SPECT imaging device and swing-type acquisition tomography method

Abstract

The invention provides an SPECT imaging device and a swing-type acquisition tomography method. The device comprises an SPECT scanning frame, and the SPECT scanning frame comprises a main rotating motor, a first large probe, a second large probe, a first small probe and a second small probe; the main rotating motor is used for synchronously driving the first large probe, the second large probe, the first small probe and the second small probe to swing back and forth around the bed according to a preset angle; wherein the first large probe and the second large probe are used for covering and scanning to obtain longitudinal data of a human body, and the first small probe and the second small probe are used for assisting in scanning to obtain transverse data of the human body; in the reciprocating swing process, all the probes can advance and retreat in the radial direction of the SPECT scanning frame in the same plane and translate left and right in the second direction perpendicular to the radial direction, so that a parallelogram imaging area which is always close to the outline formed by a bed and a human body is defined, and plane and cross-sectional image data can be obtained through single-time small-angle scanning.

Description

Technical Field

[0001] The present invention relates to the field of medical equipment, and in particular to a SPECT imaging device and a swing-type acquisition tomography method. Background Art

[0002] Single-Photon Emission Computed Tomography (SPECT) is an advanced nuclear medicine imaging diagnostic device. Its principle is to measure and display the biological activities of cells and molecules by injecting specific radioactive drugs (such as Tc-99m) into the human body. The SPECT probe rotates along the body, emitting 140keV photons (gamma rays) at specific organs or tissues. After passing through the tissues and organs, they reach the SPECT detector. The SPECT device then uses a collimator to collimate the gamma rays, which are converted into optical signals by a scintillator. This optical signal is then converted into an electrical signal by a photomultiplier tube and amplified. The resulting measurement represents the amount of radioactivity along the projection line. A computer then interprets the projections to generate a three-dimensional image, thereby pinpointing the location, nature, and extent of lesions. This is of great clinical significance. Traditional SPECT imaging devices consist of one or two symmetrically arranged detectors. During examination, the detectors must rotate around the patient's body once to obtain complete sampling data for tomographic image reconstruction.

[0003] Patent document CN116849690A discloses a SPECT imaging device, a SPECT imaging system, and a diagnostic combination. Through an asymmetric detector design and flexible adjustment of detector angle and distance, the device better conforms to the patient's contours, enabling single-bed scanning without a full 360-degree rotation, or even no rotation at all, thus shortening clinical testing time. However, this asymmetric layout often results in missed angles and missed scans during the testing process, which require an algorithm (fill-in scan module) to compensate. Summary of the Invention

[0004] In view of the defects in the prior art, the present invention aims to provide a SPECT imaging device and a swing-type acquisition tomography method.

[0005] According to the present invention, a four-probe SPECT imaging device includes a SPECT scanning frame, wherein the SPECT scanning frame includes: a main rotating motor, a first large probe, a second large probe, a first small probe, and a second small probe;

[0006] The main rotary motor is used to synchronously drive the first large probe, the second large probe, the first small probe and the second small probe to swing back and forth around the bed at a preset angle;

[0007] The first large probe and the second large probe are arranged relative to each other to obtain longitudinal data of the human body, and the first small probe and the second small probe are arranged relative to each other to obtain transverse data of the human body;

[0008] During the reciprocating swinging process, the first large probe, the second large probe, the first small probe and the second small probe can move forward and backward along the radial direction of the SPECT scanning frame and translate left and right in a second direction perpendicular to the radial direction within the same plane, thereby enclosing an imaging area formed by a parallelogram that is always close to the contour formed by the bed and the human body.

[0009] Furthermore, the first large probe, the second large probe, the first small probe and the second small probe are each controlled to advance, retreat and translate by a set of movement control systems;

[0010] Alternatively, the first large probe is connected to the second small probe and is controlled to move forward, backward and horizontally through a mobile control system, and the second large probe is connected to the first small probe and is controlled to move forward, backward and horizontally through a mobile control system.

[0011] Furthermore, the preset angle is 0° to 45°.

[0012] Furthermore, the lateral scanning field of view L1 of the first large probe and the second large probe is ≥ the human shoulder width BW, and the lateral scanning field of view L2 of the first small probe and the second small probe is ≥ the human chest thickness BT.

[0013] Furthermore, TOF sensors are installed on both end faces of each probe to control the distance between adjacent probes and prevent interference.

[0014] The front end of each probe is equipped with transverse and axial multi-layered beam-type laser or radar sensors for distance monitoring when the probe is close to the human body or bed.

[0015] Furthermore, it also includes: a power distribution unit PDU and a console, wherein the console is electrically connected to the SPECT scanning frame, and the power distribution unit PDU supplies power to the console and the SPECT scanning frame respectively.

[0016] According to a swing-type acquisition tomography method of a SPECT imaging device provided by the present invention, the SPECT imaging device is used, and the method includes:

[0017] Step 1: Control the first large probe and the second large probe to move radially close to the contour formed by the bed and the human body, and control the first small probe and the second small probe to move in opposite directions along the second direction, so that the first small probe does not interfere with the first large probe during radial movement, and the second small probe does not interfere with the second large probe during radial movement;

[0018] Step 2: Control the first small probe and the second small probe to move radially close to the contour formed by the bed and the human body, and control the first large probe and the second large probe to move in opposite directions along the second direction, so that the first large probe does not interfere with the radial movement of the second small probe, and the second large probe does not interfere with the first small probe;

[0019] Step 3: Drive the first large probe, the second large probe, the first small probe and the second small probe to rotate forward around the bed by a preset angle and obtain the tomographic data under the first bed, then reverse back to the 0 rotation angle position and continue to reversely rotate by a preset angle to obtain the tomographic data under the second bed, and repeat this process until the tomographic data under the required number of beds are obtained.

[0020] Furthermore, at the zero rotation angle position, the first large probe and the second large probe face the front and back sides of the human body respectively, and the first small probe and the second small probe face the left and right sides of the human body respectively.

[0021] Furthermore, when the parallelogram imaging area is a rectangle, the radial advance and retreat distance x1 and the translation distance x2 of the first large probe, the radial advance and retreat distance x3 and the translation distance x4 of the second large probe, the endpoints of the first large probe and the endpoints of the second large probe constitute the interference points when the first small probe is translated;

[0022] Wherein, a1=R-x1, b1=L1 / 2+x2, a2=-(R-x3), b2=-(L1 / 2-x4), R is the distance between each probe and the center point of the contour, L1 is the lateral scanning field of view of the first and second largest probes, and L2 is the lateral scanning field of view of the first and second small probes;

[0023] When the first small probe is translated, the horizontal coordinate of the front end surface of the first small probe does not exceed the position a2, and the vertical coordinate of the end surface does not exceed the position b1. The same applies to the second small probe.

[0024] Furthermore, when the parallelogram imaging area is non-rectangular, the radial advance and retreat distance x1 and the translation distance x2 of the first large probe, the radial advance and retreat distance x3 and the translation distance x4 of the second large probe, the endpoints (a1, b1) of the first large probe and the endpoints (a2, b2) of the second large probe constitute the interference points when the first small probe is translated;

[0025] Wherein, a1=(R-x1)+sinα*L1 / 2, b1=cosα*L2 / 2+x2, a2=-(R-x3-sinβ*L1 / 2), b2=-(cosβ*L2 / 2-x2), R is the distance between each probe and the center point of the contour, L1 is the lateral scanning field of view of the first and second largest probes, L2 is the lateral scanning field of view of the first and second small probes, α is the angle between the first large probe and the translation direction, and β is the angle between the second largest probe and the translation direction;

[0026] When the first small probe is translated, the horizontal coordinate of the front end surface of the first small probe does not exceed the position a2, and the vertical coordinate of the end surface does not exceed the position b1. The same applies to the second small probe.

[0027] Compared with the prior art, the present invention has the following beneficial effects:

[0028] The present invention acquires data at optimal sensitivity by moving each probe up and down, and by moving each probe laterally so that all four probes can seamlessly fit the contours of people of different body shapes, obtaining image data with optimal sensitivity and resolution over a 360-degree scanning range. This enables a single small-angle scan to acquire planar and tomographic image data, resolving the problem of conventional SPECT imaging devices requiring the dual probes to rotate at least 90 degrees to scan and acquire tomographic image data for a single bed. By adjusting each probe up and down and left and right, and by the scanning frame performing a small-angle, periodic, reciprocating Wobble motion to acquire data, the SPECT imaging device achieves rapid whole-body tomographic imaging, eliminating the need for algorithms to compensate for any missing angles. This allows for rapid acquisition of data from all angles of the human body, enabling rapid whole-body tomographic scanning by the SPECT imaging device. This resolves the problem of conventional SPECT imaging devices requiring long rotation periods to complete whole-body tomographic scanning of a patient, alleviating the discomfort experienced by patients who lie motionless for extended periods. BRIEF DESCRIPTION OF THE DRAWINGS

[0029] Other features, objects and advantages of the present invention will become more apparent upon reading the detailed description of non-limiting embodiments with reference to the following drawings:

[0030] Figure 1 Schematic diagram of the structure of a SPECT imaging device;

[0031] Figure 2 It is the structural diagram of the SPECT scanning frame;

[0032] Figure 3 This is a schematic diagram of the large probe's lateral field of view;

[0033] Figure 4 This is a schematic diagram of the lateral field of view of the small probe;

[0034] Figure 5 is the initial position of the probe;

[0035] Figure 6 This is a schematic diagram of the probe approach process;

[0036] Figure 7 、 Figure 8 、 Figure 9 and Figure 10 Schematic diagram of the swing scanning process;

[0037] Figure 11 Schematic diagram of the driving structure of each probe;

[0038] Figure 12 is a schematic diagram of the interference point;

[0039] Figure 13 This is a schematic diagram of other settings for the small probe;

[0040] Figure 14 Schematic diagram of other settings for large probes;

[0041] Figure 15 is a schematic diagram of the interference point;

[0042] Figure 16 A comparison diagram of the approach of the present application and the prior art under different body shapes;

[0043] Figure 17 A comparison diagram of the scanning method of this application and the prior art;

[0044] Figure 18 Schematic diagram of other settings for large and small probes;

[0045] Figure 19 、 Figure 20 To correspond Figure 18 Schematic diagram of the probe movement. DETAILED DESCRIPTION

[0046] The present invention will be described in detail below with reference to specific embodiments. The following examples will help those skilled in the art to further understand the present invention, but are not intended to limit the present invention in any form. It should be noted that, for those skilled in the art, several changes and improvements can be made without departing from the scope of the present invention. These all fall within the scope of protection of the present invention.

[0047] like Figure 1As shown, a SPECT imaging device includes: a power distribution unit PDU1, a SPECT scanner 2, a bed 3 and a control console 4. The power distribution unit PDU1 is connected to the SPECT scanner 2, bed 3 and control console 4 via power and signal cables, and is mainly used to power and control the SPECT scanner 2, bed 3 and control console 4. The SPECT scanner 2 is a ring structure with a through hole in the middle. The SPECT scanner 2 has multiple probes for human body scanning. The bed 3 can axially enter the through hole under control. By moving the probe close to the human body on the bed 3, image data with optimal sensitivity and resolution can be obtained. By controlling the position where the bed 3 enters, image data corresponding to different positions can be obtained. The control console 4 is connected to the SPECT scanner 2 via control and data signal cables, and is mainly used for the operator to perform scanning operations, parameter settings and image viewing.

[0048] like Figure 2 As shown, the present invention is mainly aimed at SPECT fast tomography scanning without missing angles and data truncation. Therefore, only some key components of the SPECT scanning frame 2 are introduced. The SPECT scanning frame 2 includes: a main rotating motor 101, a human-computer interaction touch screen 102, a first large probe 103, a second large probe 104, a first small probe 105 and a second small probe 106.

[0049] A first large probe 103 is positioned above the SPECT gantry 2, and a second large probe 104 is positioned below the gantry 2. The first and second large probes 103, 104 are positioned opposite each other to acquire longitudinal data (front and back of the body). A first small probe 105 is positioned on the left side of the SPECT gantry 2, and a second small probe 106 is positioned on the right side of the SPECT gantry 2. The first and second small probes 105, 106 are positioned opposite each other to acquire transverse data (left and right sides of the body).

[0050] The main rotary motor 101 is used to synchronously drive the first large probe 103, the second large probe 104, the first small probe 105, and the second small probe 106 to reciprocate around the bed 3 at a preset angle. This drives the circular structure containing the first large probe 103, the second large probe 104, the first small probe 105, and the second small probe 106 to achieve scanning at different angles. The preset angle ranges from 0° to 45°, preferably from 0° to 15°.

[0051] Each probe is capable of advancing and retreating in the radial direction of the SPECT scanning gantry and translating in a second direction perpendicular to the radial direction within the same plane, thereby enclosing an imaging area formed by a parallelogram that is always close to the outline formed by the bed 3 and the human body. The radial advance and retreat is to achieve close proximity to / away from the human body, and the translation perpendicular to the radial direction is to avoid interference between adjacent probes when close to the human body, thereby only requiring a smaller angle swing scan. In the case of four probes, the scanning angle only needs to be within 45 degrees to quickly obtain data without missing corners or truncation for multiple sections of the human body under the bed, achieving a fast full-body section scan time efficiency. In a specific implementation, the first large probe 103, the second large probe 104, the first small probe 105, and the second small probe 106 are each controlled by a set of motion control systems for advance, retreat, and translation; alternatively, the first large probe 103 and the second small probe 106 are connected in an L-shape and controlled by a set of motion control systems for advance, retreat, and translation, while the second large probe 104 and the first small probe 105 are connected in an L-shape and controlled by another set of motion control systems for advance, retreat, and translation. The position of the human-computer interaction touch screen 102 is adjustable to accommodate operations performed by hospital technicians at different positions.

[0052] When lying flat, the outline of the human body and the bed is approximately an elliptical cross-section. Four SPECT probes are arranged on the SPECT imaging device scanning frame, including two large probes on the upper and lower sides and two small probes on the left and right sides, forming a quasi-full-ring design. Data acquisition with optimal sensitivity is achieved by moving each probe up and down, and each probe is moved laterally to ensure that all four probes can fit the contours of human bodies of different body shapes without any gaps, obtaining image data with optimal sensitivity and resolution covering a 360-degree scanning range. This enables the acquisition of planar and tomographic image data in a single scan, solving the problem that the dual probes of conventional SPECT imaging devices need to rotate at least 90 degrees to scan and obtain tomographic image data of a bed.

[0053] like Figure 3 As shown, the lateral scanning field of view L1 of the first and second large probes 103, 104 is determined by the shoulder width BW of the human body, where L1 ≥ BW = 2R1, where R1 is the length of the major semi-axis of the elliptical cross-section. For thin and narrow figures, scanning is achieved by translating the first and second large probes 103, 104 in the second direction. For larger and wider figures, scanning is achieved by translating the first and second large probes 103, 104 in the second direction and adding a main rotary motor 101 to drive a small rotation of the entire probe.

[0054] like Figure 4As shown, the lateral scanning field of view L2 of the first small probe 105 and the second small probe 106 depends on the thickness BT of the human chest, L2 ≥ BT = 2*R2*cosα (0°<α≤45°, α represents the angle of the probe's initial setting along its center line), and R2 is the length of the short semi-axis of the elliptical cross section. The advantage of the α angle offset is that it can bring about the reception of photons in another direction. The principle of SPECT is that the radionuclides in the human body react with a photon in an arbitrary direction, and the parallel hole collimator is used to identify where it is emitted from. For thin and lean body types, scanning can be achieved by translating the first small probe 105 and the second small probe 106 in the second direction. For fat and thick body types, scanning can be achieved by translating the first small probe 105 and the second small probe 106 in the second direction, and adding the main rotating motor 101 to drive the entire probe to rotate at a small angle.

[0055] Figure 5 is the initial position of each probe. In a specific implementation case, taking the imaging area formed by the parallelogram formed by the four probes as a rectangle as an example, it is assumed that when the first large probe 103 is located directly above, it is in an unrotated state, that is, the rotation angle is 0°.

[0056] like Figure 6 As shown, the present invention also provides a swing acquisition tomography method of a SPECT imaging device. In a specific implementation case, first, Figure 5 The initial position of the start to close, including:

[0057] Step 1: If Figure 6 As shown, the first large probe 103 and the second large probe 104 are controlled to move radially of the SPECT gantry 2, close to the elliptical contour formed by the bed 3 and the human body. The first small probe 105 and the second small probe 106 are controlled to move in opposite directions along a second direction, so that the first small probe 105 does not interfere with the first large probe 103 during radial movement, and the second small probe 106 does not interfere with the second large probe 104 during radial movement.

[0058] Step 2: If Figure 6 As shown, the first small probe 105 and the second small probe 106 are controlled to move radially close to the contour formed by the bed 3 and the human body, and the first large probe 103 and the second large probe 104 are controlled to move in opposite directions along the second direction, so that the first large probe 103 does not interfere with the radial movement of the second small probe 106, and the second large probe 104 does not interfere with the first small probe 105. At this point, planar data at the highest sensitivity in all four directions can be obtained, and tomographic data can also be generated.

[0059] Step 3: If Figure 7As shown, the first large probe 103, the second large probe 104, the first small probe 105 and the second small probe 106 are driven to rotate forward around the bed 3 by a preset angle and to obtain the tomographic data under the first bed position, and then as shown in FIG. Figure 8 After returning to the 0 rotation angle position, continue as shown Figure 9 As shown, reverse the preset angle to obtain the fault data under the second bed. Figure 10 During the rotation process, the first large probe 103, the second large probe 104, the first small probe 105 and the second small probe 106 are dynamically adjusted in the radial direction and the second direction to keep close to the contour.

[0060] The above scanning steps, from 0 degrees to swing angle A (45 degrees forward), swing angle A to 0 degrees to swing angle B (45 degrees reverse), swing angle B to 0 degrees to swing angle A, and so on, are repeated in this way. This is called SPECT wobble scanning. It can quickly achieve tomographic data acquisition and scanning with four or more probes. This solves the problem of conventional SPECT imaging devices that require dual probes to rotate from 0 degrees to 90 degrees to acquire tomographic data, which takes too long.

[0061] like Figure 11 As shown, the disk of the SPECT scanner gantry 2 can be divided into four quadrants based on the number of probes, with each probe located in a quadrant. Each quadrant is equipped with an independent dual-axis motion control system. For example, the translation control system 107 and radial control system 108 in the first quadrant can both be servo motors driving ball screws that move on guide rails. The same applies to the other quadrants, so detailed description is omitted.

[0062] In a specific implementation case, we set a TOF sensor 109 (Time Of Flight) on the side of each probe for controlling the distance between adjacent probes and preventing interference, and set a transverse and axial multi-layered laser or radar sensor 110 on the front end face of each probe for monitoring the distance when the probe is close to the human body or bed. Specifically, the difference between the first and second transverse layers of sensors can be 5mm, 10mm, 15mm, or 20mm. The first transverse layer of sensors is used to identify the contour of the human body when the probe is close to the probe, and the second transverse layer of sensors is used to stop the approach signal. Specifically, the longitudinal sensor can be used to identify the edge of the human target to be measured, so as to better offset the probe laterally.

[0063] Figure 12This is a schematic diagram of the interference points during the scanning process. In a specific implementation case, when the parallelogram imaging area is rectangular, when the execution probe is close to the human body outline, the large probe is first used to move radially close to the target human body outline until the first lateral sensor of the probe detects a human body. At this time, the speed can be slowed down and moved between the first and second lateral sensors. Specifically, the distance can vary from 1 / 2, 1 / 3, or 2 / 3, and the distance between the two lateral sensors can be maintained. If the second lateral sensor is accidentally triggered and detects a human body, the movement will immediately stop and retreat a certain distance, which can vary from 2mm, 3mm, or 4mm. Then, based on the data collected and transmitted back and the longitudinal sensor, the large probe is translated in the second direction. At this point, we know the radial movement distance x1 (x3) and the second-direction translation distance x2 (x4). Based on the mechanical fixed distance, we know the coordinate positions of the interference points (a1, b1) and (a2, b2) of the first small probe 105. As the scanning gantry disk rotates, the coordinates rotate accordingly, but the relative coordinates remain unchanged: a1 = R - x1, b1 = L1 / 2 + x2, a2 ​​= -(R - x3), b2 = -(L1 / 2 - x4), where R is the distance each probe translates to the center point of the contour, L1 is the lateral scanning field of view of the first large probe 103 and the second large probe 104, and L2 is the lateral scanning field of view of the first small probe 105 and the second small probe 106. When the first small probe 105 translates, the horizontal coordinate of the front end of the first small probe 105 does not exceed the a2 position, and the vertical coordinate of the end face does not exceed the b1 position. The same applies to the second small probe 106.

[0064] Figure 13 This is a diagram of other small probe configurations. In specific implementations, while allowing for lateral probe redundancy, the first and second small probes can be tilted to form fixed or variable angles with the major axis of the ellipse, thereby acquiring photon counts at various angles. Similarly, small-angle counterclockwise and clockwise rotations can be used to obtain data without missing corners or truncation. Figure 14 This is a diagram of other large probe configurations. In specific implementations, while allowing for lateral probe redundancy, the first and second large probes can be tilted to a fixed or variable angle with the minor axis of the ellipse to obtain photon counting at various angles. Similarly, small-angle counterclockwise and clockwise rotations can be used to obtain data without missing corners or truncation.

[0065] Figure 15This is a schematic diagram of the interference points during the scanning process, taking the example of setting fixed angles α and β between the first and second largest probes and the horizontal line, and setting fixed angles γ and δ between the first and second small probes and the vertical line. Similarly, when the execution probe is close to the human body contour, the large probe is first used to move radially to approach the target human body contour until the first horizontal layer of the probe sensor is identified. At this time, the speed can be slowed down and moved between the first and second horizontal layers of sensors. Specifically, the spacing can vary from 1 / 2, 1 / 3, or 2 / 3, and the distance between the horizontal sensors can be maintained. If the second horizontal layer of sensors is accidentally triggered, the movement will immediately stop and retreat a certain distance, which can vary from 2mm, 3mm, or 4mm. Then, based on the data collected and transmitted back and the longitudinal sensor, the large probe is translated in the second direction. At this time, we know the radial movement distance x1 (x3) and the second direction translation distance x2 (x4), and the coordinate positions of the first small probe interference points (a1, b1) and (a2, b2) are known based on the mechanical fixed distance. The scanning frame disk rotates, and the coordinates rotate accordingly, but the relative coordinates remain unchanged: a1 = (R-x1) + sinα*L1 / 2, b1 = cosα*L2 / 2 + x2, a2 ​​= -(R-x3-sinβ*L1 / 2), b2 = -(cosβ*L2 / 2-x2), R is the distance between each probe and the center point of the contour, L1 is the lateral scanning field of view of the first large probe 103 and the second large probe 104, L2 is the lateral scanning field of view of the first small probe 105 and the second small probe 106, α is the angle between the first large probe 103 and the translation direction, and β is the angle between the second large probe 104 and the translation direction. When the first small probe 105 is translated, the horizontal coordinate of the front end surface of the first small probe 105 does not exceed the position a2, and the vertical coordinate of the end surface does not exceed the position b1. The same applies to the second small probe 106.

[0066] Figure 16The following is a comparison chart of the close approach between the present application and the original solution (i.e., the patent document indicated in the background technology) under different body shapes. The horizontal scanning field of view of the four probes is a fixed value. It can be seen from the adaptation of the original solution to different body shapes that this design solution is purely incapable of adapting to the body shapes of patients with different body shapes. For the standard body shape, it can be seen that there is a part of the missed sampling in the upper left corner, and the distance is pulled further away. Although the angle data can be compensated by rotation, for patients with fat body shapes, it is obvious that even if it is rotated, there is always a pure missed sampling at the angle between adjacent probes, which will cause data truncation, and when a tomographic image is formed, a large ring artifact will be generated. In addition, for patients with thin body shapes, it can only be guaranteed that the upper and lower large probes are as close to the patient's body contour as possible to the greatest extent possible. The distance between the two small probes on the left and right will be interfered to a longer distance, which will bring a poor sensitivity experience, and there will still be missed sampling at individual angles. In response to the above-mentioned design defects, it can be seen from the new solution that it can adapt to different body shapes. Although the lateral scanning field of view of the four probes is still a fixed value, since they can move laterally themselves, for patients with a relatively fat body shape, the data collection of the parts not covered by the probe can be supplemented by lateral offset; for patients with a relatively thin body shape, the upper and lower probes can be offset 180 degrees in opposite directions to the left and right, making room for the two small left and right probes to be infinitely close to the patient's outline, ensuring data collection at the best sensitivity and resolution, and without any missing angles or any data truncation, and no ring artifacts will be generated when the tomographic image is formed.

[0067] Figure 17 This is a comparison chart of the scanning method of this application and the original scheme. In the SPECT_Axial tomography under the original scheme, usually one bed probe is close to the patient's body contour, and the upper and lower probes are rotated to 180 degrees together to complete the 380-degree data acquisition under one bed, and the second bed needs the probe to be retracted before it can continue to be close to the probe and continue to rotate 180 degrees to complete the 360-degree data acquisition of the second bed. In this way, the whole-body tomography data acquisition of a patient is completed back and forth, which consumes a lot of time. In response to the above design defects, the SPECT_Wobble tomography under the new scheme assumes that the first bed is rotated counterclockwise (0 degrees ≤ angle ≤ 45 degrees), and there is no need to retract the probe. Then the data acquisition under the second bed only requires instantaneous clockwise rotation to the set angle, and the probe is swung back and forth to complete the data acquisition under multiple beds. With the four-probe design, only a very small angle needs to be rotated to complete the whole-body tomography data acquisition of a patient. Thereby, fast whole-body tomography imaging is realized, which provides convenience for patient examination, while avoiding motion artifacts caused by slight movement of patients who lie for a long time during the scanning process.

[0068] Figure 18 This is a diagram of other settings for large and small probes. Figure 19 、 Figure 20 The figure is a schematic diagram of the corresponding probe movement mode. In order to reduce the difficulty of controlling the probe, the first large probe and the first small probe can be combined into an L-shaped probe with a fixed angle. The fixed angle can be 90 degrees or other angles. The long side of the L-shaped probe L1 ≥ L1' = 2R1, and the short side of the L-shaped probe L2 ≥ L2' = 2*R2*cosα (0° < α ≤ 45°). Therefore, the four probes only need two sets of drive systems to control. It can be clearly seen that this solution can reduce the difficulty of the entire probe design and control, while reducing the cost of mechanical and electrical hardware.

[0069] In the description of this application, it should be understood that the terms "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside", etc., indicating the orientation or position relationship, are based on the orientation or position relationship shown in the accompanying drawings, and are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore cannot be understood as a limitation on this application.

[0070] The above describes specific embodiments of the present invention. It should be understood that the present invention is not limited to the specific embodiments described above, and those skilled in the art may make various changes or modifications within the scope of the claims, which do not affect the essence of the present invention. The embodiments of this application and the features in the embodiments may be combined with each other in any manner unless there is a conflict.

Claims

1. A SPECT imaging device, characterized in that: The SPECT scanning frame (2) includes: a main rotating motor (101), a first large probe (103), a second large probe (104), a first small probe (105) and a second small probe (106); The main rotary motor (101) is used to synchronously drive the first large probe (103), the second large probe (104), the first small probe (105) and the second small probe (106) to swing back and forth around the bed (3) at a preset angle; The first large probe (103) and the second large probe (104) are arranged relative to each other and are used to obtain longitudinal data of the human body, and the first small probe (105) and the second small probe (106) are arranged relative to each other and are used to obtain transverse data of the human body; During the reciprocating swinging process, the first large probe (103), the second large probe (104), the first small probe (105) and the second small probe (106) can move forward and backward along the radial direction of the SPECT scanning frame (2) and translate in a second direction perpendicular to the radial direction in the same plane, thereby enclosing an imaging area formed by a parallelogram that is always close to the outline formed by the bed (3) and the human body.

2. The SPECT imaging device according to claim 1, wherein: The first large probe (103), the second large probe (104), the first small probe (105) and the second small probe (106) are each controlled to advance, retreat and translate by a set of movement control systems; Alternatively, the first large probe (103) is connected to the second small probe (106) and is controlled to advance, retreat and translate via a mobile control system, and the second large probe (104) is connected to the first small probe (105) and is controlled to advance, retreat and translate via a mobile control system.

3. The SPECT imaging device according to claim 1, wherein: The preset angle is 0° to 45°.

4. The SPECT imaging device according to claim 1, wherein: The transverse scanning field of view L1 of the first large probe (103) and the second large probe (104) is greater than or equal to the width of the human shoulder BW, and the transverse scanning field of view L2 of the first small probe (105) and the second small probe (106) is greater than or equal to the thickness of the human chest BT.

5. The SPECT imaging device according to claim 1, wherein: Both end faces of each probe are provided with TOF sensors (109) for controlling the distance between adjacent probes and for interference protection; The front end surface of each probe is provided with a transverse and second direction multi-layered opposing laser or radar sensor (110) for monitoring the distance when the probe is close to a human body or a bed.

6. The SPECT imaging device according to claim 1, wherein: Also includes: A power distribution unit PDU (1) and a console (4), wherein the console (4) is electrically connected to the SPECT scanning frame (2), and the power distribution unit PDU (1) supplies power to the console (4) and the SPECT scanning frame (2) respectively.

7. A swing acquisition tomography method for a SPECT imaging device, characterized in that: Using the four-probe SPECT imaging device according to any one of claims 1 to 6, the method comprises: Step 1: Control the first large probe (103) and the second large probe (104) to move radially close to the outline formed by the bed (3) and the human body, and control the first small probe (105) and the second small probe (106) to move in opposite directions along the second direction, so that the first small probe (105) does not interfere with the first large probe (103) when moving radially, and the second small probe (106) does not interfere with the second large probe (104) when moving radially; Step 2: Control the first small probe (105) and the second small probe (106) to move radially close to the outline formed by the bed (3) and the human body, and control the first large probe (103) and the second large probe (104) to move in opposite directions along the second direction, so that the first large probe (103) does not interfere with the radial movement of the second small probe (106), and the second large probe (104) does not interfere with the first small probe (105); Step 3: Drive the first large probe (103), the second large probe (104), the first small probe (105) and the second small probe (106) to rotate forwardly around the bed (3) by a preset angle and obtain the tomographic data under the first bed, then reversely return to the zero rotation angle position and continue to rotate in the reverse direction by a preset angle to obtain the tomographic data under the second bed, and repeat this process until the tomographic data under the required number of beds are obtained.

8. The swing-type acquisition tomography method of the SPECT imaging device according to claim 7, characterized in that: At the zero rotation angle position, the first large probe (103) and the second large probe (104) face the front and back sides of the human body respectively, and the first small probe (105) and the second small probe (106) face the left and right sides of the human body respectively.

9. The swing-type acquisition tomography method of the SPECT imaging device according to claim 7, characterized in that: When the parallelogram imaging area is a rectangle, the radial advance and retreat distance x1 and the translation distance x2 of the first large probe (103), the radial advance and retreat distance x3 and the translation distance x4 of the second large probe (104), the endpoints (a1, b1) of the first large probe (103) and the endpoints (a2, b2) of the second large probe (104) constitute the interference points when the first small probe (105) translates; Wherein, a1=R-x1, b1=L1 / 2+x2, a2=-(R-x3), b2=-(L1 / 2-x4), R is the distance between each probe and the center point of the contour, L1 is the horizontal scanning field of view of the first large probe (103) and the second large probe (104), and L2 is the horizontal scanning field of view of the first small probe (105) and the second small probe (106); When the first small probe (105) is translated, the horizontal coordinate of the front end surface of the first small probe (105) does not exceed the position a2, and the vertical coordinate of the end surface does not exceed the position b1. The same applies to the second small probe (106).

10. The swing-type acquisition tomography method of the SPECT imaging device according to claim 7, characterized in that: When the parallelogram imaging area is non-rectangular, the radial advance and retreat distance x1 and translation distance x2 of the first large probe (103), the radial advance and retreat distance x3 and translation distance x4 of the second large probe (104), and the endpoints (a1, b1) of the first large probe (103) and the endpoints (a2, b2) of the second large probe (104) constitute interference points when the first small probe (105) translates; Wherein, a1=(R-x1)+sinα*L1 / 2, b1=cosα*L2 / 2+x2, a2=-(R-x3-sinβ*L1 / 2), b2=-(cosβ*L2 / 2-x2), R is the distance between each probe and the center point of the contour, L1 is the lateral scanning field of view of the first large probe (103) and the second large probe (104), L2 is the lateral scanning field of view of the first small probe (105) and the second small probe (106), α is the angle between the first large probe (103) and the translation direction, and β is the angle between the second large probe (104) and the translation direction; When the first small probe (105) is translated, the horizontal coordinate of the front end surface of the first small probe (105) does not exceed the position a2, and the vertical coordinate of the end surface does not exceed the position b1. The same applies to the second small probe (106).

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