KR20090025927A - X-ray ct apparatus - Google Patents

Abstract

An X-ray CT camera is provided to periodically perform the irradiation and non-irradiation of X-ray by mounting an X-ray irradiation control unit at the X-ray generating unit. A base(101) is horizontally arranged in a floor side. The base supports a supporting frame(102). The supporting frame is perpendicularly combined in the base. A guide rod(103) is fixed to the central part of the supporting frame. An elevating member(104) is installed at the guide rod in order to be ascended and descended. The elevating member driving part is comprised of a linear motor which straightly operates the elevating member. A rotating arm(105) has the axis of rotation which is vertical to the floor side. The rotating arm is installed at the elevating member. An X-ray generating unit is installed inside the one-side end of the rotating arm. A data processing block receives the data about X-ray.

Description

X-ray CT recording device {X-RAY CT APPARATUS}

The present invention relates to an X-ray CT imaging apparatus, and more particularly, to an X-ray CT imaging apparatus that can reduce the exposure dose received by the subject.

An X-ray computerized tomography (CT) imaging device is a device that transmits an X-ray to be examined and reconstructs the detected data into an image by detecting an X-ray that has passed through the object through a detector. X-ray CT imaging apparatus is used for visually observing an image of the internal tissue of the subject to determine the abnormality of the internal tissue of the subject.

Various types of X-ray CT imaging apparatuses have been developed and used. These X-ray CT imaging apparatuses commonly include an X-ray generating unit that generates X-rays and irradiates them to the subject. This X-ray generator is briefly described with reference to FIGS. 1 and 2 as follows.

FIG. 1 is a view schematically showing an example of an X-ray generation unit provided in a conventional X-ray CT imaging apparatus, and FIG. 2 is an exposure dose according to time when the X-ray CT imaging apparatus of FIG. 1 is used. Is a graph showing exposure dose). For reference, the term "exposure dose" means the amount of X-rays irradiated to the subject or the amount of X-rays exposed to the subject.

Referring to FIG. 1, an X-ray generation unit included in a conventional X-ray CT imaging apparatus includes a vacuum tube 10 that maintains an interior in a vacuum state and one side of the vacuum tube 10 to emit hot electrons e. The filament 20, the filament power source 30 for heating the filament 20 by supplying electric power to the filament 20, and the filament 20 in the vacuum tube 10 on the opposite side of the filament 20. Acceleration power source 50 for forming a tube voltage in the vacuum tube to accelerate the hot electrode (e) collided with the emitted hot electrons (e) and the hot electrons (e) emitted from the filament (20) toward the stop electrode 30 side It includes.

The filament 20 is a kind of resistor and emits hot electrons (e) by being heated by receiving power from the filament power source 30. The hot electrons e generated from the filament 20 are accelerated toward the low electrode 40 by an electric field formed between the filament 20 and the low electrode 40 by the accelerating power source 50, and thus the surface of the low electrode 40. Conflict with When the hot electrons (e) collide with the surface of the low electrode 40 as described above, some of the kinetic energy of the hot electrons (e) are converted to X-rays, thereby generating X-rays on the surface of the low electrode 40. The generated X-rays pass through one side of the vacuum tube 10 and are irradiated to the test subject side. The X-ray irradiated to the subject is detected through a detector through the inspector, and the detected data is reconstructed into an image through a predetermined data conversion process.

Referring to FIG. 2, it can be seen that the exposure dose received by the subject remains constant without changing with time. That is, the X-ray generating unit provided in the conventional X-ray CT imaging device irradiates the X-rays of a constant size irrespective of time to the object to be inspected. Therefore, while photographing a subject using a conventional X-ray CT imaging apparatus, the subject may be exposed to X-rays in proportion to the photographing time.

However, it is well known that X-rays are harmful to the human body as a type of radiation. Therefore, when using an X-ray CT imaging apparatus, it is desirable to irradiate a subject with a small amount of X-rays if possible. However, when the conventional X-ray CT imaging apparatus having the above-described X-ray generating unit is used, since the subject receives an exposure dose proportional to the photographing time, there is a problem that the exposure dose to which the subject is irradiated is relatively large. have.

This problem is more pronounced when the subject is a human head. This is because the thyroid gland located in the head of a person is particularly vulnerable to X-rays and is known to have a high probability of cancer if overexposed to X-rays. Therefore, in the X-ray CT imaging apparatus which treats a human head part as a subject like a dental X-ray CT imaging apparatus, it is further required to reduce the exposure dose which a subject receives.

An object of the present invention is to provide an X-ray CT imaging apparatus capable of reducing the exposure dose received by an object, which has been devised to solve the above problems.

The object is based on an X-ray generator that generates X-rays and irradiates the inspected object, a detector for detecting X-rays transmitted through the inspected object, and data about the X-rays detected by the detector. An X-ray CT imaging apparatus having an image output unit for outputting an image of the subject under test, wherein the X-ray generating unit comprises: a vacuum tube for keeping an interior in a vacuum state; A filament disposed on one side of the vacuum tube to emit hot electrons; A filament power supply for heating the filament by supplying power to the filament; A stopping electrode disposed on the opposite side of the filament inside the vacuum tube and colliding with the hot electrons emitted from the filament to generate X-rays; An acceleration power source for generating a tube voltage in the vacuum tube so that hot electrons emitted from the filament can be accelerated toward the stop electrode side; And X-ray irradiation control means for adjusting the irradiation and non-irradiation of the X-ray to the inspected subject periodically.

Herein, the X-ray irradiation control means may include a tube voltage regulator electrically connected to the acceleration power supply to adjust the tube voltage generated by the acceleration power to be generated as a rectangular pulse wave having a predetermined period.

The X-ray irradiation control means may include: a grid arranged adjacent to the filament and forming an electric field in a direction opposite to the direction of the electric field formed by the tube contact pressure in the movement path of the hot electrons near the filament; A grid power source for applying a grid voltage to the grid such that the grid forms the electric field near the filament; And a grid voltage regulator electrically connected to the grid power supply to adjust the grid voltage to be generated as a rectangular pulse wave having a predetermined period.

The X-ray irradiation control means may include an X-ray blocking member disposed adjacent to the outside of the vacuum tube and periodically blocking the X-rays generated by the low electrode and irradiated to the object under test.

The X-ray blocking member alternately includes an X-ray blocking portion for blocking the X-rays irradiated from the low electrode to the subject under test, and a slit for passing the X-ray generated from the low electrode to the test subject side. Is formed in, and disposed adjacent to the outside of the vacuum tube can be rotated at a constant speed.

In addition, the X-ray blocking member may be provided in a disk shape and disposed to be orthogonal to the irradiation direction of the X-ray generated in the stopping electrode.

The X-ray CT imaging apparatus, the base disposed horizontally on the bottom surface; A support frame vertically coupled to the base; An elevating member installed on the support frame to be capable of elevating up and down; And a rotating arm installed on the elevating member so as to be rotated with a rotation axis perpendicular to the bottom surface, wherein the X-ray generating unit is installed at one end of the rotating arm, and the detector It is provided at the other end of the rotary arm, the test subject may be disposed between the one end and the other end of the rotary arm.

Here, the test subject may be a head of a person.

According to the X-ray CT imaging apparatus according to the present invention, the X-ray generating unit is provided with an X-ray irradiation control means, the X-ray irradiation and non-irradiation to the inspected subject periodically occurs during the imaging, thereby causing the exposure to the subject Dose can be reduced.

Hereinafter, with reference to the accompanying drawings will be described embodiments of the present invention; The same reference numerals are assigned to the same components among the embodiments.

First, the X-ray CT imaging apparatus according to the first embodiment of the present invention will be described with reference to FIGS. 3 to 7.

FIG. 3 is a schematic perspective view of an X-ray CT imaging apparatus according to a first embodiment of the present invention, and FIG. 4 is a view showing an X-ray generated from an X-ray generator in the X-ray CT imaging apparatus of FIG. FIG. 5 is a schematic plan view, and FIG. 5 is a diagram schematically illustrating a configuration of an X-ray generator provided in the X-ray CT imaging apparatus of FIG. 3, and FIG. 6 is an acceleration power source provided in the X-ray generator of FIG. 5. FIG. 7 is a graph showing waveforms of generated tube voltages. FIG. 7 is a graph showing exposure doses over time when using the X-ray CT imaging apparatus of FIG. 3.

3, the X-ray CT imaging apparatus according to the first embodiment of the present invention, the base 101, the support frame 102, the guide rod 103, the elevating member 104, and elevating A member driver (not shown), a rotary arm 105, a rotary arm driver (not shown), a data processor (not shown), and an image output unit (not shown) are provided.

The base 101 is horizontally disposed on the bottom surface to support the support frame 102 coupled to the base 101. The base 101 may be provided with a chair on which the patient can sit. The support frame 102 is vertically coupled to the base 101 and the guide rod 103 is fixed to the center portion in the vertical direction.

The elevating member 104 is installed on the guide rod 103 to enable the elevating up and down. That is, the elevating member 104 is coupled to the guide rod 103 so as to be slidable, and the elevating member 104 is provided with a driving force in the vertical direction by the elevating member driver (not shown). Here, the elevating member driving unit may be provided as a linear motor that linearly drives the elevating member 104.

The rotary arm 105 is installed on the lifting member 104 to be rotated with a rotation axis perpendicular to the bottom surface. Rotating arm 105 is provided in a substantially "c" shape and the head of the patient, which is the test subject in the space between the two ends (106, 107) is located. Thus, the rotary arm 105 may rotate about the inspected object at a constant rotation angle range in a state where the inspected object is fixed. The rotary arm 105 is rotationally driven by the rotary arm driver (not shown), and the rotary arm driver may be provided as a motor.

In addition, an X-ray generating unit 108 for generating an X-ray and irradiating the object to be inspected is provided inside one end 106 of the rotating arm 105, and inside the other end 107 of the rotating arm 105. The detector 109 which detects the X-ray which permeate | transmitted the to-be-tested object is provided. Referring to FIG. 4, the X-ray generators 108 and the detectors 109 provided at both side ends 106 and 107 of the rotary arm 105 are disposed to face each other with the test subject H interposed therebetween. Thus, the X-ray irradiated from the X-ray generation unit 108 to the object under test can be detected by the detector 109 after passing through the object under test.

The detector 109 detects X-rays, converts the detected data into a form of an electrical signal, and transmits the detected data to a data processor (not shown). At this time, the detector 109 does not continuously transmit the detected data to the data processor, but detects X-rays for several ms and transmits the detected data to the data processor for several ms. That is, the detector 109 periodically detects X-rays and transfers the detected data while photographing the subject.

The X-ray generator 108 will be described in detail later.

The data processor (not shown) receives data on X-rays detected by the detector 109, and then converts the input data into a form suitable for outputting the image to an image output unit (not shown). . The image output unit (not shown) may be provided as a monitor, and the image output unit implements an image of the internal tissue of the subject as a visual image.

Referring to FIG. 5, the X-ray generator 108 (see FIG. 4) includes a vacuum tube 110, a filament 120, a filament power source 130, a stop electrode 140, and an acceleration power source 150. ) And X-ray irradiation control means (160).

The vacuum tube 110 maintains the interior in a vacuum state. The vacuum tube 110 is preferably made of boron silicate glass having a low X-ray absorption rate.

The filament 120 is disposed on one side inside the vacuum tube 110 and receives electric power from the filament power supply 130 to emit hot electrons. In other words, the filament 120 converts electrical energy provided by the filament power supply 130 into thermal energy as a kind of resistor, and a portion of the thermal energy is provided to the electrons in the filament 120 so that electrons may be emitted from the filament 120. Can be. The filament 120 is preferably made of tungsten having a high melting point and low vaporization, and the filament 120 made of tungsten emits hot electrons when heated to approximately 2200 ° C.

The stop electrode 140 is disposed on the opposite side of the filament 120 in the vacuum tube 110. The cathode of the acceleration power supply 150 is connected to the stop electrode 140, and the cathode of the acceleration power supply 150 is connected to the filament 120. Thus, a tube voltage is formed between the filament 120 and the stop electrode 140 in the vacuum tube. In other words, an electric field is formed between the filament 120 and the stop electrode 140 in the vacuum tube 110 by the acceleration power supply 150.

The hot electrons emitted from the filament 120 by this electric field may be accelerated toward the stop electrode 140 side. The accelerated hot electrons have a very high speed just before they collide with the stop electrode 140. That is, the hot electrons immediately before colliding with the low electrode 140 have a very large kinetic energy, and when the hot electrons collide with the low electrode 140, a part of the kinetic energy possessed by the hot electrons is converted into an X-ray shape. Through this process, the X-rays are generated in the stop electrode 140, and the generated X-rays are transmitted to one side of the object through the one side of the vacuum tube 110.

The X-ray irradiation control means 160 adjusts such that irradiation and non-irradiation of X-rays to the inspected object occur periodically. As described above, the conventional X-ray CT imaging apparatus continuously irradiates the X-rays of a constant intensity on the object during the imaging of the object. On the other hand, the X-ray CT imaging apparatus of this embodiment includes X-ray irradiation control means 160 to reduce the exposure dose received by the subject, and as a result, X-ray irradiation and non-irradiation of the subject照射 occurs periodically.

The X-ray irradiation control means 160 is provided as a tube voltage regulator 160 that is electrically connected to the acceleration power supply 150 in this embodiment to adjust the tube voltage.

The tube voltage adjusted by the tube voltage regulator 160 appears as shown in FIG. 6. Referring to FIG. 6, it can be seen that the tube voltage is generated as a rectangular pulse wave having a certain period rather than being maintained at a constant magnitude. That is, during the imaging of the subject, the tube voltage is maintained at a constant magnitude for several ms and disappears for several ms.

As described above, the hot electrons emitted from the filament 120 may be accelerated toward the stop electrode 140 by an electric field formed in the vacuum tube 110. Therefore, as a result of the tube voltage being generated as a rectangular pulse wave in the vacuum tube 110, the hot electrons emitted from the filament 120 are also accelerated for several ms and not accelerated for several ms. Thus, even in the low electrode 140 where X-rays are generated due to collision with hot electrons, X-rays may be generated for several ms and X-rays may not be generated for several ms. As a result, by providing the tube voltage regulator 160, the X-ray generator 108 (see FIG. 4) of the present embodiment irradiates X-rays periodically changing to the inspected object side.

Therefore, when using the X-ray CT imaging apparatus of this embodiment, the exposure dose received by the subject is represented by a rectangular waveform as shown in FIG. Therefore, as compared with the conventional X-ray CT imaging apparatus in which X-rays of a certain intensity are irradiated onto the subject, as shown in FIG. 2, the X-ray CT imaging apparatus of the present embodiment can greatly reduce the dose of the subject.

For reference, since the detector 109 periodically detects the X-ray and transmits the detected data while photographing the subject, even if the detector 109 does not irradiate the subject under X-rays while transmitting the data to the data processing unit. It's not impossible to get a video. Therefore, even if the subject is irradiated with X-rays such that the dose is represented by a rectangular pulse wave as shown in FIG. 7, the internal tissue of the subject can be imaged.

Next, an X-ray CT imaging apparatus according to a second embodiment of the present invention will be described with reference to FIGS. 6 to 8.

FIG. 8 is a view schematically showing the configuration of an X-ray generator provided in the X-ray CT apparatus according to the second embodiment of the present invention.

The configuration of the X-ray CT imaging apparatus according to the present embodiment except for the X-ray irradiation control means is the same as the configuration of the X-ray CT imaging apparatus according to the first embodiment described above. Therefore, the description of the components of the present embodiment that are the same as the first embodiment will be omitted, and the X-ray irradiation control means according to the present embodiment will be described in detail.

Referring to FIG. 8, the X-ray irradiation control means 160a according to the present embodiment includes a grid power supply 161, a grid 163, and a grid voltage regulator 162.

The grid power supply 161 applies a grid voltage to the grid 163.

The grid 163 is disposed adjacent to the filament 120 and receives a grid voltage from the grid power supply 161. The grid 163 thus creates an electric field in the hot electron transport path adjacent to the filament 20. In this case, the direction of the electric field formed by the grid 163 on the hot electron moving path is opposite to the direction of the electric field formed by the acceleration power supply 150. Accordingly, the electric field formed by the grid 163 prevents the hot electrons emitted from the filament 120 from being accelerated toward the stop electrode 140, unlike the electric field formed by the acceleration power supply 150.

The grid voltage regulator 162 is electrically connected to the grid power supply 161 to adjust the grid voltage applied from the grid power supply 161 to the grid 163 to be a rectangular pulse wave having a predetermined period. Thus, the grid voltage generated by the grid power supply 161 has a rectangular pulse waveform as shown in FIG. 6, similarly to the tube voltage in the first embodiment of the present invention described above.

Therefore, the electric field generated by the grid 163 near the filament 120 also repeats the generation and disappearance at the same period as the grid voltage.

Thus, when an electric field generated by the grid 163 is generated near the filament 120, hot electrons emitted from the filament 120 are prevented from being accelerated toward the low electrode 140 by the electric field generated by the grid 163. . In this case, since the hot electrons may not collide with the low electrode, X-rays are not generated in the low electrode 140.

On the other hand, when no electric field is generated by the grid 163 near the filament 120, the hot electrons generated in the filament 120 may be accelerated toward the low electrode 140 by the electric field generated by the acceleration power supply 150. have. In this case, since the hot electrons may collide with the low electrode 140, X-rays are generated in the low electrode 140.

Therefore, when the grid voltage is applied to the grid 163 by the grid voltage regulator 162 in a rectangular waveform, X-rays are periodically generated in the low electrode 140. Thus, when the X-ray CT imaging apparatus of the present embodiment is used, the exposure dose received by the subject is shown as in FIG. 7 as in the first embodiment described above. As a result, in the case of using the X-ray CT imaging apparatus of the present embodiment, it is possible to greatly reduce the exposure dose received by the subject under comparison with the conventional X-ray CT apparatus.

Next, an X-ray CT imaging apparatus according to a third embodiment of the present invention will be described with reference to FIGS. 7, 9, 10A, and 10B.

FIG. 9 is a view schematically showing a configuration of an X-ray generator provided in an X-ray CT apparatus according to a third embodiment of the present invention, and FIG. 10A illustrates an X-ray blocking member provided in the X-ray generator of FIG. 9. FIG. 10B is a view schematically showing how the X-rays pass, and FIG. 10B is a view schematically showing how X-rays are blocked by the X-ray blocking member provided in the X-ray generator of FIG. 9.

Among the configurations of the X-ray CT imaging apparatus according to the present embodiment, the configurations except for the X-ray irradiation control means are provided in the same manner as the configuration of the X-ray CT imaging apparatus according to the first embodiment described above. Therefore, the description of the components of the present embodiment that are the same as the first embodiment will be omitted, and the X-ray irradiation control means according to the present embodiment will be described in detail.

9, the X-ray irradiation control means 160b which concerns on a present Example is provided as X-ray blocking member 160b. The X-ray blocking member 160b is disposed adjacent to the outside of the vacuum tube 110 to periodically block X-rays generated by the low electrode 140 and irradiated to the object under test.

Accordingly, the X-ray blocking member 160b is provided in the shape of a disk, as shown in FIGS. 10A and 10B, and is disposed to be substantially orthogonal to the irradiation direction of the X-ray generated from the stop electrode 140. In addition, the X-ray blocking member 160b is provided to rotate at a constant speed.

In the X-ray blocking member 160b, a substantially flat fan-shaped slit 164 is formed regularly in the circumferential direction where the X-rays can pass. A portion of the X-ray blocking member 160b in which the slit 164 is not formed constitutes an X-ray blocking unit 165 for blocking X-rays. In this case, the X-ray blocking unit 165 may be made of lead or copper having a high X-ray absorption rate. As a result, the X-ray blocking member 160b has a shape in which a plurality of slits 164 and a plurality of X-ray blocking portions 165 are alternately disposed along the circumferential direction.

Thus, when the slit 164 is located on the path of the X-rays generated by the low electrode 140 as shown in FIG. 10A, the X-rays may be irradiated onto the subject without being blocked by the X-ray blocking member 160b. . On the other hand, when the X-ray blocking part 165 is located on the X-ray irradiation path generated from the low electrode 140 as shown in FIG. 10B, the X-ray is blocked by the X-ray blocking member 160b to be irradiated to the subject. Can't.

Therefore, when the X-ray blocking member 160b rotates at a constant speed outside the vacuum tube 110, the exposure dose received by the inspected object is a rectangular waveform having a constant period as in FIG. 7 as in the first embodiment described above. Will appear. As a result, in the case of using the X-ray CT imaging apparatus of the present embodiment, it is possible to greatly reduce the exposure dose received by the subject under comparison with the conventional X-ray CT apparatus.

As described above, according to the X-ray CT imaging apparatus according to the first to third embodiments of the present invention, by providing the X-ray irradiation control means (160, 160a, 160b) it is possible to reduce the exposure dose received by the subject have. Thus, the head part of the person under test can be prevented from being excessively exposed to X-rays during imaging.

In the first to third embodiments of the present invention described above, only the case in which the subject is a human head is described. However, the present invention may be applied to an X-ray CT imaging apparatus for inspecting a portion other than the human head. Will be apparent to those skilled in the art.

1 is a view schematically showing an example of an X-ray generator provided in a conventional X-ray CT imaging apparatus.

FIG. 2 is a graph illustrating an exposure dose with time in the case of using the X-ray CT imaging apparatus of FIG. 1.

3 is a schematic perspective view of the X-ray CT imaging apparatus according to the first embodiment of the present invention.

4 is a plan view schematically illustrating a state in which an X-ray generated from an X-ray generator is irradiated to the detector side in the X-ray CT imaging apparatus of FIG. 3.

FIG. 5 is a diagram schematically illustrating a configuration of an X-ray generator provided in the X-ray CT imaging apparatus of FIG. 3.

6 is a graph illustrating a waveform of a tube voltage generated by an acceleration power source provided in the X-ray generator of FIG. 5.

FIG. 7 is a graph illustrating an exposure dose with time in the case of using the X-ray CT imaging apparatus of FIG. 3.

FIG. 8 is a view schematically showing the configuration of an X-ray generator provided in the X-ray CT apparatus according to the second embodiment of the present invention.

FIG. 9 is a diagram schematically illustrating a configuration of an X-ray generator provided in an X-ray CT apparatus according to a third exemplary embodiment of the present invention.

FIG. 10A is a view schematically illustrating an X-ray passing through an X-ray blocking member provided in the X-ray generating unit of FIG. 9.

FIG. 10B is a view schematically illustrating a state in which X-rays are blocked by an X-ray blocking member provided in the X-ray generating unit of FIG. 9.

* Description of Major Symbols in Drawings *

101: base 102: support frame

103: guide rod 104: elevating member

105: rotary arm 108: X-ray generator

109: detector 110: vacuum tube

120: filament 130: filament power

150: acceleration power 160: tube voltage regulator

161: grid power supply 162: grid voltage regulator

163: grid 160b: X-ray blocking member

164: slit 165: X-ray blocking part

Claims (8)

An X-ray generator that generates X-rays and irradiates the inspected object, a detector that detects X-rays transmitted through the inspected object, and the inspected object based on data about the X-rays detected by the detector. An X-ray CT imaging apparatus having an image output unit for outputting an image for The X-ray generator, A vacuum tube for keeping the interior in a vacuum state; A filament disposed on one side of the vacuum tube to emit hot electrons; A filament power supply for heating the filament by supplying power to the filament; A stopping electrode disposed on the opposite side of the filament inside the vacuum tube and colliding with the hot electrons emitted from the filament to generate X-rays; An acceleration power source for generating a tube voltage in the vacuum tube so that hot electrons emitted from the filament can be accelerated toward the stop electrode side; And And X-ray irradiation control means for adjusting the irradiation and non-irradiation of the X-ray to the subject periodically occur. The method of claim 1, wherein the X-ray irradiation control means, And a tube voltage regulator electrically connected to the acceleration power source to adjust the tube voltage generated by the acceleration power source to be generated as a rectangular pulse wave having a predetermined period. The method of claim 1, wherein the X-ray irradiation control means, A grid disposed adjacent to the filament and forming an electric field in a direction opposite to the direction of the electric field formed by the tube contact pressure, in the movement path of the hot electrons near the filament; A grid power source for applying a grid voltage to the grid such that the grid forms the electric field near the filament; And And a grid voltage regulator electrically connected to the grid power supply to adjust the grid voltage to be generated as a rectangular pulse wave having a predetermined period. The method of claim 1, wherein the X-ray irradiation control means, And an X-ray blocking member disposed adjacent to the outer side of the vacuum tube and periodically blocking the X-rays generated by the low electrode and irradiated to the object under test. The method of claim 4, wherein the X-ray blocking member, An X-ray blocking portion for blocking the X-rays irradiated from the low electrode to the test object and a slit for passing the X-rays generated from the low electrode to the test object side are alternately formed. An x-ray CT imaging apparatus, characterized in that adjacently arranged to rotate at a constant speed. The method of claim 5, wherein the X-ray blocking member, An X-ray CT imaging apparatus, characterized in that it is provided in a disk shape and arranged to be orthogonal to the irradiation direction of the X-rays generated in the low electrode. The method according to any one of claims 1 to 6, A base disposed horizontally on the bottom surface; A support frame vertically coupled to the base; An elevating member installed on the support frame to be capable of elevating up and down; And And a rotation arm installed on the elevating member to be rotated with a rotation axis perpendicular to the bottom surface. The X-ray generating unit is installed on one side end of the rotary arm, the detector is installed on the other end of the rotary arm, the test subject is characterized in that disposed between the one end and the other end of the rotary arm. X-ray CT imaging device. The method of claim 7, wherein the test subject, An X-ray CT imaging apparatus, characterized in that the human head.

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