Positron emission tomography system and imaging method thereof

Abstract

The present invention relates to a positron emission tomography system and an imaging method thereof, the method comprising: arranging a plurality of detectors at the same distance around an object to be detected; performing a zoom operation of, according to a detection region, moving all or some of the plurality of detectors toward the detection region so as to capture a positron emission tomography (hereinafter, referred to as "PET") image by increasing sensitivity thereof; and while performing a wobbling operation of wobbling the plurality of detectors along a plurality of points spaced apart by a predetermined distance from the center of the detection region, capturing and acquiring the PET image by increasing resolution thereof, wherein the wobbling operation comprises a small wobbling operation performed along a plurality of points spaced apart by a preset distance from the center of the object to be detected or from the center of a specific detection region, and a large wobbling operation performed around a changed position which is obtained by changing a center position of the small wobbling operation according to a position of at least one detection region, so that, during the wobbling operation, the center position of the small wobbling operation is sequentially changed according to the position of the at least one detection region in the object to be detected, and while performing the large wobbling operation around the changed position, the PET image is captured, thereby enabling acquisition of an ultra-high resolution PET image of the at least one detection region.

Description

Positron emission tomography system and its imaging method

[0001] The present invention relates to a positron emission tomography (hereinafter referred to as 'PET') system, and more specifically, to a PET that captures high-resolution and high-sensitivity images and a method for capturing the same.

[0002] PET is a diagnostic tool capable of early detection of cancer cells as small as 5mm that are difficult to identify with conventional X-rays, ultrasound, CT (computed tomography), or MRI (magnetic resonance imaging), and can determine the presence of microscopic cancer metastasis and recurrence, the extent of treatment progression, and malignancy. Additionally, PET can locate the site where cancer or tumors first originated.

[0003] In particular, PET techniques are excellent for identifying changes in physiological and biochemical metabolism rather than anatomical images such as bones or organs, and are therefore excellent for identifying neurological and cardiovascular diseases such as coronary artery disease, cardiovascular function including myocardial infarction, differential diagnosis of dementia, early diagnosis and identification of stroke, and functional evaluation of non-damaged brain tissue for cerebral developmental disorders, motor disorders, Alzheimer's disease, and epilepsy.

[0004] The principle of the above PET is based on a radioactive sample that emits positrons at a substance having the property of concentrating on specific cells within the body (e.g., glucose, which accumulates more in cancer cells than in other cells), such as C 11 , N 13 , O 15 , F 18When a drug containing the aforementioned components is injected into the body, the injected radioactive sample decays by emitting positrons. These emitted positrons combine with electrons present in the body and annihilate, generating a pair of γ-rays—specifically 511 keV annihilation photons—that are emitted in opposite directions, forming a 180° angle. Therefore, PET can identify the location of specific cells (e.g., cancer cells) by measuring these emitted annihilation photons. Since most malignant tumor cells have a higher glucose utilization rate compared to normal cells, malignant tumor cells can be identified by locating areas in the image where glucose or amino acid utilization is high.

[0005] In other words, in PET, when a positron is emitted from a specific pixel, two 511 KeV annihilation photons are generated, and these two annihilation photons travel at a 180-degree angle. Therefore, they are detected by two detectors facing each other. The probability that the positron emission from a specific pixel is detected in the response curve (LOR) consisting of two specific detectors is referred to as the Coincidence Response Function (CRF) or Line Spread Function (LSF).

[0006] The above PET system has molecular imaging capabilities, but its spatial resolution is relatively low compared to other imaging systems such as computed tomography (CT) and MRI.

[0007] That is, the spatial resolution of the above PET system is basically determined by the intrinsic resolution of the detector, which is about half the size of the detector, and can be determined along with various other degradation factors such as scattering and penetration effects, positron range, and non-collinearity.

[0008] Along with spatial resolution, another key factor affecting PET performance is system sensitivity, which is determined by the solid angle and detector efficiency. The former depends on the geometry of the detector system, for example, the system diameter and the axial length of the detector, while the latter is characterized by the size and material of the individual detector, for example, bismuth germanate (BGO) or, more recently, lutetium-yttrium oxyorthosilicate (LYSO).

[0009] For example, the following patent documents 1 to 3 disclose a technology for obtaining high-resolution PET images by increasing the resolution of a PET system according to the prior art.

[0010] However, PET systems according to conventional technology cannot obtain a resolution lower than half (d / 2) of the detector width, and as the size of the detector decreases, the sensitivity of the system drops significantly, limiting the ability to obtain high-resolution images.

[0011] Generally, in PET systems according to the prior art in which the detector array is geometrically fixed, it is difficult to optimize the balance between the spatial resolution and system sensitivity, including the detector size, sensitivity, and result sampling mentioned above, i.e., detector size and system configuration. In addition, there has recently been an increasing demand for high-resolution imaging, particularly brain imaging, in clinical PET development.

[0012] Meanwhile, another important design factor for PET systems is the improvement of system sensitivity, such as the system solid angle. Most currently available PET systems are designed for whole-body imaging with large system diameters. The large system diameter of these PET systems is a factor that significantly reduces sensitivity, especially in the case of brain imaging.

[0013] Accordingly, to address the aforementioned problems, fusion imaging systems such as PET-CT and PET-MR are being introduced; however, due to the inherent limitations of PET performance, the performance of these fusion imaging systems is inevitably restricted.

[0014] Non-patent document 1 below discloses a technique for acquiring high-resolution PET images through the zoom and wobbling functions of a detector.

[0015] Accordingly, there is a need to develop technology capable of acquiring high-sensitivity and high-resolution PET images by improving the zoom and wobbling behavior of the detector.

[0016] (Patent Document 1) Republic of Korea Patent Registration No. 10-1375490 (Published March 17, 2014)

[0017] (Patent Document 2) Republic of Korea Patent Publication No. 10-2011-0121536 (Published November 7, 2011)

[0018] (Patent Document 3) Republic of Korea Patent Registration No. 10-1207710 (Published December 3, 2012)

[0019] (Non-patent Document 1) "Development of Positron Emission Tomography With Wobbling and Zooming for High Sensitivity and High-Resolution Molecular Imaging", Zang-Hee Cho, Young-Don Son, Hang-Keun Kim, Dae-Hyuk Kwon, Yo-Han Joo, Jong Beom Ra, Yong Choi, and Young-Bo Kim, IEEE TRANSACTIONS ON MEDICAL IMAGING, VOL. 38, NO. 12, DECEMBER 2019.

[0020] The objective of the present invention is to solve the problems described above by providing a positron emission tomography system and a method thereof capable of acquiring high-sensitivity and high-resolution positron emission tomography (PET) images through zoom and rotation operations of a detector.

[0021] Another objective of the present invention is to provide a positron emission tomography system and a method thereof that can acquire high-sensitivity and high-resolution PET images of a region by rotating a detector at the region where an image is to be acquired.

[0022] To achieve the above-mentioned purpose, the positron emission tomography system according to the present invention comprises a plurality of detectors arranged at equal distances from a detection target and, depending on the detection area, moving all or part of the plurality of detectors toward the detection area to increase the sensitivity of the positron emission tomography (hereinafter referred to as 'PET') image and taking a zoom operation, and acquiring the PET image by increasing its resolution while wobbling the plurality of detectors along a plurality of points spaced a certain distance from the center of the detection area, wherein the wobbling operation includes a small wobbling operation following a plurality of points spaced a preset distance from the center of the detection target or the center of a specific detection area, and a large wobbling operation centered on the changed position, wherein the center position of the small wobbling operation is changed according to the position of at least one detection area.

[0023] In addition, to achieve the above-mentioned purpose, the imaging method of a positron emission tomography system according to the present invention comprises: (a) a step of arranging a plurality of detectors at equal distances from a detection target and moving all or part of the plurality of detectors toward the detection area according to the detection area to increase the sensitivity of the PET image and perform a zoom operation to capture; and (b) a step of wobbling a plurality of detectors along a plurality of points spaced apart by a certain distance from the center of the detection area and capturing and acquiring a positron emission tomography (hereinafter referred to as 'PET') image with increased resolution. The wobbling operation is characterized by including a small wobbling operation along a plurality of points spaced apart by a preset distance from the center of the detection target or the center of a specific detection area, and a large wobbling operation centered on the changed position, wherein the center position of the small wobbling operation is changed according to the position of at least one detection area.

[0024] As described above, according to the positron emission tomography system and the imaging method of the present invention, the effect of improving the system sensitivity of the PET image for the detection area of ​​the detection target by the zoom operation of the detector is obtained.

[0025] In addition, according to the present invention, by capturing a PET image while performing a small wobbling motion centered on the center of a detection target or the center of a specific detection area, the resolution of the PET image is increased, thereby obtaining an ultra-high resolution PET image.

[0026] In addition, according to the present invention, the center position of a small wobbling motion is sequentially changed according to the position of at least one detection area in the detection target during a wobbling motion, and a PET image is captured while performing a large wobbling motion centered on the changed position, thereby obtaining the effect of acquiring an ultra-high resolution PET image for one or more detection areas.

[0027] FIG. 1 is a block diagram of a positron emission tomography system according to a preferred embodiment of the present invention,

[0028] FIG. 2 is a configuration diagram of the detector shown in FIG. 1,

[0029] FIG. 3 is a drawing showing the zoom-in operation of the detection unit,

[0030] FIGS. 4 and FIGS. 5 are drawings illustrating small wobbling motion and large wobbling motion, respectively.

[0031] FIGS. 6 and FIGS. 7 are drawings illustrating sampled data in a fixed state and a wobbling operation state, respectively.

[0032] FIG. 8 is a diagram illustrating wobbling data,

[0033] FIG. 9 is a drawing illustrating deblurred sampling data.

[0034] FIGS. 10 and FIGS. 11 are drawings illustrating images obtained from an HRRT-PET and a PET system according to the present embodiment, respectively, for a Derenzo phantom.

[0035] FIG. 12 is a process diagram illustrating, step-by-step, a method of imaging a PET device according to a preferred embodiment of the present invention.

[0036] A positron emission tomography system and a method for imaging the same according to a preferred embodiment of the present invention will be described in detail below with reference to the attached drawings.

[0037]

[0038] FIG. 1 is a block diagram of a positron emission tomography system according to a preferred embodiment of the present invention, FIG. 2 is a configuration diagram of a detector unit shown in FIG. 1, and FIG. 3 is a diagram showing the zoom-in operation of the detector unit.

[0039] In the following, terms indicating directions such as 'left', 'right', 'forward', 'rear', 'upward', and 'downward' are defined as indicating the respective directions based on the state depicted in each drawing.

[0040] A positron emission tomography (hereinafter referred to as 'PET') system (10) according to the present invention arranges a plurality of detectors in a ring shape at equal distances from a detection target, i.e., a patient, and, depending on the detection area, moves all or part of the plurality of detectors toward the detection area to increase the sensitivity of the PET image and captures it, and performs a wobbling operation to rotate (wobbling, hereinafter referred to as 'wobbling') the plurality of detectors along a plurality of points spaced apart by a certain distance from the center of the detection area, thereby increasing the resolution of the PET image and capturing it.

[0041] Here, the wobbling motion refers to a motion of rotating along a plurality of points spaced apart by the same distance from the detection area of ​​the detection target, such as the rotation motion of a hula hoop, unlike a rotation motion centered on the center point of the measurement target or measurement area.

[0042] Accordingly, the present invention may improve the system sensitivity of the PET image for the detection site on the patient's body by the zoom operation.

[0043] In addition, the present invention can acquire ultra-high resolution PET images by increasing the resolution of the PET images by capturing PET images while performing a wobbling motion (hereinafter referred to as 'small wobbling') along a plurality of points spaced apart by a preset distance from the center of a detection target or the center of a specific detection area.

[0044] In addition, the present invention changes the center position of the wobbling motion according to the position of at least one detection area on the user's body part during the wobbling motion, and captures a PET image while performing a wobbling motion centered on the changed position (hereinafter referred to as 'large wobblging'), thereby enabling the acquisition of an ultra-high resolution PET image for one or more detection areas.

[0045] To explain in detail, a PET system (10) according to a preferred embodiment of the present invention, as shown in FIGS. 1 and 2, includes a detection unit (20) comprising a plurality of detectors arranged radially around a detection target, and a driving unit (30) that moves the plurality of detectors in and out of closeness to or away from the detection target and wobbles around the detection target or the detection area according to the position of the detection area where an image is to be acquired from the detection target.

[0046] In addition, the PET system (10) according to a preferred embodiment of the present invention may further include an image processing unit (40) that receives image data captured by a detection unit (20) and position information of each detector to acquire a PET image, and a control unit (50) that controls the operation of each device.

[0047] The detection unit (20) and the driving unit (30) can be integrated into a single measuring device, and the image processing unit (40) and the control unit (50) can be integrated into a single computer terminal or server.

[0048] A plurality of detectors may include a plurality of first detectors (21) installed to enable zoom operation according to the measurement target, and a plurality of second detectors (22) maintaining a fixed installed position.

[0049] For example, a plurality of detectors may be arranged in a roughly circular shape on a gantry (23) placed on the outside of the detection target.

[0050] A plurality of first detectors (21) and second detectors (22) are arranged alternately and can form a roughly circular shape at a position spaced apart from the center of the detection target by a preset distance.

[0051] Each first detector (21) can zoom in to approach the center of the detection target by the first driving module (31) of the driving unit (30) described below, as shown in FIG. 3, and zoom out to return to an initial position between a plurality of second detectors (22) separated from the center of the detection target.

[0052] For example, the first detector (21) can be zoomed out so as to be separated from the patient when the detection target, i.e., the patient, is inserted into the internal space of the detection unit (30) by the horizontal movement of the bed, and when photographing a part of the patient's body with a relatively large outer diameter, such as the chest or abdomen.

[0053] And the first detector (21) can be zoomed in to get close when capturing an image of a part of the patient's body with a relatively small outer diameter, for example, the head area.

[0054] Here, when zooming in, the plurality of first detectors (21) may be arranged in a roughly circular shape having a diameter reduced compared to the diameter of the zoom-out operation.

[0055] According to the experimental results, when the diameter of the system (10) in the PET system (10) is reduced by half, the sensitivity of the system (10) increases twofold.

[0056] Meanwhile, a plurality of second detectors (22) can be fixedly installed at the approximate edge of the gantry (23).

[0057] In this embodiment, it is described that a total of 20 first and second detectors (21, 22) are provided in the detection unit (20), but the present invention is not necessarily limited thereto, and the number of first and second detectors (21, 22) can be varied by decreasing or increasing as needed.

[0058] In addition, the present invention may be modified to subdivide a plurality of detectors into a plurality of first to Nth detectors, and to change the diameter of the detector part to 1 / 2, 1 / 3, 1 / 4, etc., depending on the outer diameter of the measurement part.

[0059] In this way, the present invention can improve system sensitivity by moving all or part of a plurality of detectors provided in the detection unit closer toward the measurement target, depending on the detection area of ​​the detection target.

[0060] The driving unit (30) has the function of implementing zoom-in and zoom-out operations and small and large wobbling operations for a plurality of detectors provided in the detection unit (20).

[0061] That is, the driving unit (30) may include a plurality of first driving modules (31) that zoom in and zoom out of a plurality of first detectors (21) and a second driving module (32) that small or large wobbling operation of the gantry (23).

[0062] A plurality of rails are installed in the gantry (23) to enable a plurality of first detectors (21) to zoom in and out, and each first detector (21) can slide along the rails.

[0063] Each first drive module (31) may include a drive motor that generates rotational force by rotating in the forward and reverse directions so as to slide the first detector (21) along each rail, and a power transmission unit that transmits the rotational force generated by the drive motor to the first detector (21).

[0064] The above drive motor is installed on the gantry (23) or on the rail, is connected to the first detector (21) through the power transmission unit, and can generate rotational force to slide the first detector (21).

[0065] The above power transmission unit may connect the output shaft of the drive motor and the first detector (21) in a direct connection manner, or include various power transmission components such as one or more gears, belts, and pulleys.

[0066] Of course, the above-mentioned drive motor may be provided not only as an electric motor driven by power supply, but also as a hydraulic motor or a pneumatic motor.

[0067] Additionally, the first drive module (31) may be modified to include various drive units, such as cylinders or solenoids, that receive pneumatic or hydraulic pressure and perform extension and retraction operations instead of the drive motor.

[0068] The second drive module (32) functions to make the gantry (23) small and large wobbling.

[0069] For example, Figures 4 and 5 are drawings illustrating small wobbling motion and large wobbling motion, respectively.

[0070] A base plate is disposed on the rear side of the gantry (23), and the second drive module (32) may include at least one drive unit that generates a driving force to move the gantry in the X-axis and Y-axis directions and a power transmission unit that transmits the driving force of the drive unit to the gantry (23) to adjust the position of the gantry (23) and then performs a small wobbling or large wobbling operation on the gantry (23).

[0071] So, as shown in FIG. 4, the gantry (23) can perform a small wobbling operation (TS) in a roughly circular shape along a plurality of points (P1 to P4) spaced apart from the center (O) of the detection target by a certain distance from the center (O).

[0072] And as shown in FIG. 5, the gantry (23) can perform a large wobbling operation (TL) including a plurality of small wobbling operations (TS) along a plurality of points spaced apart by a certain distance from a plurality of detection parts (OP1 to OP3) to be detected in the detection target.

[0073] For example, when taking a PET image of a patient's brain, the gantry (23) can perform a small wobbling motion (TS) along a plurality of points spaced apart by a preset interval from the center of the patient's head area (O).

[0074] And when taking PET images of the patient's cerebrum and cerebellum, the gantry (23) can perform a small wobbling motion (TS) following multiple points spaced apart by a preset interval from the center of the cerebrum (OP1), and a large wobbling motion (TL) including a small wobbling motion (TS) following multiple points spaced apart by a preset interval from the center of the cerebellum (OP2).

[0075] Figures 6 and 7 are diagrams illustrating sampled data in a fixed state and a wobbling state, respectively.

[0076] As shown in FIG. 6, when a PET image is taken with the gantry (23) in a fixed state, sampling data at fixed intervals corresponding to the width (d) of each detector (21, 22) is obtained.

[0077] On the other hand, as shown in FIG. 7, when the gantry (23) takes a PET image while wobbling, it can acquire a number of sampling data that is several times greater than the sampling data acquired in a fixed state.

[0078] In this way, the sampling data obtained by the wobbling operation can be converted through data interpolation to have an interval (d / 4) corresponding to 1 / 4 of the detector width (d).

[0079] Meanwhile, FIG. 8 is a diagram illustrating wobbling data, and FIG. 9 is a diagram illustrating deblurred sampling data.

[0080] To apply an ideal wobbling process to PET data as illustrated in FIG. 7, the data can be deconvolved or deblurred with an estimating point spread function (p-PSF) before overlapping and interpolation as illustrated in FIG. 8, thereby obtaining deblurred sambling data as illustrated in FIG. 9.

[0081] For example, the above p-PSF model can use a Gaussian function.

[0082] FIGS. 10 and FIGS. 11 are drawings illustrating images obtained from HRRT-PET and the PET system according to the present embodiment, respectively, for a Derenzo phantom.

[0083] Comparison of Figures 10 and 11 shows that all points of the Derenzo phantom are resolved better in PET images than in HRRT (High Resolution Research Tomography)-PET.

[0084] In this way, the present invention can acquire ultra-high resolution PET images by increasing the resolution of the PET images through capturing PET images while performing a small wobbling motion centered on the center of the detection target or the center of a specific detection area.

[0085] In addition, the present invention can acquire ultra-high resolution PET images for one or more detection areas by sequentially changing the center position of a small wobbling motion according to the position of at least one detection area on the user's body part during the wobbling motion, and capturing PET images while performing a large wobbling motion centered on the changed position.

[0086]

[0087] Next, a method for imaging a PET device according to a preferred embodiment of the present invention will be described in detail with reference to FIG. 12.

[0088] FIG. 12 is a process diagram illustrating, step-by-step, a method of imaging a PET device according to a preferred embodiment of the present invention.

[0089] When power is supplied to the PET system (10) in step S10, the control unit (50) initializes each device and zooms out a plurality of first detectors (21) so that a detection target, i.e., a patient, can be introduced into the detection unit (20). Subsequently, a patient lying on a bed is introduced into the detection unit (20) by the movement of the bed.

[0090] In step S12, the control unit (50) generates a control signal to zoom in a plurality of first detectors (21) according to the outer diameter of the detection area. Then, the driving unit (30) drives a plurality of first driving modules (31) according to the control signal to zoom in a plurality of first detectors (22) along the rail so that they approach the detection area.

[0091] In step S14, the control unit (50) generates a control signal to perform a wobbling operation on at least one detection area of ​​the detection target. Then, the driving unit (30) drives the second driving module (32) according to the control signal to perform a small wobbling operation (TS) following a plurality of points spaced apart by a certain distance from one set detection area, and a large wobbling operation (TL) including a small wobbling operation (TS) following a plurality of points spaced apart by a certain distance from another detection area.

[0092] In step S16, a plurality of first and second detectors (21, 22) or the first detector (21) acquire PET data for the detection site.

[0093] Then, the image processing unit (40) obtains sampling data through deconvolution and interpolation on the acquired PET data (S18), and finally obtains a high-resolution PET image (S20).

[0094] When the PET image acquisition process is completed, the control unit (50) generates a control signal to zoom out the plurality of first detectors (21), and when the zoom out operation of the first detectors (21) by the plurality of first driving modules (31) is completed, the bed is controlled to be withdrawn from the detection unit (20) (S24).

[0095] Next, the control unit (50) stops and terminates the operation of each device.

[0096] Through the process described above, the present invention can improve the system sensitivity of the PET image for the detection area of ​​the detection target by the zoom operation of the detector.

[0097] In addition, the present invention can acquire ultra-high resolution PET images by increasing the resolution of the PET images through capturing PET images while performing a small wobbling motion centered on the center of the detection target or the center of a specific detection area.

[0098] In addition, the present invention can acquire ultra-high resolution PET images for one or more detection areas by sequentially changing the center position of a small wobbling motion according to the position of at least one detection area of ​​the detection target during the wobbling motion, and capturing PET images while performing a large wobbling motion centered on the changed position.

[0099] Although the invention made by the inventors has been specifically described according to the above embodiments, the present invention is not limited to the above embodiments and can be modified in various ways without departing from the gist thereof.

[0100] Meanwhile, although the above embodiment describes a configuration in which a PET system is provided alone, the present invention may be modified to allow the PET system and an MRI device to be fused.

[0101] In addition, the present invention may be modified to further improve the resolution of the PET image by applying a multilayer and multiple detectors in a manner such as arranging detectors in a plurality of layers on the head represented as a detector in the above embodiment and arranging multiple detectors in each layer.

[0102] The present invention is applied to a PET system and a method for capturing images thereof, which can acquire ultra-high resolution PET images for one or more detection areas by sequentially changing the center position of a small wobbling motion according to the position of at least one detection area in a detection target during a wobbling motion, and capturing PET images while performing a large wobbling motion centered on the changed position.

Claims

1. A plurality of detectors are placed at equal distances from a detection target, and a zoom operation is performed to increase the sensitivity of a positron emission tomography (hereinafter referred to as 'PET') image by moving all or part of the plurality of detectors toward the detection area according to the detection area, and a resolution of the PET image is increased and the image is acquired by wobbling the plurality of detectors along a plurality of points spaced a certain distance from the center of the detection area. The above wobbling motion is a small wobbling motion that follows a plurality of points spaced apart by a preset distance from the center of the detection target or the center of a specific detection area, and A positron emission tomography system characterized by changing the center position of the small wobbling motion according to the position of at least one detection site, and including a large wobbling motion centered on the changed position.

2. In Paragraph 1, A detection unit comprising a plurality of detectors arranged radially around the above-mentioned detection target and A positron emission tomography system characterized by including a zoom operation that moves the plurality of detectors in and out so as to be close to or farther away from the detection target, and a driving unit that performs a wobbling operation centered on the detection target or the detection area according to the position of the detection area where an image is to be acquired from the detection target.

3. In Paragraph 2, An image processing unit that receives the PET data captured by the detection unit and the position information of each detector to acquire a PET image, and It further includes a control unit that controls the operation of each device, and A positron emission tomography system characterized by the image processing unit acquiring the PET image by deblurring the data sampled from the detection unit through deconvolution and interpolation.

4. In Paragraph 2, The above detection unit comprises a plurality of first detectors installed on a gantry capable of zoom operation according to the measurement target, and A positron emission tomography system characterized by including a plurality of second detectors that maintain a fixed position on the gantry.

5. In Paragraph 4, The above driving unit comprises a plurality of first driving modules that perform zoom-in and zoom-out operations on the plurality of first detectors, and A positron emission tomography system characterized by including a second driving module that performs the small or large wobbling operation of the gantry.

6. (a) A step of performing a zoom operation to increase the sensitivity of a PET image and capture it by placing a plurality of detectors at equal distances centered on a detection target, and moving all or part of the plurality of detectors toward the detection area according to the detection area. (b) a step of acquiring a positron emission tomography (hereinafter referred to as 'PET') image with increased resolution while wobbling a plurality of detectors along a plurality of points spaced apart by a certain distance from the center of the detection area, and The above wobbling motion is a small wobbling motion that follows a plurality of points spaced apart by a preset distance from the center of the detection target or the center of a specific detection area, and A method for imaging a positron emission tomography system characterized by changing the center position of the small wobbling motion according to the position of at least one detection site, and including a large wobbling motion centered on the changed position.

7. In Paragraph 6, (c) further includes the step of acquiring a PET image by receiving the PET data captured by the detection unit and the position information of each detector using an image processing unit, and A method for imaging a positron emission tomography system, characterized in that the image processing unit obtains the PET image by deblurring the data sampled from the detection unit through deconvolution and interpolation.

Images