KR20170112777A - Portable x-ray generating apparatus having field emission x-ray source - Google Patents

Abstract

Disclosed is a portable X-ray generator having a field emission X-ray source having a structure that is advantageous in downsizing and lightweight, and has excellent insulation stability. The portable X-ray generator according to the present invention includes: a field emission X-ray source for emitting an X-ray toward a forward direction; An X-ray emission cone having a cone shape whose diameter gradually increases toward the front and which is disposed in front of the X-ray emission point of the field emission X-ray source and controls the emitted X-rays in the form of an X-ray beam in a predetermined angle range; And a driving circuit unit for generating a driving voltage of the field emission X-ray source using a direct current or an AC power source, wherein the driving circuit unit is disposed below the X-ray emitting cone, And at least one printed circuit board disposed such that an outer wall of the lower portion of the X-ray emitting cone is inclined at an angle equal to or greater than an inclined angle.

Description

Field of the Invention [0001] The present invention relates to a portable X-ray generator having a field emission X-ray source,

Field of the Invention [0002] The present invention relates to a portable X-ray generator, and more particularly, to a portable X-ray generator suitable for intra-oral X-ray imaging in a dental clinic, which is miniaturized using a field emission X-ray source.

X-ray imaging is a radiography method using the straightness and damping property of an X-ray, and provides an X-ray image of the internal structure of the object to be imaged based on accumulated X-ray attenuation during the process of transmitting the object. An X-ray imaging apparatus includes an X-ray generator for irradiating an X-ray toward an object to be imaged, an X-ray sensor for detecting an X-ray passing through an object to be imaged arranged opposite to the object, And an image processing device that implements a gray level x-ray image of the internal structure of the photographing area with projection data.

In recent years, X-ray imaging has rapidly been replaced by DR (Digital Radiograhpy) using digital sensors due to the development of semiconductor and information processing technologies. For example, intraoral x-rays taken mainly in the field of dentistry. Oral X-ray imaging is an X-ray imaging technique for acquiring X-ray images of a limited area of the subject's mouth. An X-ray sensor is placed inside the oral cavity of the subject and X-rays are emitted from the X- Obtain an x-ray image of the tissue. Such intraoral X-ray images have advantages such as low distortion, excellent resolution and sharpness, and relatively low radiation exposure, and thus they are mainly used for implant treatment or root canal treatment requiring high resolution. In order to improve the convenience and accuracy of the intraoral x-ray imaging and to improve the utilization thereof, it is required to reduce the weight and size of the x-ray emitting device.

Recently, field emission X-ray sources using nanostructures such as carbon nanotubes (CNTs) have been studied for miniaturization of X-ray emitting devices. An X-ray source using carbon nanotubes is an electric field emission type, and differs from a conventional tungsten filament-based X-ray source device by its electron emission mechanism. Since the carbon nanotube-based X-ray source can emit electrons with a relatively low voltage and the emitted electrons are emitted along the longitudinal direction of the carbon nanotubes, the directionality of electrons toward the X-ray target surface on the anode electrode side The X-ray emission efficiency is very high because it is excellent. In addition, it is easy to emit pulse-shaped X-rays, so it is possible to acquire an X-ray image at low dose, and also it is possible to shoot an X-ray movie, and thus it is very likely to be used for dental diagnosis, especially for intraoral x-ray imaging.

A field emission X-ray source known so far has an electron emitter disposed on a cathode electrode and a gate electrode disposed adjacent to the electron emitter in a vacuum container, And electrons are emitted by an electric field formed between the electron emission sources. The gate electrode has a metal plate shape in which a plurality of holes are arranged in a mesh shape or an arrangement of electron emission sources. When an electron beam emitted from an electron emitter passes through such a mesh structure or a plurality of holes, electrons are accelerated by several kV by an electric field formed between the anode and the cathode So that the X-ray is emitted from the X-ray target surface provided on the anode side. Further, a focusing electrode disposed around the electron beam traveling path between the cathode and the anode is provided to form an electric field for focusing the electron beam.

The field emission X-ray source has an advantage in miniaturizing and lightening the X-ray emitting device, but on the contrary, in a small-sized device, a potential difference as high as about 65 kV is formed between the anode and the cathode. In order to increase the insulation stability, it is possible to increase the insulation distance or to add an insulating structure, but this has a problem in that it may lead to downsizing and weight reduction.

SUMMARY OF THE INVENTION The present invention has been proposed in order to solve the above-mentioned problems. It is an object of the present invention to provide a field emission X-ray source having a structure which is advantageous in downsizing and lightweight, The object of the present invention is to provide a portable X-ray generator.

According to an aspect of the present invention, there is provided a portable X-ray radiating apparatus including: a field emission X-ray source for emitting X-rays toward a front side; An X-ray emission cone having a cone shape whose diameter gradually increases toward the front and which is disposed in front of the X-ray emission point of the field emission X-ray source and controls the emitted X-rays in the form of an X-ray beam in a predetermined angle range; And a driving circuit for generating a driving voltage of the field emission X-ray source using a direct current or an AC power source,

Wherein the driving circuit unit is disposed below the X-ray emitting cone and includes at least one X-ray emitting cone, at least one of which is arranged to be inclined at an angle greater than or equal to an inclined angle of an outer wall of the lower part of the X- Of the printed circuit board.

The driving circuit includes: a first driving circuit for generating a first driving voltage having a relatively low voltage; And a second driving circuit portion for generating a second driving voltage having a relatively high voltage, wherein a first printed circuit board constituting the first driving circuit portion can be disposed under the X-ray emitting cone.

The first driving circuit unit includes at least one step-up transformer to step up an input voltage to a gate driving voltage level of the field emission X-ray source. The step-up transformer is connected to the X- As shown in FIG.

The second driving circuit portion boosts the first driving voltage supplied from the first driving circuit portion to an anode driving voltage level of the field emission X-ray source, and a part thereof is overlapped under the field emission X-ray source And a second printed circuit board disposed on the rear side.

In this case, the first printed circuit board and the second printed circuit board are disposed at different heights relative to the field emission X-ray source, and the first printed circuit board is positioned at a relatively higher position than the second printed circuit board .

According to an aspect of the present invention, there is provided a portable X-ray radiating apparatus comprising: a field emission X-ray source; An X-ray emitting cone for forming an X-ray beam emitted from the field emission X-ray source in a predetermined angle range; And an x-ray source driving assembly including at least one printed circuit board for fixing the x-ray source and supplying voltage to the x-ray source,

The X-ray source driving assembly allows a high-voltage printed circuit board, which supplies a voltage to the electrodes of the field emission X-ray source, to be positioned behind the X-ray beam emitting direction.

Herein, the emission of the X-ray beam may be at a predetermined angle with the plane of the X-ray source driving assembly.

The electrode of the field emission X-ray source may be an anode electrode, and a high voltage that has been stepped up by at least two stages may be input to the anode electrode.

The high-voltage printed circuit board may include a step-up unit including a plurality of diodes and a plurality of capacitors.

The high voltage printed circuit board may include a first driving circuit portion that is stepped up to a gate driving level of the field emission X-ray source and a second driving circuit portion that is stepped up to an anode driving level of the field emission X-ray.

In this case, the field emission X-ray source may be located closer to the second driving circuit than the first driving circuit. The first driving circuit portion and the second driving circuit portion may be disposed on different planes. The second driving circuit portion may be surrounded by the insulating filler more than the first driving circuit portion.

According to the present invention, a field emission X-ray source driven by a high voltage of several tens kV is employed, and a portable X-ray generator having a field emission X-ray source having a structure that is advantageous in downsizing and light weight and excellent in insulation stability is provided.

The lightweight and compact portable X-ray emitting device with efficient space utilization and ergonomic weight distribution and insulation stability enhancement structure helps to reduce fatigue of X-ray image photographer and improves operation accuracy. Not only has an effect of improving the accuracy, but also has an effect of improving the lifetime of the device.

1 shows an internal structure of a portable X-ray emitting apparatus according to an embodiment of the present invention.
2 shows an internal structure of a portable X-ray radiating apparatus according to an embodiment of the present invention.
FIG. 3 shows an example of an x-ray source driving assembly in the embodiment of FIG. 1 or FIG.
4 is an exploded perspective view showing the X-ray source driving assembly of FIG. 3 in an opposite direction.
5 is a perspective view showing the X-ray source driving assembly of FIG. 3 in an opposite direction.
6 shows the internal structure of the portable X-ray radiating apparatus according to the embodiment of FIG. 2 in terms of weight distribution.

Hereinafter, various embodiments of the present invention will be described with reference to the drawings. The technical idea of the present invention can be understood more clearly by way of examples. It will be apparent to those skilled in the art that various modifications and variations can be made in the present invention without departing from the spirit or scope of the invention. something to do. The same reference numerals denote elements having the same characteristics, and description of elements having the same reference numerals as those described in the drawings may be omitted in the description of other drawings.

1 shows an internal structure of a portable X-ray emitting apparatus according to an embodiment of the present invention.

The portable X-ray radiating apparatus 100 according to the present embodiment includes a body 11 having a field emission X-ray source 40 installed therein, a cylindrical collimator 12 disposed in front of the body 11, And a grip portion 13 disposed under the body portion 11. A trigger switch 14 may be disposed on the upper portion of the handle 13 and a rechargeable battery pack 15 may be disposed below the handle 13. The portable X-ray radiating apparatus 100 according to the present embodiment may take the form of reminding a hair dryer or an electric drill as a whole.

The field emission X-ray source 40 is not installed in the body part 11 but is disposed in a frame forming the X-ray source driving assembly 50. The field emission X-ray source 40 has a cylindrical shape in a simplified form, and is laid out in a direction perpendicular to the plane of the drawing. In other words, the field emission X-ray source 40 of a cylindrical shape is arranged in the transverse direction in the forward direction (left side of the drawing) in which the X-ray beam XB is emitted. Hereinafter, the direction in which the X-ray beam is emitted from the field emission X-ray source 40 to the outside will be referred to as forward, and the opposite direction will be referred to as rearward.

The X-ray source accommodating portion 51 in which the field emission X-ray source 40 is installed may be formed in a partial cylindrical shape corresponding to the outer circumferential surface of the field emission X-ray source 40 in the above-described frame. The X-ray source driving assembly 50 includes a first driving circuit portion 52 extending obliquely downward from the X-ray source accommodating portion 51 and a second driving circuit portion 52 extending obliquely rearward and upward from the lower side of the X- 2 driving circuit portion 53. [ A first printed circuit board 521 constituted by a first step-up circuit including a first step-up transformer 522 is disposed in the first drive circuit part 52. The second drive circuit part 53 includes a plurality of diodes a second printed circuit board 531 provided with a secondary up-converter 532 including a diode and a capacitor is disposed. The field emission X-ray source 40 may be disposed on the second printed circuit board 531 in an overlapping manner.

The frame constituting the outer shape of the X-ray source driving assembly 50 surrounds an upper portion and a side surface of the frame, and the lower portion thereof is formed in an open shape. The first printed circuit board 521 and the second printed circuit board 531, And the periphery of the field emission X-ray source 40 are filled with an insulating filler to form insulating molding parts 51B, 52B and 53B as indicated by shaded areas in the drawing. Although not shown in the drawing, a window may be formed at a position where the X-ray is emitted forward in the X-ray source accommodating portion 51 to expose a part of the field emission X-ray source 40. In addition, the surface of the field emission X-ray source 40 is surrounded by an X-ray shielding layer except for the portion corresponding to the window, so that unintentional X-ray emission does not occur.

An X-ray emitting cone (60) is disposed in front of the field emission X-ray source (40) between the X-ray source accommodating part (51) and the cylindrical collimating part (12). The x-ray emitting cone 60 is a cone-shaped structure formed of an x-ray shielding material or at least an x-ray shielding layer. The X-ray emitted from the field emission X-ray source 40 passes through the X-ray emitting cone 60 and becomes an X-ray beam having a predetermined irradiation range. The cylindrical collimation part 12 also has an X-ray shielding layer inside thereof to block the X-ray traveling in a direction not intended due to diffuse reflection and to control the irradiation range of the X-ray beam. It is of course also possible to provide an X-ray shielding member having a fixed or variable rectangular or linear opening in the cylindrical collimating unit 12 in order to control the shape of the X-ray beam as required.

Now, the inside of the body portion 11 of the portable X-ray radiating apparatus 100 according to the present embodiment will be examined in terms of space utilization and structure arrangement. The above-described X-ray emitting cone 60 is arranged so that the center line of the X-ray emitting cone 60 is aligned with the center line XB of the cylindrical collimating unit 12. As a result, the center line XB becomes the center line of the x-ray beam passing through them. The first driving circuit portion 52 is disposed under the X-ray emitting cone 60. The plane P to which the first printed circuit board 521 belongs is a horizontal plane including the center line XB, As shown in Fig. The angle? Is equal to or greater than the angle? Of the outer wall of the X-ray emitting cone 60 with respect to the center line XB. The first driving circuit portion 52 including the first printed circuit board 521 can be brought closer to the X-ray emitting cone 60 as the angle? Approaches the value of the angle? It is advantageous for efficient use of space. This means that it is advantageous to miniaturize the device.

This may be indicated by the X-ray drive assembly 50 having a predetermined angle with the center line XB of the X-ray emitting cone 60. This allows the field emission x-ray source 40 to be as close as possible to the first printed circuit board so as not to affect the surrounding electrical components, so that the predetermined x-ray emitting range and the x-ray drive assembly 50 are not interfered with. The characteristics of the field emission X-ray source 40 and the characteristics of the first driving circuit portion 52 and the second driving circuit portion 53 will be described in further detail. As described above, the field emission X-ray source 40 has a triode structure of a cathode electrode, a gate electrode, and an anode electrode. For example, a first driving voltage having a potential difference of about 5 to 10 kV is applied as a switching signal to the gate electrode based on a voltage applied to the cathode electrode, and a second driving voltage having a potential difference of about 65 kV is applied to the anode electrode A voltage is applied as an electron acceleration voltage. However, this driving voltage value is an example according to the tube voltage standard of the medical X-ray radiating device, and the present invention is not limited thereto.

The first driving circuit portion 52 functions as a primary boosting portion and the second driving circuit portion 52 functions as a secondary boosting portion. The first driving circuit portion 52 primarily boosts a predetermined DC power or AC power converted through the inverter circuit to generate a first driving voltage of about 5 to 10 kV, for example. To this end, the first driving circuit part 52 includes a first printed circuit board 521 on which a first step-up transformer 522 is mounted. The first printed circuit board 521 is provided with an electrode pattern for connecting various other parts with the first printed circuit board 521 to constitute a circuit. Among them, the largest volume and weight are the primary boost transformer 522, that is, a transformer )All. The electrode portion near the substrate in the first step-up transformer 522 is covered with the electrode pattern on the first printed circuit board 521 and the low-height elements by the insulating filler forming the insulating molding portion 52B , And the upper portion thereof is exposed to the outside of the insulating molding part 52B.

The first driving voltage generated by the first driving circuit portion 52 is provided as a switching signal to the gate electrode of the field emission X-ray source 40, and the second driving voltage is supplied to the gate electrode of the field emission X- And is also provided in the drive circuit portion 53. The second printed circuit board 531 included in the second driving circuit unit 53 is provided with a secondary step-up unit 532 including a plurality of diodes and capacitors. The secondary boosting unit 532 may be configured as an n-times voltage rectifying circuit or a nocouple voltage rectifying circuit for boosting the input voltage to a voltage of n times. This rectifier can simultaneously increase the first driving voltage to a second driving voltage of about 65 kV, which is the anode electrode driving voltage of the field emission X-ray source 40. The second driving voltage thus boosted is supplied from the output terminal on the second printed circuit board 531 to the anode electrode of the field emission X-ray source 40 arranged close to the upper side. Most of the elements constituting the second printed circuit board 531 and the second step-up part 532 are buried in the insulating filler to form another insulating molding part 53B. As described above, the second driving circuit portion 53 covers a voltage of several tens kV, which is relatively higher than that of the first driving circuit portion 52 described above. Therefore, it is preferable that the second driving circuit portion 53 is completely covered with the insulating filler for improving the insulation stability and lifetime.

The portable X-ray radiating apparatus 100 according to the present embodiment has a first driving circuit 52 for generating a relatively low voltage and a driving circuit for generating a driving signal for driving the field emission X- A second driving circuit portion 53 for dealing with a high voltage and a deeper insulating molding portion 53B on the side of the second driving circuit portion 53 which requires a more stable insulation performance and the first driving circuit portion 52, A shallow insulation molding part 52B covering the first printed circuit board 521 and its electrode pattern is formed to reduce the weight increase due to the insulating filler.

In view of miniaturization of the portable X-ray radiating device 100, the first driving circuit portion 52 provided with the first booster transformer 522, which is a relatively bulky component, is moved toward the front of the field emission X-ray source 40 And the angle of the first printed circuit board 521 is inclined along the outer angle of the X-ray emitting cone 60 to utilize the secured space below. In addition, the height of the first printed circuit board 521 and the second printed circuit board 531 with respect to the field emission X-ray source 40 are different from each other. However, the first printed circuit board 521 is arranged at a relatively higher height But also to have more space underneath.

2 shows an internal structure of a portable X-ray radiating apparatus according to an embodiment of the present invention.

The portable X-ray radiating apparatus 101 according to the present embodiment includes all the configurations of the portable X-ray emitting apparatus 100 according to the embodiment of FIG. 1, specifically, the configuration of the X-ray source driving assembly 50. Therefore, redundant description will be omitted here, and only the added configuration will be described.

The apparatus 101 according to the present embodiment includes a bracket structure 58 erected by avoiding the X-ray emitting cone 60 on the frame of the above-described X-ray source driving assembly 50 and a third bracket frame 58 fixed to the bracket structure 58. [ And may further comprise a printed circuit board (54). The third printed circuit board 54 may include an inverter circuit for converting the power supplied from the battery pack 15, which is a DC power source, into AC. No separate insulation molding is required for the third printed circuit board 54.

In this embodiment, a fourth printed circuit board 55 may be disposed behind the x-ray source driving assembly 50. The fourth printed circuit board 55 may include a control circuit connected to a control panel 56 including a user operation interface 57 to display an operation state of the device and to control operation modes and the like. Although not shown, the fourth printed circuit board 55 may also be coupled to the frame of the x-ray source driving assembly 50 through a bracket structure. However, it is also possible that the fourth printed circuit board and the control panel are disposed on the third printed circuit board 54 or on the side surface of the body 11.

FIG. 3 shows an example of an x-ray source driving assembly in the embodiment of FIG. 1 or FIG.

This figure shows the x-ray source driving assembly 50 described with reference to Fig. 1 as viewed from the upper rear side thereof. There is an X-ray source accommodating portion 51 in the center, and a window 511 opened toward the front is shown in the center. One side of the X-ray source accommodating portion 51 is provided with a heat radiating portion 411 protruding out of the frame 50F for discharging the heat generated from the anode electrode of the field emission X-ray source disposed inside thereof to the outside . The heat dissipation unit 411 may be formed of a ceramic material that is electrically insulative and has excellent thermal conductivity. In the X-ray source driving assembly 50, the frame 50F is formed of a synthetic resin material so as to surround the upper and side surfaces except for the window 511 and the heat dissipating unit 411, and to open the lower surface of the frame 50F .

4 is an exploded perspective view showing the X-ray source driving assembly of FIG. 3 in an opposite direction.

In this figure, an insulating filler for an insulating molding is not shown to help understand the internal structure of the frame 50F. As described above with reference to FIG. 1, the portion corresponding to the first driving circuit portion 52 in the frame 50F is relatively shallower and the portion corresponding to the second driving circuit portion 53 is formed relatively deeper do. In addition, the X-ray source accommodating portion 51 is formed deeper inside the portion corresponding to the second driving circuit portion 53. A plurality of boss structures 523 for fixing and fixing the first printed circuit board 521 are provided inside the first driving circuit portion 52 in the frame 50F, A plurality of boss structures 533 for seating and fixing the printed circuit board 531 are provided. Although not shown, a three-dimensional structure for supporting a part of the field emission X-ray source 40 may be provided in the X-ray source accommodating portion 51 as well. The plurality of boss structures 523 and 533 described above are formed such that when the first printed circuit board 521 is fixed and the insulating filler in a fluid state is injected in a state where the second printed circuit board 531 is fixed , A space is formed so that both surfaces of the first and second printed circuit boards (521, 531) are filled with an insulating filler.

As the insulating filler, for example, an epoxy resin may be used. The first printed circuit board 521 and the second printed circuit board 531 and the field emission X-ray source 40 are arranged in a space inside the above-described frame 50F in a state where they are interconnected with each other, Epoxy resin is injected. The insulating molding portions 52B and 53B are formed when epoxy resin, which is an insulating filler, is filled and hardened at an intended depth according to the height of the sidewall of the portion respectively accommodating them in the frame 50F.

5 is a perspective view showing the X-ray source driving assembly of FIG. 3 in an opposite direction.

As shown in the drawing, the insulating molding portion 52B in the first driving circuit portion 52 is formed to have a shallow depth enough to cover the both surfaces of the first printed circuit board and the small-sized elements mounted on the surface of the first printed circuit board, The electrode portion of the secondary step-up transformer 522 is submerged in the insulating molding portion 52B, and a portion of the opposite side is exposed to the outside. On the other hand, the insulating molding part 53B in the second driving circuit part 53 is formed deep enough to lock the second printed circuit board 531 shown in FIG. 4 and the second step-up part 532 mounted on the second printed circuit board 531 . As shown in the drawing, the depths of the insulating molding parts 52B and 53B may be different depending on the sidewall height of the corresponding part of the frame 50F. In other words, the side walls surrounding the second driving circuit portion 53 in the frame 50F can be formed to be relatively higher from the respective bottom surfaces than the side walls surrounding the first driving circuit portion 52.

6 shows the internal structure of the portable X-ray radiating apparatus according to the embodiment of FIG. 2 in terms of weight distribution.

The portable X-ray radiating apparatus 101 according to the present embodiment is designed so that the user can grasp the handle 13 by grasping the handle 13 with the hand H held by the user. According to the present embodiment, not only the main parts are lightened but also the device itself can be balanced even if no extra force is applied through proper weight distribution of the front / rear, top / bottom, left / right. It is also one of the technical features of the present invention that the arrangement of the components in consideration of the weight distribution does not go against the downsizing of the apparatus.

There are limitations on the placement of the components in the device, which are the distance from the focal spot where the x-ray beam is emitted to the time the x-ray beam is emitted outside the device, i.e. the distance from the front end of the above- The distance D to the central part of the emitting X-ray source 40 should be secured to 200 mm or more. The cylindrical collimating unit 12 shields the uncontrolled x-ray beam from being emitted from the inside thereof to the outside and emits x-rays emitted from the cylindrical collimating unit 12 and the field emission x- The cone 60 also includes a x-ray shielding layer made of x-ray shielding material such as lead or bismuth oxide since it serves to control the x-rays emitted in a wide range in a beam shape of a certain angle range. This x-ray shielding layer is a factor of increasing the weight of the component.

The cylindrical collimating unit 12 and the X-ray emitting cone 60 are positioned forward when viewed from the center line HP of the handle 13. And a part thereof which is balanced with the weight of the second printed circuit board 531 is an insulating molding part 53B in which the second printed circuit board 531 is embedded. This is because a large number of diodes and capacitors as well as the insulating fill that fills them are heavy. Of course, since the field emission X-ray source 40 itself is constituted by a metal electrode and a ceramic spacer, it functions as a weighting portion behind the center line HP.

On the other hand, the first step-up transformer 522 is another component that is heavy in weight. This is because a large amount of copper wire is wound around the primary step-up transformer 522. According to the present embodiment, the primary step-up transformer 522 can be disposed at a position where the center line HP of the handle 13 passes. As a more specific example, the center of gravity 522C of the primary step-up transformer 522 may be disposed on the center line HP. The battery pack 15 may be disposed at a position below the handle 13 at a position where the center line HP of the handle 13 passes. It is advantageous that the parts that occupy a high proportion of the weight of the apparatus are easily balanced on or near the center line HP of the grip 13 gripped by the user's hand H, On the other hand, since the inverter circuit, the control circuit, and the like described above are relatively light in weight, they may be disposed somewhat farther from the center line HP.

11:
12: Cylindrical collimating part 13: Handle part
14: Trigger type switch 15: Battery pack
40: Field emission X-ray source 411:
50: X-ray source driving assembly 51: X-ray source accommodating part
52: first driving circuit part 521: first printed circuit board
522: primary boost transformer 53: second drive circuit part
531: second printed circuit board 532: second boosting unit
54: third printed circuit board 55: fourth printed circuit board

Claims (14)

A field emission x-ray source emitting x-rays toward the front;
An X-ray emission cone having a cone shape whose diameter gradually increases toward the front and which is disposed in front of the X-ray emission point of the field emission X-ray source and controls the emitted X-rays in the form of an X-ray beam in a predetermined angle range; And
And a driving circuit for generating a driving voltage of the field emission X-ray source by using a direct current or an AC power,
The driving circuit unit includes:
And at least one printed circuit board disposed below the X-ray emitting cone and arranged to be inclined at an angle greater than or equal to an inclined angle of the outer wall of the lower portion of the X-ray emitting cone with respect to a horizontal plane including a center line of the X- Including,
Portable x-ray emitting device. The method according to claim 1,
The driving circuit unit includes:
A first driving circuit for generating a first driving voltage having a relatively low voltage; And
And a second driving circuit portion for generating a second driving voltage having a relatively high voltage,
Wherein the first printed circuit board constituting the first driving circuit portion is disposed below the X-ray emitting cone,
Portable x-ray emitting device. 3. The method of claim 2,
Wherein the first driving circuit portion includes at least one step-up transformer to step up an input voltage to a gate driving voltage level of the field emission X-ray source,
Wherein the step-up transformer is mounted on the opposite side of the X-ray emitting cone in the first printed circuit board,
Portable x-ray emitting device. The method of claim 3,
The second driving circuit part boosts the first driving voltage supplied from the first driving circuit part to an anode driving voltage level of the field emission X-ray source, and partly overlaps under the field emission X- A second printed circuit board,
Portable x-ray emitting device. 5. The method of claim 4,
Wherein the first printed circuit board and the second printed circuit board are disposed at different heights relative to the field emission X-ray source, and the first printed circuit board is disposed at a relatively higher position than the second printed circuit board,
Portable x-ray emitting device. In a portable portable x-ray emitting apparatus,
Field emission X - ray sources;
An X-ray emitting cone for forming an X-ray beam emitted from the field emission X-ray source in a predetermined angle range; And
And an x-ray source driving assembly including at least one printed circuit board for fixing the x-ray source and supplying voltage to the x-ray source,
Wherein the X-ray source driving assembly has a high-voltage printed circuit board positioned behind the X-ray beam emitting direction for supplying a voltage to an electrode of the X-
Portable x-ray emitting device. The method according to claim 6,
Wherein the emission of the x-ray beam is at an angle to the horizontal plane of the x-
Portable x-ray emitting device. The method according to claim 6,
Wherein the electrode of the field emission X-ray source is an anode electrode,
Portable x-ray emitting device. 9. The method of claim 8,
Wherein the anode electrode is supplied with a high voltage that has been stepped up by at least two steps,
Portable x-ray emitting device. 9. The method of claim 8,
Wherein the high voltage printed circuit board includes a step-up portion composed of a plurality of diodes and a plurality of capacitors,
Portable x-ray emitting device. The method according to claim 6,
Wherein the high voltage printed circuit board includes a first driving circuit portion for stepping up to a gate driving level of the field emission X-ray source and a second driving circuit portion for stepping up to an anode driving level of the field emission X-
Portable x-ray emitting device. 12. The method of claim 11,
Wherein the field emission X-ray source is located closer to the second driving circuit than the first driving circuit,
Portable x-ray emitting device. 12. The method of claim 11,
Wherein the first driving circuit portion and the second driving circuit portion are located on different planes,
Portable x-ray emitting device. 12. The method of claim 11,
And the second driving circuit portion is surrounded by more insulating filler than the first driving circuit portion,
Portable x-ray emitting device.

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