KR101307673B1 - Images obtaining method synchronized with respiration for computed tomography scanner - Google Patents

Abstract

PURPOSE: A respiration-synchronized image acquisition method for computed tomography (CT) scanner is provided to analyze a photographed CT image without external factors, thereby preventing the deterioration of accuracy of photographing caused by the external factor. CONSTITUTION: A respiration-synchronized image acquisition method for CT scanner comprises the steps of: rotating and moving a gantry; obtaining sequentially a plurality of CT images by an X-ray detector while the gantry rotates (S12); generating a difference image between each of the plurality of CT images and a previous CT image adjacent to each of the plurality of CT images (S13); outputting a respiration synchronization signal if similarity between the difference images is more than a predetermined reference value, and setting a CT image corresponding the difference image in response to the respiration synchronization signal as a respiration synchronization image (S15-S17); and completing the photographing if a plurality of respiration synchronization images for a subject is obtained at all predetermined angles (S18,S19). [Reference numerals] (AA) Start; (BB,DD) No; (CC,EE) Yes; (FF) End; (S11) Set an area of interest; (S12) Obtain sequentially a plurality of CT images; (S13) Generate a difference image between a previous angle image and the current angle image; (S14) Calculate a similarity level between difference images; (S15) Decide whether the similarity level is larger than a reference value; (S16) Output a respiration synchronization signal; (S17) Set a respiration synchronization image; (S18) Decide if a plurality of respiration synchronization images for a subject is obtained at all predetermined angles; (S19) Complete the photographing

Description

Respiratory Synchronization Image Acquisition Method of Computerized Tomography System {IMAGES OBTAINING METHOD SYNCHRONIZED WITH RESPIRATION FOR COMPUTED TOMOGRAPHY SCANNER}

The present invention relates to a method for acquiring a respiratory synchronous image of a computerized tomography apparatus, and more particularly to a method for acquiring a respiratory synchronous image of a computerized tomography apparatus using only a captured image of a computerized tomography apparatus, excluding external factors.

In general, tomography imaging using a computerized tomography scanner (CT scanner) is performed by using an X-ray irradiator and a gantry equipped with an X-ray detector. A tomography image is obtained by performing imaging while rotating around an anesthetized animal or a person breathing on a couch disposed between line detectors.

While the X-ray computed tomography apparatus photographs an animal or a person, motion artifacts are caused in the acquired tomography image when movement occurs due to the breathing movement of the animal or the person. Here, motion artifacts are shades in which the image does not look right but appears blurred and shaken.

The motion artifacts of such tomographic images are a major cause of lowering the spatial resolution (special resolution) and the signal to noise ratio (SNR) of the X-ray computed tomography apparatus.

Fig. 1 shows an example of a conventional CT apparatus.

1, the computed tomography apparatus 100 includes an X-ray irradiator 110, a needle bed 130, a gantry 140, a gantry motor 150, a camera 160, a bed support 170, A breathing image display unit 180, a breathing image processing unit 190, and a breathing recognition unit 190a.

The X-ray irradiator 110 irradiates an X-ray to photograph a tomographic image.

The X-ray detector 120 is irradiated from the X-ray irradiator 110 by performing imaging when the respiratory sync signal is input in a state in which the X-ray radiator 110 is disposed to face each other. The line is detected to acquire a tomography image and output a photographing signal.

The needle bed 130 is disposed between the X-ray irradiator 110 and the X-ray detector 120, and the object to be imaged is fixed. At this time, the subject to be photographed can perform an anesthesia breathing exercise.

An X-ray irradiator 110 is fixed to the upper end of the gantry 140, an X-ray detector 120 is fixed to the lower end thereof, and the gantry 140 is supported by a support 141.

The gantry motor 150 rotates the gantry 140 at a predetermined angular velocity about a rotation axis 151 that is rotatably fixed near the center between the upper and lower ends of the gantry 140.

The camera 160 is fixed to one side of the bed 130 and photographs the abdomen or chest area of the subject to be photographed, which is fixed on the bed 130 and anesthetized. The camera 160 can photograph the abdomen or the chest area of the subject to be photographed at least 30 frames per second. As the camera 160, a CCD camera having an infrared (IR) LED illumination device may be used.

The needle bed support 170 supports the X-ray irradiator 110 and the X-ray detector 120 (see FIG. 1) by transferring the upper plate 171 fixing the needle bed 130 to which the camera 160 is fixed by the electric motor M, Ray source 110 and the X-ray detector 120, the needle bed 130 is placed at the origin position for exchanging the sample (for example, the object to be imaged) . The structure in which the upper plate 171 of the needle bed support 170 is reciprocated by the electric motor M as shown in Fig. 1 can be realized by a reciprocating transportation structure using a ball screw, an LM guide, or the like.

The respiration image display unit 180, the respiration image processing unit 190, and the respiration recognition unit 190a are respiration detection units for sensing respiration of the object to be imaged.

The respiration image display unit 180 converts the image of the abdomen or chest area of the subject to be imaged by the camera 160 in real time onto the bed 130, and displays the converted digital image as a screen.

The respiration image processing unit 190 generates position displacement data according to a temporal change of the window image selected by the user at a specific size among the images displayed on the respiratory image display unit 180.

The respiration image processing unit 190 estimates the motion vector of the current window image and the previous window image based on the coordinates of the center of the current window image and the center coordinates of the previous window image, And obtains the similarity between the current window image and the previous window image at the compensated position as the positional displacement data and transmits the positional displacement data to the respiration recognition unit 190a.

The respiration recognition unit 190a acquires a respiration cycle in which the inspiration and expiration of the object to be imaged are repeated from the positional displacement data according to the time change generated by the respiration image processor 190 and measures the respiration rate based on the acquired respiration cycle And generates a breathing synchronization signal for synchronizing the X-ray detector 120 to be photographed when the respiratory motion is temporarily stopped.

The CT apparatus of FIG. 1 photographs the abdomen or chest of a subject breathing in an anesthesia state to remove motion artifacts with the camera 160, acquires the respiratory cycle of the animal from the image of the camera 160 A method of synchronizing the point of time when the respiration of the subject stops and the point of time of photographing is used.

However, there is a problem that the breathing synchronization method by the camera 160 may become anxiety factor of photography due to the influence of the external lighting due to the characteristics of the camera.

Another technique used to remove motion artifacts is to use a ventilator to synchronize the subject's breath and the time of the shot. The synchronizing method using the ventilator is a method of photographing a subject when breathing is stopped by artificially controlling the breathing cycle of the subject. The breathing synchronization method using the artificial respirator has a problem that the state of the subject may not be normal because the breathing cycle of the subject is artificially controlled.

Another way to remove motion artifacts is to use anesthesia to slow the subject's breathing cycle, and then to synchronize breathing and imaging using an air pressure sensor attached to the subject's abdomen or chest. Synchronous method using the air pressure sensor attaches the air pressure sensor to the subject's abdomen or chest, so external elements other than the X-ray computed tomography system exist like the camera's respiratory sync method, so accurate respiration is not performed. You may not.

SUMMARY OF THE INVENTION An object of the present invention is to provide a method for acquiring a respiratory synchronous image of a computed tomography apparatus which excludes an external element and obtains a computed tomography image in which a subject and a breath are synchronized using only a tomography image photographed by the computed tomography apparatus. It is.

Respiratory synchronization image acquisition method of a computerized tomography apparatus for achieving the above object is fixed to the gantry rotated by a gantry motor computerized tomography having an X-ray irradiator and X-ray detector to take a tomography image A method for acquiring a respiratory synchronous image of a device, the method comprising: rotating the gantry; Sequentially obtaining a plurality of tomographic images by the X-ray detector while the gantry is rotated; Generating a difference image between each of the plurality of tomography images and a previous tomography image adjacent to each of the plurality of tomography images; If a similarity between the plurality of difference images is equal to or greater than a predetermined reference value, a respiration synchronization signal is output, and a tomography image corresponding to the difference image is set as a respiration synchronization image in response to the respiration synchronization signal; And ending photographing when a plurality of respiratory synchronization images of the subject are obtained at all preset angles; .

The similarity between the plurality of difference images may be calculated by using sum of absolute differences (SAD).

The setting of the respiratory synch image may include calculating the SAD between the plurality of difference images; Determining whether the calculated SAD is equal to or less than a preset reference SAD value; Outputting the respiratory sync signal if the SAD is less than or equal to the reference SAD value; And setting a tomography image corresponding to the difference image as a respiration synchronization image in response to the respiration synchronization signal. And a control unit.

Respiratory synchronization image acquisition method of the computed tomography apparatus comprises the steps of setting the region of interest to be photographed in the subject before the step of moving the gantry; And further comprising:

The region of interest is characterized in that the diaphragm region of the subject is set to facilitate checking of the breathing state of the subject.

The step of rotating the gantry is characterized in that the gantry is rotated regardless of the breathing state of the subject.

The step of terminating the photographing may include determining whether the rotational speed of the gantry reaches a preset maximum rotational speed when it is determined that the respiration synchronization image for all the angles has not been obtained; If it is determined that the rotational speed of the gantry reaches the maximum rotational speed, the rotation of the gantry is stopped, and the gantry is moved to a position for an unacquired respiratory sync image; And obtaining a tomography image for the respiratory sync image non-acquisition angle; And further comprising:

The acquiring of the image for the non-acquisition section may include acquiring an image regardless of the breathing state of the photographing target.

Therefore, the respiratory synchronous image acquisition method of the computed tomography apparatus of the present invention can extract the respiratory synchronous image of the subject by analyzing the tomography image photographed by the computed tomography apparatus without any external factors. Falling can be prevented and stable observation can be performed since the state of the subject is not artificially manipulated.

Fig. 1 shows an example of a conventional CT apparatus.
2 shows a CT apparatus according to an embodiment of the present invention.
FIG. 3 illustrates a method for acquiring respiratory synchronous images of the computed tomography apparatus of FIG. 2.
4 illustrates an example of an ROI setting step of FIG. 3.
FIG. 5 illustrates an example of a tomography image acquired for each angle in the subject photographing step of FIG. 3.
FIG. 6 illustrates a difference image between angle-specific images of FIG. 5.
7 shows a graph comparing similarities between a plurality of difference images.
8 shows a graph confirming whether the acquired images are synchronized with respiration.

In order to fully understand the present invention, operational advantages of the present invention, and objects achieved by the practice of the present invention, reference should be made to the accompanying drawings and the accompanying drawings which illustrate preferred embodiments of the present invention.

Hereinafter, the present invention will be described in detail with reference to the preferred embodiments of the present invention with reference to the accompanying drawings. However, the present invention can be implemented in various different forms, and is not limited to the embodiments described. In order to clearly describe the present invention, parts that are not related to the description are omitted, and the same reference numerals in the drawings denote the same members.

Throughout the specification, when an element is referred to as " including " an element, it does not exclude other elements unless specifically stated to the contrary. The terms "part", "unit", "module", "block", and the like described in the specification mean units for processing at least one function or operation, And a combination of software.

2 shows a CT apparatus according to an embodiment of the present invention.

The configuration of the computed tomography apparatus 100 'according to the present invention shown in FIG. 2 is similar to that of the computerized tomography apparatus 100 shown in FIG. 1, the X-ray irradiator 110, the needle 130, the gantry 140, the gantry motor 150, the needle support 170, and the top plate 171 of the CT apparatus 100 ' Is the same as that of the computerized tomography apparatus 100. However, the CT apparatus 100 'of FIG. 2 does not have a separate camera 160. Since the computerized tomography apparatus 100 'does not include the camera 160, a breathing detection unit (a breathing image display unit 180 and a respiration detection unit 180 in FIG. 1) for sensing respiration of a subject using an image acquired from the camera 160, Image processing unit 190 and respiration recognition unit 190a).

The computed tomography apparatus 100 ′ of FIG. 2 includes an image processor 200 that processes a tomography image photographed by the computed tomography apparatus 100 ′ without a breath detector. The image processor 200 includes an image acquisition unit 210, a difference image generation unit 220, a similarity determination unit 230, and a respiratory sync image storage unit 240.

The image processor 200 acquires a plurality of tomography images captured by the computed tomography apparatus 100 ′. In this case, the plurality of tomography images are images obtained while the gantry 140 is rotated. The computerized tomography apparatus 100 ′ of the present invention rotates the gantry 140 regardless of the breathing state of the subject when the imaging is started. To shoot the subject from various angles.

In the computed tomography apparatus 100 ′ of the present invention, the gantry 140 may stop at a specific angle and photograph the subject, and then move to the next set angle, while the gantry 140 continuously rotates the subject at a predetermined angle. A plurality of tomography images may be obtained by photographing.

The difference image generator 220 generates and stores a difference image between tomographic images between angles adjacent to each other among a plurality of images acquired by the image acquirer. The difference image may be generated as a difference between the tomography image acquired at the previous angle and the tomography image obtained at the current angle.

The similarity determination unit 230 determines similarity according to time change between a plurality of difference images generated and stored by the difference image generation unit 220 by using sum of absolute differences (SAD), and the similarity is greater than or equal to a preset reference value. If so, it outputs a breathing synchronous signal.

The respiratory sync image storage unit 240 selects the tomographic images outputted by the respiratory sync signal among the plurality of tomographic images acquired by the image acquirer 210 and stores the respiratory sync images, and the respiratory sync images are set at all angles. Determine if it is saved. That is, it is determined whether a respiratory synch image is acquired from all angles with respect to the subject to determine whether additional tomography image is required.

In FIG. 2, the image processing unit 200 is illustrated as a separate device from the computerized tomography apparatus 100 ′, but this is for convenience of description, and the image processing unit 200 is a control unit of the computerized tomography apparatus 100 ′. It may be included in the configuration (not shown), and may be implemented as software.

3 is a diagram illustrating a method for acquiring a respiratory synchronous image of the computed tomography apparatus of FIG. 2, FIG. 4 is an example of a region of interest setting in FIG. 3, and FIG. 6 illustrates an image of a difference between angle-specific images of FIG. 5.

Referring to FIGS. 3 to 6, the method for acquiring a respiratory synchronous image according to the present invention will be described. First, the region of interest IA to be captured by the subject is set as shown in FIG. 4 (S11). The region of interest IA refers to a region that the user wishes to observe with respect to a subject which is a subject. That is, it represents a specific part of the subject to be observed in the experiment. The region of interest IA may be simply an area to be observed in the experiment, but as shown in FIG. 4, when the breathing occurs in the subject in order to easily obtain the respiratory synch image, the diaphragm is most easily identified. The site may be set to the region of interest IA.

The region of interest IA may be set by a user applying a command to the CT apparatus 100 ', and the CT apparatus 100' may receive a user's command or display the set region of interest IA to the user. An interface unit (not shown) may be further provided.

When the region of interest IA is set, the computed tomography apparatus 100 ′ continuously rotates and starts continuous shooting of the subject (S12). Here, the computerized tomography apparatus 100 ′ may stop the rotation of the gantry at a preset angle to photograph the subject and rotate the subject again after the subject is photographed. The subject may be rotated continuously without stopping at a plurality of preset angles. By photographing a plurality of tomography images taken from different angles may be obtained. In addition, the image acquisition unit 210 of FIG. 2 sequentially acquires a plurality of tomographic images to the subject photographed at each angle and transmits the plurality of tomography images to the difference image generation unit 220.

The tomography image of FIG. 5 represents three tomography images a, b, and c photographed from adjacent angles among a plurality of tomography images photographed from different angles, and all of them are photographed with respect to the region of interest IA set in FIG. 4. It can be seen that. In FIG. 5, (a) shows a tomography image photographed at a previous angle, (b) shows a tomography image photographed at a current angle, and (c) shows a tomography image photographed at a next angle.

The difference image generator 220 generates and stores a difference image between the tomography image acquired at the current angle and the tomography image acquired at the previous angle among the plurality of tomography images sequentially applied (S13). Likewise, a difference image is generated and stored in comparison with the previous tomography image for the subsequently applied tomography image. That is, when the (b) image is obtained from the three tomography images illustrated in FIG. 5, the difference image generator 220 generates a difference image by comparing the (a) tomography image and (b) the tomography image, and (c) When a tomography image is obtained, a difference image is generated by comparing the tomography image with the tomography image.

In FIG. 6, (a) is a difference image generated by comparing (a) tomography image and (b) tomography image of FIG. 5, and (b) is comparing (b) tomography image and (c) tomography image of FIG. The difference image is generated.

Thereafter, the similarity determining unit 230 calculates similarity between the stored difference images (S14). In the respiratory synchronous image acquisition method according to the present invention, the similarity may be obtained using SAD (Sum Of Absolute Differences) as an example. Since SAD is a well-known technique, it will not be described separately. In addition to the SAD, other techniques for determining similarity of an image, such as sum of squared differences (SSD), may be applied.

The method of acquiring the respiratory synchronous image of the present invention does not directly determine the similarity from the tomography image acquired by the image acquisition unit 210, but generates a difference image, and determining the similarity between the difference images accurately determines the state of breathing of the subject. This is to determine. There is an inhale and an exhalation when a creature breathes. The computerized tomography apparatus 100 'is preferable to photograph the subject when the breathing is temporarily stopped to remove the motion artifact as described above, but the breathing changes from exhalation to exhalation and from exhalation to exhalation. In two cases, the image is temporarily stopped, and the CT apparatus 100 ′ does not distinguish between the case where the subject's breathing stops in inhalation and the case where he stops in exhalation. In each of the inhalation and exhalation, the state of the subject varies depending on the state of the breathing stopped.

That is, when a similar tomography image is selected by calculating similarity between the tomography images acquired by the image acquisition unit 210, the CT apparatus 100 ′ stops the breathing of the subject in the inhalation and the exhalation. In this case, since the state of the subject is different from each other according to the state in which the breathing is stopped in each of the inhalation and the exhalation, motion artifacts occur.

In this regard, the computed tomography apparatus 100 ′ generates a difference image between a tomography image acquired at a previous adjacent angle and a current acquired tomography image, and calculates similarity for the difference image, thereby breathing in a state where breathing stops and exhales. This stopped state can be determined. Therefore, the similarity determining unit 230 may calculate the similarity to distinguish and distinguish not only the stop state of the breath of the subject but also the stop state in the inhalation and the stop state in the exhalation.

In operation S15, the calculated similarity is determined to be equal to or greater than a predetermined reference value. Here, the expression that the degree of similarity is higher than the reference value is an expression for understanding according to the expression of similarity. When the similarity is calculated by using the SAD, the SAD value is actually similar to each other. Therefore, the step of determining whether the similarity is equal to or greater than the predetermined reference value is the same as determining whether the SAD value is equal to or smaller than the predetermined reference SAD value.

If the similarity is greater than or equal to the reference value (the SAD value is less than or equal to the reference SAD value), the similarity determination unit 230 outputs a respiration synchronization signal, indicating that the tomographic image acquired at the previous angle and the tomographic image obtained at the current angle are high similarities. It is displayed (S16).

When the respiratory sync image storage unit 240 receives the respiratory sync signal, the tomography image acquired at the current angle and the tomography image obtained at the previous angle are set and stored as the respiratory sync image (S17). However, if no breath sync signal is received, the tomography image obtained at the current angle is not stored.

In addition, the respiratory sync image storage unit 240 determines whether the stored respiratory sync images are acquired for all preset angles (S18). If the respiratory synch image is acquired from all angles as a result of the determination, the shooting is terminated (S19). However, if it is determined that there is an angle at which the respiratory sync image is not obtained, the gantry continuously rotates to photograph the subject and additionally acquires the tomography image (S12).

In the present invention, the gantry motor 150 starts to rotate when the computerized tomography apparatus 100 'starts to take the tomography image, and stops the rotation when the imaging is completed. That is, in the present invention, the gantry motor 150 rotates irrespective of the breathing of the photographing target, and thus the X-ray irradiator 110 and the X-ray detector 120 may also be irrelevant to the breathing of the photographing subject. Rotate continuously according to the rotation speed.

7 shows a graph comparing similarities between a plurality of difference images.

In FIG. 7, each of the three graphs shows the SAD value between the difference images for the tomographic images obtained by the gantry at the 1 st to 3 rd rotations. As described above, the computed tomography apparatus 100 ′ according to the present invention determines the similarity between the difference images using the SAD, and if the SAD value is less than or equal to the reference value according to the characteristics of the SAD, the two images are determined to be similar. Can be. In addition, as shown in FIG. 7, it is often difficult to obtain a tomography image having high similarity at all angles with one rotation of the gantry. In some cases, even to three rotations, it is difficult to obtain a tomography image having high similarity at all angles. In some cases. That is, a high degree of similarity may not be obtained from a tomography image acquired during one to three rotations of the gantry at a specific angle.

In FIG. 7, all of the difference images around 25 degrees in the SAD value between the difference images acquired while the gantry is rotated three times are marked with high SAD. In the present invention, when the SAD value is 170 or less, it may be determined that the respiratory sync signal is output by determining that the image is acquired in a stable state of breathing.

8 shows a graph confirming whether the acquired images are synchronized with respiration.

FIG. 8 graphically shows the SAD values between the respiratory synch signals obtained during one to three rotations of the gantry in the graph of FIG. In FIG. 7, the SAD was high in all images near 25 degrees while the gantry was rotated three times. Thus, in the graph of FIG. That is, for images around 25 degrees among the images of the subject acquired during 1 to 3 rotations, it indicates that a respiratory synchronized stable image was not obtained.

In this case, the computed tomography apparatus 100 ′ according to the present invention may rotate the gantry to photograph the subject.

However, in some cases, the maximum rotational speed of the gantry (for example, 5 rotations) is preset, and the respiratory synch image for all angles is not obtained from the tomographic images acquired until the gantry reaches the maximum rotational speed. If determined, the gantry may be moved and fixed at an angle at which the respiratory sync image is not obtained, and then the respiratory sync image may be obtained by photographing a subject.

That is, when it is determined that the number of revolutions of the gantry reaches the maximum number of revolutions, the continuous rotation of the gantry is stopped, the gantry is moved at a position angle with respect to the non-acquisition section of breath synchronization, and when the gantry is moved to the non-acquisition section, it is not acquired. An image of a section may be obtained.

Here, when acquiring an image for the unacquired section, it may be assumed that the unacquired section is very small (for example, two sections or less), and the image may be taken regardless of the breathing state of the photographing subject. This is because the error of the tomographic image is not large because the unacquired section is relatively small compared to the entire image section.

The apparatus according to the present invention can be implemented as a computer-readable code on a computer-readable recording medium. A computer-readable recording medium includes all kinds of recording apparatuses in which data that can be read by a computer system is stored. Examples of the recording medium include a ROM, a RAM, a CD-ROM, a magnetic tape, a floppy disk, an optical data storage device, and the like, and a carrier wave (for example, transmission via the Internet). The computer readable recording medium can also be distributed over network coupled computer systems so that the computer readable code is stored and executed in a distributed fashion.

While the present invention has been particularly shown and described with reference to exemplary embodiments thereof, it is evident that many alternatives, modifications and variations will be apparent to those skilled in the art.

Therefore, the true technical protection scope of the present invention will be defined by the technical spirit of the appended claims.

Claims (8)

In the respiratory synchronization image acquisition method of a computerized tomography apparatus having an X-ray irradiator and an X-ray detector fixed to face each other on a gantry rotated by a gantry motor to take a tomography image,
The gantry is rotated and moved;
Sequentially obtaining a plurality of tomographic images by the X-ray detector while the gantry is rotated;
Generating a difference image between each of the plurality of tomography images and a previous tomography image adjacent to each of the plurality of tomography images;
If a similarity between the plurality of difference images is equal to or greater than a predetermined reference value, a respiration synchronization signal is output, and a tomography image corresponding to the difference image is set as a respiration synchronization image in response to the respiration synchronization signal; And
Ending photographing when a plurality of respiratory synchronization images of the subject are obtained at all preset angles; Respiratory synchronous image acquisition method of a computed tomography device comprising a.
The method of claim 1, wherein the similarity between the plurality of difference images is
Respiratory synchronous image acquisition method of a computed tomography device, characterized in that calculated using SAD (Sum Of Absolute Differences).
The method of claim 2, wherein the setting of the respiratory sync image is
Calculating the SAD between the plurality of difference images;
Determining whether the calculated SAD is equal to or less than a preset reference SAD value;
Outputting the respiratory sync signal if the SAD is less than or equal to the reference SAD value; And
Setting a tomography image corresponding to the difference image as a respiration synchronization image in response to the respiration synchronization signal; Respiratory synchronous image acquisition method of a computed tomography apparatus comprising a.
The method of claim 1, wherein the respiratory synchronization image acquisition method of the computed tomography apparatus is
Setting a region of interest to be captured by the subject before the gantry is moved; Respiratory synch image acquisition method of a computed tomography device further comprising a.
The method of claim 4, wherein the region of interest is
And a diaphragm region of the subject is set to facilitate checking of the breathing state of the subject. The method of claim 1, wherein the gantry is rotated and moved
Respiratory synchronization image acquisition method of a computed tomography device, characterized in that the gantry is rotated irrespective of the breathing state of the subject.
The method of claim 1, wherein the step of terminating the photography
Determining that the rotational speed of the gantry reaches a preset maximum rotational speed when it is determined that the respiration synchronization image for all the angles is not obtained;
If it is determined that the rotational speed of the gantry reaches the maximum rotational speed, the rotation of the gantry is stopped, and the gantry is moved to a position for an unacquired respiratory sync image; And
Obtaining a tomography image for the respiratory sync image non-acquisition angle; Respiratory synch image acquisition method of a computed tomography device further comprising a.
The method of claim 7, wherein the acquiring an image for the image non-acquisition section
Respiratory synch image acquisition method of a computed tomography device, characterized in that for acquiring an image irrespective of the breathing state of the subject.

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