by the cylindrical body base end and the cylinder tip, and the front side of the irradiation body side end of this cylindrical body base end portion. The support piece protruding to the end is fixed, and the tip of the tube is detachably attached to the base end of the cylinder by this support piece. The length of the support piece protruding from the end of the X-ray base end is allowable. The distance SSD is selected to be a value that spreads out, so that the allowable distance SSD is secured even if X-rays are radiated to the illuminated surface without the cylinder tip being mounted. Patient safety is ensured.

According to the present invention, the X-ray generation unit is attached to the arm so as to be angularly displaceable around a rotation axis such as a horizontal axis, and the planar switch is provided with respect to this rotation axis in the X-axis axial direction. When the operator touches the X-ray generation unit or the irradiation tube when performing the positioning operation by angularly displacing the X-ray generation unit about the rotation axis line on one side or both sides, the visible optical means. ON / OFF control can be easily performed, and operability is improved.

Further, in the present invention, the battery for supplying electric power to the visible optical means and the drive circuit are also housed in the irradiation tube and detachably attached to the X-ray generator, so that they can be easily attached to already-delivered products and repaired. And can be easily replaced.

Furthermore, according to the present invention, a cylindrical body having a hollow portion that allows invisible electromagnetic waves such as X-rays, ultraviolet rays and infrared rays, and laser light to pass therethrough, and a circumferential space that surrounds the hollow portion. A plurality of visible optical means are provided to open the visible optical means, and each visible optical means generates visible light in a plane including the axis of the invisible electromagnetic wave passing through the hollow portion and displays the irradiation position of the invisible electromagnetic wave. You can Therefore, when performing invisible laser light or radiation treatment, it is possible to accurately irradiate the affected area of the living body for treatment.

Further, according to the present invention, since the visible light from the light source is condensed in a plane by the lens, the expansion of the light in the direction orthogonal to the optical axis is reduced, and the light is almost the same over a predetermined width in the optical axis direction. By irradiating the axis with a size, it is possible to accurately display the irradiation position of the invisible electromagnetic wave. Therefore, even if the irradiation position is not a uniform circle such as the face, distortion of the visible light shape due to unevenness of the irradiation surface can be reduced and the irradiation position of invisible electromagnetic waves can be accurately determined by the operator. It becomes possible to show in.

Further, according to the present invention, the visible light emitted by each visible optical means intersects with the axis of the invisible electromagnetic wave as an intersection, so that the irradiation position of the invisible electromagnetic wave can be displayed more accurately. Is possible.

Further, according to the present invention, the visible light emitted by each visible optical means is made orthogonal to each other with the axis line of the invisible electromagnetic wave intersecting with each other, so that the point centered on the axis line of the invisible electromagnetic wave on the irradiation surface. It is possible to grasp the irradiation field symmetrically, which makes it possible to accurately display the irradiation position of the invisible electromagnetic wave.

Further, according to the present invention, since the operation switch is provided on the outer periphery of the cylindrical body and the light source is turned on for a predetermined time when the operation switch is turned on, the operator turns off the operation switch. This eliminates the need for operation, simplifies the operation, eliminates wasteful power consumption, and makes it possible to set the invisible electromagnetic wave irradiation position easily and accurately in a short time.

Further, according to the present invention, since each light source is composed of a light emitting diode, the configuration is extremely simple and the present invention can be implemented inexpensively as compared with the case of using a semiconductor laser oscillator or the like. Therefore, the manufacturing cost can be reduced.

[Submission date] November 11, 1993

[Procedure Amendment 1]

[Document name to be amended] Statement

[Correction target item name] 0071

[Correction method] Change

[Correction content]

FIG. 16 is a diagram showing an arrangement state of each cylindrical lens 107, and FIG. 17A is a simplified sectional view taken along the section line AA of FIG. In this figure, 132Pa, 132Pb, and 132Pc are light patterns 132 viewed from the beam irradiation direction in Pa, Pb, and Pc, respectively. The cylindrical lenses 107 are arranged at intervals of 90 degrees on a virtual circle C centered on the optical axis m of the X-ray. Explaining the cylindrical lenses 107a and 107b arranged symmetrically with respect to a virtual plane including the optical axis m, one cylindrical lens 107a shapes the light source light into a fan-shaped beam indicated by reference numeral 126, and the other. The cylindrical lens 107b is shaped into a fan-shaped beam as indicated by reference numeral 127. The beams 126 and 127 can form thin linear light patterns 131 and 132 having substantially the same width B on the irradiation surfaces Pa, Pb, and Pc that are spaced apart in the optical axis direction. FIG. 17B shows the light patterns 131 and 132 at the positions Pa, Pb, and Pc along the optical axis m of the X-ray. At the positions of Pa, Pb, and Pc, the optical patterns 131 and 132 have an intersection Q on the optical axis m of the X-ray, and have a constant cross-shaped size, and have almost the same size as the X-ray irradiation area. . Therefore, at the time of positioning the X-ray irradiation position, there is no possibility that the light patterns 131 and 132 will extend even if the distance to the surface to be irradiated changes a little, and the light patterns 131 and 132 are different from the actual X-ray irradiation area. Since it illuminates areas of almost the same size, the disadvantages such as cone cutting can be eliminated.

[Procedure Amendment 2]

[Document name to be amended] Statement

[Correction target item name] 0075

[Correction method] Change

[Correction content]

As another embodiment of the present invention, the visible light irradiation pattern is not limited to the cross shape shown in FIG. 20 (1), but may be an X shape as shown in FIG. 20 (2). Of course, as shown in FIG. 20 (3), the two light patterns 131, 132 may intersect at an angle other than a right angle. Further, by setting the light patterns 131, 132 on the irradiated surface as horizontal lines "-" extending in the horizontal direction, in order to position the X-ray irradiation position on the occlusal plane of the patient during panoramic general radiography called panorama. The present invention can also be implemented. Further, by using a vertical line “|” that extends in the vertical direction, it is possible to accurately irradiate the affected part, which is long in the vertical direction, with infrared rays or ultraviolet rays for treatment.

[Brief description of drawings]

FIG. 1 is a cross-sectional view showing a part of an X-ray generator 2 and an irradiation tube 1 according to an embodiment of the present invention.

FIG. 2 is a front view of an irradiation cylinder 2.

FIG. 3 is a perspective view showing the overall configuration of a dental X-ray device.

FIG. 4 is a cross-sectional view of visible optical means 23.

5 is an electric circuit diagram showing a configuration related to the visible optical means 23. FIG.

FIG. 6 is a sectional view of a visible optical means 23 according to another embodiment of the present invention.

FIG. 7 is a simplified side view showing a state where planar visible light 25, 26 is irradiated by visible optical means 23, 24.

8 is a diagram showing an optical pattern on a surface to be irradiated which is perpendicular to the axis 22 at a plurality of positions pa, pb, pc along the axis 22 of the X-ray shown in FIG.

FIG. 9 is a perspective view showing a state in which the planar switch 42 is provided in the X-ray generation unit 2 according to still another embodiment of the present invention.

FIG. 10 is a simplified cross-sectional view showing a configuration in which a cylinder tip 18 is supported by using a support piece 20.

FIG. 11 is a perspective view showing a state in which a cylinder tip 18 is separated from a cylinder body base end portion 19;

FIG. 12 is a sectional view showing a cylinder tip 49 of another embodiment of the present invention.

FIG. 13 is a bottom view of an embodiment of the present invention showing a configuration for allowing the irradiation cylinder 1 to be angularly displaced.

FIG. 14 is a cross-sectional view showing a cylindrical body 101 of another embodiment of the present invention and an X-ray generation section 2 to which the cylindrical body 101 is mounted.

15 is a cross-sectional view of the cylindrical body 101 as viewed from the right side of FIG.

16 is a diagram showing an arrangement state of each cylindrical lens 107. FIG.

17 is a simplified diagram showing the cylindrical lenses 107a and 107b and the beams 126 and 127 condensed by these, as seen from the section line AA in FIG.

FIG. 18 is a simplified block diagram showing an electrical configuration of a control board 119.

FIG. 19 is a timing chart for explaining an on / off operation of the control board 119.

FIG. 20 shows an irradiation pattern 129 displayed on the surface to be irradiated,
It is a figure for demonstrating the shape of 130.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Irradiation cylinder 2 X-ray generation part 3 X-ray apparatus main body 4 Support 7,8,9 Arm 11 X-ray tube 15 Aperture 16 X-ray emission cone 17 Irradiation cylinder main body 18 Tube tip 19 Cylindrical base end 20 Support piece 21 Tube Body 22 X-ray axis 23, 24 Visible optical means 25, 26 Planar visible light 27, 27a Laser diode 31 Battery 32, 42 Sheet switch 33 Drive circuit 36 Incandescent lamp 37 Linear filament 49 Tube tip 50 Secondary aperture 56 Bolt 58, 59 Long hole 101 Cylindrical body 103 Medical position display device 104 Hollow part 105 Visible optical means 106 Light emitting diode 107 Cylindrical lens 119 Control means 120 Operation switch 121 Battery 128 Timer circuit

─────────────────────────────────────────────────── ───

[Procedure amendment]

[Submission date] November 11, 1993

[Procedure 3]

[Document name to be corrected] Drawing

[Correction target item name] Fig. 16

[Correction method] Change

[Correction content]

FIG. 16

[Procedure amendment 4]

[Document name to be corrected] Drawing

[Name of item to be corrected] Fig. 17

[Correction method] Change

[Correction content]

FIG. 17

[Procedure Amendment 5]

[Document name to be corrected] Drawing

[Name of item to be corrected] Fig. 20

[Correction method] Change

[Correction content]

FIG. 20

 ─────────────────────────────────────────────────── ─── Continuation of the front page (72) Creator Yoshihide Okagami 680, Higashihamananmachi, Fushimi-ku, Kyoto-shi, Kyoto Inside Morita Manufacturing Co., Ltd.

Claims (17)

[Scope of utility model registration request] 1. A medical X-ray device in which a radiation cone of X-rays emitted from an X-ray generator is regulated by an irradiation cylinder, wherein the irradiation cylinder is provided outside the radiation cone with a plurality of visible portions at intervals in the circumferential direction. An X-ray apparatus for medical use, comprising optical means, each visible optical means generating planar visible light including an axis of X-rays. 2. An X-ray generation unit, and an X from the X-ray generation unit.
An irradiation cylinder for controlling the radiation cone of the X-ray is attached, and the irradiation cylinder has visible optical means for illuminating the X-ray irradiation target with visible light to display the X-ray irradiation position. At least one of the parts
A medical X, which is provided on the outer periphery thereof and has a planar switch for controlling on / off of visible optical means.
Line device. 3. The X-ray generation unit is attached to an arm so as to be angularly displaceable about a rotation axis intersecting the X-ray axis, and the planar switch is one side of the X-ray axis direction with respect to the rotation axis. Or, it is arranged on both sides.
The medical X-ray device described. 4. The medical X-ray apparatus according to claim 1, wherein at least the tip of the irradiation tube is made of a translucent material. 5. The medical X-ray apparatus according to claim 1, wherein a tip of the irradiation tube is removable. 6. The medical X-ray apparatus according to claim 1, wherein the irradiation cylinder is attached to the X-ray generation unit so as to be angularly displaceable around the X-ray axis. 7. A cylindrical body for guiding a radiation cone of X-rays, and a plurality of visible optical means provided on the cylindrical body outside the radiation cone and arranged at intervals in the circumferential direction of the cylindrical body. An irradiating tube characterized in that each visible optical means generates planar visible light including an X-ray axis. 8. A cylindrical body that draws a radiation cone of X-rays, and X-rays that are provided on the cylindrical body and are irradiated with visible light to an X-ray irradiation target.
An irradiation tube, comprising: a visible optical means for displaying a line irradiation position; and a planar switch provided on the outer periphery of the cylindrical body for controlling ON / OFF of the visible optical means. 9. The irradiation cylinder according to claim 7, wherein at least the tip of the cylinder is made of a translucent material. 10. The irradiation cylinder according to claim 7, wherein a battery for supplying electric power to the visible optical means is built in the cylindrical body, and the irradiation cylinder is attachable to and detachable from the X-ray generator. 11. A tube tip is detachably provided at a tube base end of a tube for guiding a radiation cone of X-rays, and a support piece projecting forward from an end of the tube base end on the irradiation target side is fixed. This support piece is supported so that the tip of the cylinder is mounted on the end of the base end of the cylinder, and the protruding length of the support piece is between the X-ray tube focus and the irradiation surface of the irradiation target. An irradiation tube characterized in that the allowable distance SSD of is selected to be a value that is secured. 12. A cylindrical body having a hollow portion that allows invisible electromagnetic waves to pass therethrough, and a plurality of visible optical means provided on the cylindrical body so as to surround the hollow portion of the cylindrical body and be spaced apart in the circumferential direction. The medical position display device, wherein each visible optical means generates planar visible light including the axis of the invisible electromagnetic wave. 13. The medical position according to claim 12, wherein each visible optical means includes a light source that emits visible light and a lens that condenses the visible light from the light source into a planar shape. Display device. 14. The medical position display device according to claim 13, wherein the planar visible light intersects with an axis of the invisible electromagnetic wave as an intersection. 15. The medical position display apparatus according to claim 13, wherein the planar visible light is orthogonal to the axis of the invisible electromagnetic wave as an intersection. 16. An operating switch for turning on / off each light source is provided on the outer periphery of the cylindrical body, and when the operating switch is turned on, each light source is turned on for a predetermined time. The medical position display device according to claim 13. 17. The medical position display device according to claim 13, wherein each light source is a light emitting diode.