阅读说明：本技术 旋转型模块结合型离子发生器 (Rotary module combined ion generator ) 是由 李东勋 李炳俊 孙康荣 朴进哲 于 2021-05-21 设计创作，主要内容包括：本发明的旋转型模块结合型离子发生器的特征在于,包括：主体,所述主体在内部形成一个以上的收纳空间,形成与所述收纳空间连通的插入槽；X射线管模块,所述X射线管模块插入于所述主体的收纳空间,且包括具有第一连接器的第一接线插座、与所述第一连接器电气连接的X射线管；旋转体,所述旋转体在所述主体的收纳空间一侧形成,能以旋转轴为中心旋转地结合；及第二接线插座,所述第二接线插座结合于所述旋转体,能借助于所述旋转体的旋转而旋转,包括向所述第一连接器传递电源的第二连接器；所述第二接线插座在所述主体外侧结合于所述X射线管模块的第一接线插座,所述第一连接器导电接触所述第二连接器后,所述旋转体随着旋转所述X射线管模块而旋转,所述X射线管模块容纳于所述收纳空间。(The rotary module combined ionizer of the present invention is characterized by comprising: a main body having one or more receiving spaces formed therein and an insertion groove formed therein to communicate with the receiving spaces; an X-ray tube module inserted into the receiving space of the main body and including a first connection socket having a first connector, and an X-ray tube electrically connected to the first connector; a rotating body formed on one side of the housing space of the main body and coupled to be rotatable about a rotation axis; and a second connection socket coupled to the rotating body, rotatable by rotation of the rotating body, and including a second connector for transmitting power to the first connector; the second connection socket is in the main part outside combine in the first connection socket of X ray tube module, first connector electrically conductive contact behind the second connector, the rotator is along with the rotation the X ray tube module rotates, the X ray tube module hold in take-up space.)

1. A rotary module-combined ionizer, comprising:

a main body having one or more receiving spaces formed therein and an insertion groove formed therein to communicate with the receiving spaces;

an X-ray tube module inserted into the receiving space of the main body and including a first connection socket having a first connector, and an X-ray tube electrically connected to the first connector;

a rotating body formed on one side of the housing space of the main body and coupled to be rotatable about a rotation axis; and

a second connection socket coupled to the rotating body, rotatable by rotation of the rotating body, and including a second connector for transmitting power to the first connector;

the second connection socket is in the main part outside combine in the first connection socket of X ray tube module, first connector electrically conductive contact behind the second connector, the rotator is along with the rotation the X ray tube module rotates, the X ray tube module hold in take-up space.

2. The rotary module combined ionizer according to claim 1,

in the body, an anti-collision groove is formed at a side surface of the insertion groove so that the X-ray tube module does not collide with the body when being coupled to the second connection socket at an outer side.

3. The rotary module combined ionizer according to claim 1,

a portion of the second connection receptacle can be projected outside the insertion groove by means of rotation.

4. The rotary module combined ionizer according to claim 1,

a cylindrical electrode portion having an empty interior is formed in the first connection socket, a fixing protrusion for fixing the electrode portion is formed, a groove is formed around the fixing protrusion, an outer protrusion surrounds the groove,

the second socket has a projection formed around a pin-shaped second connector, the pin-shaped second connector of the second socket is inserted into a cylindrical electrode portion having a hollow interior of the first socket, and the projection of the second socket is inserted into the recess of the first socket, thereby sufficiently securing a creepage distance as a distance between a contact point of the electrode portion and the second connector and an outer surface of the metal body.

5. The rotary module combined ionizer according to claim 4,

the second connector and the electrode portion are horizontally disposed along a longitudinal direction of the main body when the X-ray tube module is accommodated in the accommodation space.

6. The rotary module combined ionizer according to claim 1,

the rotating body is a hinge type rotatable about a rotation axis.

Technical Field

The present invention relates to a rotary module-combined type ionizer, and more particularly, to a rotary module-combined type ionizer formed in a structure in which an X-ray tube module is easily attached and detached.

Background

In general, in the manufacturing process of LCD, semiconductor, etc., a static eliminator is installed to prevent the adhesion of fine dust to LCD or semiconductor wafers, or the damage of elements due to static electricity.

The static electricity removing apparatus is roughly classified into a corona discharge type apparatus and an X-ray radiation type apparatus, and recently, an X-ray radiation type apparatus, i.e., an X-ray Ionizer (X-ray Ionizer), is mainly used, which overcomes the disadvantages of the corona discharge type apparatus, such as a sputtering phenomenon caused by high voltage discharge, generation of ozone, inconvenience in ion balance adjustment, and the like.

An X-ray ionizer is a device that generates and irradiates X-rays (X-rays) to ionize gas molecules and neutralize static electricity on the surface of an object to be neutralized, and is mainly embodied by irradiating Soft X-rays (Soft X-rays). Such an X-ray ionizer is not generating fine dust and not requiring convection of air, and thus has attracted much attention and been developed in various forms.

Korean patent No. 10-1656781 entitled "X-ray ionizer for easy replacement of X-ray tube" is a patent that was filed on 5/2016 and granted on 6/2016/9/2016 by the present applicant, and relates to an X-ray ionizer for easy replacement of X-ray tube, comprising: the X-ray tube module is used for placing a specially manufactured connecting bolt in a hanging mode; a voltage generating assembly formed to be detachable from the X-ray tube module; and a main body accommodating the voltage generating assembly therein; the X-ray tube module is easily detached from the voltage generating assembly accommodated in the main body by using the connecting bolt, so that the X-ray tube module has the effect of easily replacing only the X-ray tube as a consumable component without using a separate tool.

However, in the above-described technique, due to the limitation of the structure in which the X-ray tube module is simply vertically inserted into the voltage generating module, the second electrode portion in the X-ray tube module faces the vertical insertion direction, and not only is there a problem that a load is concentrated on the end surface portion of the second electrode portion due to the action of gravity, but also there is a disadvantage that it is difficult to secure a sufficient creeping distance necessary for preventing occurrence of creeping discharge when a high voltage is applied.

Korean laid-open patent No. 10-2020-0046850, which is directed to solving the problems of the prior art, discloses an X-ray ionizer that an X-ray tube is easily disassembled and assembled and that ensures a safe distance for discharging, which is a patent that the applicant filed 2018 on 26/10 and 2020 on 5/7, relates to an X-ray ionizer that an X-ray tube is easily disassembled and assembled and that ensures a safe distance for discharging, and more particularly, to an X-ray ionizer that is formed in a structure in which an X-ray tube is easily disassembled and assembled and that ensures a sufficient creeping distance in order to prevent creeping discharge when a high voltage is applied, but due to the limitation of the construction in which the X-ray tube module slides inside the voltage generation assembly for bonding, when the X-ray tube module is assembled and disassembled, the connector part is difficult to be visually confirmed, so that the X-ray tube module is inconvenient to combine.

Documents of the prior art

[ patent document ]

(patent document 1) Korean patent No. 10-1656781 (2016, 9, 6/month)

(patent document 2) Korean laid-open patent publication No. 10-2020-0046850 (5/7/5/2020)

Disclosure of Invention

The present invention has been made to solve the above problems, and an object of the present invention is to provide a rotary module-coupled ionizer in which a second connection socket is coupled to a first connection socket of an X-ray tube module at an outer side of a main body, and then the X-ray tube module is rotated to be accommodated in an accommodation space, so that the main body and the X-ray tube are easily disassembled.

The object of the present invention is not limited to the above-mentioned object, and other objects not mentioned are clearly understood by those skilled in the art of the present invention from the following description.

Technical scheme

In order to achieve the above object, a rotary module-combined ionizer according to the present invention comprises: a main body having one or more receiving spaces formed therein and an insertion groove formed therein to communicate with the receiving spaces; an X-ray tube module inserted into the receiving space of the main body and including a first connection socket having a first connector, and an X-ray tube electrically connected to the first connector; a rotating body formed on one side of the housing space of the main body and coupled to be rotatable about a rotation axis; and a second connection socket coupled to the rotating body, rotatable by rotation of the rotating body, and including a second connector for transmitting power to the first connector; the second connection socket is in the main part outside combine in the first connection socket of X ray tube module, first connector electrically conductive contact behind the second connector, the rotator is along with the rotation the X ray tube module rotates, the X ray tube module hold in take-up space.

In addition, the body may be formed with an anti-collision groove on a side surface of the insertion groove so that the X-ray tube module does not collide with the body when the X-ray tube module is externally coupled to the second connection socket.

Further, it is characterized in that a part of the second connection receptacle can be projected outside the insertion groove by means of rotation.

Further, the first socket is provided with a cylindrical electrode portion having a hollow interior, a fixing projection for fixing the electrode portion is formed, a recess is formed around the fixing projection, an outer projection surrounds the recess, the second socket is provided with a projection around a needle-like second connector, the needle-like second connector of the second socket is inserted into the cylindrical electrode portion having a hollow interior of the first socket, and the projection of the second socket is inserted into the recess of the first socket, thereby sufficiently securing a creepage distance as a distance between a contact point of the electrode portion and the second connector and an outer surface of the metal body.

Further, the second connector and the electrode portion are horizontally arranged along a longitudinal direction of the main body when the X-ray tube module is accommodated in the accommodation space.

Further, the rotating body is of a hinge type rotatable about a rotation axis.

[ Effect of the invention ]

The rotary module combined ion generator of the invention can combine the second connection socket formed by a part protruding to the outside of the main body and the first connection socket of the X-ray tube module when the X-ray tube module is combined with the main body, and can be combined at the outside of the main body, when the module is assembled and disassembled, the connector part can be visually confirmed, thereby having the effect of easy assembly and disassembly.

In addition, a storage space is formed on one side of the main body, the rotary body rotatably mounted on one side of the storage space and a second connection socket formed by extending the rotary body are connected with the first connection socket of the X-ray tube module on the outer side, and the soft X-ray tube module is rotatably stored in the storage space, so that the module is easily assembled and disassembled on the outer side.

In addition, the needle-like second connector of the second socket is inserted into the hollow cylindrical electrode portion inside the first socket, and the projection of the second socket is inserted into the recess of the first socket, so that a sufficient creeping distance is secured as a distance between the contact point of the electrode portion and the second connector and the outer surface of the metal body.

Drawings

Fig. 1 is a perspective view illustrating a structure of a rotary module combined type ionizer according to the present invention.

Fig. 2 is an exploded perspective view of an X-ray tube module of the present invention.

Fig. 3 is an enlarged sectional view of a main part illustrating a relation before the X-ray tube module of the present invention is coupled to the rotary body.

Fig. 4 is an enlarged sectional view and an enlarged view of a main part illustrating a coupling relationship between the X-ray tube module and the rotary body according to the present invention.

Fig. 5 is a conceptual diagram showing the front and rear of the combination of the X-ray tube module and the rotator according to the embodiment of the present invention.

Fig. 6 is a conceptual diagram showing the front and rear of the combination of the X-ray tube module and the rotator according to another embodiment of the present invention.

Fig. 7 is a conceptual diagram illustrating a process in which the X-ray tube module of the present invention rotates and moves to the inside of the housing space.

Reference numerals

100X-ray tube module 110X-ray tube

120 first connection socket 121 fixing projection

122 groove 123 external protrusion

130 first connector 131 electrode part

200 main body 201 unit ion generator

205, a housing space 210, an insertion slot

211 anti-collision groove 300 rotating body

301 rotating shaft 310 insertion hole

320 second connection socket 321 projection

330: a second connector.

Detailed Description

The advantages and features of the invention and the methods of accomplishing the same will become apparent with reference to the following detailed description of the embodiments taken in conjunction with the accompanying drawings. However, the present invention is not limited to the embodiments disclosed below, and may be embodied in various forms different from each other, but the embodiments are provided to make the disclosure of the present invention more complete, and to fully inform the scope of the present invention to those skilled in the art to which the present invention pertains, and the present invention is defined only by the scope of the claims.

The details required for carrying out the present invention are described below with reference to the accompanying drawings. The same reference numerals refer to the same constituent elements and "and/or" includes all combinations of the items and one or more, regardless of the drawings.

Although the terms "first", "second", and the like are used to describe various components, it is needless to say that these components are not limited by these terms. These terms are only used to distinguish one constituent element from other constituent elements. Therefore, the first component mentioned below is within the technical idea of the present invention, and may be a second component.

The terminology used in the description is for the purpose of describing the embodiments and is not intended to be limiting of the invention. In this specification, the singular forms also include the plural forms as long as they are not specifically mentioned in the sentence. The use of "comprising" and/or "comprising" in the specification does not preclude the presence or addition of one or more other components in addition to the recited components.

Unless otherwise defined, all terms (including technical and scientific terms) used in the present specification may be used as meanings commonly understood by those skilled in the art to which the present invention belongs. In addition, generally used dictionary-defined terms should not be interpreted too much or excessively as long as they are not specifically defined.

Preferred embodiments of the present invention will be described in detail below with reference to the accompanying drawings.

Fig. 1 is a perspective view illustrating a structure of a rotary module combined type ionizer according to the present invention.

Referring to fig. 1, the rotary-type module-combined ionizer roughly includes an X-ray tube module 100, a main body 200, a voltage generating module (not shown), a rotary body 300, and a second connection socket 320.

First, the main body 200 has one or more receiving spaces 205 formed therein, and an insertion groove 210 communicating with the receiving spaces 205. In addition, the body 200 may be formed in a rod shape.

In fig. 1, as an example of the main body 200, if more specifically explained, a rod-like structure in which a plurality of X-ray tube modules can be attached in a length direction thereof is illustrated. However, the main body 200 may be formed in various length structures, for example, a length structure corresponding to the size of a single X-ray tube module, or the like, and the accommodation spaces 205 may be formed in various numbers corresponding to the length thereof. That is, the size of the main body 200 and the number of the storage spaces 205 corresponding to the number of modules that can be stored inside the main body 200 may be designed to have various specifications depending on various factors such as the environment in which electricity is removed.

Then, the X-ray tube module 100 is inserted into the receiving space 205 of the main body 200, and includes a first connection socket 120 having a first connector 130, and an X-ray tube 110 electrically connected to the first connector 130.

Then, the voltage generating module (not shown) may be formed in at least one or more of the main body 200, and in addition, not only inside the main body 200 but also outside the main body 200 may be provided. The voltage generating module is configured to generate a voltage by receiving a supply voltage from the outside, and may be configured in various specifications based on a capacity thereof according to various factors such as a discharge environment.

The rotating body 300 is formed on the side of the housing space 205 of the main body 200 and is coupled to be rotatable about a rotation axis. In addition, an insertion hole 310 formed with a groove into which the rotation shaft is inserted is included at one side. For the rotation axis, it will be described in more detail below.

Then, the second connection socket 320 is coupled to the rotating body 300, can rotate by the rotation of the rotating body 300, and includes a second connector 330 for transmitting power to the first connector 130. The second connector 330 may be electrically connected to at least one of the voltage generating modules provided in the main body 200. In addition, the second connector 330 may receive a transfer voltage from the voltage generation module through a voltage line.

The X-ray tube module 100 penetrates the lower portion of the main body 200, and is detachably mounted to the main body 200 by physically and electrically coupling the first and second connection sockets 120 and 320 to each other. That is, in a state of being coupled to each other, the voltage generated by the voltage generation module is transmitted to the X-ray tube 110 so that the X-ray for removing static electricity can be radiated, and if the X-ray tube 110 is old and requires replacement, the X-ray tube module 100 can be easily separated from the main body 200 and a replacement operation can be performed.

At this time, after the X-ray tube module 100 and the rotator 300 are coupled to each other at the outside of the insertion groove 210 by the first and second connection sockets 120 and 320, respectively, if the X-ray tube module 100 is rotated, the X-ray tube module is rotated by the rotator 300 and is accommodated in the accommodation space 205 in the main body 200. More detailed description will be described later.

In fig. 1, a plurality of unit ion generators 201 are inserted into the rod-shaped body 200, but it is needless to say that a voltage generation module (not shown), a rotary shaft 301, a second wire insertion port 320, and the like, which are constituent members of the unit ion generators 201, may be directly inserted into the rod-shaped body 200 without constituting the unit ion generators 201. The unit ionizer 201 may have the same structure as the main body 200, or may be formed in a single-product structure as the unit ionizer 201.

Fig. 2 is an exploded perspective view of an X-ray tube module of the present invention. As shown in fig. 2, the X-ray tube module 100 includes an X-ray tube 110 that generates and radiates soft X-rays, a first connector 130 connected to the X-ray tube 110 to transmit a voltage to the X-ray tube 110, as a basic configuration, and includes a support cover that surrounds and protects the X-ray tube 110 and supports the X-ray tube 110, and a first connector socket 120 that is slidably coupled to the support cover and supports and fixes the first connector 130.

The first connector 130 includes an electrode portion 131 selectively detachably connected to the second connector 330 and an X-ray tube electrode portion 132 connected to the X-ray tube 110.

The electrode portion 131 is inserted through a portion formed to protrude from the center portion of the inside of the first connection socket 120, and is mounted perpendicular to the central axis of the X-ray tube 110, and the X-ray tube electrode portion 132 has one end coupled to the upper portion of the X-ray tube in a horizontal direction and the other end disposed at the rear side of the first connection socket 120.

In this case, the other end of the X-ray tube electrode 132 is preferably bent downward and extended so as to be stably coupled to the electrode 131 by means of a medium such as a coupling bolt 133.

In other words, the first connector 130 is connected and fixed to the X-ray tube 110 via the first connection socket 120, the electrode portion 131 is disposed toward the front of the X-ray tube module 100, and the X-ray tube electrode portion 132 is attached to be able to contact and connect with the upper portion of the X-ray tube 110.

Fig. 3 is an enlarged sectional view of a main part illustrating a relation before the X-ray tube module of the present invention is coupled to the rotary body.

Referring to fig. 3, the body 200 is recessed at one side to form a receiving space 205 for the X-ray tube module 100 to be inserted, and a rotation shaft 301 is provided at one side of the receiving space 205.

A rotating body 300 is mounted, the rotating body 301 is inserted into an insertion hole 310 of the rotating body 300, the rotating body 300 is rotatably coupled to the rotating body 301, and a second socket 320 is provided, the second socket 320 being extended by being coupled to the rotating body 300 and rotated by the rotation of the rotating body 300.

In other words, an insertion hole 310 is formed at one side of the rotating body 300, the insertion hole 310 is inserted into the rotating shaft 301, and the rotating body 300 rotates around the rotating shaft 301.

Although the rotation of the rotating body 300 has been described above by taking the hinge system as an example, a rotation system using a ball bearing, a rotation system using a gear, a rotation system using a spring, or the like may be used.

On the inner side of the second connection socket 320, the second connector 330 physically combined with the first connector 130 and transmitting the voltage is installed, and the second connector 330 is fixed by the second connection socket 320.

The second connector 330 is connected to the voltage generation module (not shown) by a voltage line (not shown), and the voltage generated from the voltage generation module may be transferred to the second connector 330. It is preferable that the high voltage line is installed such that the second connector 330 and the second socket 320 can be freely rotated by the rotator 300.

In more detail, if the first and second wire sockets 120 and 320 are explained, the electrode part 131 is formed in the first wire socket 120 to have a cylindrical shape with a hollow inside, and the fixing protrusion 121 for fixing the electrode part 131 is formed. A groove 122 is formed around the fixing protrusion 121, and an outer protrusion 123 is formed around the groove 122.

The second connection socket 320 is formed with a projection 321 around the needle-shaped second connector 330.

Fig. 4 is an enlarged sectional view and an enlarged view of a main part illustrating a coupling relationship between the X-ray tube module and the rotary body according to the present invention.

Referring to fig. 3 to 4, the coupling relationship between the X-ray tube module 100 and the rotating body 300 will be described, and as shown in fig. 4, after the second connection socket 320 is coupled to the first connection socket 120 of the X-ray tube module 100 on the outside, the X-ray tube module 100 is rotated, and the X-ray tube module 100 is accommodated in the accommodating space 205.

The needle-like second connector 330 of the second socket 320 is inserted into the hollow cylindrical electrode portion 131 of the first socket 120, and the projection 321 of the second socket 320 is inserted into the recess 122 of the first socket 120. Therefore, a sufficient creepage distance can be secured as a distance between the contact point between the electrode portion 131 and the second connector 330 and the outer surface of the metal main body 200.

The minimum creepage distance is 32mm or more when the applied voltage value is 11.2kV based on the CEI IEC 60065 international standard, and the creepage distance, which is the distance between the contact point of the electrode portion 131 and the second connector 330 and the outer surface of the metal body 200, is 32mm at the minimum according to this standard.

In order to secure such a creepage distance, as shown in fig. 4, it is preferable that the distance between the contact point of the electrode portion 131 and the second connector 330 and the outer surface of the metal body 200 is formed to have a length structure that can be separated by a predetermined distance or more, based on the state where the first and second wire sockets 120 and 320 are completely coupled. That is, as shown in fig. 4, the electrodes may be formed to be spaced apart from each other by a predetermined distance with respect to the completely bonded state.

If more specifically explained, the first connector 130 and the second connector 330 of the present invention are formed in a socket structure, and due to the characteristic of such a socket structure, a plurality of projections are coupled by male and female insertion facing each other. Therefore, the circumferential length of the body increases corresponding to the number, width, etc. of the projections with respect to the same reference unit space, and therefore, the creeping distance, which is a distance that can guide the discharge, also increases.

That is, in the above-described socket structure, by changing the number of the projections, the width of each projection, and the like, it is possible to secure a creeping distance corresponding to the value of the applied voltage of the aforementioned international standard and the like.

As a specific example of this, a configuration of a length (width) of a periphery directly/indirectly coupled to the second connector 330 including the fixing protrusion 121, the recess 122, the external protrusion 123 of the first socket 120 and the protrusion 321 of the second socket 320 is changed, so that a creeping distance corresponding to an applied voltage value of an ionizer can be secured.

On the other hand, when the X-ray tube module 100 is accommodated in the accommodation space 205, the second connector 330 and the electrode portion 131 are horizontally arranged along the longitudinal direction (horizontal direction) of the main body 200.

This is because, when the main body 200 is embodied in a bar shape, the length of the long axis is much longer than the width due to the basic bar structure, and it is certainly much more advantageous in terms of space interference or space utilization to use the long axis of the main body 200 in order to secure the aforementioned creeping distance.

On the other hand, the coupling structure between the first connector 130 and the second connector 330 has been described by way of example in which the coupling between the electrode portion 131 and the second connector 330 is male-female, but a coupling structure using a wire-drawing spring, a coupling structure using a banana jack, a coupling structure using a leaf spring, or the like may be used.

Fig. 5 is a conceptual view showing before and after the X-ray tube module and the rotator according to the embodiment of the present invention are combined, and fig. 6 is a conceptual view showing before and after the X-ray tube module and the rotator according to another embodiment of the present invention are combined.

If referring to fig. 5 to 6, a portion of the second connection receptacle 320 may be protruded to the outside of the insertion groove 210 by means of rotation.

As shown in the drawing, in the ready state of the soft X-ray module 100, since a spatial interference occurs when the soft X-ray module and the connector are coupled in the width direction (vertical direction) of the bar as in the conventional art, in order to prevent this, it is preferable that the second connection socket 320 is disposed downward by a predetermined distance or more (protruding structure) than in the conventional art.

On the other hand, as shown in fig. 5 (a) or 6 (a), the maximum tilt angle of the second connection socket 320 may be variously changed within a range in which the soft X-ray module 100 can be coupled without interference outside the housing space 205 or the main body 200.

Fig. 7 is a conceptual diagram illustrating a process in which the X-ray tube module of the present invention rotates and moves to the inside of the housing space.

Therefore, after the rotary module-coupled ionizer including the above-described structure is coupled to the first and second connection sockets 120 and 320 of the soft X-ray module 100 outside the insertion slot 210, that is, the first and second connectors 130 and 330 are coupled to rotate the X-ray tube module 100, the X-ray tube module 100 is accommodated inside the accommodation space 205. This is because the rotary shaft 301 provided in the housing space 205 is rotatably coupled to the rotary body 300, and the first socket 120 is coupled to the second socket 320 extended from the rotary body 300.

As shown in fig. 7 (b), an anti-collision groove 211 is formed on a side surface of the insertion groove 210 so that the X-ray tube module 100 does not collide with the main body 200 at an outer side of the main body 200. The anti-collision groove 211 may be formed to be extended from or separated from the insertion groove 210. Preferably, the anti-collision groove 211 is formed by cutting a portion of the outer surface of the body 200 to extend from the insertion groove 210.

As shown in fig. 5 (b), when the X-ray tube module 100 is directed to the outside in a state of being connected to the second socket 320, a part of the X-ray tube module 100 is necessarily directed to the outside of the main body 200, and an interference phenomenon such as a collision occurs, and thus it is preferable to form an appropriate escape space portion and form the collision preventing groove 211 corresponding to the escape space portion.

Therefore, in the rotary module-coupled ionizer configured as described above, the second socket 320 is coupled to the first socket 120 of the X-ray tube module 100 on the outside of the main body 200, and after the first connector 130 is conductively contacted to the second connector 330, the rotary body 300 is rotated as the X-ray tube module 100 is rotated, so that the X-ray tube module 100 can be accommodated in the accommodation space 205.

After the X-ray tube module 100 is accommodated in the accommodation space 205, the X-ray tube module 100 may be coupled to the main body 200 by a bolt, or by various methods such as a knob, a hook, a locking ring, a ball, a magnet, a cam lock, a ball flange, a fixing pin, a compression tongue, and an additional screw. In addition, when disassembling, it is preferable to perform the processes in reverse order.

While the embodiments of the present invention have been described with reference to the drawings, it will be understood by those skilled in the art that the present invention may be embodied in other specific forms without departing from the spirit or essential characteristics thereof. The embodiments described above are therefore to be considered in all respects as illustrative and not restrictive.