KR20120120849A - computed tomography system including small-size x-ray source - Google Patents

Abstract

PURPOSE: A tomography system including a small X-ray source is provided to effectively obtain a high quality radiation 3D reconstructed image by taking a photograph of an object while rotating a gantry in a predetermined angle to obtain image information. CONSTITUTION: A small vacuum chamber(20) is separated from an X-ray detector(10). A circular gantry unit(30) fixes the X-ray detector and the small vacuum chamber. The circular gantry unit is rotationally formed. A unit X-ray source is attached in the small vacuum chamber. An object and an X-ray filter are located between the X-ray detector and the small vacuum chamber. [Reference numerals] (60) Controller

Description

Computed tomography system including small-size x-ray source}

The present invention relates to a tomography imaging system including a small x-ray source, and more particularly, to a circular 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. A tomographic system comprising a small x-ray source that can be fixed to the gantry of the image, and obtain a high-quality radiographic three-dimensional reconstructed image by capturing the subject while rotating the gantry 360 degrees or a certain angle to obtain image information will be.

Digital tomography is a simplified form of computed tomography (CT) called limited angle computed tomography.

In particular, since the angle used for irradiation is limited, the 3D reconstructed image is obtained through very limited image information compared with general CT, but the level of the reconstructed image is somewhat low, but the effect on the human body is relatively small. It is an advantage that is being used to diagnose diseases of specific parts of the human body.

Specifically, the digital tomography synthesizer relies on limited image information. In the human region where hard and soft tissues coexist, streaking occurs on the boundary of hard tissues. (Breast) has the advantage that the level of the reconstructed image is high enough to be used for diagnosis. In addition, since the digital tomography synthesizer operates only at a limited angle, the size of the equipment is smaller than that of the conventional CT, and the 3D image can be reconstructed with only a relatively small dose. Moreover, there is ample room for development of algorithms optimized for each part or use, and through this, competitive 3D reconstructed images can be obtained, which can be said to have competitiveness and potential to offset the shortcomings of limited image information.

On the other hand, such X-ray digital tomography synthesizer can be said to be mainly a cone beam (micro CT) using a micro focus X-ray tube of a small focus (cone beam) using a two-dimensional detector.

For example, 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 gantry rotating units ( It is mounted in 2) and this gantry rotating part 2 has a structure which scans while rotating. The gantry rotating part 2 and the gantry fixing part 3 are fastened by bearings and have a structure for rotating 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 part, and the subject is enlarged according to the distance between the focus and the center of rotation of the X-ray tube and the distance from the center of rotation to the detector. Scanning results in tomographic images with spatial resolutions ranging from a few micrometers to tens of micrometers.

In some circumstances, in order to obtain a very high spatial resolution tomographic image, it is necessary to increase the geometric magnification by shortening the distance from the center of rotation to the focal point of the X-ray tube and increasing the distance from the center of rotation to the detector. In the case of the gantry rotation type, it may be possible to attach the X-ray source and the detector to the linear motion device and change the magnification through the motor control in order to achieve the object.

In this case, however, 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, which makes it difficult to precisely rotate. Therefore, a problem arises in that the resolution of the tomography image is deteriorated. In addition, when scanning at high magnification, the radial accuracy of the bearing connecting the gantry fixing part and the gantry rotating part is several tens of micrometers due to the weight of the X-ray source device. will be.

Therefore, the present inventors have a simpler structure, can easily adjust the position of various electrodes used in the X-ray source and the distance between the electrodes, and can easily control the trajectory of the emitted electrons, It has come to invent a tomography imaging system comprising a small manufacturable x-ray source.

SUMMARY OF THE INVENTION The present invention has been made to solve the above-described problems, and an object of the present invention is to provide a circular X-ray source of a form in which a gate electrode and a focusing electrode are separated and fixed through at least one insulating pillar provided on a cathode electrode. A tomographic imaging system including a small x-ray source that is secured to the gantry, and obtains image information by capturing the subject while rotating the gantry 360 degrees or a certain angle to obtain a high quality radiographic three-dimensional reconstruction image more effectively. To provide.

A tomography imaging system including a small x-ray source according to the present invention includes an x-ray detector; A small vacuum chamber spaced apart from the X-ray detector by a predetermined distance; A circular gantry unit fixed to the X-ray detector and the small vacuum chamber and configured to be rotatable; And a unit x-ray source attached to the small vacuum chamber. Here, the small vacuum chamber is characterized in that it comprises a high vacuum pump.

Preferably, a platform on which the subject can be positioned is provided between the X-ray detector and the small vacuum chamber.

Preferably, an x-ray filter is provided between the small vacuum chamber and the x-ray detector.

Preferably, the tomography imaging system further comprises a control unit for controlling any one or more of the rotational speed of the circular gantry unit and the time interval in which the unit X-ray source generates X-rays.

Preferably, the tomography imaging system further comprises a control unit for controlling the position interval of the X-ray detector and the small vacuum chamber fixed to the circular gantry unit.

Preferably, the small x-ray source is detachably attached from the small vacuum chamber.

Preferably, the unit X-ray source, the 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 is provided with at least one insulating pillar capable of fixing and adjusting positions of the gate electrode and the focusing electrode.

Preferably, the gate electrode and the focusing electrode is characterized in that the one or more insulating pillars are configured to pass through.

Preferably, 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.

Preferably, the one or more insulated pillars are formed in the form of hollow hollow or full pillars, and when the one or more insulated pillars are hollow hollow, the one or more insulated pillars have a wire connected to an external power source. It is characterized in that the location.

Preferably, 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 penetrates the second hole and the first hole. Power is applied to each of the gate electrode and the focusing electrode from an external power source through a power connection member contacting the wire.

Preferably, the shape of the at least one insulating pillar is characterized in that any one or more of a circle, oval, triangle, square, polyhedron, and combinations thereof.

Preferably, the at least one insulating pillar is made of a material selected from the group consisting of ceramics, quartz, glass, Teflon, polymers and mixtures thereof.

Preferably, the position of each of the gate electrode and the focusing electrode is adjusted through the one or more insulating pillars to control the trajectory of electrons emitted from the emitter.

Preferably, at least one of the gate electrode and the focusing electrode is present, and the gate electrode and the focusing electrode are configured to be detachable from the at least one insulating pillar.

Preferably, the gate electrode and the focusing electrode is in the form of a plate member having a constant thickness in which there is a plate-shaped or circular hole having a constant thickness arranged at a constant interval.

Preferably, the gate electrode and the focusing electrode is characterized in that the same as the circular ring shape or the gate shape.

According to the present invention, a small vacuum chamber having an x-ray source in a form in which the gate electrode and the focusing electrode are separated and fixed through at least one insulating pillar provided on the cathode electrode is fixed to a circular gantry, and the gantry is 360 It is possible to obtain a high quality radiographic three-dimensional reconstructed image by photographing a subject while rotating a degree or a certain angle to obtain image information.

In addition, by using a field emission type X-ray light source using carbon nanotubes (CNTs), which are nanomaterials in a unit X-ray source, the kinetic energy of the emitted electrons is higher than that of a conventional X-ray light source. Since it is almost constant and has a good electron emission direction, the focal size can be easily controlled through an electrostatic lens or the like, so that an extremely clear radiographic image can be obtained.

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 view of a tomography imaging system including a small x-ray source according to the present invention,
3A is a perspective view of a unit X-ray source 100 used in a tomography imaging system including a small X-ray source according to the present invention.
3B is a cross-sectional view of a unit X-ray source 100 used in a tomography imaging system including a small X-ray source according to the present invention.
4 is a perspective view from below of a unit x-ray source 100 used in a tomography imaging system including a small x-ray source according to the present invention,
FIG. 5 is a diagram schematically illustrating an insulation pillar used in a unit x-ray source 100 used in a tomography imaging system including a small x-ray source according to the present invention.

Hereinafter, a preferred embodiment of a tomography imaging system including a small x-ray source 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>

2 is a schematic view of a tomography imaging system including a small x-ray source according to the present invention.

In the tomography imaging system according to the exemplary embodiment, the small vacuum chamber 20, the X-ray detector 10, and the small vacuum chamber 20, which are spaced apart from the X-ray detector 10 and the X-ray detector 10 by a predetermined distance, may be provided. The unit x-ray source 100 fixed in the rotatable gantry unit 30 and the small vacuum chamber 20 (in FIG. 1, the unit x-ray source is present inside the small vacuum chamber 20) Note that not shown).

The X-ray detector 10 detects the emitted X-rays and serves to image them. That is, when the transmitted X-rays are 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 to digital image information. To perform. Meanwhile, since the X-ray detector 10 uses known components, detailed description thereof will be omitted.

The small vacuum chamber 20 is spaced apart from the X-ray detector 10 by a predetermined distance. In addition, such a small vacuum chamber 20 is configured to be maintained in a high vacuum using a vacuum pump or the like. 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 X-ray detector 10 and the small vacuum chamber 20 are attached and fixed to the circular gantry unit 30. The circular gantry unit 30 is configured to be rotated 360 degrees by using a component such as a motor. That is, due to the rotation of the gantry unit 30 it is possible to obtain a high-quality radiation three-dimensional reconstruction image for the subject 40. To this end, the platform 50 may be provided between the X-ray detector 10 and the small vacuum chamber 20 so that the subject 40 may be positioned.

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

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 small 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 also uses a known component, a detailed configuration thereof will be omitted.

The controller 60 controls the tomography imaging system according to the present invention. Specifically, the controller 60 may control the rotation speed of the circular gantry unit 30 or control the time interval at which the unit X-ray source 100 located in the small vacuum chamber 20 generates X-rays. Will be. In addition, the control unit 60 may also control the position interval of the X-ray detector 10 and the small vacuum chamber 20 fixed to the circular gantry unit 30 using a slice lamp mechanism (not shown). . On the other hand, since the components constituting the control unit 60 also uses a known technology, a detailed description thereof will be omitted.

Due to this configuration, when using the tomography imaging system according to the present invention, the circular gantry unit 30 with respect to the subject 40 is rotated 360 degrees or a predetermined angle at a user-specified speed, X-rays generated from the unit X-ray source 100 located in the vacuum chamber 20 penetrate the subject 40, and the X-ray detector 10 measures the amount of radiation transmitted and converts the data into an electrical signal. In addition, the computer converts the signal into a computer to produce a high quality three-dimensional image, which is then displayed on a monitor.

In particular, (1) the X-ray emission characteristics can be controlled, and (2) the rotation speed of the circular gantry unit 30 and the time interval at which the unit X-ray source 100 generates the X-rays through the control of the controller. Controllability, (3) long-life of equipment through stable electron emission, reducing maintenance costs, (4) easy extraction of electrodes used in the unit X-ray source 100, (5) repetition Due to the simple shape of the unit X-ray source 100 to be reduced the manufacturing cost by reducing the processing cost, and (6) by adjusting the unit beam diameter it is easy to control the high resolution and power.

FIG. 3A is a perspective view of a unit X-ray source 100 used in a tomography imaging system including a small X-ray source according to the present invention, and FIG. 3B is a view showing the small X-ray source according to the present invention. 4 is a cross-sectional view of a unit x-ray source 100 used in a tomography imaging system, and FIG. 4 is a perspective view of the unit x-ray source 100 used in a tomography imaging system including a small x-ray source according to the present invention. FIG. 3 schematically illustrates an insulating pillar used in a unit X-ray source 100 used in a tomography imaging system including a small X-ray source according to the present invention.

3 to 5, the unit X-ray source 100 may include a cathode electrode 110, an emitter 120, an anode electrode 130, a gate electrode 140, a 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. The cathode 110 has 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 has a pointed shape from which electrons are emitted. 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 having the above-described size and scale, 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 is to note that the emitter in the form of a surface light source as well as a point light source can be used according to the control of the trajectory of the electrons emitted or the performance of the desired 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. Also, in the case of a thin film type X-ray, 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 gate electrode 140 exists and two focusing electrodes 150a and 150b exist. However, the gate electrode 140 and the gate electrode 140 may be adjusted according to the characteristics of the electrons emitted or the performance of a desired 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 full column, but referring to Figure 5, in one embodiment of the present invention, the one or more insulating pillars 160 is formed of a hollow hollow inside A wire 161 connected to an external power source is positioned inside the insulation 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 columnar shape is filled inside, it can be configured to apply power to each electrode have.

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 composed 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 may adjust the fixed positions and the distances between the gate electrodes and the focusing electrodes, respectively, by adjusting the positions of the first holes 162 formed in the insulation pillars. 2) it is possible to control the number of electrodes that can be used by adjusting the number of insulating pillars, 3) by adjusting the shape and arrangement of the insulating pillar, it is possible to easily control the change in the electron trajectory emitted from the emitter 120 It becomes possible.

Therefore, according to the unit X-ray source 100, 1) it is possible to control the electron emission characteristics of high efficiency by adjusting the position of the electrodes through the insulating pillar, 2) easy to adjust the beam diameter through the removable method, 3) stable Electron emission extends the life of equipment to reduce maintenance costs, 4) facilitates extraction of electrodes used in x-ray sources, and 5) reduces manufacturing costs due to the simple form of insulating pillars. And 6) miniaturization of the beam diameter results in high resolution and easy output control.

While the present invention has been particularly shown and described with reference to specific embodiments thereof, it is to be understood that the invention is not limited to the disclosed embodiments, but, on the contrary, It will be readily apparent to those skilled in the art that the present invention can be modified and changed without departing from the scope of the present invention.

<Description of Major Symbols in Drawing>
10: X-ray detector
20: small vacuum chamber
30: Gantry Unit
40:
50: platform
60: control unit
100: unit x-ray source
110: cathode electrode
120: emitter
130: anode electrode
140: gate electrode
150a, 150b: focusing electrode
151: Second Hall
160: insulated pillar
161: wire
162: Hall 1

Claims (17)

X-ray detectors;
A small vacuum chamber spaced apart from the X-ray detector by a predetermined distance;
A circular gantry unit fixed to the X-ray detector and the small vacuum chamber and configured to be rotatable; And
And a unit x-ray source attached to the small vacuum chamber.
Tomographic imaging system including a small x-ray source.
The method of claim 1,
A platform on which the subject may be positioned is provided between the x-ray detector and the small vacuum chamber.
Tomographic imaging system including a small x-ray source.
The method of claim 2,
An X-ray filter is provided between the small vacuum chamber and the X-ray detector,
Tomographic imaging system including a small x-ray source.
The method of claim 1,
The tomography imaging system may further include a controller configured to control at least one of a rotational speed of the circular gantry unit and a time interval at which the unit X-ray source generates X-rays.
Tomographic imaging system including a small x-ray source.
The method of claim 1,
The tomography imaging system may further include a controller configured to control a position interval between the X-ray detector and the small vacuum chamber fixed to the circular gantry unit.
Tomographic imaging system including a small x-ray source.
The method of claim 1,
The small x-ray source is detachably attached from the small vacuum chamber,
Tomographic imaging system including a small x-ray source.
7. The method according to any one of claims 1 to 6,
The unit x-ray source,
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.
Characterized in that the cathode electrode is provided with one or more insulating pillars for fixing and adjusting the position of the gate electrode and the focusing electrode,
Tomographic imaging system including a small x-ray source.
The method of claim 7, wherein
The gate electrode and the focusing electrode is configured to be configured so that the one or more insulating pillars,
Tomographic imaging system including a small x-ray source.
The method of claim 7, wherein
The emitter is characterized in that it has a form of any one or more of the point light source form and the surface light source form,
Tomographic imaging system including a small x-ray source.
The method of claim 7, wherein
The at least one insulated pillar is formed in the form of a hollow hollow or tight 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 imaging system including a small x-ray source.
The method of claim 10,
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,
Characterized in that the power is applied to each of the gate electrode and the focusing electrode from an external power source through a power connection member which penetrates the second hole and the first hole to contact the wire.
Tomographic imaging system including a small x-ray source.
The method of claim 7, wherein
The shape of the at least one insulating pillar is characterized in that at least one of circular, oval, triangular, square, polyhedral and combinations thereof.
Tomographic imaging system including a small x-ray source.
The method of claim 7, wherein
The at least one insulating pillar is characterized in that consisting of a material selected from the group consisting of ceramic, quartz, glass, Teflon, polymer and mixtures thereof,
Tomographic imaging system including a small x-ray source.
The method of claim 7, wherein
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 imaging system including a small x-ray source.
The method of claim 7, wherein
At least one gate electrode and at least one focusing electrode are present.
The gate electrode and the focusing electrode is configured to be detachable from the at least one insulating pillar,
Tomographic imaging system including a small x-ray source.
The method of claim 7, wherein
The gate electrode and the focusing electrode,
Characterized in that it is in the form of a plate member having a predetermined thickness in which a plate-shaped or circular hole having a predetermined thickness arranged at regular intervals,
Tomographic imaging system including a small x-ray source.
The method of claim 7, wherein
And the gate electrode and the focusing electrode are the same as a circular ring shape or a gate shape.

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