Flow restriction device, cooling system and medical device

Abstract

The utility model relates to a flow restriction device is arranged in the cooling circuit for cooling the cooled equipment, adjusts the fluid flow of the first heat load and the second heat load contained to the cooled equipment, the flow restriction device is characterized in that, at least contains first throttling portion, second throttling portion and third throttling portion, wherein, the first throttling portion sets up in the output stream section of first cooling branch for the first heat load, the second throttling portion and the third throttling portion set up in the input stream section of second cooling branch for the second heat load.

Description

Technical Field

[0001] This utility model relates to the field of fluid control technology, and in particular to a flow limiting device, a cooling system, and a medical device. Background Technology

[0002] In the field of fluid control technology, flow control devices are crucial for ensuring stable system operation. This is especially true in medical equipment, such as magnetic resonance imaging (MRI) systems, where the stability and efficiency of the cooling system directly affect the reliability of the equipment and the quality of imaging. The Integrated Cooling Cabinet (ICC), as the core distribution unit of the cooling system, needs to dynamically allocate water flow to the cooling loops of the Gradient Coil (GC) and the Integrated System Cabinet (ISC). The ISC is a core mechatronic module in the MRI system, typically located within the MRI equipment room, and is a key support system for maintaining the cryogenic stability of the superconducting magnet. The ISC's core functions are to drive cooling, manage quench safety, and monitor liquid helium. It is directly connected to the magnet body via piping, and its internal cold head compressor receives cooling water from the cooling system for heat dissipation. Because the flow requirements of the GC loop and the ISC loop differ significantly under different operating modes (such as scan mode and standby mode), flow control devices are needed to precisely limit the flow rate under different operating modes. Similarly, in other application scenarios such as industrial hydraulic systems and automotive cooling systems, the flow demand of each heat load of the cooled equipment changes dynamically under different modes, so flow limiting devices are also needed to make corresponding dynamic adjustments.

[0003] In existing technologies, throttle valves or balancing valves are commonly used as flow limiting devices. However, traditional throttle valves or balancing valves have the following technical drawbacks: For example, in the cooling systems of medical equipment, valves are prone to blockage due to the accumulation of impurities in the cooling water or the intrusion of particulate matter during long-term operation, leading to valve jamming or flow control failure. Especially in magnetic resonance imaging (MRI) equipment, such failures can cause cooling system failure, directly affecting image quality and even equipment safety. Similarly, in industrial environments, particulate contaminants (such as metal shavings and dust) can exacerbate valve wear and blockage risks, and antifreeze crystallization in automotive cooling systems can also cause valve failure. Furthermore, once traditional throttle valves or balancing valves become blocked or fail, they require shutdown and disassembly for maintenance, which is time-consuming and costly. For example, downtime maintenance of MRI equipment not only affects normal hospital operations but may also delay patient diagnosis. In addition, in industrial settings, valve failures can cause production line shutdowns, resulting in significant economic losses. Utility Model Content

[0004] This invention was made in view of the above-mentioned problems. Its purpose is to provide a flow limiting device, a cooling system and a medical device that can achieve flow limiting with a simple and reliable structure, fundamentally avoiding the risk of blockage or failure, reducing system operating noise, ensuring long-term stable operation of the system and significantly reducing maintenance costs.

[0005] The first aspect of this utility model relates to a flow limiting device, which is installed in a cooling circuit for cooling a device being cooled, and regulates the flow rate of fluid flowing through a first heat load and a second heat load contained in the device being cooled. The flow limiting device is characterized by comprising at least a first throttling section, a second throttling section, and a third throttling section. The first throttling section is located at the output section of a first cooling branch for the first heat load, and the second and third throttling sections are located at the input section of a second cooling branch for the second heat load. The first, second, and third throttling sections are configured such that: in the first cooling branch, the fluid flows through the first heat load and then through the first throttling section; in the second cooling branch, the fluid flows through the second throttling section only and then through the second heat load, and then the two flows converge and are output; when the device being cooled is in standby mode, in the first cooling branch, the fluid flows through a bypass circuit provided in the first heat load and then through the first throttling section; in the second cooling branch, the fluid flows sequentially through the second throttling section and the third throttling section, and then the two flows converge and are output.

[0006] The second aspect of this utility model is that, in the first aspect, the first throttling portion, the second throttling portion and the third throttling portion are formed as plate-shaped throttling plates, and the throttling plates have at least one throttling hole.

[0007] A third aspect of this invention is that, in the second aspect, the orifice diameter of the throttling orifice is determined based on the pressure difference before and after the fluid passes through the throttling plate.

[0008] A fourth aspect of this invention is that, in the first aspect, when the cooled device is in operating mode and standby mode respectively, the flow direction of the fluid in the second cooling branch is different.

[0009] The fifth aspect of this utility model is that, in any one of the first to fourth aspects, it further includes a fourth throttling section, which is disposed in the output section of the first cooling branch. When the cooled device is in working mode, the fluid in the first cooling branch flows sequentially through the first throttling section and the fourth throttling section, and the fluid in the second cooling branch flows only through the second throttling section. Then, the two flow together and are output. When the cooled device is in standby mode, the fluid in the first cooling branch flows through the first throttling section, and the fluid in the second cooling branch flows sequentially through the second throttling section and the third throttling section. Then, the two flow together and are output through the fourth throttling section.

[0010] A sixth aspect of this invention is that, in any one of the first to fourth aspects, the first thermal load and the second thermal load have different flow requirements in the operating mode and the standby mode, respectively.

[0011] The seventh aspect of this utility model is that, in the fifth aspect, the fourth throttling portion is a throttling plate formed in the shape of a plate, having at least one throttling orifice on the throttling plate.

[0012] The eighth aspect of this invention is that, in the first aspect, the cooled device is a magnetic resonance imaging device, the first heat load is an integrated system component, and the second heat load is a gradient coil.

[0013] A ninth aspect of the present invention is that, in the eighth aspect, a helium compressor is further connected in front of the first heat load.

[0014] This utility model also relates to a cooling system for cooling equipment, characterized in that it includes the flow limiting device described in any one of the first to ninth aspects above.

[0015] This utility model also relates to a medical device, comprising: a heat load; and a cooling system provided with the flow limiting device described in any one of the first to ninth aspects above. Attached Figure Description

[0016] A better understanding of the present invention can be achieved by describing exemplary embodiments of the invention in conjunction with the accompanying drawings. In the drawings: Figure 1 This is a schematic diagram illustrating the operation of a cooling system according to an embodiment of the present invention in a working mode.

[0017] Figure 2 This is a schematic diagram illustrating the operation of a cooling system in standby mode according to an embodiment of the present invention.

[0018] Figure 3This is a schematic diagram showing a throttling section in a flow limiting device according to an embodiment of the present invention.

[0019] Figure 4 This is a schematic diagram illustrating the operation of a cooling system in working mode according to another embodiment of the present invention.

[0020] Figure 5 This is a schematic diagram illustrating the operation of a cooling system in standby mode according to another embodiment of the present invention.

[0021] Figure 6 This is a schematic diagram illustrating the operation of a cooling system for an MRI device in scanning mode according to another embodiment of the present invention.

[0022] Figure 7 This is a schematic diagram illustrating the operation of a cooling system for an MRI device in standby mode according to another embodiment of the present invention. Detailed Implementation

[0023] The following describes specific embodiments of this utility model. It should be noted that, in order to provide a concise description, this specification cannot provide a detailed description of all features of the actual embodiments. It should be understood that, in the actual implementation of any embodiment, just as in any engineering or design project, various specific decisions are often made to achieve the developer's specific goals and to meet system-related or business-related constraints, and this can change from one embodiment to another. Furthermore, it is understood that although the efforts made in this development process may be complex and lengthy, for those skilled in the art related to the content disclosed in this utility model, some design, manufacturing, or production modifications based on the technical content disclosed in this disclosure are merely conventional technical means and should not be construed as insufficient content of this disclosure.

[0024] Unless otherwise defined, the technical or scientific terms used in the claims and description shall have the ordinary meaning understood by one of ordinary skill in the art to which this utility model pertains. The terms "first," "second," and similar words used in the specification and claims of this utility model patent application do not indicate any order, quantity, or importance, but are merely used to distinguish different components. The terms "an" or "a" and similar words do not indicate a quantity limitation, but rather indicate the presence of at least one. The terms "comprising" or "including" and similar words mean that the element or object preceding "comprising" or "including" encompasses the element or object listed following "comprising" or "including" and its equivalents, and do not exclude other elements or objects. The terms "connected" or "linked" and similar words are not limited to physical or mechanical connections, nor are they limited to direct or indirect connections.

[0025] The following is a detailed description of the various embodiments of this utility model.

[0026] One embodiment of this utility model provides a flow limiting device. This embodiment illustrates the case where the flow limiting device is configured in a cooling system for a medical device. This cooling system cools one or more thermal loads in the medical device. However, the application scenarios of the flow limiting device are not limited to this; it can also be applied to other technical fields requiring flow limiting, including but not limited to industrial process control, energy systems, electronics, and semiconductors. Furthermore, in some embodiments, the aforementioned medical device may include, for example, one or more of a magnetic resonance imaging (MRI) device, a computed tomography (CT) device, and other diagnostic and therapeutic devices. The aforementioned one or more thermal loads may be, for example, thermal loads of electronic systems, electromagnetic systems, mechanical systems, radiation sources, etc. In particular, when the aforementioned medical device is an MRI device, the aforementioned thermal load may include, for example, one or more of the components in the MRI device, such as a superconducting magnet assembly, a gradient coil system, a power amplifier, an electronic control unit, and a cooling compressor.

[0027] Figure 1 , Figure 2 This is a schematic diagram illustrating a cooling system 1000 according to an embodiment of the present invention. The cooling system 1000 is used to cool one or more heat loads 1001, such as in a medical device. The heat load 1001, as the object to be cooled, generates heat during operation. The cooling system 1000 absorbs this heat by allowing a fluid circulating therein to flow through the heat load 1001, thereby achieving efficient cooling. Furthermore, Figure 1The diagram shows the fluid flow in the cooling system 1000 when the medical device is running in standby mode. Standby mode is typically a low-power mode, during which less heat is generated by the heat load 1001, and the flow requirement of the cooling system is lower. Figure 2 The diagram illustrates the fluid flow in the cooling system 1000 when the medical device is operating in its working mode. This operating mode is typically a high-power mode, such as at least one of scanning, treatment, or diagnostic modes. In this mode, the heat generated by the heat load 1001 increases significantly, requiring the cooling system to provide a higher flow rate to meet the heat dissipation demands.

[0028] also, Figure 1 and Figure 2 The illustration exemplarily depicts a first thermal load 1001a and a second thermal load 1001b as thermal loads 1001, connected in parallel. In this embodiment, the first thermal load 1001a and the second thermal load 1001b are configured to have different flow requirements under different operating modes (standby mode or operating mode) of the medical device. Specifically, in operating mode (high power consumption state), the second thermal load 1001b, as a high-power component, generates a large amount of heat, thus requiring a higher cooling flow to maintain its temperature stability. At this time, the flow of the first thermal load 1001a is adjusted synchronously, but the heat dissipation priority of the second thermal load 1001b is prioritized. In standby mode (low power consumption state), the heat generation of the second thermal load 1001b is significantly reduced, requiring a reduction in its cooling flow allocation. Simultaneously, it is also necessary to limit the cooling flow to the first thermal load 1001a to avoid overcooling or energy waste.

[0029] like Figure 1 and Figure 2 As shown, the cooling system 1000 of this embodiment mainly includes: a heat exchange system 100, which is used for heat exchange and performs heat exchange operations on the fluid circulating in the cooling loop of the cooling system to remove heat; and a flow limiting device 200, which is disposed in the cooling loop and is used to dynamically regulate the flow rate of the fluid circulating in the cooling loop. The fluid flowing in the cooling loop may include, but is not limited to, water, aqueous glycol solution, oil, cooling medium (such as R134a, R410a, R32, R744 or hydrocarbons), fluorinated liquid (such as electronic fluorinated liquid HFE, Novec, etc.), or combinations thereof. In the following description, the fluid may sometimes be referred to as the cooling medium.

[0030] like Figure 1 and Figure 2As shown, the cooling circuit of the cooling system 1000 includes a first cooling branch for cooling a first heat load 1001a and a second cooling branch for cooling a second heat load 1001b, with the first and second cooling branches connected in parallel. The flow limiting device 200 includes at least a first throttling section 201, a second throttling section 202, and a third throttling section 203 as throttling components. The first throttling section 201 is disposed in the output flow section of the first cooling branch, and the second throttling section 202 and the third throttling section 203 are disposed in the input flow section of the second cooling branch. In this embodiment, the flow direction control module 210 controls the switching of the flow direction of the fluid in the cooling system 1000 under different modes. In some implementations, the flow direction control module can achieve flow direction switching through electronic control, such as using electrically driven components like solenoid valves or electric ball valves, switching the flow path direction by controlling the on / off state of the solenoid coil or motor drive. Alternatively, in some implementations, the flow control module can also achieve flow direction switching through mechanical means, such as using mechanical components like manual valves or temperature-controlled expansion valves.

[0031] The following details the specific flow of the cooling medium in the cooling circuit when the cooled equipment is in different modes.

[0032] like Figure 1 As shown, when the medical device being cooled is in working mode, the cooling medium flows out from the heat exchange system 100 and branches into a first cooling branch and a second cooling branch at the branch point a of the input flow section. Figure 1 The hollow arrows indicate the flow direction of the cooling medium in the first cooling branch, and the solid arrows indicate the flow direction of the cooling medium in the second cooling branch. In the first cooling branch, as shown by the hollow arrows, the cooling medium flows sequentially from branch point a through the first heat load 1001a and the first throttling section 201 before reaching the confluence point b of the output flow section. In the second cooling branch, under the action of the flow direction control module 210, as shown by the solid arrows, the cooling medium flows sequentially from branch point a through the second throttling section 202 and the second heat load 1001b before reaching the confluence point b of the output flow section. At the confluence point b, the cooling medium from the first cooling branch and the cooling medium from the second cooling branch merge and flow back to the heat exchange system 100 to complete the heat exchange cycle.

[0033] like Figure 2 As shown, when the medical device being cooled is in standby mode, the cooling medium flows out from the heat exchange system 100, and similarly branches into a first cooling branch and a second cooling branch at the branch point a of the input flow section. Figure 2The hollow arrows indicate the flow direction of the cooling medium in the first cooling branch, and the solid arrows indicate the flow direction of the cooling medium in the second cooling branch. In the first cooling branch, as shown by the hollow arrows, the cooling medium flows sequentially from branch point a through the bypass loop bp (i.e., not cooling the first heat load 1001a) and the first throttling section 201 before reaching the confluence point c of the output flow section. In the second cooling branch, under the action of the flow direction control module 210, as shown by the solid arrows, the cooling medium flows sequentially from branch point a through the second throttling section 202 and the third throttling section 203 before reaching the confluence point c of the output flow section. At the confluence point c, the cooling medium from the first cooling branch and the cooling medium from the second cooling branch merge and flow back to the heat exchange system 100 to complete the heat exchange cycle.

[0034] Therefore, in the operating mode, the cooling medium in the second cooling branch undergoes only one stage of throttling through the second throttling section 202 before flowing directly into the second heat load 1001b, which is a high-power component. This ensures sufficient cooling flow to the second heat load 1001b, maintains the temperature stability of the high-power component in the operating mode, reduces flow resistance loss, and improves system energy efficiency. In the standby mode, under the action of the flow direction control module 210, the cooling medium flow is single-stage throttling limited by the first throttling section 201 in the first cooling branch, and two-stage series throttling limited by the second throttling section 202 and the third throttling section 203 in the second cooling branch. This significantly reduces the cooling flow in the second cooling branch, avoids overcooling and energy waste, and effectively reduces fluid noise in the system by dispersing the pressure drop through staged throttling.

[0035] The first throttling section 201, the second throttling section 202, and the third throttling section 203 involved in this embodiment can be implemented using throttling plates. Specifically, in this embodiment, the throttling plate is configured as a plate-shaped member with a throttling orifice. However, it is not limited to this; in some implementations, it can also be configured to have more than one throttling orifice. Furthermore, in this embodiment, the shape of the throttling orifice is set to circular, but it is not limited to this; in some implementations, it can also be set as a slit, a porous array, or other geometric shapes. In addition, in some implementations, the shape and configuration of the throttling orifice can be adjusted according to fluid characteristics (such as corrosivity, particulate matter content, etc.).

[0036] In this embodiment, the orifice diameter of the throttling plate is precisely calculated based on the fluid resistance, flow control accuracy, and noise suppression requirements in the cooling circuit of the cooling system 1000. This enables efficient flow restriction with a simple and reliable structure while reducing noise, thus meeting the high requirements of medical equipment (such as MRI equipment) for quiet operation.

[0037] Figure 3A schematic diagram of a throttling section in a flow limiting device 200 according to an embodiment of the present invention is shown. Figure 3 As shown, the throttling plate, acting as a throttling element, is installed in the cooling pipe (cooling circuit) of the cooling system 1000 via bolts, welding, or clips. The following is a detailed explanation of the calculation method for the orifice diameter of the throttling plate.

[0038] In the diagram, "d-hole" represents the orifice size (diameter) of the throttling orifice installed on the throttling plate, and "u-hole" represents the fluid velocity within the orifice. "d2," shown upstream of the orifice, represents the diameter of the cooling pipe in which the fluid resides before passing through the orifice, and "u2" represents the fluid velocity at that location. "d3," shown downstream of the orifice, represents the diameter of the cooling pipe in which the fluid resides after passing through the orifice, and "u3" represents the fluid velocity at that location.

[0039] First, the pressure difference Δp of the fluid before and after passing through the throttling plate is measured; for example, the measured value is Δp = 2.2 Pa. Then, the diameters d2 and d3 of the cooling pipes are measured. Furthermore, it is assumed that the diameter of the cooling pipes is the same before and after the throttling orifice, i.e., d2 = d3.

[0040] Then, the local resistance coefficient ξ2 (unit: Pa), local head loss hj2 (unit: m), and pressure loss Δp2 when the fluid suddenly narrows upstream of the orifice are calculated according to the following mathematical formula (1). Here, Aorifice refers to the cross-sectional area of ​​the orifice, A2 refers to the cross-sectional area of ​​the cooling pipe in which the fluid is located before passing through the orifice, and ρorifice refers to the fluid density.

[0041] Mathematical formula (1):

[0042] Next, the local resistance coefficient ξ3 (unit: Pa), local head loss hj3 (unit: m), and pressure loss Δp3 are calculated according to the following mathematical formula (2) when the fluid suddenly expands downstream of the throttling orifice. Here, Aorifice refers to the cross-sectional area of ​​the throttling orifice, and A3 refers to the cross-sectional area of ​​the cooling pipe where the fluid is located after passing through the throttling orifice. ρorifice refers to the fluid density.

[0043] Mathematical expression (2):

[0044] Next, solve the following equations simultaneously.

[0045]

[0046] Where qm and qm_orifice represent mass flow rates, and V_orifice represents the flow rate at the throttling orifice. The final orifice diameter (d_orifice) is calculated to be 6.5 mm.

[0047] In some embodiments, a method for measuring the pressure difference of fluid before and after passing through a throttling plate is provided, comprising the following steps: a simulated throttling adjustment step, in which an adjustable valve (such as a manual regulating valve or a throttling valve) is installed in the cooling circuit at the location where the throttling plate will be installed subsequently, to simulate the flow resistance characteristics of the throttling plate; a valve adjustment step, in which the opening of the adjustable valve is adjusted according to a preset value of the required flow rate in the cooling circuit of the cooling system 1000 to meet the flow requirements of the cooled equipment in different modes; and a pressure difference measurement step, in which pressure measuring devices (such as pressure gauges, pressure sensors, or differential pressure transmitters) are installed upstream and downstream of the adjustable valve, respectively, and the pressure values ​​of the fluid before and after passing through the adjustable valve are actually measured and the difference between the two is calculated to obtain the simulated pressure difference Δp before and after the throttling plate. Based on the actually measured pressure difference Δp and the measured diameters d2 and d3 of the cooling pipe, the orifice size of the throttling orifice provided in the throttling plate can be calculated based on the above mathematical formulas. After the calculation is completed, the adjustable valve is replaced with a throttling plate with the same orifice size, thereby completing the configuration of the flow limiting device 200.

[0048] Furthermore, in some implementations, the number of throttling plates and / or the orifice size can be further optimized based on the flow and noise requirements of the cooled equipment in different modes, achieving synergistic optimization of flow limiting performance and noise suppression effect. Alternatively, in some implementations, the number of throttling plates and / or the orifice size can be modularly combined according to actual application requirements to adapt to application scenarios with different cooling power and noise requirements.

[0049] According to the flow limiting device 200 involved in this embodiment, it can not only achieve accurate flow limiting function with a simple and reliable structure, but also significantly reduce the aerodynamic noise generated when the fluid passes through through multi-stage throttling and orifice optimization, thereby achieving a balance in multiple technical dimensions such as system compactness, flow control accuracy and noise suppression effect, and ultimately achieving efficient and stable operation of the cooling system.

[0050] Another embodiment of this utility model provides a flow limiting device. Figure 4 , Figure 5 This is a schematic diagram illustrating a cooling system 2000 according to yet another embodiment of the present invention. Figure 4 and Figure 5 In China, for the sake of Figure 1 and Figure 2The same structures are labeled with the same reference numerals, and their detailed descriptions are omitted. This embodiment differs from the aforementioned cooling system 1000 in that a flow limiting device 200' is provided in the cooling circuit of the cooling system 2000 to replace the flow limiting device 200. This flow limiting device 200' is provided in the cooling circuit of the cooling system 2000 to dynamically regulate the flow rate of the fluid circulating within the cooling circuit. Furthermore, Figure 4 and Figure 5 The diagram also shows the fluid flow in the cooling system 2000 when the medical device is running in both working and standby modes.

[0051] like Figure 4 and Figure 5 As shown, similar to the cooling system 1000, the cooling circuit of the cooling system 2000 includes a first cooling branch for cooling the first heat load 1001a and a second cooling branch for cooling the second heat load 1001b, with the first and second cooling branches connected in parallel. In addition to the first throttling section 201, the second throttling section 202, and the third throttling section 203 described in the aforementioned embodiments, the flow limiting device 200' also includes a fourth throttling section 204. The first throttling section 201 and the fourth throttling section 204 are disposed in the output flow section of the first cooling branch, and the second throttling section 202 and the third throttling section 203 are disposed in the input flow section of the second cooling branch. Hereinafter, based on... Figure 4 and Figure 5 Provide a detailed description of the flow of the cooling medium in the cooling circuit equipped with the flow restriction device 200'.

[0052] like Figure 4 As shown, when the medical device being cooled is in working mode, the cooling medium flows out from the heat exchange system 100 and branches into a first cooling branch and a second cooling branch at the branch point a of the input flow section. Figure 4 The hollow arrows indicate the flow direction of the cooling medium in the first cooling branch, and the solid arrows indicate the flow direction of the cooling medium in the second cooling branch. In the first cooling branch, as shown by the hollow arrows, the cooling medium flows sequentially from branch point a through the first heat load 1001a, the first throttling section 201, and the fourth throttling section 204 before reaching the confluence point b of the output flow section. In the second cooling branch, under the action of the flow direction control module 210, as shown by the solid arrows, the cooling medium flows sequentially from branch point a through the second throttling section 202 and the second heat load 1001b before reaching the confluence point b of the output flow section. At the confluence point b, the cooling medium from the first cooling branch and the cooling medium from the second cooling branch merge and flow back to the heat exchange system 100 to complete the heat exchange cycle.

[0053] like Figure 5As shown, when the medical device being cooled is in standby mode, the cooling medium flows out from the heat exchange system 100, and similarly branches into a first cooling branch and a second cooling branch at the branch point a of the input flow section. Figure 5 The hollow arrows indicate the flow direction of the cooling medium in the first cooling branch, and the solid arrows indicate the flow direction of the cooling medium in the second cooling branch. In the first cooling branch, as shown by the hollow arrows, the cooling medium flows from branch point a sequentially through the bypass loop bp (i.e., not cooling the first heat load 1001a) and the first throttling section 201 before reaching the confluence point c of the output flow section. In the second cooling branch, under the action of the flow direction control module 210, as shown by the solid arrows, the cooling medium flows from branch point a sequentially through the second throttling section 202 and the third throttling section 203 before reaching the confluence point c of the output flow section. At the confluence point c, the cooling medium from the first cooling branch and the cooling medium from the second cooling branch merge and then flow back to the heat exchange system 100 via the fourth throttling section 204 to complete the heat exchange cycle.

[0054] Therefore, in the working mode, the cooling medium in the second cooling branch only undergoes a single-stage throttling process through the second throttling section 202 before flowing directly into the second heat load 1001b, which is a high-power component. In the first cooling branch, the flow rate of the cooling medium is restricted by two stages of series throttling through the first throttling section 201 and the fourth throttling section 204. Thus, compared with the cooling system 1000, a more sufficient cooling flow rate can be provided to the second heat load 1001b, further improving the cooling effect of the second heat load 100b. In standby mode, under the action of the flow control module, the flow rate of the cooling medium in the first cooling branch is limited by two-stage series throttling through the first throttling section 201 and the fourth throttling section 204. In the second cooling branch, three-stage series throttling is implemented through the second throttling section 202, the third throttling section 203 and the fourth throttling section 204. Compared with the cooling system 1000, the cooling flow rate in the second cooling branch can be further reduced, avoiding overcooling and energy waste. Furthermore, by dispersing the pressure drop through more staged throttling, the fluid noise in the system can be reduced more effectively.

[0055] The fourth throttling section 204 involved in this embodiment can also be implemented by a throttling plate. Specifically, in this embodiment, the fourth throttling plate 204 can also be configured as a plate-shaped member with a throttling orifice. However, it is not limited to this; in some implementations, it can also be configured to have more than one throttling orifice. Furthermore, in this embodiment, the shape of the throttling orifice is set to circular, but it is not limited to this; in some implementations, it can also be set as a slit, a porous array, or other geometric shapes. In addition, in some implementations, the shape and configuration of the throttling orifice can be adjusted according to fluid characteristics (such as corrosivity, particulate matter content, etc.). Furthermore, the specific configuration of the fourth throttling section 204 can be designed using the same method as the flow limiting device 200, and will not be described in detail here.

[0056] According to the flow limiting device 200' involved in this embodiment, by adding a fourth throttling section, compared with the flow limiting device 200, it can not only achieve a more accurate flow limiting function with a simple and reliable structure, but also provide a higher degree of design freedom, and it is easier to achieve a balance in multiple technical dimensions such as system compactness, flow control accuracy and noise suppression effect, so as to achieve efficient and stable operation of the cooling system.

[0057] As described above, the flow limiting devices 200 and 200' involved in the above embodiments can be applied to various fields requiring flow limiting. The following is a specific description of an example of using the flow limiting device 200' to cool a magnetic resonance imaging (MRI) system. As is well known, magnetic resonance imaging (MRI) equipment is a key device in modern medical diagnostics, and the stability and efficiency of its cooling system directly affect not only the reliability and imaging quality of the equipment, but also patient safety and the operational efficiency of medical institutions. Figure 6 and Figure 7 This is a schematic diagram illustrating a cooling system 3000 for an MRI device according to another embodiment of the present invention.

[0058] Figure 6 and Figure 7The image exemplifies a heat load 2001 in an MRI device. In an MRI device, the heat load 2001 may include, for example, an integrated system cabinet (ISC) as a first heat load 2001a and a gradient coil (GC) as a second heat load 2001b. However, it is not limited to this; it may include one or more other components of the magnetic resonance system, such as a superconducting magnet assembly, a power amplifier, an electronic control unit, a cooling compressor, etc. The ISC and GC circuits have different flow requirements under different operating modes of the MRI device (standby mode or scan mode). Specifically, in scan mode (high power consumption), a large amount of heat is generated in the GC circuit, thus requiring a higher cooling flow rate to maintain its temperature stability. At this time, the flow rate in the ISC circuit is adjusted synchronously, but with priority given to the heat dissipation of the GC circuit. In standby mode (low power consumption), heat generation in the GC circuit is significantly reduced, requiring a reduction in its cooling flow rate allocation. Simultaneously, the cooling flow rate to the ISC circuit needs to be limited to avoid overcooling or energy waste. Furthermore, in certain configurations of MRI equipment, a helium compressor is connected upstream of the ISC circuit, for example, before the first thermal load. The helium compressor is a core component for maintaining the cryogenic environment of the superconducting magnet. The helium compressor is sensitive to inlet flow rate; to prevent lubrication failure or mechanical damage, the flow rate into the helium compressor needs to be limited to, for example, below 10 L / min. Therefore, in standby mode, the fluid flow to the ISC circuit needs to be precisely limited.

[0059] In some embodiments, the cooling system 3000 can be implemented using an integrated cooling cabinet (ICC). The ICC serves as the core distribution unit of the cooling system, dynamically distributing the fluid used for cooling to the cooling loop.

[0060] like Figure 6 and Figure 7 As shown, the cooling system 3000 mainly includes: a heat exchange system 100, which is used for heat exchange and performs heat exchange operations on the fluid circulating in the cooling loop of the cooling system to remove heat; and a flow limiting device 200', which is disposed in the cooling loop and is used to dynamically adjust the flow rate of the fluid circulating in the cooling loop. Figure 6 and Figure 7The diagram also illustrates the fluid flow in the cooling system 3000 when the MRI equipment is operating in scanning and standby modes, respectively. In some embodiments, the heat exchange system 100 includes at least components such as a heat exchanger, water tank, pump, filter, and temperature / flow sensor, which dissipates heat from the heat load 2001 via the heat exchanger. Furthermore, in some embodiments, the heat exchange system 100 may also include various auxiliary components, such as expansion valves, buffers, solenoid valves, or redundant backup modules. Moreover, there are no particular limitations on the connection order and layout of the components in the heat exchange system 100; they can be configured according to actual design requirements.

[0061] like Figure 6 and Figure 7 As shown, similar to the cooling system 2000, the cooling system 3000 includes a first cooling branch for cooling the ISC circuit, which serves as a first heat load 2001a, and a second cooling branch for cooling the GC circuit, which serves as a second heat load 2001b. The first cooling branch and the second cooling branch are connected in parallel. As described above, the flow limiting device 200' includes a first throttling section 201, a second throttling section 202, a third throttling section 203, and a fourth throttling section 204. The first throttling section 201 and the fourth throttling section 204 are provided in the output flow section of the first cooling branch, and the second throttling section 202 and the third throttling section 203 are provided in the input flow section of the second cooling branch. Hereinafter, based on Figure 6 and Figure 7 Provide a detailed description of the flow of the cooling medium in the cooling circuit equipped with the flow restriction device 200'.

[0062] like Figure 6 As shown, when the MRI equipment is in scanning mode, the cooling medium flows out from the heat exchange system 100. Figure 6 The hollow arrows indicate the flow direction of the cooling medium in the first cooling branch, and the solid arrows indicate the flow direction of the cooling medium in the second cooling branch. In the first cooling branch, as shown by the hollow arrows, the cooling medium flows sequentially from branch point a through the helium compressor, ISC, first throttling section 201, and fourth throttling section 204 before reaching the confluence point b of the output flow section. In the second cooling branch, under the action of the flow control module 210, as shown by the solid arrows, the cooling medium flows sequentially from branch point a through the second throttling section 202 and GC before reaching the confluence point b of the output flow section. At the confluence point b, the cooling medium from the first cooling branch and the cooling medium from the second cooling branch merge and flow back to the heat exchange system 100 to complete the heat exchange cycle.

[0063] like Figure 7 As shown, when the MRI device is in standby mode, the cooling medium flows out from the heat exchange system 100, and similarly, it branches into the first cooling branch and the second cooling branch at the branch point a of the input flow section. Figure 7 The hollow arrows indicate the flow direction of the cooling medium in the first cooling branch, and the solid arrows indicate the flow direction of the cooling medium in the second cooling branch. In the first cooling branch, as shown by the hollow arrows, the cooling medium flows sequentially from branch point a through the helium compressor, the bypass loop bp (i.e., not cooling the ISC) in the ISC, and the first throttling section 201 before reaching the confluence point c of the output flow section. In the second cooling branch, under the action of the flow direction control module 210, as shown by the solid arrows, the cooling medium flows sequentially from branch point a through the second throttling section 202 and the third throttling section 203 before reaching the confluence point c of the output flow section. At the confluence point c, the cooling medium from the first cooling branch and the cooling medium from the second cooling branch merge and then flow back to the heat exchange system 100 via the fourth throttling section 204 to complete the heat exchange cycle.

[0064] The following diagram illustrates the flow of fluid through the first throttling section 201 to the fourth throttling section 204 in each cooling branch under both scan and standby modes. A "√" indicates that fluid has passed through that throttling section in that cooling branch.

[0065]

[0066] As shown in the above charts, in scanning mode, the cooling medium in the second cooling branch undergoes only one stage of throttling through the second throttling section 202 before flowing directly into the second heat load 2001b (GC), which is a high-power component. Furthermore, in the first cooling branch, the cooling medium flow rate is limited by two stages of series throttling through the first throttling section 201 and the fourth throttling section 204, thus providing sufficient cooling flow to the GC circuit and significantly improving the cooling effect of the GC. In standby mode, under the action of the flow direction control module, in the first cooling branch, the cooling medium flow rate is limited by two stages of series throttling through the first throttling section 201 and the fourth throttling section 204, ensuring a safe flow rate into the helium compressor. In the second cooling branch, three stages of series throttling are implemented through the second throttling section 202, the third throttling section 203, and the fourth throttling section 204, thereby significantly reducing the cooling flow rate in the second cooling branch and avoiding overcooling and energy waste. In addition, by dispersing the pressure drop through multi-stage throttling, fluid noise in the system can be reduced more effectively.

[0067] The cooling system 3000 described in this embodiment achieves precise flow restriction with a simple and reliable structure, fundamentally avoiding the risk of blockage or failure, ensuring long-term stable operation of the system, and significantly reducing maintenance costs. Furthermore, by precisely controlling the safe flow rate into the helium compressor, physical impact damage to precision components (such as valve plates and impellers) inside the helium compressor due to excessive flow can be avoided, ensuring smooth operation of the helium compressor. In addition, the system features multi-stage throttling, reducing operating noise and meeting the high requirements for quiet operation in medical equipment (such as MRI equipment). It also provides greater design freedom, making it easier to achieve a balance between system compactness, flow control accuracy, and noise suppression, resulting in efficient and stable system operation.

[0068] Furthermore, this utility model also relates to a medical device comprising a heat load and a cooling system for cooling the heat load. The cooling system is equipped with the flow limiting devices described in the above embodiments. According to this medical device, long-term stable system operation can be ensured, significantly reducing maintenance costs. Moreover, a balance can be achieved in multiple technical dimensions such as system compactness, flow control accuracy, and noise suppression, resulting in efficient and stable system operation.

[0069] The flow limiting device, cooling system, and medical device involved in this utility model have been described above. However, the structures shown in the above exemplary embodiments are only examples of the content of this utility model and can be combined with other known technologies. A part of the structure can also be omitted or modified without departing from the spirit of this utility model.

[0070] Furthermore, within the scope of this utility model, the various embodiments can be freely combined, any structural elements of the various embodiments can be modified, or any structural elements of the various embodiments can be omitted.

Claims

1. A flow limiting device, disposed in a cooling circuit for cooling equipment, for regulating the flow rate of fluids flowing through the equipment containing a first heat load and a second heat load. The flow limiting device is characterized in that... It includes at least a first throttling section, a second throttling section, and a third throttling section. in, The first throttling section is disposed in the output flow section of the first cooling branch for the first heat load. The second and third throttling sections are disposed in the input flow section of the second cooling branch for the second heat load, and The first throttling section, the second throttling section, and the third throttling section are configured as follows: When the cooled equipment is in working mode, In the first cooling branch, the fluid flows through the first heat load and then through the first throttling section. In the second cooling branch, the fluid flows through the second heat load only through the second throttling section, and then the two flows merge and are output. When the cooled device is in standby mode In the first cooling branch, the fluid flows through the bypass circuit provided in the first heat load and then through the first throttling section. In the second cooling branch, it flows through the second throttling section and the third throttling section in sequence, and then the two flow together and are output.

2. The flow limiting device as described in claim 1, characterized in that, The first throttling section, the second throttling section, and the third throttling section are throttling plates formed in the shape of plates. The throttling plate has at least one throttling orifice.

3. The flow limiting device as described in claim 2, characterized in that, The orifice diameter is determined based on the pressure difference before and after the fluid passes through the throttling plate.

4. The flow limiting device as described in claim 1, characterized in that, When the cooled equipment is in working mode or standby mode, the flow direction of the fluid in the second cooling branch is different.

5. The flow limiting device according to any one of claims 1 to 4, characterized in that, It also includes a fourth throttling section. The fourth throttling section is located in the output section of the first cooling branch. When the cooled equipment is in working mode, In the first cooling branch, the fluid flows sequentially through the first throttling section and the fourth throttling section; in the second cooling branch, the fluid flows only through the second throttling section. The two flows then merge and are output. When the cooled device is in standby mode In the first cooling branch, the fluid flows through the first throttling section. In the second cooling branch, the fluid flows sequentially through the second throttling section and the third throttling section, and then the two flow together and are output through the fourth throttling section.

6. The flow limiting device according to any one of claims 1 to 4, characterized in that, The first thermal load and the second thermal load have different flow requirements in the operating mode and the standby mode, respectively.

7. The flow limiting device as described in claim 5, characterized in that, The fourth throttling section is a throttling plate formed in the shape of a plate. The throttling plate has at least one throttling orifice.

8. The flow limiting device as claimed in claim 1, characterized in that, The device being cooled is a magnetic resonance imaging (MRI) device. The first thermal load is an integrated system component, and the second thermal load is a gradient coil.

9. The flow limiting device as described in claim 8, characterized in that, A helium compressor is also connected in front of the first heat load.

10. A cooling system for cooling equipment, characterized in that, Includes the flow limiting device according to any one of claims 1 to 9.

11. A medical device, characterized in that, include: Thermal load; as well as A cooling system provided with the flow limiting device as described in any one of claims 1 to 9.

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