KR101299297B1 - A computed tomosynthesis system including rotatable platform - Google Patents

Abstract

The present invention relates to a tomographic image synthesis system having a rotating platform. The present invention X-ray detector; A vacuum chamber spaced apart from the X-ray detector by a predetermined distance; A rotatable platform positioned between the x-ray detector and the vacuum chamber to accommodate a subject; A moving plate positioned under the X-ray detector, the vacuum chamber, and the platform, respectively, to support the X-ray detector, the vacuum chamber, and the platform; A moving shaft positioned below the moving plate to move the moving plate; And a unit X-ray source having one or more insulating pillars attached to the vacuum chamber and emitting X-rays.

Description

A computed tomosynthesis system including rotatable platform}

The present invention relates to a tomographic image synthesis system having a rotating platform, and more particularly, to one or more insulating pillars provided on a cathode electrode while fixing the subject to the platform and rotating the platform 360 degrees or at an angle. A tomography with a rotating platform capable of obtaining high quality radiographic two-dimensional tomography or three-dimensional reconstruction images by acquiring image information by capturing the subject with a small X-ray source in which the gate electrode and the focusing electrode are separated and fixed. An image synthesis system.

In general, the gantry used in the tomography imaging system is equipped with an X-ray tube, an X-ray detector, a temperature controller, a high pressure generator, a slip ring, and the like, and the gantry is rotated in such a state.

Such a gantry is capable of variable speed control at a constant speed, speed control up to a high speed range to obtain more image information per unit time, and a uniform speed quality is required.

However, the devices mounted in the tomography imaging system are made for different purposes, and the weights thereof are also different so that it is very difficult to mount them so as not to have an eccentricity on the gantry surface for the computer tomography device which forms a circle trajectory.

Therefore, a dummy weight may be used to balance the weight. In this case, there is a problem in that there is a limit in adjusting the gantry.

The conventional apparatus is described with reference to FIG.

As shown in FIG. 1, the conventional gantry rotatable X-ray micro-tomography apparatus fixes the subject 5 to a predetermined bed 6, and the X-ray source 1 and the detector 8 are the gantry rotating unit 2. It is mounted on the gantry rotating part 2 has a structure to scan while rotating. The gantry rotating part 2 and the gantry fixing part 3 are fastened by a bearing, and are structured to rotate the gantry rotating part by the gantry rotating motor 2.

At this time, the subject 5 is placed around the center of rotation of the gantry rotating unit, and the subject is enlarged and photographed according to the distance between the focus of the X-ray tube and the center of rotation (Iso Center) and the distance from the center of rotation to the detector. Scanning in the state results in a tomographic image having a spatial resolution of several micrometers to several tens of micrometers.

In certain situations, in order to acquire a tomographic image having a very high spatial resolution, it is necessary to shorten the distance from the center of rotation to the focal point of the X-ray tube and to increase the geometric magnification by slightly increasing the distance from the center of rotation to the detector. In order to achieve the above object, in the case of the gantry rotation type, the X-ray source and the detector may be attached to the linear motion device, and the magnification may be changed by controlling the motor.

However, in this case, if the X-ray source and the detector are moved in the radial direction of the gantry rotating part to obtain a high magnification, the weight of the X-ray source device does not balance the center of gravity of the gantry rotating part, resulting in precise rotational movement. Since this becomes difficult, a problem arises in that the resolution of the tomographic image becomes worse.

In addition, the rotation radius of the gantry increases according to the size and weight of the devices that the gantry face can support, making installation difficult and expensive, and there is a practical limit to the size and weight of the equipment that can be installed on the gantry face. There is.

In addition, the tomography imaging system having an eccentric load has a problem in that the rotation of the gantry surface is limited because the speed ripple is large when the driving speed is increased.

In addition, the method of removing the eccentric load component by hand in the manufacturing step of the gantry is effective up to a certain level, but there is a problem that it is difficult to adjust the degree to reduce the speed ripple to zero in the normal state.

Therefore, the present inventors have a simpler structure, can easily adjust the positions of the various electrodes used in the unit X-ray source and the spacing between the electrodes, and can easily control the trajectory of the emitted electrons. It has also led to the invention of a tomographic image synthesis system having a manufacturable rotating platform.

The present invention has been made to solve the above-described problems, an object of the present invention is to rotate to shoot a two-dimensional X-ray image for each angle of the subject while fixing the subject to the platform, while rotating the platform by an angle To provide a tomographic image synthesis system with a platform.

The present invention also provides a tomographic image synthesis system having a rotating platform that can adjust the position, angle and height of the vacuum chamber, platform, and x-ray detector.

In addition, high-quality radiation 2D tomography and 3D are obtained by photographing a subject with a small X-ray source in which a gate electrode and a focusing electrode are separated and fixed through one or more insulating pillars provided on the cathode electrode. The present invention provides a tomographic image synthesis system capable of acquiring a reconstructed image.

Tomographic image synthesis system according to the present invention, the X-ray detector; A vacuum chamber spaced apart from the x-ray detector; A rotatable platform positioned between the x-ray detector and the vacuum chamber to accommodate a subject; A plurality of moving plates positioned under the X-ray detector, the vacuum chamber, and the platform, respectively, to support the X-ray detector, the vacuum chamber, and the platform; A moving shaft of the moving plate positioned below the moving plate; And a unit x-ray source having one or more insulating pillars attached to the vacuum chamber and emitting X-rays.

In addition, the tomography image synthesis system according to the present invention may further include a control unit, the control unit is the rotational speed of the platform, the rotation angle of the platform, the angle of stopping during the rotation of the platform, the stopping of the rotation of the platform At least one of a time interval, a time interval at which the unit X-ray source generates X-rays, X-ray emission control of the unit X-ray source during the stop time of the platform, and the X-ray detector, the platform, and the vacuum chamber positioned on the moving axis. There is a feature that can control any one or more of the positions.

In addition, any one or more of the unit X-ray source, the vacuum chamber, and the platform is characterized in that any one or more of the inclination and height is adjusted.

The unit X-ray source may be detachably attached to the vacuum chamber, and the unit X-ray source may include a cathode electrode; An emitter formed on the cathode electrode; An anode located above the emitter; A gate electrode positioned between the emitter and the anode electrode; And a focusing electrode positioned between the emitter and the anode electrode, wherein the cathode electrode includes one or more insulating pillars to fix and adjust positions of the gate electrode and the focusing electrode.

The at least one insulating pillar may be configured to penetrate the gate electrode and the focusing electrode, and the emitter may have at least one of a point light source form and a surface light source form.

In addition, the at least one insulating pillar is made of any one material selected from the group consisting of ceramic, quartz, glass, Teflon, polymer, and mixtures thereof, and is formed in the form of hollow hollow or filled pillars therein, and When the at least one insulating pillar is hollow, the at least one insulating pillar may be connected to an external power source.

In addition, at least one first hole is provided in each of the at least one insulating pillar, and at least one second hole is provided in each of the gate electrode and the focusing electrode, and the wire is formed through the first hole and the second hole. The power supply is applied to each of the gate electrode and the focusing electrode from an external power source through a power connection member contacting the power supply.

In addition, the tomographic image synthesis system according to the present invention is characterized by controlling the trajectory of electrons emitted from the emitter by adjusting the fixed position of each of the gate electrode and the focusing electrode through the at least one insulating pillar. .

According to the present invention, the gate electrode and the focusing electrode are separated and fixed through at least one insulated pillar provided on the cathode while the object is fixed to the platform and the platform is rotated by an angle. It is possible to obtain high quality radiation 3D reconstructed image by acquiring image information by photographing with a unit X-ray source in the form of a unit. It can reduce the constraint on.

In addition, the operation of the platform and the unit X-ray source and the arrangement of the X-ray detector, the unit X-ray source and the platform may be mechanically controlled by the controller to obtain a high quality radiographic image.

In addition, the position, height, and tilt of the X-ray detector, the unit X-ray source, and the platform may be adjusted to obtain an image at a desired position according to the subject.

In addition, the unit X-ray source can be detachable from the vacuum chamber to select the unit X-ray source according to the subject to take a radiographic image.

In addition, the unit X-ray source can easily control the position and spacing of the electrodes by separating and fixing the gate electrode and the focusing electrode through one or more insulating pillars provided on the cathode electrode, so that the trajectory of the X-ray emitted It can be easily controlled in a simpler structure, and the number of electrodes that can be used by adjusting the number of insulating pillars can be adjusted, so that the change in the electron trajectory emitted from the emitter can be easily controlled.

In addition, the unit X-ray source can easily control the emission trajectory of the electrons emitted from the emitter by selecting the shape of the emitter of the unit X-ray source according to the subject.

In addition, the unit X-ray source can easily control the change in the electron trajectory emitted from the emitter by selectively adjusting the shape, arrangement and material of the insulating pillar.

In addition, the unit X-ray source can control the electron emission characteristics of high efficiency by adjusting the position of the electrodes through the insulating pillar, the beam diameter can be easily adjusted by the removable method, the extraction of the electrodes is easy to reduce the manufacturing cost Can reduce the cost.

1 is a view schematically showing the main components of the X-ray micro-tomography apparatus of the method of rotating the gantry equipped with the X-ray tube and the detector according to the prior art,
2 is a schematic illustration of a tomographic image synthesis system with a rotating platform according to the present invention;
Figure 3 (a) is a perspective view of a unit x-ray source used in a tomography image synthesis system having a rotating platform according to the present invention,
3B is a cross-sectional view of a unit X-ray source used in a tomography image synthesis system with a rotating platform according to the present invention,
4 is a perspective view from below of a unit x-ray source for use in a tomographic image synthesis system with a rotating platform according to the present invention;
FIG. 5 is a diagram schematically illustrating an insulation pillar used in a unit X-ray source used in a tomography image synthesis system having a rotating platform according to the present invention.
6 is a plan view and a cross-sectional view of a result of converting a 2D X-ray image photographed by a conventional tomography imaging system into a 3D image by back projection to a 3D image matrix,
7 is a plan view and a cross-sectional view of a result of converting a 2D X-ray image photographed in a tomographic image synthesis system having a rotating platform according to the present invention through a filter and then back-projecting the 3D image matrix into a 3D image. do.

Hereinafter, a preferred embodiment of a tomographic image synthesis system having a rotating platform according to the present invention will be described with reference to the accompanying drawings. In this process, the thicknesses of the lines and the sizes of the components shown in the drawings may be exaggerated for clarity and convenience of explanation. In addition, terms to be described below are terms defined in consideration of functions in the present invention, which may vary according to the intention or convention of a user or an operator. Therefore, definitions of these terms should be made based on the contents throughout this specification.

<Examples>

Configuration of Tomographic Image Synthesis System According to the Present Invention

2 is a schematic illustration of a tomographic image synthesis system with a rotating platform according to the present invention.

In the tomography imaging system according to the exemplary embodiment, the X-ray detector 10 and the vacuum chamber 20 positioned at a predetermined distance apart from the X-ray detector 10 may be disposed between the X-ray detector 10 and the vacuum chamber 20. The platform 50, the x-ray detector 10, the vacuum chamber 20 and the moving shaft 30 on which the platform 50 is located, and the unit x-ray source 100 attached to the vacuum chamber 20 (in FIG. 2). Note that the unit X-ray source is not shown because it is present inside the vacuum chamber 20).

The X-ray detector 10 detects the emitted X-rays and serves to image them. That is, when the transmitted X-ray is converted into visible light through the X-ray converter, the X-ray detector 10 converts the visible light back into an electric signal and transmits the digital light into digital image information by the photo diodes installed for each of millions of pixels. Do this. Meanwhile, since the X-ray detector 10 uses known components, detailed description thereof will be omitted.

The vacuum chamber 20 is spaced apart from the X-ray detector 10 by a predetermined distance. In addition, such a vacuum chamber 20 is maintained at high vacuum using a vacuum pump or the like or is configured in a package form. That is, the unit X-ray source 100 to be described later serves to provide an appropriate environment for emitting X-rays by emitting electrons in a vacuum state.

The platform 50 is where the subject 40 is located and may include means for fixing the subject 40. It is configured to rotate 360 degrees with the rotating shaft 53 using a motor or the like. That is, due to the rotation of the platform 50, it is possible to obtain a high quality radiographic three-dimensional reconstruction image for the subject 40.

More specifically, the subject 40 is positioned on the top plate 54 and fixed with a tape 55 or the like. The rotation shaft 53 has a scale to recognize the rotation angle during the photographing, and has a height adjusting unit 53 to adjust the height of the subject 40 is located.

The moving plate 32 may have a fixing unit 11 and a wheel 33 to fix an object located on the upper surface of the moving plate 32. In an embodiment, the X-ray detector 10, the vacuum chamber 20, and the platform 50 are respectively positioned below and support them. The fixing part 11 included in the moving plate 32 fixes the moving plate 32 to any one of the X-ray detector 10, the vacuum chamber 20, and the platform 50 positioned on the moving plate 32. The moving plate 32 is provided with wheels 33 so as not to shake. The moving plate 32 may be positioned on the moving shaft 30 to be described later and moved by the moving shaft 30.

The moving shaft 30 includes a moving plate 32 supporting the X-ray detector 10, the vacuum chamber 20, and the platform 50. The moving shaft 30 includes an actuator that can change the position of the moving plate 32, and can adjust the distance between the object 40, the X-ray detector 10, and the vacuum chamber 20.

In addition, the X-ray detector 10, the vacuum chamber 20 and the platform 50 is added with means for adjusting the height and inclination can be adjusted according to the user's needs.

The unit X-ray source 100 is located in the vacuum chamber 20. In this case, the unit X-ray source 100 may be detachably attached from the vacuum chamber 20 for easy maintenance and repair. Meanwhile, a detailed configuration of the unit X-ray source 100 will be described later with reference to FIGS. 3 to 5.

Meanwhile, the tomography imaging system according to the exemplary embodiment may further include an X-ray filter (not shown) and the controller 60.

The X-ray filter is positioned between the vacuum chamber 20 and the X-ray detector 10 and serves to filter the X-rays generated from the unit X-ray source 100. Since the X-ray filter may also be made of known components, detailed description thereof will be omitted.

The controller 60 controls the tomography imaging system according to the present invention. In detail, the controller 60 may include a rotation speed and a total rotation angle of the platform 50, an angle and a stop time of the platform 50 for X-ray imaging during rotation, and a unit X-ray source located in the vacuum chamber 20 ( X-ray emission of the unit X-ray source may be controlled during a time interval in which 100) generates X-rays and a stop time of the platform.

In addition, the controller 60 may also control the position, height, or inclination of the X-ray detector 10, the vacuum chamber 20, and the platform 50 positioned on the moving shaft 30 using an actuator (not shown). have.

The controller 60 has control variables used to control the platform 50, the unit X-ray source 100, the moving shaft 30, and the like.

Variables used to control the platform 50 are the rotational speed of the platform 50, the total angle of rotation of the platform 50, the angle at which the platform 50 stops for X-ray imaging during rotation, and the platform 50 after the stop. It includes the stop time which is waiting time before rotation again.

Variables for controlling the unit X-ray source 100 located in the vacuum chamber 20 include a time interval during which the unit X-ray source 100 generates X-rays and other control variables of the unit X-ray source 100.

The variable used to control the moving shaft 30 includes a value for setting where the X-ray detector 10, the vacuum chamber 20, and the platform 50 are located on the moving shaft 30.

In addition, the control variable input to the control unit 60 includes values for the height, inclination, and angle to be set by the X-ray detector 10, the vacuum chamber 20, and the platform 50.

The controller 60 may have a default value for the control variable, use the default value as a control variable for a control variable not input by the user, and control a value directly input by the user for the control variable input by the user. Can be used as a variable.

On the other hand, since the components constituting the control unit 60 may also be made of known technology, a detailed description thereof will be omitted.

Due to this configuration, in the case of using the tomography imaging system according to the present invention, the platform 50 on which the subject 40 is positioned is stopped at a predetermined angle while rotating at a speed and an angle designated by the user, and the platform ( While 50 is stopped during rotation, X-rays generated from the unit X-ray source 100 located in the vacuum chamber 20 penetrate the object 40 and the X-ray detector 10 measures the amount of radiation transmitted. After measuring and converting the data into an electrical signal, the computer converts the signal into a computer and converts the signal into a high quality stereoscopic two-dimensional tomographic or three-dimensional image, which is shown on a monitor.

In particular, (1) through the control of the control unit 60, the rotation speed of the platform 50, the rotation angle of the platform 50, the stopping angle of the platform 50, the stop time of the platform 50 can be adjusted, ( 2) the time interval during which the unit X-ray source 100 generates X-rays under the control of the control unit 60 (3) the X-ray detector 10, the vacuum chamber 20, under the control of the control unit 60, Position, height and inclination of the platform 50 can be adjusted to adjust the position of each part according to the shooting conditions.

In addition, (4) the solid fixation of the unit X-ray source 100 and the X-ray detector 10 can reduce the maintenance cost by extending the life of the equipment through stable electron emission, and (5) the object in the platform 50 There is no need to rotate the unit X-ray source 100 or X-ray detector 10 to use less space to install and use, the unit X-ray source 100 without limiting the size and weight of the unit X-ray source 100 You can choose to use it.

(6) Since the unit X-ray source 100 and the X-ray detector 10 are fixed without rotation, there is no eccentric load and there is no shaking due to the rotation of the unit X-ray source 100 and the X-ray detector 10, There is no need to add a separate device, such as a weight to balance the weight, the speed ripple does not appear even if the rotation speed of the platform 50 is increased.

3 to 5, the unit X-ray source 100 of the tomography image synthesis system according to the present invention includes a cathode electrode 110, an emitter 120, an anode electrode 130, a gate electrode 140, and focusing. Electrode 150 and one or more insulating pillars 160. Note that the unit X-ray source 100 operates in a vacuum even if not mentioned otherwise.

The cathode electrode 110 is positioned on an upper portion of a substrate (not shown) formed of glass, metal, quartz, silicon, or alumina. On the cathode electrode 110, an emitter (in the form of a point light source and / or a surface light source described below) 120 is located.

In addition, the cathode electrode 110 is provided with one or more insulating pillars 160 to separate and fix the gate electrode 140 and the focusing electrode 150, which will be described later, to easily control the position and the distance between the electrodes. This can be done, which will be described later.

The emitter 120 serves to emit electrons and is illustrated as having a point light source configuration.

The emitter 120 in the form of such a point light source is not particularly limited as long as the tip at which the electrons are emitted has a pointed shape. However, preferably, it may be any one of a conical shape, a tetrahedron shape and a cylindrical shape having a pointed tip and a polyhedron having a pointed tip.

The emitter 120 in the form of a point light source is characterized in that the diameter of the bottom surface of about 0.1 ~ 4mm and its height is 0.5 ~ 5cm. This is because the electrons can be effectively emitted as a point light source in the case of the size and scale of the above-mentioned degree, and the effect according to the present invention can be achieved.

In addition, the type of emitter 120 is not particularly limited, but is preferably a conductive material composed of a metal or a carbon-based material.

On the other hand, the emitter 120, it is noted that the emitter in the form of a surface light source as well as the point light source may be used according to the control of the trajectory of the electrons emitted or the performance of the desired unit X-ray source. In this case, the emitter in the form of a surface light source is preferably a carbon structure or metal formed on silicon, metal, carbon series.

The anode electrode 130 is located above the emitter 120.

The anode electrode 130 is provided with an electrode and / or a DC power supply (not shown) for applying power, but this is well known and the detailed description thereof will be omitted.

The material of the anode electrode 130 is generally formed of a material selected from the group consisting of copper, tungsten, manganese, Maldives and combinations thereof. In addition, in the case of a thin film type X-ray, it is noted that the anode electrode 130 may be formed of a metal thin film.

Due to this configuration, when the emitter 120 described above emits electrons, the emitted electrons collide with the metal constituting the anode electrode 130, and then generate X-rays while reflecting or passing through the metal. do.

The gate electrode 140 is positioned between the emitter 120 and the anode electrode 130. The gate electrode 140 increases the amount of electrons emitted from the emitter 120 and accelerates the speed of the emitted electrons.

The focusing electrodes 150a and 150b are positioned between the gate electrode 140 and the anode electrode 130. The focusing electrode 150 allows electrons emitted from the emitter 120 to move toward the anode electrode 130 without spreading or scattering.

In the drawing, one such gate electrode 140 exists and two focusing electrodes 150a and 150b exist. However, the gate electrode 140 may be adjusted depending on the trajectory of emitted electrons or the performance of a desired unit X-ray source. Note that the number of focusing electrodes 150a and 150b may vary.

In addition, the gate electrode 140 and the focusing electrodes 150a and 150b may be detachably configured from one or more insulating pillars 160 to be described later, so that the extraction thereof may be easily performed.

The shape of the gate electrode 140 and the focusing electrodes 150a and 150b may be determined according to the trajectory of electrons emitted from the emitter 120. In the drawings, the electrodes are shown as a plate-shaped member having a constant thickness in which a circular hole exists, but the electrodes are arranged in a circular ring shape or a cylindrical cylinder having a hole therein or at regular intervals. Note that it may be formed in the form of a plate having a certain thickness.

One or more insulating pillars 160 are provided on top of the cathode electrode 110 or inserted to be perpendicular to the cathode electrode 110 to separate the gate electrode 140 and the focusing electrodes 150a and 150b described above. It also serves to fix and adjust the positions of the gate electrode 140 and the focusing electrodes 150a and 150b.

The principle of controlling the positions of the at least one insulating pillar 160 and the gate electrode 140 and the focusing electrodes 150a and 150b will be described below.

One or more insulating pillars 160 are configured to penetrate through the gate electrode 140 and the focusing electrodes 150a and 150b. That is, through-holes corresponding to the size and shape of the insulating pillar 160 are formed in the gate electrode 140 and the focusing electrodes 150a and 150b so that the insulating pillar 160 can pass therethrough. In addition, at least one first hole 162 is formed in the side surface of the insulating pillar 160, and at least one second hole 151 is formed in each of the gate electrode 140 and the focusing electrodes 150a and 150b. Will be formed.

In the drawing, three first holes 162 are formed in the side surface of the cylindrical insulating pillar 160, but this is merely illustrative, and also in the side portions of each of the gate electrode 140 and the focusing electrodes 150a and 150b. Note that four or more second holes 151 are formed, but these are merely exemplary.

The insulating pillar 160 and each electrode using a power connection member (not shown, for example, a screw or a fastening member having a predetermined shape) that can penetrate the second hole 151 and the first hole 162. By fixing the, the gate electrode 140 and the focusing electrodes 150a and 150b can be separated from each other and maintained at a predetermined position.

At this time, by selectively adjusting the position of the first hole 162 formed in each insulating pillar 160, it is possible to easily control the distance between the electrodes.

On the other hand, the one or more insulating pillars 160 may be in the form of a pillar filled with the inside, but referring to Figure 5, in one embodiment of the present invention, the one or more insulating pillars 160 is hollow inside the hollow Is formed, the wire 161 connected to the external power source is located inside the insulating pillar.

In this case, the power supply connecting member penetrates through the second hole 151 and the first hole 162 and contacts the wire located inside the insulating pillar 160, so that the gate electrode 140 and the focusing electrode 150a, 150b) Appropriate power can be applied to each.

For example, when there is only one gate electrode 140 used for the unit X-ray source 100 and two focusing electrodes 150a and 150b, it is preferable that there are three insulating pillars 160. In this case, the emitter 120 is located in the center of the cathode electrode 110, it is preferable that the three insulating pillars are positioned to surround the emitter 120, but the position of the three insulating pillars is not necessarily limited thereto. do. On the other hand, when one more focusing electrode is added, it is preferable that four insulating pillars 160 are positioned.

Inside the three insulated pillars, wires connected to an external power source are respectively located, and one electrode per one insulated pillar is connected to a power through a second hole formed in each electrode and a first hole formed in each insulated pillar. By being connected and fixed by the member, appropriate power can be applied to each electrode.

On the other hand, the insulating pillar 160 is provided with a separate DC power supply (not shown) for applying power to each electrode in the case of a pillar shape filled inside, to be configured to apply power to each electrode Can be.

Here, it is preferable that the shape of one or more insulating pillars is any one or more of circular, elliptical, triangular, square, polyhedral and combinations thereof.

In addition, the at least one insulating pillar is preferably made of a material selected from the group consisting of ceramic, quartz, glass, Teflon, polymer and mixtures thereof.

Due to this configuration, the unit X-ray source 100 can adjust the number of electrodes that can be used by adjusting the number of the insulating pillars, and by controlling the shape and arrangement of the insulating pillars, the electrons emitted from the emitter 120 It is possible to easily control the change of trajectory, to control the electron emission characteristics of high efficiency by adjusting the position of the electrodes through the insulating pillar, to easily extract the electrodes used in the unit X-ray source, due to the simple shape of the insulating pillar By reducing the processing cost, there is an effect that can reduce the manufacturing cost.

Operation method of tomographic image synthesis system according to the present invention

After the user places the subject 40 on the upper plate 54 of the platform 50 and fixes the subject 40 with the fixing tape 55, the user inputs a control variable through the controller 60.

Next, the controller 60 controls the moving plate 32 to have a position value on the moving shaft 30 of the X-ray detector 10, the vacuum chamber 20, and the platform 50 to control the X-ray detector 10 and the vacuum chamber. 20 and the platform 50 are positioned at the corresponding positions.

In addition, the controller 60 may control the X-ray detector 10, the vacuum chamber 20, and the X-ray detector 10, the vacuum chamber 20, and the platform 50 by using control variables for the height, the tilt, and the angle to be set. The tomography imaging system according to the present invention is adjusted to suit the imaging of the subject 40 by controlling the height, tilt and angle of the platform 50.

Thereafter, the controller 60 controls the platform 50 to rotate the subject 40. The controller 60 rotates the platform 50 according to the rotation speed of the platform 50 stored in the control variable. The platform 50 stops rotation when it corresponds to an angle for stopping X-ray imaging during rotation, and starts to rotate again after a stop time, which is a waiting time for the platform 50 to rotate again.

While the platform 50 is stopped during the rotation, the controller 60 photographs a cross section of the object 40 under X-ray using the unit X-ray source 100 of the vacuum chamber 20. This is done within the down time, which is the waiting time for the platform 50 to rotate again.

Finally, when the platform 50 rotates to the total rotation angle, the controller 60 stops the rotation of the platform 50 and ends the shooting.

The photographing method is not limited to using the controller 60. The user may manually control the controller 60 without using it. The user may manually control the rotation and stop of the platform 50 and operate the unit X-ray source 100 of the vacuum chamber 20 to perform X-ray imaging of the subject 40.

Method for converting 2D X-ray image taken by tomographic image synthesis system according to the present invention into 3D X-ray image

Referring to FIGS. 6 and 7, the conversion of the 2D X-ray image of the object 40 to the 3D X-ray image will be described. The data obtained by capturing the tomographic image synthesis system having the rotating platform according to the present invention is a two-dimensional image having the photographing angle and the photographing distance as metadata. In order to image the 3D image, a computer program such as a back projector that converts the image into a 3D image is used. Meanwhile, since the conversion program uses well-known components, detailed description thereof will be omitted.

As an example, a reverse projector may be used to convert a 2D image by multiple axes into a 3D image. 6 and 7, a plan view and a cross-sectional view are shown. The plan view is an image along the axis of the three-dimensional reconstructed x-ray image and the cross-sectional view is an image shown from the side.

As shown in FIG. 7, unlike the three-dimensional image illustrated in FIG. 6, the three-dimensional image is passed through a two-dimensional X-ray image photographed in a tomographic image synthesis system having a rotating platform according to the present invention. In addition, the low frequency component video signal may be converted by passing through a filter that does not pass and then back projecting onto a 3D image matrix.

As mentioned above, although the present invention has been illustrated and described with reference to specific embodiments, the present invention is not limited thereto, and the scope of the following claims is not limited to the scope of the present invention. It will be readily apparent to those skilled in the art that these various modifications and variations can be made.

10: X-ray detector 11, 21, 51: set screw
12, 22, 52: height adjustment unit 20: vacuum chamber
30: moving shaft 31: groove
32: moving plate 33: wheels
40: subject 50: platform
53: axis of rotation 54: top plate
55: fixed tape 60: control unit

Claims (10)

X-ray detectors;
A vacuum chamber spaced apart from the x-ray detector;
A rotatable platform positioned between the x-ray detector and the vacuum chamber to accommodate a subject;
A plurality of moving plates positioned under the X-ray detector, the vacuum chamber, and the platform, respectively, to support the X-ray detector, the vacuum chamber, and the platform;
A moving shaft of the moving plate positioned below the moving plate;
A unit x-ray source having one or more insulating pillars attached within said vacuum chamber and emitting X-rays; And
The rotational speed of the platform, the rotational angle of the platform, the angle of stopping during the rotation of the platform, the time of stopping the rotation of the platform, the position of any one of the X-ray detector and the platform and the vacuum chamber located on the moving axis A control unit configured to control at least one of an X-ray emission control of the unit X-ray source and a time interval in which the unit X-ray source generates X-rays during the stop time of the platform;
&Lt; / RTI &gt;
Tomographic Image Synthesis System.
delete The method of claim 1,
At least one of the unit X-ray source, the vacuum chamber and the platform is characterized in that any one or more of the inclination and height is adjusted by the control unit,
Tomographic Image Synthesis System.
The method of claim 1,
The unit x-ray source is characterized in that detachably attached from the vacuum chamber,
Tomographic Image Synthesis System.
The method according to any one of claims 1, 3, and 4,
The unit x-ray source,
A cathode electrode;
An emitter formed on the cathode electrode;
An anode located above the emitter;
A gate electrode positioned between the emitter and the anode electrode; And
And a focusing electrode positioned between the emitter and the anode electrode.
The cathode electrode includes the at least one insulating pillar capable of fixing and adjusting the position of the gate electrode and the focusing electrode, and
The gate electrode and the focusing electrode is characterized in that the one or more insulating pillars are configured to pass through,
Tomographic Image Synthesis System.
The method of claim 5,
The emitter is characterized in that it has any one or more of the form of a point light source and a surface light source,
Tomographic Image Synthesis System.
The method of claim 5,
The at least one insulating pillar is formed in the form of a hollow hollow or filled pillar, and
When the at least one insulated pillar is hollow, the at least one insulated pillar is characterized in that a wire connected to an external power source is located,
Tomographic Image Synthesis System.
The method of claim 7, wherein
Each of the one or more insulating pillars is provided with one or more first holes,
At least one second hole is provided in each of the gate electrode and the focusing electrode, and
Characterized in that power is applied to each of the gate electrode and the focusing electrode from an external power source through a power connection member that penetrates the first hole and the second hole to contact the wire.
Tomographic Image Synthesis System.
The method of claim 5,
The one or more insulating pillars,
Characterized in that it is composed of any one material selected from the group consisting of ceramic, quartz, glass, Teflon, polymer and mixtures thereof,
Tomographic Image Synthesis System.
The method of claim 5,
By controlling the fixing position of each of the gate electrode and the focusing electrode through the at least one insulating pillar, the trajectory of the electrons emitted from the emitter is controlled,
Tomographic Image Synthesis System.

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