KR101667145B1 - Method for correction of shaking of gamma camera - Google Patents

Method for correction of shaking of gamma camera Download PDF

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KR101667145B1
KR101667145B1 KR1020150055190A KR20150055190A KR101667145B1 KR 101667145 B1 KR101667145 B1 KR 101667145B1 KR 1020150055190 A KR1020150055190 A KR 1020150055190A KR 20150055190 A KR20150055190 A KR 20150055190A KR 101667145 B1 KR101667145 B1 KR 101667145B1
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photon
correction reference
gamma camera
reference plane
gamma
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민은기
이학재
이기성
김현구
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고려대학교 산학협력단
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/164—Scintigraphy
    • G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
    • G01T1/1642—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras using a scintillation crystal and position sensing photodetector arrays, e.g. ANGER cameras
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
    • A61B6/4258—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector for detecting non x-ray radiation, e.g. gamma radiation

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Abstract

The present invention relates to a shake correction method of a gamma camera, comprising: (a) setting a correction reference position value for the gamma camera; (b) a photon event generated by the gamma camera during a predetermined photographing time and a sensor position value sensed by a position sensor installed in the gamma camera are collected; (c) setting a correction reference plane on an x-y plane based on the correction reference position value, setting a three-dimensional inverse projection space having the correction reference plane as one side and the z axis direction as a depth; (d) imaging each of the photon events at a corresponding location on the correction reference plane and comparing the correction reference location value with the sensor location value corresponding to each photon event, Projecting back from the correction reference plane to the three-dimensional inverse projection space; (e) generating a gamma image by projecting the photon event back-projected in the three-dimensional inverse projection space back in the z-axis direction on a lamination plane facing the correction reference plane. Accordingly, the blur phenomenon of the gamma image caused by the operation noise such as the shake of the gamma camera can be eliminated, so that the gamma image of higher resolution and higher quality can be obtained.

Description

{METHOD FOR CORRECTION OF SHAKING OF GAMMA CAMERA}

The present invention relates to a shake correction method of a gamma camera, and more particularly, to a shake correction method of a gamma camera capable of correcting a shake of a gamma camera applied to a gamma ray imaging apparatus.

Nuclear medicine imaging technology is a technique of reconstructing images by injecting and diffusing a small amount of radioactive material into the human body to detect gamma rays emitted by radioactive isotopes (tracers) in specific organs, bones and tissues.

Positron Emission Tomography (PET) and Single Photon Emission Computed Tomography (SPECT) are two types of gamma-ray imaging techniques. They are CT, MRI, In addition, biochemical functional images such as blood flow and cell metabolism are provided, so that cancer and disease can be diagnosed early.

The gamma ray imaging apparatus to which the gamma ray imaging technique is applied is provided with a gamma camera 300 (or gamma probe) for detecting gamma ray photons. 1 is a view showing a configuration of a general gamma camera 300. As shown in FIG. 1, the gamma camera 300 includes a collimator 310, a detector crystal 320, a photomultiplier tube array 330, and a position logic circuit (not shown) 340 (position logic circuit).

The collimator 310 is formed of a lead material having holes formed therein. The collimator 310 controls the direction of radiation emitted from the radioisotope injected into the human body. The collimator 310 passes radiation incident perpendicularly to the hole formed in the collimator 310, Shields the radiation incident at a certain angle or more.

The radiation passing through the collimator 310 hits the detection crystal 320, and a photon is generated through the collimator 310. Then, the photon generated in the detection crystal 320 is amplified through the optoelectronic amplifier array 330, and then the detection position is determined by the position logic circuit unit 340. Here, among photons generated by the detection crystal 320, only the photons generated by the gamma rays of the energy region to be photographed are used for gamma ray imaging to acquire gamma ray images.

The gamma camera 300 is classified into a fixed-type gamma camera fixed on a support and a camera, and a hand-held gamma camera taken by a practitioner in a hand.

In the nuclear medicine imaging technique using the gamma camera 300 or the like, various image processing techniques for obtaining high resolution or clear images by removing noise and the like have been proposed.

For example, in the radiographic image processing apparatus disclosed in Japanese Patent Application Laid-Open No. 2011-027601, a look-up-table generated in advance and a photon event are selectively obtained in comparison with the detected photon events Discloses a technique capable of quickly processing a large number of photon events without reducing the resolution and quantification.

However, in the case of the gamma camera 300, the photographing time varies from several seconds to several minutes, and image quality deterioration due to operation noise generated by the shake of the gamma camera 300 is a problem. In particular, in the case of a hand-held gamma camera, deterioration in image quality caused by shaking of the gamma camera 300 is relatively greater.

In the case of a conventional optical camera, an optical correction method is often used to remove motion noise such as a camera shake. A sensor shift method and a lens shift method are typically used.

2 (a) conceptually illustrates the sensor shift method, and a method of moving the image sensor 20 according to a shake of an optical camera sensed by a position sensor (not shown) is used. FIG. 2B conceptually illustrates the lens shift method, and a method of moving the light collecting stove 10 according to the shaking of the optical camera sensed by the position sensor is used.

In the case of the gamma camera 300, as shown in FIG. 1, the sensor structure for detecting gamma rays is not only large in size but also attached to the collimator 310 so that it is structurally limited to apply the sensor shift method . Further, in the case of the gamma camera 300, since the lens is not used unlike the optical camera, the lens shift method can not be applied.

In addition, in the case of the shake correction method used in a general optical camera image processing technique, since a method of correcting the operation noise by moving the entire shot to be photographed is used, the photon is photographed in water every few seconds, It is not suitable to apply the general shake correction method of the optical camera to the gamma camera 300 that obtains the image.

SUMMARY OF THE INVENTION Accordingly, the present invention has been made in order to solve the above-mentioned problems, and it is an object of the present invention to provide a gamma camera which removes operational noise generated by shaking of a gamma camera, And to provide a camera shake correction method.

According to another aspect of the present invention, there is provided a shake correction method of a gamma camera, including: (a) setting a correction reference position value for the gamma camera; (b) a photon event generated by the gamma camera during a predetermined photographing time and a sensor position value sensed by a position sensor installed in the gamma camera are collected; (c) setting a correction reference plane on an x-y plane based on the correction reference position value, setting a three-dimensional inverse projection space having the correction reference plane as one side and the z axis direction as a depth; (d) imaging each of the photon events at a corresponding location on the correction reference plane and comparing the correction reference location value with the sensor location value corresponding to each photon event, Projecting back from the correction reference plane to the three-dimensional inverse projection space; (e) laminating the photon events, which are projected back to the three-dimensional inverse projection space, in the z-axis direction on a lamination plane facing the correction reference plane to generate a gamma image. Is achieved by a shake correction method.

Here, the photon event includes information on the sensing time of the photon, the energy of the photon, and the sensing position of the photon in the gamma camera; The sensor position value may include a coordinate value for the x-axis, the y-axis, and the z-axis, and an angle value for each of the x-axis, the y-axis, and the z-axis.

In the step (c), the correction reference plane is set in the form of an MxN matrix, and the three-dimensional back projection space is an M × N × K three-dimensional cubic shape having a K layer in the z- Is set; In the step (d), the energy of the photons is imaged on a row and a column on the correction reference plane corresponding to the photon sensing position of the photon event, and the sensing time of the photon of the photon event Axis, the y-axis and the z-axis direction are determined according to a deviation between the sensor position value and the correction reference position value at a corresponding time, The energy of the photon can be projected back to the layer of the three-dimensional back projection space at the back projection angle.

In the step (d), the energy of the photon is projected back to each unit cube forming the three-dimensional inverse projection space in the form of M × N × K three-dimensional cubes, and is projected back to each of the unit cubes Wherein the energy of the photons is summed in each of the unit cube units to form a unit cube photon value; In the step (e), the cube photon values of the unit cubes located in the same row and column may be summed and stacked on the corresponding rows and columns on the layer plane.

In the step (a), the correction reference position value may be set to any one of the sensor position values collected during the photographing time in the step (b).

Further, the laminating plane may be set as the correction reference plane.

According to the present invention, according to the present invention, a blur phenomenon of a gamma image caused by a motion noise such as a shake of a gamma camera is eliminated, and a gamma image of higher resolution and higher quality can be obtained .

This makes it possible to improve the accuracy of the surveillance lymph node search of the cancer. Through this, it is possible to more accurately detect the cancer metastasis, and the incision of the lymph node during surgery can be minimized.

1 is a view showing a configuration of a general gamma camera,
2 is a view for explaining examples of a method of correcting shaking in a general optical camera,
FIG. 3 is a view showing a configuration of a gamma ray imaging apparatus according to the present invention,
4 is a control flowchart for explaining a shake correction method of a gamma camera according to the present invention,
5 is a view showing an example of a three-dimensional back projection space in the shake correction method of the gamma camera according to the present invention,
6 to 10 are views for explaining the principle of a shake correction method of a gamma camera according to the present invention.

Hereinafter, the present invention will be described in detail with reference to the accompanying drawings showing embodiments of the present invention.

FIG. 3 is a view showing a configuration of a gamma ray imaging apparatus 100 according to the present invention. 3, the gamma ray imaging apparatus 100 according to the present invention includes a gamma camera 300, a stab sensor 400, and a gamma image processor 500.

The gamma camera 300 detects the radiation emitted from the human body and generates a photon event. 1, a gamma camera 300 according to the present invention includes a collimator 310, a detector crystal 320, a photomultiplier tube array 330, And a position logic circuit (340). Here, the configuration of the gamma camera 300 is not limited to the examples shown in FIGS. 1 and 3, and it goes without saying that the gamma camera 300 may be provided in various forms for detecting the radiation to generate photon events.

The stab sensor 400 is installed in the gamma camera 300 and senses a sensor position value with respect to the position of the gamma camera 300. In the present invention, as shown in FIG. 3, it is assumed that the sensor position value is located in a central region of the gamma camera 300, that is, a central region of the image detected by the gamma camera 300.

The gamma imaging processor receives the photon event from the gamma camera 300 and generates a two-dimensional gamma image. The sensor position value is received from the stasis sensor 400 to correct the shake of the gamma camera 300.

Hereinafter, a method of correcting the shake of the gamma camera 300 in the gamma-ray imaging apparatus 100 according to the present invention will be described in detail with reference to FIG.

First, the gamma ray imaging apparatus 100 operates and the imaging is performed by the gamma camera 300 (S40). When the photographing is started by the gamma camera 300, the gamma imaging processor sets a correction reference position value associated with the position of the gamma camera 300 (S41). Here, it is assumed that the correction reference position value is set to any one of the sensor position values collected from the stuck sensor 400 during the photographing time of the gamma camera 300. In the present invention, the first photon from the gamma camera 300 And the sensor position value of the detected time is set as the correction reference position value.

Then, photon events are collected from the gamma camera 300 until the preset photographing time is terminated (S43), and the stover sensor 400 values are collected from the staccato sensor 400 (S42). Here, the photon events collected from the gamma camera 300 include information on the detection time of the photon, the energy of the photon, and the sensing position of the photon in the gamma camera 300, The position values include coordinate values for the x, y, and z axes, and angle values for the x, y, and z axes, respectively.

When all the photon events and the stab sensor 400 values are collected as described above, the gamma image processor 500 sets the correction reference plane CRP and the 3D backprojection space BPA based on the correction reference position value S44).

More specifically, the gamma image processing unit 500 sets a correction reference plane (CRP) on the x-y plane on the basis of the correction reference position value. As described above, when the staccato sensor 400 is disposed at the center of the gamma camera 300, the correction reference plane CRP is set around the correction reference position value. As another example, when the staple sensor 400 is installed at one end of the gamma camera 300, a correction reference plane (CRP) may be formed by setting the end of the stapler 400 to the end of the correction reference plane (CRP). Accordingly, even if the position of the staple sensor 400 is variable according to the structure of the gamma camera 300, the correction reference plane (CRP) can be variably set according to the position of the staple sensor 400, The installation position can be arbitrarily selected.

When the correction reference plane (CRP) is set, a three-dimensional inverse projection space (BPA) in which the correction reference plane (CRP) is set as one side and the z axis direction is set as a depth is set. 5 is a diagram showing an example of a three-dimensional back projection space (BPA) set in the shake correction method of the gamma camera 300 according to the present invention.

5, the correction reference plane CRP is set in the form of an M × N matrix on the xy plane, and the three-dimensional back projection space BPA is set as M X N x K three-dimensional cubes.

At this time, the number of rows and columns of the correction reference plane (CRP) forming the three-dimensional back projection space BPA is set corresponding to the resolution of the gamma camera 300, The position of the photon may correspond to the row and column of the correction reference plane CRP.

When the three-dimensional back projection space BPA is set as described above, the photon event is imaged at a corresponding position on the correction reference plane CRP in units of photon events (S45), and the correction reference position value and the sensor position value The photon events imaged on the correction reference plane CRP are reflected from the correction reference plane CRP into the three-dimensional back projection space BPA (S46).

Hereinafter, a method of reversely projecting a photon event to a three-dimensional inverse projection space (BPA) in the shake correction method of the gamma camera 300 according to the present invention will be described in detail with reference to FIG. 6 to FIG. 6 to 8 are plan views of a correction reference plane (CRP) constituting a three-dimensional cubic-shaped three-dimensional back projection space (BPA), and the second drawing from the top is a correction reference plane (CRP), and the third figure from the top is a side view of the three-dimensional back projection space (BPA).

First, energy of a photon is imaged on a row and column on a correction reference plane (CRP) corresponding to a sensing position of a photon event sensed at a time t. Figures 6 through 8 illustrate schematically the first and second figures from which the energy of the photons is imaged in rows and columns on the correction reference plane (CRP).

Then, the backprojection angle in the x-axis, y-axis, and z-axis directions is determined according to the deviation between the sensor position value sensed at time t and the correction reference position value. FIG. 6 is a diagram illustrating a case where there is no deviation between the sensor position value and the correction reference position value and the back projection angle of the corresponding photon is equal to the correction reference plane (CRP). FIGS. 7 and 8 show the relationship between the sensor position value and the correction reference position value And the back projection angle of the photon is changed from the correction reference plane (CRP). The angle of the correction reference plane (CRP) is changed to schematically show the change of the back projection angle.

As described above, when the back projection angle is determined, the energy of the photons imaged on the row and column on the correction reference plane (CRP) is converted to the z-axis Lt; RTI ID = 0.0 > direction. ≪ / RTI >

At this time, the energy of the photon is reversely projected to each unit cube UC forming the three-dimensional back projection space BPA in the form of M × N × K three-dimensional cubes. As shown in FIGS. 6 to 8 When the back projection for all the photon events collected during the imaging time is completed, the magnitudes of the photons reflected back to each unit cube UC are summed in units of a unit cube (UC).

That is, when the back projection for the first photon event is completed, the energy of the photon is projected back to the unit cube UC in the z-axis direction as shown in the third figure from above in Fig. 7, when the back projection for the second photon event is completed, in the unit cube (UC) where the first photon event and the second photon event are both reversely projected, the photon intensity of the two photon events Summed.

Similarly, as shown in Fig. 8, when the back projection for the third photon event is completed, the unit photon event, the second photon event, and the third photon event are all projected backward in the unit cube (UC) The intensity of the photons of the photodetector becomes summed. On the other hand, in a unit cube (UC) in which one or two photon events are reversely projected, only the intensity of the photons of one or two photon events is reflected. Hereinafter, the energy of the summed photons in one unit cube (UC) will be described as unit cube photon values.

When the back projection to the three-dimensional back projection space (BPA) is completed for all the photon events collected from the gamma camera 300 (S47), the back projection (BPA) And the generated photon events are laminated in a z-axis direction on a lamination plane opposite to the correction reference plane (CRP) to generate a two-dimensional gamma image (S48).

9, when a photon event is backprojected to each unit cube UC on a three-dimensional back projection space BPA and a photon event is added to each unit cube UC, The unit cube photon values of the unit cubes UC located in the same row and column in the back projection space BPA are summed and stacked on the corresponding rows and columns on the lamination plane.

In other words, the unit cubic photon values of the unit cubes (UC) of the corresponding row and column in the z-axis direction in the three-dimensional back projection space (BPA) having the three-dimensional cubic shape are summed, And the unit cube photon values added on the plane of the stack form a corresponding row and column on the plane of the stack, that is, a photon value at the corresponding pixel, , Gamma images can be generated. In FIG. 9, the correction reference plane (CRP) is set as the lamination plane.

According to the above configuration, the blur phenomenon of the gamma image caused by the operation noise such as the shake of the gamma camera 300 can be eliminated, so that it is possible to obtain a higher quality gamma image having higher resolution.

FIG. 10 is a graphical representation of a gamma image when the shake correction method according to the present invention is not applied in the state of FIGS. 6 to 8. FIG. As shown in FIG. 10, blurring occurs in the gamma image due to shaking of the gamma camera 300. However, when the shake correction method according to the present invention is applied as shown in FIG. 9, It is possible to conceptually confirm that the blur phenomenon of the gamma image can be eliminated.

In this manner, the blur phenomenon of the gamma image is removed to obtain a high-quality gamma image with high resolution, so that the accuracy of the surveillance lymph node search of the cancer can be improved. Through this, it is possible to more accurately detect the cancer metastasis, and the incision of the lymph node during surgery can be minimized.

Although several embodiments of the present invention have been shown and described, those skilled in the art will readily appreciate that many modifications may be made without departing from the spirit or scope of the invention . The scope of the invention will be determined by the appended claims and their equivalents.

100: gamma ray imaging device 300: gamma camera
310: collimator 320: detection crystal
330: optoelectronic amplifier array 340: position logic circuit
400: position sensor 500: gamma image processor
PA: 3D inverse projection space CRP: Correction plane
UC: Unit Cube

Claims (6)

In a shake correction method of a gamma camera,
(a) setting a correction reference position value for the gamma camera;
(b) a photon event generated by the gamma camera during a predetermined photographing time and a sensor position value sensed by a position sensor installed in the gamma camera are collected;
(c) setting a correction reference plane on the xy plane based on the correction reference position value, setting a three-dimensional inverse projection space having the correction reference plane as one side and the z axis direction as a depth;
(d) imaging each of the photon events at a corresponding location on the correction reference plane and comparing the correction reference location value with the sensor location value corresponding to each photon event, Projecting back from the correction reference plane to the three-dimensional inverse projection space;
(e) laminating the photon events, which are projected back to the three-dimensional inverse projection space, in the z-axis direction on a lamination plane facing the correction reference plane to generate a gamma image. Shake correction method. The method according to claim 1,
Wherein the photon event comprises information on the sensing time of the photon, the energy of the photon and the sensing position of the photon in the gamma camera;
Wherein the sensor position value includes a coordinate value for the x-axis, the y-axis, and the z-axis, and an angle value for each of the x-axis, the y-axis, and the z-axis. 3. The method of claim 2,
In the step (c), the correction reference plane is set in the form of an M × N matrix, and the three-dimensional back projection space is set in an M × N × K three-dimensional cubic form having a K layer in the z-axis direction ;
In the step (d)
Energy of the photons is imaged in a row and a column on the correction reference plane corresponding to a sensing position of the photon of the photon event,
Axis, the y-axis and the z-axis direction are determined according to a deviation between the sensor position value and the correction reference position value in a time corresponding to the sensing time of the photon of the photon event,
Wherein the energy of the photons imaged in the rows and columns on the correction reference plane is projected back to the layer of the three-dimensional back projection space at the back projection angle. The method of claim 3,
In the step (d), the energy of the photon is projected back to each unit cube forming the three-dimensional inverse projection space in the form of M × N × K three-dimensional cubes, The energy of each unit cube being summed to form a unit cube photon value;
In the step (e)
Wherein the cube photon values of the unit cubes located in the same row and column are summed and stacked on corresponding rows and columns on the lamination plane. . The method according to claim 1,
Wherein the correction reference position value in the step (a) is set to any one of the sensor position values collected during the photographing time in the step (b). The method according to claim 1,
And the lamination plane is set as the correction reference plane.
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Cited By (1)

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Publication number Priority date Publication date Assignee Title
CN108776322A (en) * 2018-02-26 2018-11-09 奕瑞新材料科技（太仓）有限公司 Radiographic source localization method

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KR20130121317A (en) * 2012-04-27 2013-11-06 가천대학교 산학협력단 A real-time motion tracking of the subject and medical imaging correction method

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Publication number Priority date Publication date Assignee Title
JPH05180941A (en) * 1991-06-07 1993-07-23 Digital Scintigraphics Inc Method and apparatus for position analysis and radioactivity nuclide camera apparatus
JP2008245695A (en) * 2007-03-29 2008-10-16 Natl Inst Of Radiological Sciences Image reconstruction method of tomograph, failure diagnosis method, tomograph, and management program of system matrix
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Publication number Priority date Publication date Assignee Title
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CN108776322B (en) * 2018-02-26 2020-10-16 张岚 Ray source positioning method

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