CN220608330U - kVCT imaging system for spiral tomotherapy equipment with arc detector - Google Patents
kVCT imaging system for spiral tomotherapy equipment with arc detector Download PDFInfo
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- CN220608330U CN220608330U CN202321541090.6U CN202321541090U CN220608330U CN 220608330 U CN220608330 U CN 220608330U CN 202321541090 U CN202321541090 U CN 202321541090U CN 220608330 U CN220608330 U CN 220608330U
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Abstract
The utility model relates to a kVCT imaging system for spiral fault radiotherapy equipment with an arc detector, which comprises the arc detector arranged on an arc guide rail, wherein the arc detector is arranged opposite to an X-ray source bulb tube and a collimator, the arc detector and the X-ray source bulb tube are respectively positioned at two sides of a field of view of an FOV, rays emitted by the X-ray source bulb tube are perpendicular to the arc detector, and the radius of the arc detector and the radius of the arc guide rail are equal to the vertical distance between the X-ray source bulb tube and the arc detector; the arc detector is arranged on the arc guide rail in a sliding way through the executing mechanism or is fixed on the arc guide rail, the definition of the image edge in a large-field state can be improved, and the method is beneficial to more clearly distinguishing the peripheral soft tissue structure of the target area; the accuracy of image guidance of the spiral tomography system is improved; the X-ray detector which is more suitable for the kV-level imaging system of the spiral tomography equipment is used for reducing the cost and improving the utilization efficiency of the detector.
Description
Technical Field
The utility model relates to the technical field of radiotherapy equipment, in particular to a kVCT imaging system for spiral tomography radiotherapy equipment with an arc detector.
Background
Malignant tumor is a main disease threatening human health, and has become the first cause of death of urban and rural residents in China. According to WHO statistics of world health organization, the current tumor treatment adopts three means of operation, radiotherapy and chemotherapy for comprehensive treatment, the cure rate of malignant tumor can reach 45% after 5 years, and 18% of 40% absolute value is contributed by radiotherapy. This cure rate contribution ratio has risen to 20% of the 44% absolute in the latest us 2019 statistics. As technology continues to evolve, radiation therapy will play a more important role in the future.
With the development of radiotherapy technology, people notice that the focus is changed due to organ movement in the radiotherapy process, and the tumor is reduced and deformed with the treatment, so that the radiotherapy dose distribution is changed. One technique known as image guided radiation therapy IGRT has evolved. In the radiation treatment process, the image guiding technology is utilized to accurately position the tumor irradiation field planned to be treated, a multidimensional mode is adopted to definitely determine the target area, the problem of target area movement possibly caused by factors such as human respiration, weight increase and decrease is fully considered, the target area and surrounding tissues can be distinguished, rays can accurately irradiate the target area and avoid the surrounding tissues, errors are reduced, and the accuracy of tumor radiation treatment is further improved. Image guidance techniques commonly employed for image guided radiation therapy include electron portal imaging systems EPID, orthogonal X-ray image guidance systems, cone beam CTCBCT, megavoltage computed tomography MVCT, and the like. Early, image guided radiotherapy mainly adopts an electron field imaging system and an orthogonal X-ray image guiding system, and with the progress of technology, cone beam CT and megavolt computer tomography are currently mainstream by virtue of three-dimensional imaging advantages.
The TOMOTHERAPY of the spiral tomographic radiotherapy system is integrated with a 6MV accelerator and a kV-level fan-shaped beam CT guide system in the same CT frame in a breakthrough manner, the frame moves in a continuous spiral or non-spiral mode along with the stepping of a treatment bed in the treatment process, three-dimensional images of a patient are acquired, the patient always maintains a fixed treatment position, and the swing error is reduced. The length of the kV-level CT image can exceed one meter, and the visual field can reach 50cm. Unlike conventional cone beam imaging, kV-level CT images are collimated with a nominal field width of 5, 10, or 14 cm at the isocenter within the limited longitudinal extent of the kV detector panel, which helps to reduce image scatter.
The traditional kVCT image system mainly comprises a flat dynamic detector, a bulb tube, a collimator and other components, wherein the flat detector in the system generally does not have a scattered grating, and the field of view of the reconstructed image FOV is limited by the size of the detector. For the smallest FOV, the detector effective imaging area projection at the isocenter is 28.8cm x28.8cm in size, with the data direction used in reconstruction centered on the source ray passing through the isocenter. To achieve a large FOV of 50cm maximum, the detector needs to translate laterally on a linear rail, and the scan FOV is determined by the position of the data acquired at the outer edge of the detector. The farther the detector is laterally from the center, the larger the scan FOV. Since flat panel detectors are used in kVCT imaging, for flat panel detectors, obliquely incident X-rays can lead to degradation of spatial resolution at edges and corners, as the interaction points in the layers determine lateral displacement and cause image blurring. This produces deviations in the resolution of the tissue-specific representation, such as tissue, surrounding the target region, thereby affecting the accuracy of the image guidance.
Disclosure of Invention
The utility model aims to solve the defects of the prior art and provides a kVCT imaging system for spiral tomography radiotherapy equipment with an arc detector.
The utility model adopts the following technical scheme to realize the aim:
the kVCT imaging system for the spiral fault radiotherapy equipment with the arc detector comprises the arc detector which is arranged on an arc guide rail, wherein the arc detector is opposite to an X-ray source bulb tube and a collimator, the arc detector and the X-ray source bulb tube are respectively positioned at two sides of a field of view of an FOV, rays emitted by the X-ray source bulb tube are perpendicular to the arc detector, and the radius of the arc detector and the radius of the arc guide rail are equal to the vertical distance between the X-ray source bulb tube and the arc detector;
the arc detector is arranged on the arc guide rail in a sliding way through the actuating mechanism or is fixed on the arc guide rail,
the arc detector comprises a scintillator layer, a photodiode, a thin film transistor layer, a digital-to-analog conversion circuit, a substrate layer and a mounting seat which are sequentially arranged, wherein the scintillator layer is arranged facing an X-ray source bulb tube and a collimator.
When the arc detector is arranged on the arc guide rail in a sliding way through the actuating mechanism, the actuating mechanism comprises a driving wheel, a driving shaft is arranged at the center of the driving wheel and connected with a driving motor, a connecting rod is hinged to the outer edge of the driving wheel, a sliding block is hinged to the other end of the connecting rod, the sliding block is arranged on the arc guide rail in a sliding way, and the sliding block is connected with one side of the bottom of a mounting seat of the arc detector.
The radius of the driving wheel is R, the length of the connecting rod is L, and the distance from the center of the driving wheel to the bottom dead center of the arc-shaped guide rail is L+R.
When the sliding block slides to the lower dead point of the arc-shaped guide rail, the corresponding FOV visual field diameter is 28.8cm; when the slide block slides to the upper dead point of the arc-shaped guide rail, the corresponding FOV field of view diameter is 50cm.
The beneficial effects of the utility model are as follows: the utility model can improve the definition of the image edge in the large-field state after replacing the arc X-ray detector, thereby being beneficial to more clearly distinguishing the peripheral soft tissue structure of the target area; the accuracy of image guidance of the spiral tomography system is improved; the X-ray detector which is more suitable for the kV-level imaging system of the spiral tomography equipment is used for reducing the cost and improving the utilization efficiency of the detector.
Drawings
FIG. 1 is a schematic diagram of the structure of an arc detector of the present utility model when driven by an actuator;
FIG. 2 is a schematic view of the arcuate detector of FIG. 1;
FIG. 3 is a schematic diagram of an actuator according to the present utility model;
FIG. 4 is a schematic view of the arcuate detector as it moves to the bottom dead center of the arcuate guide rail via the actuator;
FIG. 5 is a schematic view of the arcuate detector moving to an arcuate rail top dead center by an actuator;
FIG. 6 is a graph of actuator angular velocity, arcuate detector angular velocity versus time;
FIG. 7 is a schematic view of the structure of the arc detector of the present utility model when directly fixed to an arc guide rail;
FIG. 8 is a schematic view of the arcuate detector of FIG. 7;
in the figure: 1-an arc detector; 2-arc guide rails; 3-X-ray source bulb; a 4-collimator; 5-FOV field of view; 6-an actuator;
11-a scintillator layer; 12-photodiode and thin film transistor layer; 13-a digital-to-analog conversion circuit; 14-substrate layers; 15-mounting seats;
21-arc guide rail bottom dead center; 22-arc guide rail top dead center;
61-driving wheels; 62-a drive shaft; 63-a connecting rod;
the embodiments of the present utility model will be described in detail below with reference to the accompanying drawings.
Detailed Description
The principles and features of the present utility model are described below with reference to the drawings, the examples are illustrated for the purpose of illustrating the utility model and are not to be construed as limiting the scope of the utility model. The utility model is more particularly described by way of example in the following paragraphs with reference to the drawings. The advantages and features of the present utility model will become more apparent from the following description. It should be noted that the drawings are in a very simplified form and are all to a non-precise scale, merely for convenience and clarity in aiding in the description of embodiments of the utility model.
It will be understood that when an element is referred to as being "fixed to" another element, it can be directly on the other element or intervening elements may also be present. When a component is considered to be "connected" to another component, it can be directly connected to the other component or intervening components may also be present. When an element is referred to as being "disposed on" another element, it can be directly on the other element or intervening elements may also be present. The terms "vertical," "horizontal," "left," "right," and the like are used herein for illustrative purposes only.
Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this utility model belongs. The terminology used herein in the description of the utility model is for the purpose of describing particular embodiments only and is not intended to be limiting of the utility model. The term "and/or" as used herein includes any and all combinations of one or more of the associated listed items.
The utility model is further illustrated by the following examples in conjunction with the accompanying drawings:
the kVCT imaging system for spiral fault radiotherapy equipment with arc detectors comprises an arc detector 1 arranged on an arc guide rail 2, wherein the arc detector 1 is arranged opposite to an X-ray source bulb tube 3 and a collimator 4, the arc detector 1 and the X-ray source bulb tube 3 are respectively positioned on two sides of a FOV visual field 5, rays emitted by the X-ray source bulb tube 3 are perpendicular to the arc detector 1, and the radius of the arc detector 1 and the radius of the arc guide rail 2 are equal to the perpendicular distance between the X-ray source bulb tube 3 and the arc detector 1. All X-rays emitted by the X-ray source bulb 3 are irradiated perpendicularly to the surface of the arcuate detector 1 and no degradation due to non-perpendicularly incident X-rays occurs.
The structure of the arc detector 1 is shown in fig. 2 and 8, and comprises a scintillator layer 11, a photodiode, a thin film transistor layer 12, a digital-to-analog conversion circuit 13, a substrate layer 14 and a mounting seat 15 which are sequentially arranged, wherein the scintillator layer 11 faces an X-ray source bulb tube 3 and a collimator 4.
The scintillator layer 11 is prepared from cesium iodide or gadolinium oxysulfide; the substrate layer 14 is a glass substrate or an organic thin film substrate.
The arc detector 1 can be arranged on the arc guide rail 2 in a sliding way through the actuating mechanism 6, as shown in figures 1 to 2.
When the arc detector 1 is slidably arranged on the arc guide rail 2 through the actuating mechanism 6, the actuating mechanism 6 is shown in fig. 3, and comprises a driving wheel 61, a driving shaft 62 is arranged at the center of the driving wheel 61, the driving shaft 62 is connected with a driving motor, the outer edge of the driving wheel 61 is hinged with a connecting rod 63, the other end of the connecting rod 63 is hinged with a sliding block, the sliding block is slidably arranged on the arc guide rail 2, and the sliding block is connected with one side of the bottom of the mounting seat 15 of the arc detector 1.
The driving mode of the driving motor, the driving shaft, the driving wheel 61 and the connecting rod 63 can enable the sliding block to move between two points, the driving is simple, reversing is not needed, and the movement is smooth and free of impact.
The radius of the driving wheel 61 is R, the length of the connecting rod 63 is L, and the distance from the center of the driving wheel 61 to the arc guide rail bottom dead center 21 is l+r. The center of the driving wheel 61 is over the center of the driving shaft 62 by a distance L from the outer circumference of the driving wheel 61.
The sequence of the driving operation is as follows: the driving motor rotates in one direction to drive the arc detector 1 to move between an arc guide rail bottom dead center 21 and an arc guide rail top dead center 22 of the arc guide rail 2. When the sliding block slides to the arc-shaped guide rail bottom dead center 21, the corresponding FOV field of view 5 has a diameter of 28.8cm; when the slider slides to the arc guide rail top dead center 22, the corresponding FOV view 5 is 50cm in diameter. The driving motor rotates at a constant speed, the speed of the arc detector 1 changes periodically within the interval of 0-180 degrees in a sinusoidal curve, and the speed when reaching two dead points is zero. As shown in fig. 4 to 6.
Of course, in order to simplify the overall construction, the utility model also makes it possible to fix the arc detector 1 to the arc guide rail 2, as shown in fig. 7 to 8. That is, the size of the arc detector 1 can be increased, different irradiation field sizes can be realized according to the spiral tomography equipment from small to large, and the full-size arc detector 1 is used for covering the moving imaging range. The arc detector 1 can realize the change from small visual field to large visual field without moving, and the change only needs to adjust the size of the ball tube end lead door
The utility model replaces plane detection in the existing kVCT imaging system by using the arc detector 1. From the application of the medical imaging field, the human body through which the X-rays pass can be regarded as an object with cambered surfaces having different densities, and the light beam passing through the cambered object is received by using the cambered image sensing to reduce more distortion and keep high image quality. For example, the eyeball of a human body is a good arc-shaped spherical image receiving sensor.
An X-ray detector is an image sensor capable of receiving X-ray photons, which can be converted into visible light by a scintillator layer 11 attached to a photodiode and thin film transistor layer 12. With the rapid development of LCD and material industries in recent years, the original glass substrate is gradually thinned from 1.1 mm to 0.2 mm, and even the use of photodiodes and thin film transistor layers 12 of organic materials attached to PET substrates has been started. The progress of the technology has led to the arc-shaped X-ray detector being mainly applied to industrial nondestructive detection and pipeline detection.
According to the utility model, the arc detector 1 is applied to a kV-level image system in a radiotherapy device, so that the image guiding accuracy of the spiral tomography radiotherapy system is improved.
While the utility model has been described above with reference to the accompanying drawings, it will be apparent that the utility model is not limited to the above embodiments, but is intended to cover various modifications, either made by the method concepts and technical solutions of the utility model, or applied directly to other applications without modification, within the scope of the utility model.
Claims (5)
1. The kVCT imaging system for the spiral fault radiotherapy equipment with the arc detector is characterized by comprising the arc detector (1) arranged on an arc guide rail (2), wherein the arc detector (1) is opposite to an X-ray source bulb tube (3) and a collimator (4), the arc detector (1) and the X-ray source bulb tube (3) are respectively positioned at two sides of a FOV (field of view) field (5), rays emitted by the X-ray source bulb tube (3) are perpendicular to the arc detector (1), and the radius of the arc detector (1) and the radius of the arc guide rail (2) are equal to the perpendicular distance between the X-ray source bulb tube (3) and the arc detector (1); the arc detector (1) is arranged on the arc guide rail (2) in a sliding way through the actuating mechanism (6) or the arc detector (1) is fixed on the arc guide rail (2).
2. kVCT imaging system for spiral tomotherapy equipment with arc detector according to claim 1, characterized in that the arc detector (1) comprises a scintillator layer (11), a photodiode and thin film transistor layer (12), a digital-to-analogue conversion circuit (13), a substrate layer (14) and a mounting seat (15) which are arranged in sequence, the scintillator layer (11) being arranged facing the X-ray source bulb (3), the collimator (4).
3. kVCT imaging system for spiral tomotherapy equipment with arc detector according to claim 2, characterized in that when arc detector (1) is slidingly arranged on arc guide rail (2) through actuating mechanism (6), actuating mechanism (6) comprises driving wheel (61), driving shaft (62) is arranged in the center of driving wheel (61), driving shaft (62) is connected with driving motor, connecting rod (63) is hinged at the outer edge of driving wheel (61), sliding block is hinged at the other end of connecting rod (63), sliding block is slidingly arranged on arc guide rail (2), sliding block is connected with one side of the bottom of mounting seat (15) of arc detector (1).
4. A kVCT imaging system for a helical tomotherapy apparatus with arc detector according to claim 3, characterized in that the radius of the driving wheel (61) is R and the length of the connecting rod (63) is L, the distance from the center of the driving wheel (61) to the arc guide bottom dead center (21) is l+r.
5. kVCT imaging system for a helical tomotherapy apparatus with arc detector according to claim 4, characterized in that when the slide is slid to arc rail bottom dead center (21), the corresponding FOV field of view (5) is 28.8cm in diameter; when the slide block slides to the upper dead point (22) of the arc-shaped guide rail, the corresponding FOV field of view (5) has a diameter of 50cm.
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202321541090.6U CN220608330U (en) | 2023-06-16 | 2023-06-16 | kVCT imaging system for spiral tomotherapy equipment with arc detector |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202321541090.6U CN220608330U (en) | 2023-06-16 | 2023-06-16 | kVCT imaging system for spiral tomotherapy equipment with arc detector |
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| CN220608330U true CN220608330U (en) | 2024-03-19 |
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| CN202321541090.6U Active CN220608330U (en) | 2023-06-16 | 2023-06-16 | kVCT imaging system for spiral tomotherapy equipment with arc detector |
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- 2023-06-16 CN CN202321541090.6U patent/CN220608330U/en active Active
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