Medical imaging system and thermal control method thereof for preventing overheat of detector

Abstract

The invention provides a medical imaging system and a thermal control method thereof for preventing overheating of a detector. The method comprises the steps of judging whether the detector assembly is parked at a preset parking position or not based on obtained position information of the detector assembly; and in response to one of: (1) determining that the detector assembly is not parked in the predetermined parking position, or (2) determining that the detector assembly is not parked in the predetermined parking position and a user allows the detector assembly to return to the predetermined parking position, when the detector assembly is parked at the preset parking position, at least most of the detector assembly is located in the airflow jet flow area of at least one rack bottom fan.

Description

Technical Field

[0001] The present disclosure relates generally to medical imaging, and more particularly to a medical imaging system and a thermal control method of the system for preventing detector overheating. Background Art

[0002] Non-invasive radiographic techniques allow images of the internal structures of a scanned object (e.g., a patient) to be obtained without performing an invasive procedure on the scanned object. Specifically, techniques such as computed tomography (CT) use various physical principles (such as differential transmission of x-rays through a target volume) to acquire image data and construct a tomographic image (e.g., a three-dimensional representation of the interior of a human body or other imaged structure).

[0003] In modern CT imaging systems, the CT gantry includes an annular frame with an x-ray radiation source on one side of the frame and an x-ray detector array or detector assembly on the opposite side. The scanned object is positioned on a workbench, and the annular frame can rotate around the scanned object, thereby generating thousands of cross-sectional views of the scanned object in one scan. The x-ray radiation source generally includes an x-ray tube, which emits a fan-shaped or cone-shaped x-ray beam at a focal point. The x-ray beam passes through the scanned object, is attenuated by the scanned object, and then impinges on the x-ray detector array. The radiation intensity received at the x-ray detector array generally depends on the attenuation of the x-ray beam by the scanned object. The detector array includes a plurality of x-ray detector elements, and the x-ray detector elements generally include a collimator, a scintillator, and a photodiode, wherein the collimator is used to collimate the x-ray beam received at the detector element, and each scintillator in the scintillator array converts the x-ray into light energy and releases the light energy to the photodiode adjacent thereto. Each photodiode detects the light energy and generates a corresponding electrical signal. The electrical signal output by the photodiode is transmitted to the data processing system after A / D conversion by an application specific integrated circuit (ASIC) for image reconstruction.

[0004] On one hand, during a CT imaging system scan, the x-ray tube and electronic devices such as the A / D ASIC generate a lot of heat. On the other hand, some electronic devices within the detector assembly, such as the scintillator, photodiode, and A / D ASIC, are sensitive to temperature. If the temperature of these electronic devices drifts during the use of the system, image quality problems (e.g., artifacts) may occur. Therefore, it is desirable to maintain the environment within the gantry at a controlled temperature to minimize thermal drift during use.

[0005] In order to maintain the environment in the gantry at a controlled temperature, the CT imaging system is usually placed in a room with a temperature range of 18°C ​​to 26°C. However, due to the large differences in the use of CT imaging systems, the large or small use of x-ray tubes and electronic equipment will cause the air temperature inside the CT gantry to experience a large range of changes, for example, the temperature inside the CT gantry can range from 18°C ​​to more than 38°C. For this reason, the temperature control range of the detector assembly usually needs to be designed, for example, from about 26°C to about 43°C, so that the CT imaging system can work in various regions and various working conditions (for example, different latitudes and different altitudes) as much as possible.

[0006] In the prior art, three or four levels of temperature control are usually used to adjust the air temperature inside the CT gantry and the temperature of the detector assembly, such as controlling the speed of the fan on the top of the CT gantry, controlling the speed of the fan of the detector assembly, controlling the temperature of the heater of the detector module, etc. In some cases, it is also necessary to control the air temperature at the entrance of the gantry, the air temperature at the entrance of the detector assembly, etc. Multi-level temperature control increases the complexity of the CT imaging system and also increases the difficulty of designing the temperature control system.

[0007] Air cooling is usually used to dissipate heat from electronic devices in the detector assembly. In an existing implementation, the detector assembly is contained in a closed structure, on which multiple detector assembly fans and multiple air outlets are installed. The airflow generated by the fan is sent into the closed structure, and the airflow is discharged from the air outlet through the ventilation chamber in the closed structure, thereby taking away the heat generated by the electronic devices to achieve heat dissipation and cooling. However, each detector assembly fan provides convection for its own "area". Due to the influence of geometric factors in the CT frame, each area may experience very different thermal conditions. For example, fans located in the front area in the direction of rotation of the frame will experience larger airflows, while fans located in the center area or the rear area may experience different amounts of airflow. Therefore, thermal gradients may be generated between areas. Taking into account widely varying environmental conditions, system operating conditions, and geometric effects, the fan speed for each area is controlled separately.

[0008] However, individual control of the fans can cause crosstalk between zones within the plenum, where airflow in one zone can affect airflow in adjacent zones, affecting control efficiency. Additionally, fan speeds are switched over a wide range of speeds during system use. Fan cycling shortens fan life, leading to expensive repairs. Also, high-speed rotation of the frame can cause lateral impacts on the bearings of the detector assembly fan, affecting fan life. Additionally, fan cycling can cause increased noise as the fan bearings age. When system users hear the noise of fan switching, they may suspect that the fan is about to fail and become annoyed.

[0009] Therefore, there is a need for a thermal control method for improving thermal performance within a gantry in a medical imaging system, and a medical imaging system using the same. Summary of the invention

[0010] The object of the present disclosure is to overcome the above and / or other problems in the prior art and to provide a thermal control method for improving the thermal performance within a rack in a medical imaging system, and a medical imaging system using the method.

[0011] According to a first aspect of the present invention, a thermal control method for a medical imaging system is provided, the method comprising: determining whether the detector assembly is parked at a first predetermined docking position based on acquired position information of the detector assembly; and rotating the detector assembly to park the detector assembly at the first predetermined docking position in response to one of the following events: determining that the detector assembly is not parked at the first predetermined docking position, or determining that the detector assembly is not parked at the first predetermined docking position and a user allows the detector assembly to return to the first predetermined docking position, wherein, when the detector assembly is parked at the first predetermined docking position, at least most of the detector assembly is located within an airflow jet area of ​​at least one rack bottom fan.

[0012] Preferably, the method also includes: during the scanning operation phase of the medical imaging system, in response to determining that the detector assembly is overheated, rotating the detector assembly until the temperature of the detector assembly meets a predetermined temperature control standard; and in response to determining that the temperature of the detector assembly meets the predetermined temperature control standard, parking the detector assembly at the first predetermined parking position.

[0013] Preferably, during the scanning operation phase of the medical imaging system, the step of rotating the detector assembly until the temperature of the detector assembly meets a predetermined temperature control standard in response to determining that the detector assembly is overheated includes: obtaining the position information of the detector assembly for determining whether the detector assembly is parked in the first predetermined parking position in response to determining that the detector assembly is overheated; rotating the detector assembly until the temperature of the detector assembly meets the predetermined temperature control standard in response to one of the following events: determining that the detector assembly is not parked in the first predetermined parking position, or determining that the detector assembly is not parked in the first predetermined parking position and the user allows the detector assembly to return to the first predetermined parking position.

[0014] Preferably, the detector assembly includes a plurality of detector modules, and the method further includes: during a scanning operation phase of the medical imaging system, determining whether the detector assembly is overheated by determining whether the highest temperature of the plurality of detector modules exceeds a predetermined temperature; or determining whether the temperature of the detector assembly meets a predetermined temperature control standard by determining whether the highest temperature of the plurality of detector modules drops within a predetermined temperature range.

[0015] Preferably, the method further comprises: during a scanning operation phase of the medical imaging system, when a user allows the detector assembly to return to the first predetermined parking position, rotating the detector assembly until a highest temperature of the plurality of detector modules drops within a predetermined temperature range.

[0016] Preferably, the method further comprises: during a scanning operation phase of the medical imaging system, in response to determining that the highest temperature of the plurality of detector modules exceeds the predetermined temperature and that the detector assembly has been parked at the first predetermined parking position, determining whether the at least one rack bottom fan has failed; and in response to determining that none of the at least one rack bottom fan has failed, detecting whether other cooling devices except the rack bottom fan are operating normally.

[0017] Preferably, the method further comprises: during a scanning operation phase of the medical imaging system, performing one of the following thermal controls: when the at least one rack bottom fan comprises only one rack bottom fan, in response to determining that the single rack bottom fan has failed, issuing a warning indicating that the single rack bottom fan has failed, and rotating the detector assembly until the highest temperature of the plurality of detector modules drops to within the predetermined temperature range; or, when the at least one rack bottom fan comprises at least two rack bottom fans, in response to determining that a portion of the at least one rack bottom fans have failed, rotating the detector assembly until the highest temperature of the plurality of detector modules drops to within the predetermined temperature range. temperature range, and the detector assembly is parked at a second predetermined parking position, wherein, when the detector assembly is parked at the second predetermined parking position, at least most of the detector assembly is located in an airflow jet area formed by one or more of the other rack bottom fans among the at least two rack bottom fans except the faulty rack bottom fan; or, when the at least one rack bottom fan includes at least two rack bottom fans, in response to determining that all of the at least one rack bottom fans have failed, the detector assembly is rotated until the highest temperature of the multiple detector modules drops to within the predetermined temperature range, and the detector assembly is parked at the first predetermined parking position.

[0018] Preferably, the method further comprises: issuing a warning indicating that the detector assembly is not parked in the first predetermined docking position in response to one of the following events: determining that the detector assembly is not parked in the first predetermined docking position, or determining that the detector assembly is not parked in the first predetermined docking position and the user refuses to return the detector assembly to the first predetermined docking position.

[0019] Preferably, the method also includes: during the startup phase of the medical imaging system, allowing the medical imaging system to continue normal operation in response to one of the following events: determining that the detector assembly is parked at or rotated to the first predetermined docking position, or the user refuses to return the detector assembly to the first predetermined docking position.

[0020] Preferably, the method also includes: during the scanning operation phase of the medical imaging system, prohibiting the scanning operation in response to the following events: determining that the detector assembly is overheated; determining that the detector assembly is not parked in the first predetermined parking position; and the user refusing to return the detector assembly to the first predetermined parking position.

[0021] According to a second aspect of the present invention, a medical imaging system is provided, comprising: a frame, the frame comprising a radiation source, a detector assembly, wherein the detector assembly comprises a detector module for sensing radiation from the radiation source, and the radiation source and the detector assembly are rotatable relative to the frame; at least one fan, the at least one fan being located at the bottom of the frame; and a thermal controller configured to execute the thermal control method according to the first aspect of the present invention.

[0022] Preferably, the detector assembly also includes a detector module temperature sensor and a detector module heater, but does not include a heat dissipation device, wherein the detector module temperature sensor is located on the detector module and is used to sense the temperature of the detector module, and the detector module heater is located at the bottom of the detector module and is used to heat the detector module.

[0023] Preferably, the at least one fan has a corresponding airflow jet area, and the at least one fan is positioned so that when the detector assembly is parked in the first predetermined parking position, at least most of the detector assembly is located in the airflow jet area of ​​the at least one fan.

[0024] Preferably, the at least one rack bottom fan includes at least two rack bottom fans, and the at least one fan is further positioned so that when the detector assembly is parked at the second predetermined parking position, at least most of the detector assembly is located in an airflow jet area formed by one or more of the other rack bottom fans among the at least two rack bottom fans except the faulty rack bottom fan.

[0025] Preferably, the first predetermined parking position is associated with the positioning of the at least one wind turbine.

[0026] Preferably, the at least one rack bottom fan comprises at least two rack bottom fans, and

[0027] The first predetermined parking position and the second predetermined parking position are associated with positioning of one or more bottom-of-rack fans among the at least two bottom-of-rack fans.

[0028] Preferably, the first predetermined docking position and the second predetermined docking position are associated with directions and opening sizes of air guide ducts of one or more rack bottom fans among the at least two rack bottom fans.

[0029] The present disclosure provides a fan at the bottom of the rack of the medical imaging system, and utilizes the airflow jet area of ​​the fan at the bottom of the rack to prevent the detector assembly from overheating through the above-mentioned thermal control method. The technical solution of the present disclosure does not require the use of a detector assembly fan and a ventilation chamber. Compared with the solution of using a detector assembly fan and a ventilation chamber to prevent the detector assembly from overheating, the solution of the present disclosure has many advantages, including at least: (1) it can simplify the structure of the detector assembly and reduce manufacturing costs and replacement costs; (2) it can reduce the difficulty of cooling control; (3) it can eliminate the safety hazards of the original assembly structure and improve the reliability of the medical imaging system; (4) when the detector module is heated by a detector module heater, the heating speed is accelerated and the heating efficiency is improved. BRIEF DESCRIPTION OF THE DRAWINGS

[0030] The present invention can be better understood by describing the exemplary embodiments of the present invention in conjunction with the accompanying drawings. It should be understood that these drawings only depict typical embodiments of the present invention and should not be considered as limiting the scope of protection claimed by the present invention. In the accompanying drawings,

[0031] Figure 1 is a schematic diagram of an exemplary CT imaging system 100;

[0032] Figure 2 is similar to Figure 1 A block schematic diagram of an exemplary imaging system 200 of the illustrated CT imaging system 100;

[0033] Figure 3is a schematic plan view of a rack with a bottom fan according to an embodiment of the present invention;

[0034] Figure 4A is a perspective schematic diagram depicting the air inlet side of a fan at the bottom of a rack according to an embodiment of the present invention;

[0035] Figure 4B is a perspective schematic diagram depicting the fan air outlet side at the bottom of a rack according to an embodiment of the present invention;

[0036] Figure 4C is a schematic diagram depicting an airflow jet area of ​​a fan at the bottom of a rack according to an embodiment of the present invention;

[0037] Figure 5A is a plan view of a separate airflow jet area formed by a fan on the left side of the bottom of a rack according to an embodiment of the present invention;

[0038] Figure 5B is a plan view of a separate airflow jet area formed by a fan on the right side of the bottom of a rack according to an embodiment of the present invention;

[0039] Figure 5C is a plan view of a mixed airflow jet area formed by fans on both sides of the bottom of a rack according to an embodiment of the present invention;

[0040] Figure 6 is a flow chart of a thermal control method for a medical imaging system according to an embodiment of the present invention;

[0041] Figure 7 is a flow chart of a thermal control method performed during a startup phase of a medical imaging system according to an embodiment of the present invention;

[0042] Fig. 8A is a flow chart of a first portion 800A of a thermal control method performed during a scanning operation phase of a medical imaging system according to an embodiment of the present invention;

[0043] Figure 8B is a flow chart of a second part 800B of a thermal control method performed during a scanning operation phase of a medical imaging system according to an embodiment of the present invention;

[0044] Figure 8C is a flow chart of a third portion 800C of a thermal control method performed during a scanning operation phase of a medical imaging system according to an embodiment of the present invention;

[0045] Fig.8D is a flow chart of a fourth portion 800D of a thermal control method performed during a scanning operation phase of a medical imaging system according to an embodiment of the present invention;

[0046] Fig. 8Eis a flow chart of a fourth portion 800E of a thermal control method performed during a scanning operation phase of a medical imaging system according to an embodiment of the present invention.

[0047] In the drawings, similar components and / or features may have the same numerical reference numeral. In addition, components of the same type may be distinguished by following the reference numeral with a letter that distinguishes between similar components and / or features. If only the first numerical reference numeral is used in the specification, the description applies to any similar component and / or feature having the same first numerical reference numeral, regardless of the subsequent letters.

[0048] In the accompanying drawings, some structural or method features may be shown in a particular arrangement and / or order. However, it should be understood that such a particular arrangement and / or order may not be required. Rather, in some embodiments, these features may be arranged in a manner and / or order different from that shown in the accompanying drawings of the specification. In addition, the inclusion of structural or method features in a particular figure does not imply that such features are required in all embodiments, and in some embodiments, these features may not be included or may be combined with other features. DETAILED DESCRIPTION

[0049] The specific embodiments of the present invention will be described below. It should be noted that in the specific description of these embodiments, in order to be concise and clear, this specification cannot provide a detailed description of all the features of the actual embodiments. It should be understood that in the actual implementation of any embodiment, just as in the process of any engineering project or design project, in order to achieve the specific goals of the developer and to meet system-related or business-related restrictions, various specific decisions are often made, and this will also change from one embodiment to another. In addition, it can also be understood that although the efforts made in this development process may be complex and lengthy, for ordinary technicians in the field related to the content disclosed by the present invention, some changes in design, manufacturing or production based on the technical content disclosed in this disclosure are just conventional technical means, and should not be understood as insufficient content of this disclosure.

[0050] References in the specification to "one embodiment", "an embodiment", "an example embodiment", etc. indicate that the described embodiment may include a particular feature, structure, or characteristic, but not every embodiment may include the particular feature, structure, or characteristic. In addition, such phrases do not necessarily refer to the same embodiment. In addition, when a particular feature, structure, or characteristic is described in conjunction with an embodiment, it is considered that it is within the knowledge of those skilled in the art to affect such feature, structure, or characteristic in conjunction with other embodiments (whether or not explicitly described).

[0051] For purposes of this disclosure, the phrase "A and / or B" means (A), (B), or (A and B) and the phrase "A, B, and / or C" means (A), (B), (C), (A and B), (A and C), (B and C), or (A, B, and C).

[0052] Unless otherwise defined, the technical or scientific terms used in the claims and the specification shall have the common meanings understood by persons with ordinary skills in the technical field to which the invention belongs. The words "first", "second" and similar words used in the patent application specification and the claims of the present invention do not indicate any order, quantity or importance, but are only used to distinguish different components. Words such as "one" or "a" do not indicate a quantity limitation, but indicate the existence of at least one. Words such as "include" or "comprise" mean that the elements or objects appearing before "include" or "comprise" include the elements or objects listed after "include" or "comprise" and their equivalent elements, and do not exclude other elements or objects. Words such as "connect" or "connected" are not limited to physical or mechanical connections, nor are they limited to direct or indirect connections. "Scanning objects" generally include but are not limited to patients, animals, inanimate objects, one or more manufactured parts, industrial parts and / or foreign objects (such as implants, stents and / or contrast agents present in the body), etc. "Majority" generally refers to more than 50% of the object. For example, the majority of the detector assembly is greater than 50% of the detector assembly.

[0053] The following will take the example of Figure 1 8 to describe an embodiment of the present disclosure.

[0054] I. Imaging System

[0055] Although the operating environment of the present invention is described for an x-ray computed tomography (CT) imaging system, it should be understood that the technology of the present invention is also applicable to medical imaging systems and / or medical imaging devices that utilize other imaging modalities to acquire images, such as x-ray imaging systems, magnetic resonance imaging (MRI) systems, positron emission tomography (PET) imaging systems, single photon emission computed tomography (SPECT) imaging systems, and combinations thereof (e.g., multi-modality imaging systems, such as PET / CT, PET / MR imaging systems). The description of the CT imaging system is provided only as an example of a suitable imaging system.

[0056] Figure 1is a schematic diagram of an exemplary CT imaging system 100. Specifically, the CT imaging system 100 is configured to image a subject 112 (such as a patient, an inanimate object, one or more manufactured parts, industrial parts) and / or a foreign object (such as an implant, a stent, and / or a contrast agent present in the body). Throughout this disclosure, the terms "subject" and "scanned object" may be used interchangeably, and it should be understood that, at least in some embodiments, a patient is a type of subject that can be imaged by the CT imaging system 100, and the subject may include a patient. In some embodiments, the CT imaging system 100 includes a gantry 102, which in turn may also include at least one x-ray radiation source 104, which at least one x-ray radiation source 104 may be configured to project an x-ray beam (or x-rays) 106 (see Figure 2 ) for imaging the subject 112. Specifically, the x-ray radiation source 104 can be configured to project the x-ray beam 106 toward the detector array 108 positioned on the opposite side of the gantry 102. Figure 1 Only a single x-ray radiation source 104 is depicted, but in some embodiments, multiple x-ray radiation sources 104 may be employed to project multiple x-ray beams 106 toward multiple detectors to acquire projection data corresponding to the subject 112 at different energy levels.

[0057] In some embodiments, the x-ray radiation source 104 projects a fan-shaped or cone-shaped x-ray beam 106 that is collimated to lie in an XY plane (generally referred to as an "imaging plane" or "scanning plane") of a Cartesian coordinate system. The x-ray beam 106 passes through a subject 112. The x-ray beam 106 is incident on a detector array 108 after being attenuated by the subject 112. The intensity of the attenuated radiation beam received at the detector array 108 depends on the attenuation of the x-ray beam 106 by the subject 112. Each detector element in the detector array 108 generates a separate electrical signal that is a measure of the intensity of the x-ray beam at the corresponding detector element position. Intensity measurements from all detector elements are acquired separately to produce a transmission distribution.

[0058] In a third generation CT imaging system, a gantry 102 may include a rotatable annular frame 103, with at least one x-ray radiation source 104 and a detector array 108 arranged on opposite sides of the annular frame 103. The rotation of the frame 103 causes the x-ray radiation source 104 and the detector array 108 to rotate around the subject 112 in the imaging plane, causing the angle at which the x-ray beam 106 intersects the subject 112 to continuously change. A full gantry rotation occurs when the frame 103 completes a full 360 degree rotation. A set of x-ray attenuation measurements (e.g., projection data) from the detector array 108 at one frame angle is referred to as a "view." Thus, a view is each incremental position of the frame 103. A "scan" of the subject 112 includes a set of views made at different frame angles or viewing angles during one rotation cycle of the x-ray radiation source 104 and the detector array 108.

[0059] In an axial scan, the projection data is processed to construct an image corresponding to a two-dimensional slice taken through the subject 112. One method of reconstructing an image from a set of projection data is known in the art as a filtered back projection technique. This method converts attenuation measurements from a scan into an integer called a "CT number" or "Houan Unit" (HU), which is used to control the brightness of a corresponding pixel on, for example, a cathode ray tube display.

[0060] In some embodiments, the CT imaging system 100 may include a depth camera 114 positioned on or outside the gantry 102. Figure 1As shown, the depth camera 114 is mounted on a ceiling 116 located above the subject 112 and is oriented to image the subject when the subject 112 is at least partially outside the rack 102. The depth camera 114 may include one or more light sensors, and the one or more light sensors may include one or more visible light sensors and / or one or more infrared (IR) light sensors. In some embodiments, the one or more IR sensors may include one or more sensors in both the near IR range and the far IR range to achieve thermal imaging. In some embodiments, the depth camera 114 may also include an IR light source. The light sensor may be any 3D depth sensor, such as a time of flight (ToF) sensor, a stereo sensor, or a structured light depth sensor, which is operable to generate a 3D depth image, while in other embodiments, the light sensor may be a two-dimensional (2D) sensor, which is operable to generate a 2D image. In some such embodiments, the 2D light sensor can be used to infer depth based on an understanding of light reflection phenomena to estimate the 3D depth. Regardless of whether the optical sensor is a 3D depth sensor or a 2D sensor, the depth camera 114 may be configured to output a signal encoding an image to a suitable interface, which may be configured to receive the signal encoding the image from the depth camera 114. In other embodiments, the depth camera 114 may also include other components, such as a microphone, to enable reception and analysis of directional and / or non-directional sounds from an observed subject and / or other sound sources.

[0061] In some embodiments, the CT imaging system 100 may further include an image processing unit 110 configured to reconstruct an image of a target volume of a subject using a suitable reconstruction method, such as an iterative image reconstruction method or an analytical image reconstruction method. For example, the image processing unit 110 may reconstruct an image of a target volume of a subject using an analytical image reconstruction method, such as filtered back projection (FBP). As another example, the image processing unit 110 may reconstruct an image of a target volume of a subject using an iterative image reconstruction method, such as adaptive statistical iterative reconstruction (ASIR), conjugate gradient (CG), maximum likelihood expectation maximization (MLEM), model-based iterative reconstruction (MBIR), etc.

[0062] As used herein, the phrase "reconstructing an image" is not intended to exclude embodiments in which data representing an image is generated rather than a visible image. Thus, as used herein, the term "image" broadly refers to both a visible image and data representing a visible image. However, many embodiments generate (or are configured to generate) at least one visible image.

[0063] The CT imaging system 100 further includes a table 115 on which the subject 112 is positioned for imaging. The table 115 may be motorized so as to be movable in the horizontal direction (XZ plane) and the vertical direction (Y). The horizontal direction includes the transverse direction (X direction of the medical imaging system) and the longitudinal direction (Z direction of the medical imaging system). During scanning imaging, the table 115 moves in the longitudinal direction. Therefore, as will be described below with respect to Figure 2 As described, the table 115 may include a motor and a motor controller. The table motor controller moves the table 115 by adjusting the motor so as to properly position the subject in the gantry 102 to acquire projection data corresponding to a target volume of the subject. The table motor controller may adjust the height of the table 115 (e.g., a vertical position relative to the ground on which the table is located) and the horizontal position of the table 115 (e.g., a horizontal position parallel to a transverse direction or a longitudinal direction).

[0064] Figure 2 is a block diagram showing a diagram similar to Figure 1 1. An exemplary imaging system 200 of the CT imaging system 100 is shown. In some embodiments, the imaging system 200 includes a detector array 108 (see Figure 1 ). The detector array 108 also includes a plurality of detector elements 202 that together collect the x-ray beam 106 that passes through the subject 112 (see Figure 1 ) to obtain corresponding projection data. Therefore, in some embodiments, the detector array 108 is manufactured in a multi-slice configuration including multiple rows of units or detector elements 202. In such a configuration, one or more additional rows of detector elements 202 are arranged in a parallel configuration for collecting projection data. In some examples, the individual detectors or detector elements 202 of the detector array 108 may include photon counting detectors that register the interaction of individual photons into one or more energy bins. It should be understood that the methods described herein may also be implemented using energy integrating detectors.

[0065] In some embodiments, the imaging system 200 is configured to traverse different angular positions around the subject 112 to obtain the desired projection measurement data. Therefore, the frame 103 and the components mounted thereon can be configured to rotate about the rotation center 206 to obtain, for example, projection measurement data at different energy levels. Alternatively, in embodiments where the projection angle relative to the subject 112 varies over time, the mounted components can be configured to move along a general arc rather than along a section of a circle.

[0066] In some embodiments, the imaging system 200 includes a control mechanism 208 to control the movement of components, such as the rotation of the frame 103 and the operation of the x-ray radiation source 104. In some embodiments, the control mechanism 208 also includes an x-ray controller 210, which is configured to provide power and timing signals to the x-ray radiation source 104. In addition, the control mechanism 208 includes a gantry motor controller 212, which is configured to control the rotation speed and / or position of the frame 103 based on imaging requirements.

[0067] In some embodiments, the control mechanism 208 also includes a data acquisition system (DAS) 214 that is configured to sample analog data received from the detector elements 202 and convert the analog data into digital signals for subsequent processing. The data sampled and digitized by the DAS 214 is transmitted to a computer or computing device 216. In one example, the computing device 216 stores the data in a mass storage device 218. For example, the storage device 218 may include a hard drive, a floppy disk drive, a compact disk-read / write (CD-R / W) drive, a digital versatile disk (DVD) drive, a flash drive, and / or a solid-state storage drive.

[0068] In addition, the computing device 216 provides commands and parameters to one or more of the DAS 214, the x-ray controller 210, and the gantry motor controller 212 to control system operations, such as data acquisition and / or processing. In some embodiments, the computing device 216 controls system operations based on operator input. The computing device 216 receives operator input, which includes, for example, commands and / or scan parameters, via an operator console 220 operatively coupled to the computing device 216. The operator console 220 may include a keyboard (not shown) or a touch screen to allow an operator to specify commands and / or scan parameters.

[0069] Although Figure 2 Only one operator console 220 is shown, but more than one operator console may be coupled to the imaging system 200 for use, for example, in inputting or outputting system parameters, requesting exams, and / or viewing images. Additionally, in some embodiments, the imaging system 200 may be coupled to multiple displays, printers, workstations, and / or the like located locally or remotely, for example, within an institution or hospital or at an entirely different location, via one or more configurable wired and / or wireless networks, such as the Internet and / or a virtual private network.

[0070] In some embodiments, for example, the imaging system 200 may include or be coupled to a picture archiving and communication system (PACS) 224. In an exemplary embodiment, the PACS 224 is further coupled to a remote system (such as a radiology department information system, a hospital information system) and / or to an internal or external network (not shown) to allow operators at different locations to provide commands and parameters and / or gain access to image data.

[0071] The computing device 216 may use operator-supplied and / or system-defined commands and parameters to operate the table motor controller 226, which in turn may control the table motor to adjust the Figure 1 Specifically, the table motor controller 226 moves the table 115 via the table motor so as to appropriately position the subject 112 in the gantry 102 to acquire projection data corresponding to a target volume of the subject 112. For example, the computing device 216 may send a command to the table motor controller 226, thereby instructing the table motor controller 226 to adjust the vertical position and / or horizontal position of the table 115 via the motor.

[0072] As described above, the DAS 214 samples and digitizes the projection data acquired by the detector elements 202. Subsequently, the image reconstructor 230 uses the sampled and digitized x-ray data to perform high-speed reconstruction. Figure 2 The image reconstructor 230 is shown as a separate entity, but in some embodiments, the image reconstructor 230 may be formed as part of the computing device 216. Alternatively, the image reconstructor 230 may not be present in the imaging system 200, and instead the computing device 216 may perform one or more functions of the image reconstructor 230. In addition, the image reconstructor 230 may be located locally or remotely, and may be operably connected to the imaging system 200 using a wired or wireless network. In particular, one exemplary embodiment may use computing resources in a "cloud" network cluster for the image reconstructor 230.

[0073] In some embodiments, the image reconstructor 230 stores the reconstructed image in the mass storage device 218. Alternatively, the image reconstructor 230 transmits the reconstructed image to the computing device 216 to generate available subject information (also referred to as scan object information) for diagnosis and evaluation. In some embodiments, the computing device 216 transmits the reconstructed image and / or subject information to a display 232, which is communicatively coupled to the computing device 216 and / or the image reconstructor 230. In some embodiments, the display 232 allows an operator to evaluate the imaged anatomical structure. The display 232 can also allow the operator to select a volume of interest (VOI) and / or request subject information, for example, via a graphical user interface (GUI), for subsequent scanning or processing.

[0074] The computing device 216 may include computer-readable instructions executable to send commands and / or control parameters to one or more of the DAS 214, the x-ray controller 210, the gantry motor controller 212, and the table motor controller 226 according to an examination imaging plan. In addition, the computing device 216 may set and / or adjust various scan parameters (e.g., dose, gantry rotation angle, kV, mA, attenuation filter) according to the imaging plan. For example, the imaging plan may be selected by an operator from a plurality of imaging plans stored in a memory on the computing device 216 and / or a remote computing device, or the imaging plan may be automatically selected by the computing device 216 according to received subject information.

[0075] The depth camera 114 may be operably and / or communicatively coupled to the computing device 216 to provide image data to determine the structure of the subject, including posture and orientation. In addition, various methods and processes for determining the structure of the patient based on the image data generated by the depth camera 114 may be stored as executable instructions in the non-transitory memory of the computing device 216.

[0076] In some examples, the computing device 216 may include a camera image data processor 215 that includes instructions for processing information received from the depth camera 114. The information received from the depth camera 114 (which may include depth information and / or visible light information) may be processed to determine various subject parameters, such as subject identity, subject physique (e.g., height, weight, patient thickness), and current subject position relative to the table and the depth camera 114. In some embodiments, the information from the depth camera 114 may be used by the camera image data processor 215 to perform tracking of one or more subjects in the field of view of the depth camera 114.

[0077] Figure 31 is a schematic plan view of a rack 102 with a bottom fan according to an embodiment of the present invention. In some embodiments, the rack 102 may include an annular frame 103, at least one x-ray radiation source 104, and a detector array (or detector assembly) 108, wherein the x-ray radiation source 104 and the detector array 108 are arranged on opposite sides of the annular frame 103. The detector assembly may include a plurality of detector modules, each of which may include a plurality of detector elements 202. The detector assembly may also include a plurality of detector module temperature sensors and a plurality of detector module heaters (not shown), but does not include a heat dissipation device (e.g., a detector assembly fan, a ventilation chamber, etc.), wherein each detector module temperature sensor is located on a corresponding detector module for sensing the temperature of the corresponding detector module, and each detector module heater is located at the bottom of the corresponding detector module for heating the detector module. In some embodiments, the computing device 216 further includes a thermal controller (not shown), which is configured to control the detector module heater to heat the detector module based on the temperature of the corresponding detector module measured by each detector module temperature sensor according to a thermal control requirement, so that all detector modules in the detector assembly have a substantially consistent target temperature. The annular frame 103 together with the radiation source and detector assembly disposed thereon can rotate relative to the rack 102. In some embodiments, the rack 102 may include at least one top fan 302, which may be disposed at the top of the rack 102 to exhaust air in the rack to the outside of the housing. Figure 3 In the illustrated embodiment, the rack 102 includes two top fans 302. The control mechanism 208 (see Figure 2 ) may include a top fan controller (not shown), which is configured to control the rotation speed of the top fan 302. In some embodiments, the rack 102 may include at least one bottom fan 306 located at the bottom thereof, for directing cool air outside the rack 102 toward the frame 103. Figure 3 In the illustrated embodiment, the rack 102 includes two bottom fans 306. In some embodiments, the bottom fans 306 can be fixed to side brackets of the rack 102.

[0078] Figure 4A is a perspective schematic diagram depicting the air inlet side of a fan at the bottom of a rack according to an embodiment of the present invention. Figure 4B is a perspective schematic diagram depicting the air outlet side of a fan at the bottom of a rack according to an embodiment of the present invention. Figure 4Cis a schematic diagram depicting the airflow jet area of ​​the bottom fan according to an embodiment of the present invention. In some embodiments, the bottom fan 306 may be a centrifugal fan, which includes an air inlet 402 and an air outlet 404. The air inlet 402 may be arranged to align with the bottom air inlet 304 of the rack 102. The centrifugal fan 306 inhales cold air outside the rack 102 through the air inlet 402, and the cold air is compressed inside the fan cavity and then ejected from the air outlet 404 at high speed through the guide pipe. The high-speed ejected airflow may include an airflow jet area 406 and an airflow mixing area 408, wherein the gas in the airflow jet area 406 is mainly cold air outside the rack, with a fast airflow speed and low temperature; and the gas in the airflow mixing area 408 is a mixed gas of cold air outside the rack and hot air inside the rack, and the airflow speed of the mixed gas is much slower and the temperature is higher than the gas in the airflow jet area 406.

[0079] In some embodiments, the existing bottom fan 306 of the rack in the medical imaging system 200 can be directly used, and the airflow jet area 406 ejected at high speed from the air outlet 404 by the bottom fan 306 can cover a part of the space through which the detector assembly 108 rotates. As the frame 103 rotates, at least at a certain frame angle or position, all or most of the detector assembly 108 can be located in the airflow jet area 406. In this article, one or more positions where the detector assembly can meet the above situation (that is, all or most of the detector assembly 108 can be located in the airflow jet area 406) are referred to as the predetermined docking position of the detector assembly. When the detector assembly is located at the predetermined docking position, the airflow jet area 406 of the bottom fan 306 can be used to dissipate heat from the detector assembly to achieve cooling. In some embodiments, the thermal controller in the computing device 216 may be configured to provide commands and parameters to the gantry motor controller 212 based on thermal control requirements to control the rotation speed and / or docking of the frame 103 so that when the frame 103 is located in a predetermined docked position, all or at least most of the detector assembly 108 is located within the airflow jet region 406.

[0080] In other embodiments, one or more commercially available fans 306 may be added to the bottom of the rack 102, and the fans 306 may be positioned and designed so that there is a predetermined docking position associated with the airflow jet area 406 of the positioned fans 306. Similarly, the thermal controller in the computing device 216 may be configured to provide commands and parameters to the rack motor controller 212 based on thermal control requirements to control the rotation speed and / or docking of the frame 103, so that when the frame 103 is located at the predetermined docking position, all or at least most of the detector assembly 108 is located within the airflow jet area 406.

[0081] In some other embodiments, in addition to designing the positioning of the bottom fan 306, the flow direction of the guide tube in the bottom fan 306 and / or the size of the air outlet 404 can be further configured so that there is a predetermined parking position associated with the airflow jet area 406 of the configured fan 306. Similarly, the thermal controller in the computing device 216 can be configured to provide commands and parameters to the rack motor controller 212 based on the thermal control requirements to control the rotation speed and / or parking of the frame 103, so that when the frame 103 is located at the predetermined parking position, all or at least most of the detector assembly 108 is located in the airflow jet area 406.

[0082] Figure 5A It is a plan view of a separate airflow jet area formed by the fan on the left side of the bottom of the rack according to an embodiment of the present invention. Figure 5B 3 is a schematic plan view of a separate airflow jet zone formed by a fan at the bottom right of the rack according to an embodiment of the present invention. In some embodiments, the rack 102 may include a single bottom fan 306. Figure 5A As shown, a single bottom fan 306 can be set on the left side of the rack 102, and the detector assembly 108 can pass through the airflow jet area 406 of the left bottom fan 306 when rotating with the frame 103. The thermal controller is configured to provide commands and parameters to the rack motor controller 212 based on the docking requirements (such as conditions that trigger docking, predetermined docking positions, etc.) to control the rotation and docking of the frame 103, so that when the frame 103 is docked at the predetermined docking position on the right side, all or at least most of the detector assembly 108 is located in the airflow jet area 406 of the left bottom fan 306. Similarly, as Figure 5B As shown, a single bottom fan 306 can be arranged on the right side of the rack 102, and the detector assembly 108 can pass through the airflow jet area 406 of the bottom fan 306 of the right machine part when rotating with the frame 103. The thermal controller is configured to provide commands and parameters to the rack motor controller 212 based on the docking requirement to control the rotation and docking of the frame 103, so that when the frame 103 is located at the predetermined docking position on the left side, all or at least most of the detector assembly 108 is located in the airflow jet area 406 of the bottom fan 306 on the right side. It can be understood that in this embodiment, the predetermined docking position of the frame 103 or the detector assembly 108 is associated with a separate airflow jet area 406 of the bottom fan of the machine part.

[0083] Figure 5C 3 is a schematic plan view of a mixed airflow jet region formed by fans on both sides of the bottom of the rack according to an embodiment of the present invention. In some embodiments, the rack 102 may include two bottom fans 306. Figure 5CAs shown, in this embodiment, two bottom fans 306 can be respectively arranged on both sides of the bottom of the frame 102, and the high-speed airflows of the two bottom fans 306 can interact with each other to form a mixed airflow jet zone in the middle. The detector assembly 108 can pass through the mixed airflow jet zone when rotating with the frame 103. The thermal controller is configured to provide commands and parameters to the frame motor controller 212 based on the docking requirements to control the rotation and docking of the frame 103, so that when the frame 103 is located in the predetermined docking position in the middle, all or at least most of the detector assembly 108 is located in the mixed airflow jet zone 406 of the bottom fans 306 on both sides. It can be understood that in this embodiment, the predetermined docking position of the frame 103 or the detector assembly 108 is associated with the mixed airflow jet zone of the bottom fans of the machine parts on both sides.

[0084] In some embodiments, the rack 102 may include three or more bottom fans. These bottom fans 306 may be arranged around the bottom of the rack 102. One or more of the more bottom fans 306 may independently form a separate airflow jet zone, or may interact with the airflow jet zones of other bottom fans to form a mixed airflow jet zone. It is understood that the predetermined docking position of the frame 103 or the detector assembly 108 may be associated with a separate or mixed airflow jet zone of one or more bottom fans of the machine.

[0085] Regardless of whether a single airflow jet zone is formed by one bottom fan or a mixed airflow jet zone is formed by multiple bottom fans, since the gas in the airflow jet zone is mainly cold air outside the rack and has a lower temperature, the cold air in the airflow jet zone can be used to cool down the detector assembly 108 docked therein. Based on this, the detector assembly fan for heat dissipation of the detector assembly and the closed housing for mounting the detector assembly fan and forming a ventilation chamber inside can be removed from the detector assembly 108 of the medical imaging system 200. The controller for controlling the detector assembly fan can also be removed from the control mechanism 206.

[0086] The following will be combined Figure 6 - FIG. 8 depicts a thermal control method according to an embodiment of the present invention, which may be used to prevent overheating of a detector assembly when the medical imaging system does not include a detector assembly fan.

[0087] In some embodiments, the thermal controller in the computing device 216 can be configured to perform the thermal control methods of various embodiments. In some embodiments, the thermal controller can be a combination of the computing device 216 and the rack motor controller 212 .

[0088] II. Thermal Control Methods

[0089] Figure 6600 is a flow chart of a thermal control method 600 for a medical imaging system according to an embodiment of the present invention. Figure 6 As shown, in step 602, the detector assembly 108 identifies its own position to obtain position information of the detector assembly. In step 604, the thermal controller determines whether the detector assembly is parked in a predetermined docking position based on the obtained position information of the detector assembly, wherein the predetermined docking position may be associated with a separate or mixed airflow jet area 406 of one or more rack bottom fans 306. If the judgment result is yes, the process proceeds to step 608, and the medical imaging system continues to operate normally. If the judgment result is no, the process proceeds to step 606. In step 606, the thermal controller rotates the detector assembly 108 by controlling the frame 103, and parks the detector assembly in a predetermined docking position. When the detector assembly is parked in the predetermined docking position, all or most of the detector assembly 108 is located in a separate or mixed airflow jet area 410 formed by one or more rack bottom fans 306 (see Figure 5A -5C), the cool air in the single or mixed airflow jet region 410 dissipates heat to the detector assembly 108. Then, the process proceeds to step 608, and the medical imaging system continues to operate normally.

[0090] In some embodiments, the thermal controller can be configured to control the frame 103 so that the detector assembly 108 is parked at a predetermined parking position for a predetermined period of time (e.g., 15 minutes). In other embodiments, the thermal controller can be configured to control the frame 103 so that the detector assembly 108 is parked at the predetermined parking position until the temperature of the detector assembly 108 is within a predetermined temperature range (e.g., 26° C.-43° C.). In some embodiments, the thermal controller can be configured to control the output power of one or more rack bottom fans based on the temperature of the detector assembly 108.

[0091] In some embodiments, the thermal controller can be configured to: determine whether the detector assembly is parked in a first predetermined docking position based on the obtained position information of the detector assembly; and rotate the detector assembly to park the detector assembly in the first predetermined docking position in response to one of the following events: (1) determining that the detector assembly is not parked in the first predetermined docking position, or (2) determining that the detector assembly is not parked in the first predetermined docking position and the user allows the detector assembly to return to the first predetermined docking position, wherein, when the detector assembly is parked in the first predetermined docking position, at least a majority of the detector assembly is located within the airflow jet area of ​​at least one rack bottom fan.

[0092] In some embodiments, the thermal controller can be configured to control the indicator to issue a warning indicating that the detector assembly is not parked in the predetermined docking position in response to one of the following events: (1) determining that the detector assembly is not parked in the predetermined docking position; or (2) determining that the detector assembly is not parked in the first predetermined docking position and the user allows the detector assembly to return to the first predetermined docking position.

[0093] Combination of the above Figure 6 The thermal control method for a medical imaging system according to an embodiment of the present invention may be performed in either a startup phase of the medical imaging system or a scanning operation phase of the medical imaging system.

[0094] Figure 7 FIG. 7 is a flow chart of a thermal control method 700 performed during the startup phase of a medical imaging system according to an embodiment of the present invention. Figure 7 As shown, in step 702, the detector assembly 108 identifies its own position to obtain the position information of the detector assembly. In step 704, the thermal controller determines whether the detector assembly is parked in a predetermined docking position based on the obtained position information of the detector assembly, wherein the predetermined docking position can be associated with a single or mixed airflow jet area 406 of one or more rack bottom fans 306. If the judgment result is yes, the process proceeds to step 712, and the medical imaging system continues the normal operation of the startup phase. If the judgment result is no, the process proceeds to step 706. In step 706, the thermal controller controls an indicator (such as an indicator light, a display and / or an audible alarm, etc.) to issue a warning indicating that the detector assembly is in an abnormal docking position. In step 708, the thermal controller asks the user whether to refuse the detector assembly to return to the predetermined docking position. In some cases, such as when the user is repairing the medical imaging system, the user may refuse the detector assembly to return to the predetermined docking position. If the user refuses the detector assembly to return, the process proceeds to step 712, and the medical imaging system continues the normal operation of the startup phase. If the user allows the detector assembly to return, the process proceeds to step 710, and the thermal controller rotates the detector assembly 108 by controlling the frame 103 and parks the detector assembly at a predetermined parking position. When the detector assembly is parked at the predetermined parking position, all or most of the detector assembly 108 is located in the single or mixed airflow jet area 410 formed by one or more rack bottom fans 306 (see Figure 5A -5C), the cold air in the single or mixed airflow jet area 410 dissipates heat from the detector assembly 108 to achieve cooling. Then, the process proceeds to step 712, and the medical imaging system continues normal operation in the startup phase.

[0095] In some embodiments, the thermal controller can be configured to allow the medical imaging system to continue normal operation during the startup phase of the medical imaging system in response to one of the following events: (1) determining that the detector assembly is parked in a predetermined docking position; (2) the detector assembly is rotated to park in the predetermined docking position; or (3) the user refuses to return the detector assembly to the predetermined docking position.

[0096] Fig. 8A 8 is a flow chart of a first portion 800A of a thermal control method performed during a scanning operation phase of a medical imaging system according to an embodiment of the present invention. Fig. 8A As shown, in step 802, the thermal controller determines whether the detector assembly is overheated. For example, if the highest temperature of the detector module in the detector assembly 108 is less than or equal to a predetermined temperature, such as 43°C, the thermal controller determines that the detector assembly is not overheated. The process proceeds to step 880, and the medical imaging system continues normal operation of the scanning operation phase. If the thermal controller determines that the detector assembly is overheated, the process proceeds to step 804. In step 804, the thermal controller determines whether the detector assembly is parked in a first predetermined parking position, wherein the first predetermined parking position can be associated with a single or mixed airflow jet area 406 of one or more rack bottom fans 306. If the judgment result is yes, the process proceeds to Figure 8BStep 820. If the result of the judgment is no, the process proceeds to step 806. In step 806, the thermal controller controls an indicator (such as an indicator light, a display and / or an audible alarm, etc.) to issue a warning indicating that the detector assembly is in an abnormal docking position. In step 808, the thermal controller asks the user whether to refuse the detector assembly to return to the first predetermined docking position. If the user refuses to return the detector assembly to the first predetermined docking position, the process proceeds to step 814, and the thermal controller rotates the detector assembly 108 by controlling the frame 103 until the temperature of the detector assembly meets the predetermined temperature control standard, and prohibits subsequent scanning operations. The predetermined temperature control standard can be that the maximum temperature of the detector module is within a predetermined temperature range (for example, 26°C-43°C). Alternatively, the predetermined temperature control standard can be that the average temperature of the detector module is within a predetermined temperature range. In some cases, if the system is performing a scout scan (also known as a flat film scan), the user may refuse the detector assembly to return to the first predetermined docking position. If the user allows the detector assembly to be rotated back to the first predetermined docking position, the process proceeds to step 810. In step 810, the thermal controller rotates the detector assembly 108 by controlling the frame 103 until the temperature of the detector assembly meets the predetermined temperature control standard. In step 812, the thermal controller parks the detector assembly at a first predetermined parking position by controlling the frame 103. When the detector assembly is parked at the first predetermined parking position, all or most of the detector assembly 108 is located in a separate or mixed airflow jet area 410 formed by one or more rack bottom fans 306, and the cold air in the separate or mixed airflow jet area 410 further dissipates heat for the detector assembly 108. Then, the process proceeds to step 880, and the medical imaging system continues normal operation of the scanning operation phase.

[0097] Figure 8B 800B is a flow chart of a second portion 800B of a thermal control method performed during a scanning operation phase of a medical imaging system according to an embodiment of the present invention. Figure 8B As shown, in step 820, the thermal controller determines whether there is a rack bottom fan failure. If the determination result is yes, the process proceeds to Figure 8CStep 830. If the result of the judgment is no, the process proceeds to step 822. In step 822, the thermal controller controls an indicator (such as an indicator light, a display and / or an audible alarm, etc.) to issue a warning indicating that there is a rack bottom fan failure, and prompts to detect whether other cooling devices (such as rack top fans and / or indoor air conditioning devices) other than the rack bottom fan are working normally. In step 824, the thermal controller rotates the detector assembly 108 by controlling the frame 103 until the temperature of the detector assembly meets the predetermined temperature control standard. In step 826, the thermal controller parks the detector assembly at a first predetermined parking position by controlling the frame 103. When the detector assembly is parked at the first predetermined parking position, all or most of the detector assembly 108 is located in a single or mixed airflow jet area 410 formed by one or more rack bottom fans 306, and the cold air in the single or mixed airflow jet area 410 further dissipates heat for the detector assembly 108. Then, the process proceeds to step 880, and the medical imaging system continues normal operation of the scanning operation phase.

[0098] Figure 8C 800C is a flow chart of a third portion 800C of a thermal control method performed during a scanning operation phase of a medical imaging system according to an embodiment of the present invention. Figure 8C As shown, at step 830, the thermal controller determines whether the medical imaging system has a configuration of multiple rack bottom fans. If the determination result is yes, the process proceeds to Fig.8D Step 840. If the result of the judgment is no, the process proceeds to step 832. In step 832, the thermal controller controls an indicator (such as an indicator light, a display and / or an audible alarm, etc.) to issue a warning indicating that the detector assembly is overheated and a single rack bottom fan has failed. In step 834, the thermal controller rotates the detector assembly 108 by controlling the frame 103 until the temperature of the detector assembly meets the predetermined temperature control standard. In step 836, the thermal controller parks the detector assembly at a first predetermined parking position by controlling the frame 103. When the detector assembly is parked at the first predetermined parking position, all or most of the detector assembly 108 is located in a separate or mixed airflow jet area 410 formed by one or more rack bottom fans 306, and the cold air in the separate or mixed airflow jet area 410 further dissipates heat for the detector assembly 108. Then, the process proceeds to step 880, and the medical imaging system continues normal operation of the scanning operation phase.

[0099] Fig.8D 800D is a flow chart of a fourth portion of a thermal control method performed during a scanning operation phase of a medical imaging system according to an embodiment of the present invention. Fig.8DAs shown, at step 840, the thermal controller rotates the detector assembly 108 by controlling the frame 103 until the temperature of the detector assembly meets the predetermined temperature control standard. At step 842, the thermal controller determines whether there is a second predetermined parking position associated with the single or mixed airflow jet area 410 of one or more rack bottom fans 306, wherein the second predetermined parking position is different from the first predetermined parking position. If the determination result at step 842 is no, the process proceeds to Fig. 8E Step 850. If the result of the judgment in step 842 is yes, the process proceeds to step 844. In step 844, the thermal controller parks the detector assembly at the second predetermined parking position by controlling the frame 103. When the detector assembly is parked at the second predetermined parking position, all or most of the detector assembly 108 is located in the separate or mixed airflow jet area 410 formed by one or more rack bottom fans 306, and the cold air in the separate or mixed airflow jet area 410 further dissipates heat from the detector assembly 108. Then, the process proceeds to step 880, and the medical imaging system continues normal operation of the scanning operation phase.

[0100] In some embodiments, the Figure 5C The intermediate parking position associated with the airflow jet area 406 shown is used as the first predetermined parking position. Figure 5A If the bottom left fan shown fails, the thermal controller can Figure 5B The docking position associated with the airflow jet region 406 shown is used as the second predetermined docking position, and the detector assembly is docked at the second predetermined docking position. Figure 5B If the bottom fan on the right side fails, the thermal controller can Figure 5A The parking position associated with the airflow jet region 406 shown is used as a second predetermined parking position, and the detector assembly is parked in this second predetermined parking position.

[0101] Fig. 8E 800E is a flowchart of a fifth portion of a thermal control method performed during a scanning operation phase of a medical imaging system according to an embodiment of the present invention. Fig. 8EAs shown, in step 850, the thermal controller controls an indicator (such as an indicator light, a display and / or an audible alarm, etc.) to issue a warning indicating that the detector assembly is overheated and the related rack bottom fan is faulty. In step 852, the thermal controller rotates the detector assembly 108 by controlling the frame 103 until the temperature of the detector assembly meets the predetermined temperature control standard. In step 854, the thermal controller parks the detector assembly at a second predetermined parking position by controlling the frame 103. When the detector assembly is parked at the second predetermined parking position, all or most of the detector assembly 108 is located in a separate or mixed airflow jet area 410 formed by one or more rack bottom fans 306, and the cold air in the separate or mixed airflow jet area 410 further dissipates heat for the detector assembly 108. Then, the process proceeds to step 880, and the medical imaging system continues normal operation of the scanning operation phase.

[0102] In some embodiments, the thermal controller can be configured to, during a scanning operation phase of the medical imaging system, in response to determining that the detector assembly is overheated, rotate the detector assembly until the temperature of the detector assembly meets a predetermined temperature control standard; and in response to determining that the temperature of the detector assembly meets the predetermined temperature control standard, park the detector assembly in a first predetermined parking position.

[0103] In some embodiments, the thermal controller can be configured to, during a scanning operation phase of the medical imaging system, in response to determining that the detector assembly is overheated, obtain position information of the detector assembly for determining whether the detector assembly is parked in a first predetermined docking position; and rotate the detector assembly until the temperature of the detector assembly meets a predetermined temperature control standard in response to one of the following events: determining that the detector assembly is not parked in the first predetermined docking position, or determining that the detector assembly is not parked in the first predetermined docking position and the user allows the detector assembly to return to the first predetermined docking position.

[0104] In some embodiments, the thermal controller may be configured to, during a scanning operation phase of the medical imaging system, when the at least one bottom-rack fan includes only one bottom-rack fan, in response to determining that a single bottom-rack fan has failed, issue a warning indicating that the single bottom-rack fan has failed, and rotate the detector assembly until a highest temperature of the plurality of detector modules drops within a predetermined temperature range.

[0105] In some embodiments, the thermal controller can be configured to rotate the detector assembly until the highest temperature of the plurality of detector modules drops to within a predetermined temperature range and park the detector assembly at a second predetermined parking position in response to determining that a portion of the at least one rack bottom fan has failed during a scanning operation phase of the medical imaging system when the at least one rack bottom fan includes at least two rack bottom fans, wherein when the detector assembly is parked at the second predetermined parking position, at least a majority of the detector assembly is located within an airflow jet region formed by one or more of the other rack bottom fans among the at least two rack bottom fans except the failed rack bottom fan.

[0106] In some embodiments, the thermal controller may be configured to, during a scanning operation phase of the medical imaging system, when the at least one bottom rack fan includes at least two bottom rack fans, in response to determining that all of the at least one bottom rack fan have failed, rotate the detector assembly until a highest temperature of the plurality of detector modules drops within a predetermined temperature range, and park the detector assembly in a first predetermined parking position.

[0107] In some embodiments, the thermal controller can be configured to inhibit a scanning operation during a scanning operation phase of the medical imaging system in response to the following events: determining that the detector assembly is overheated; the detector assembly is not parked in a first predetermined parking position; and the user refuses to return the detector assembly to the first predetermined parking position.

[0108] In some embodiments, the first predetermined docking position is associated with positioning of one or more bottom-of-rack fans.

[0109] In some embodiments, the medical imaging system includes two or more bottom-of-rack fans, and the first predetermined docking position and the second predetermined docking position are associated with positioning of one or more of the bottom-of-rack fans.

[0110] In some embodiments, the medical imaging system includes two or more bottom-of-rack fans, and the first predetermined docking position and the second predetermined docking position are associated with a direction and an opening size of a duct of one or more of the bottom-of-rack fans.

[0111] The technology described herein can be implemented in hardware, software, firmware, or any combination thereof, unless specifically described as being implemented in a particular manner. Any features described as modules or components can also be implemented together in an integrated logic device, or separately implemented as discrete but interoperable logic devices. If implemented in software, the technology can be implemented at least in part by a non-transient processor-readable storage medium including instructions, and when the instructions are executed, one or more of the above methods are executed. The non-transient processor-readable data storage medium can form a part of a computer program product that may include packaging materials. The program code can be implemented in a high-level procedural programming language or an object-oriented programming language to communicate with a processing system. If necessary, the program code can also be implemented in assembly language or machine language. In fact, the mechanism described herein is not limited to the scope of any particular programming language. In any case, the language can be a compiled language or an interpreted language.

[0112] One or more aspects of at least some embodiments may be implemented by representative instructions stored on a machine-readable medium that represent various logic within a processor, which when read by a machine causes the machine to fabricate logic for performing the techniques described herein.

[0113] Such machine-readable storage media may include, but are not limited to, a non-transitory tangible arrangement of articles manufactured or formed by a machine or apparatus, including storage media such as: a hard disk; any other type of disk, including floppy disks, optical disks, compact disk-read only memory (CD-ROM), compact disk-rewritable (CD-RW), and magneto-optical disks; semiconductor devices, such as read-only memory (ROM), random access memory (RAM) such as dynamic random access memory (DRAM) and static random access memory (SRAM), erasable programmable read-only memory (EPROM), flash memory, electrically erasable programmable read-only memory (EEPROM); phase change memory (PCM); magnetic or optical cards; or any other type of medium suitable for storing electronic instructions.

[0114] So far, the medical imaging system according to the present invention has been described, and the thermal control method for preventing overheating of the detector in the medical imaging system according to the present invention has also been described.

[0115] Some exemplary embodiments have been described above. However, it should be understood that various modifications may be made to the exemplary embodiments described above without departing from the spirit and scope of the present invention. For example, if the described techniques are performed in a different order and / or if the components in the described systems, architectures, devices, or circuits are combined in different ways and / or replaced or supplemented by other components or their equivalents, suitable results may be achieved, and accordingly, these modified other implementations also fall within the scope of protection of the claims.

Claims

1. A thermal control method for a medical imaging system, the method comprising: Based on the obtained position information of the detector assembly, determining whether the detector assembly is parked at a first predetermined parking position; as well as The detector assembly is rotated to park the detector assembly in the first predetermined parking position in response to one of the following events: determining that the detector assembly is not parked at the first predetermined parking position, or determining that the detector assembly is not parked in the first predetermined parking position and a user allows the detector assembly to return to the first predetermined parking position, Wherein, when the detector assembly is parked at the first predetermined parking position, at least most of the detector assembly is located in the airflow jet area of ​​at least one fan at the bottom of the rack.

2. The thermal control method according to claim 1, wherein the method further comprises: During a scanning operation phase of the medical imaging system, In response to determining that the detector assembly is overheated, rotating the detector assembly until a temperature of the detector assembly meets a predetermined temperature control standard; as well as In response to determining that the temperature of the detector assembly meets the predetermined temperature control standard, the detector assembly is parked in the first predetermined parking position.

3. The heat control method according to claim 2, wherein: During a scanning operation phase of the medical imaging system, in response to determining that the detector assembly is overheated, the step of rotating the detector assembly until the temperature of the detector assembly meets a predetermined temperature control standard comprises: In response to determining that the detector assembly is overheated, obtaining the position information of the detector assembly for determining whether the detector assembly is parked at the first predetermined parking position; In response to one of the following events, the detector assembly is rotated until the temperature of the detector assembly meets the predetermined temperature control standard: determining that the detector assembly is not parked at the first predetermined parking position, or It is determined that the detector assembly is not parked in the first predetermined parking position and a user allows the detector assembly to return to the first predetermined parking position.

4. The heat control method according to claim 2 or 3, wherein: The detector assembly includes a plurality of detector modules, and The method further comprises: during a scanning operation phase of the medical imaging system, Determining whether the detector assembly is overheated by determining whether the highest temperature of the plurality of detector modules exceeds a predetermined temperature; or Whether the temperature of the detector assembly meets a predetermined temperature control standard is determined by judging whether the highest temperature of the plurality of detector modules drops within a predetermined temperature range.

5. The heat control method according to claim 4, further comprising: During a scanning operation phase of the medical imaging system, When the user allows the detector assembly to return to the first predetermined parking position, the detector assembly is rotated until the highest temperature of the plurality of detector modules drops to within a predetermined temperature range.

6. The heat control method according to claim 5, further comprising: During a scanning operation phase of the medical imaging system, In response to determining that the highest temperature of the plurality of detector modules exceeds the predetermined temperature and determining that the detector assembly has been parked at the first predetermined parking position, determining whether the at least one rack bottom fan fails; In response to determining that none of the at least one bottom-of-rack fans fails, it is detected whether other cooling devices except the bottom-of-rack fans operate normally.

7. The heat control method according to claim 6, further comprising: During a scanning operation phase of the medical imaging system, one of the following thermal controls is performed: When the at least one rack bottom fan includes only one rack bottom fan, in response to determining that the single rack bottom fan fails, a warning indicating that the single rack bottom fan fails is issued, and the detector assembly is rotated until the highest temperature of the plurality of detector modules drops within the predetermined temperature range; or When the at least one rack bottom fan includes at least two rack bottom fans, in response to determining that a portion of the at least one rack bottom fans fail, the detector assembly is rotated until the highest temperature of the plurality of detector modules drops within the predetermined temperature range, and the detector assembly is parked at a second predetermined parking position, wherein when the detector assembly is parked at the second predetermined parking position, at least most of the detector assembly is located within an airflow jet area formed by one or more of the other rack bottom fans among the at least two rack bottom fans except the failed rack bottom fan; or, When the at least one rack bottom fan includes at least two rack bottom fans, in response to determining that all of the at least one rack bottom fans have failed, the detector assembly is rotated until the highest temperature of the multiple detector modules drops to within the predetermined temperature range, and the detector assembly is parked in the first predetermined parking position.

8. The thermal control method of claim 1, wherein the method further comprises: In response to one of the following events, issuing a warning indicating that the detector assembly is not parked in the first predetermined parking position: determining that the detector assembly is not parked at the first predetermined parking position, or It is determined that the detector assembly is not parked in the first predetermined parking position and a user denies the detector assembly from returning to the first predetermined parking position.

9. The heat control method according to claim 1, further comprising: During a startup phase of the medical imaging system, the medical imaging system is allowed to continue normal operation in response to one of the following events: Determine that the detector assembly is parked at or rotated to the first predetermined parking position, or The user denies the detector assembly from returning to the first predetermined docking position.

10. The heat control method according to claim 9, further comprising: During a scanning operation phase of the medical imaging system, the scanning operation is prohibited in response to the following events: determining that the detector assembly is overheated; determining that the detector assembly is not parked at the first predetermined parking position; and The user denies the detector assembly from returning to the first predetermined docking position.

11. A medical imaging system, comprising: A frame, the frame comprising a radiation source and a detector assembly, wherein the detector assembly comprises a detector module for sensing radiation from the radiation source, and the radiation source and the detector assembly are rotatable relative to the frame; at least one fan, wherein the at least one fan is located at the bottom of the rack; as well as A thermal controller is configured to execute the thermal control method according to claims 1 to 10.

12. The medical imaging system of claim 11, wherein: The detector assembly also includes a detector module temperature sensor and a detector module heater, but does not include a heat dissipation device, wherein the detector module temperature sensor is located on the detector module and is used to sense the temperature of the detector module, and the detector module heater is located at the bottom of the detector module and is used to heat the detector module.

13. The medical imaging system of claim 12, wherein: The at least one fan has a corresponding air flow jet area, and The at least one blower is positioned such that when the detector assembly is parked in the first predetermined parking position, at least a majority of the detector assembly is located within an airflow jet region of the at least one blower.

14. The medical imaging system of claim 13, wherein: The at least one bottom-of-rack fan includes at least two bottom-of-rack fans, and The at least one fan is further positioned so that when the detector assembly is parked in the second predetermined parking position, at least a majority of the detector assembly is located within an airflow jet area formed by one or more of the at least two rack bottom fans other than the faulty rack bottom fan.

15. The medical imaging system of claim 12, wherein: The first predetermined parking position is associated with a positioning of the at least one wind turbine.

16. The medical imaging system of claim 15, wherein: The at least one bottom-of-rack fan includes at least two bottom-of-rack fans, and The first predetermined parking position and the second predetermined parking position are associated with positioning of one or more bottom-of-rack fans among the at least two bottom-of-rack fans.

17. The medical imaging system of claim 16, wherein: The first predetermined docking position and the second predetermined docking position are associated with directions and opening sizes of air guide ducts of one or more rack bottom fans among the at least two rack bottom fans.

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