Magnetic resonance imaging apparatus and airflow distribution method

Abstract

The present application relates to a magnetic resonance imaging apparatus and an air flow distribution method capable of uniformly and equally discharging air flows to a plurality of discharge ports with a small number of parts and a compact structure. The magnetic resonance imaging apparatus is characterized by having: a magnet that generates a magnetic field; a stand that stores the magnet; and a duct that is provided to the stand and discharges air into a hole formed by the stand, the duct having: a first guide portion that guides an air flow drawn in; a branch portion that branches the flow of air guided by the first guide portion; a first discharge port that discharges air branched by the branch portion in a first direction into the hole; a second guide portion that is provided at a position downstream of the first discharge port and guides air branched by the branch portion in a second direction; and a second discharge port that discharges air guided by the second guide portion into the hole.

Description

Technical Field

[0001] This invention relates to a magnetic resonance imaging device and an airflow distribution method. Background Technology

[0002] Medical imaging diagnostic examinations such as MRI scans typically require a long examination time, during which the patient must remain inside the dome. Because the dome is a long, thin, tubular structure, air exchange within the tubular space is often insufficient, potentially causing discomfort such as tension for the patient. To address this issue, it is necessary to continuously provide and expel fresh air to the patient during the examination to minimize discomfort.

[0003] Reference Figure 8A , 8B The ventilation system 400 of a prior art magnetic resonance imaging device will be described. Figure 8A This is a three-dimensional view of the ventilation system 400 of a prior art magnetic resonance imaging device. Figure 8B This is a three-dimensional diagram showing the airflow path of the ventilation system 400 in a prior art magnetic resonance imaging (MRI) device. In existing MRI devices, such as... Figure 8A , 8B As shown, the ventilation system 400 of the magnetic resonance imaging device allows fresh air to enter the interior of the stand.

[0004] Specifically, the ventilation system 400 includes a duct 401, a tee connector 402, a first branch duct 4031, a second branch duct 4032, a first duct 4041, a second duct 4042, a first outlet 4051, and a second outlet 4052. The duct 401 is formed on the platform side of the ventilation system 400. Airflow passes from the duct 401 through the tee connector 402, which distributes the airflow to the first branch duct 4031 and the second branch duct 4032. Thus, the airflow forms two airflow paths via the first branch duct 4031 and the second branch duct 4032, respectively entering the platform through the first duct 4041 and the second duct 4042, and exiting to the outside through the first outlet 4051 and the second outlet 4052 on both sides.

[0005] However, in Figure 8A , 8B In the ventilation system 400, there is an issue of uneven airflow at the exhaust outlets on both sides. Furthermore, due to the use of components such as T-joints, there are also problems such as a large number of component points, complex and large structure, inconvenient maintenance, and high cost. Summary of the Invention

[0006] The present invention was made in view of the above problems, and its purpose is to provide a magnetic resonance imaging device and an airflow distribution method that can uniformly and equally discharge airflow to multiple outlets with fewer component points and a compact structure.

[0007] According to the present invention, a magnetic resonance imaging apparatus comprises: a magnet that generates a magnetic field; a stage that stores the magnet; and a conduit disposed on the stage for discharging air into an aperture formed by the stage, the conduit comprising: a first guide portion for guiding an intake airflow; a branch portion for branching the airflow guided by the first guide portion; a first outlet for discharging air branched in a first direction into the aperture by the branch portion; a second guide portion disposed downstream of the first outlet for guiding air branched in a second direction by the branch portion; and a second outlet for discharging air guided by the second guide portion into the aperture. Thus, since the conduit is formed as an arc-shaped channel matching the shape of the stage, it is not necessary to allow other components in the magnetic resonance imaging apparatus to be avoided, simplifying the surrounding sheet metal structure.

[0008] According to the magnetic resonance imaging apparatus of the present invention, the curvature of the branch is different from the curvature of the second guide portion.

[0009] According to the magnetic resonance imaging apparatus of the present invention, the branch portion distributes the intake airflow to the first direction and the second direction with equal flow rates.

[0010] Therefore, by eliminating the use of tee fittings and multiple branch pipes, and instead arranging multiple outlets along a pipe system that matches the shape of the support frame, the need for support components for tee fittings and multiple branch pipes is eliminated, reducing the number of required components and achieving a more compact structure. Furthermore, it reduces the space occupied in the magnetic resonance imaging device, saves on-site assembly time, and lowers costs.

[0011] According to the magnetic resonance imaging apparatus of the present invention, the conduit has a third outlet, which is disposed between the first outlet and the second outlet in the direction in which the air is guided, and discharges air guided by the second guide into the hole.

[0012] Therefore, without increasing the number of component points, airflow can be discharged from the test subject through more outlets, which can improve the user experience of the test subject.

[0013] According to the magnetic resonance imaging apparatus of the present invention, the cross-sectional area of ​​the first outlet is smaller than the cross-sectional area of ​​the second outlet.

[0014] According to the magnetic resonance imaging apparatus of the present invention, the second guide portion is formed in a smooth arc shape that matches the shape of the stage.

[0015] According to the magnetic resonance imaging apparatus of the present invention, the orientation of the first outlet and the second outlet is variable.

[0016] According to the magnetic resonance imaging apparatus of the present invention, a rotating member capable of adjusting the orientation of the first outlet and the second outlet is provided at the first outlet and the second outlet respectively.

[0017] Therefore, by setting baffles, it is possible to ensure that the airflow is consistent when it reaches the near-end outlet and the far-end outlet, and to further distribute the airflow evenly and equally to multiple outlets.

[0018] Furthermore, it reduces air resistance and air loss during airflow through the duct, ensuring uniform airflow. This airflow path also allows for more even airflow distribution, reducing pressure loss and improving airflow utilization efficiency. It can also uniformly and equally discharge airflow to multiple outlets.

[0019] Furthermore, it can control the airflow discharged to the subject, so that multiple discharge ports can provide a consistent blowing experience to the subject.

[0020] According to the airflow distribution method of the present invention, the method comprises the following steps: determining structural parameters based on the shape and structure of the platform; determining the number of outlets and the length of the airflow path; determining the cross-sectional area and pipeline pressure loss of each outlet in such a way that the flow rate of the airflow discharged from each outlet is equal, wherein the outlets include a near-end outlet located at the nearest end of the main pipeline, a far-end outlet located at the farthest end of the main pipeline and disposed at the end of the pipeline, and one or more intermediate outlets located between the nearest and farthest ends of the main pipeline; and calculating the cross-sectional area of ​​each outlet.

[0021] Therefore, it is possible to design the structural parameters such as the location, opening shape, and cross-sectional area of ​​the outlet in the pipeline of a magnetic resonance imaging device, so as to ensure that the airflow is discharged uniformly and equally from each outlet.

[0022] According to the airflow distribution method of the present invention, the pipeline pressure loss at the near-end outlet includes local pressure loss, the pipeline pressure loss at the far-end outlet includes extended pressure loss, and the pipeline pressure loss at the intermediate outlet includes both the local pressure loss and the extended pressure loss.

[0023] Therefore, it is possible to take into account factors such as the path length of the airflow and the presence or absence of baffles, and use different pipeline pressure losses to determine the structural parameters. It is possible to accurately calculate the airflow rate at each outlet, and to ensure that the airflow is discharged uniformly and in equal amounts from each outlet.

[0024] Invention Effects

[0025] According to the magnetic resonance imaging apparatus and airflow distribution method of the present invention, airflow can be uniformly and equally discharged to multiple outlets with fewer component points and a compact structure.

[0026] Furthermore, the magnetic resonance imaging device and airflow distribution method of the present invention can design structural parameters such as the position, opening shape and cross-sectional area of ​​the outlet in the pipeline of the magnetic resonance imaging device, so as to enable the airflow to be discharged uniformly and equally from each outlet. Attached Figure Description

[0027] Figure 1 This is a three-dimensional diagram showing the stand of a magnetic resonance imaging device.

[0028] Figure 2 This is a partially enlarged perspective view of the magnetic resonance imaging apparatus according to the first embodiment of the present invention.

[0029] Figure 3 It is a 3D diagram representing a pipeline.

[0030] Figure 4A This is a three-dimensional diagram representing the distribution port.

[0031] Figure 4B It is a three-dimensional representation of the baffle.

[0032] Figure 5 This is a perspective view of a magnetic resonance imaging apparatus according to a second embodiment of the present invention.

[0033] Figure 6 This is a perspective view of a magnetic resonance imaging apparatus according to a third embodiment of the present invention.

[0034] Figure 7 This is a flowchart illustrating the flow of the airflow distribution method of the present invention.

[0035] Figure 8A This is a three-dimensional diagram showing the ventilation system of a conventional magnetic resonance imaging device.

[0036] Figure 8B This is a three-dimensional diagram showing the airflow path of the ventilation system in a conventional magnetic resonance imaging device.

[0037] Explanation of reference numerals in the attached figures

[0038] Magnetic resonance imaging device 100, pipe 1, first guide part 11, input end 111, output end 112, branch part 12, channel 121, first outlet 13, second guide part 14, second outlet 15, third outlet 16, distribution port 17, proximal distribution port 17A, distal distribution port 17B, baffle 18, fourth outlet 19, stand 2, magnetic resonance imaging device 200, magnetic resonance imaging device 300, rotating part 20, ventilation system 400, pipe 401, tee connector 402, first branch pipe 4031, second branch pipe 4032, first pipe 4041, second pipe 4042, first outlet 4051, second outlet 4052. Detailed Implementation

[0039] Hereinafter, embodiments of the magnetic resonance imaging apparatus and airflow distribution method of the present invention will be described with reference to the accompanying drawings. In the following embodiments, the same or equivalent parts will be given the same reference numerals for description.

[0040] Furthermore, in the following description, the airflow distribution method of the present invention is used as an example of a stand for a magnetic resonance imaging device, but the present invention is not limited thereto, and can also be applied to other medical imaging examination devices with stands that are formed as elongated tubular structures or have tubular channels.

[0041] Furthermore, in the following description, only components related to the technical concept of the present invention are described and shown, while other components are omitted. For clarity, the lengths, widths, thicknesses, etc., in the accompanying drawings are merely illustrative and not intended to limit the invention.

[0042] (Magnetic resonance imaging device)

[0043] (First Implementation)

[0044] First, refer to Figures 1-3 The magnetic resonance imaging apparatus 100 of the first embodiment of the present invention will be described. Figure 1 This is a three-dimensional view of the stand 2 of the magnetic resonance imaging device. Figure 2 This is a partial magnification of the magnetic resonance imaging apparatus 100 according to the first embodiment of the present invention. Figure 1 A 3D view (with a dashed frame in the image). Figure 3 This is a 3D diagram representing pipe 1. Figure 2 In the illustration, a portion of the stage 2 is made transparent to show the magnetic resonance imaging device 100.

[0045] like Figures 1-3As shown, the magnetic resonance imaging (MRI) apparatus 100 includes a magnet M, a stage 2, and a conduit 1. The MRI apparatus 100 is disposed on one side of the stage 2; in this embodiment, the MRI apparatus 100 is disposed on the side of the stage 2 facing the Y1 direction.

[0046] Specifically, the magnet M generates a static magnetic field in the imaging space where the subject is placed. Specifically, the magnet M is formed as a hollow, generally cylindrical shape (including those with an elliptical cross-section orthogonal to the central axis), generating a static magnetic field in the imaging space formed on its inner periphery. For example, the magnet M is a superconducting magnet, a permanent magnet, etc. The superconducting magnet mentioned here, for example, consists of a container filled with a coolant such as liquid helium and a superconducting coil immersed in that container.

[0047] The stage 2 has a hollow bore that is generally cylindrical (including those with an elliptical cross-section orthogonal to the central axis) to house the magnet M, as well as a gradient magnetic field coil (not shown), a whole-body RF coil, and an RF shield. Here, the space within the bore of the stage 2 serves as the imaging space for placing the subject during imaging.

[0048] In addition, such as Figure 2 , 3 As shown, the duct 1 is disposed on the stand 2, and discharges air into the hole formed by the stand 2, allowing airflow to enter. The duct 1 includes: a first guide section 11, a branch section 12, a first outlet 13, a second guide section 14, and a second outlet 15. The duct 1 is used to allow airflow to enter the magnetic resonance imaging device 100 and flow in the stand 2.

[0049] The first guide section 11 guides the intake airflow. In addition, the first guide section 11 includes an input end 111 and an output end 112. The input end 111 faces the air inlet side to allow airflow to enter, and the output end 112 is connected to the branch section 12 described later.

[0050] Branch section 12 branches the airflow guided by first guide section 11. Additionally, branch section 12 has an arc-shaped channel 121, and is connected to the output end 112 of first guide section 11 for airflow. Branch section 12 guides the airflow entering from first guide section 11. Here, branch section 12 branches the airflow drawn in and guided by first guide section 11 into a first direction and a second direction intersecting the first direction, such as the direction along pipe 1. Branch section 12 distributes the airflow with equal flow rates to the first direction and the second direction.

[0051] Pipe 1, for example Figure 2 , 3As shown, it is formed into a smooth arc shape that matches the shape of the platform 2. Here, the pipe 1 is formed, for example, into a smooth arc shape without any protrusions. Specifically, as... Figure 2 , 3 As shown, in order to match the shape of the support platform 2, a large curvature arc is formed in the pipe 1 between the first guide section 11 and the first outlet 13 (described later), thereby conforming to the shape of the support platform 2. Figure 1 The shape of the platform 2 shown matches a smooth arc.

[0052] The first outlet 13 discharges air branched into a first direction by the branch portion 13 into the hole formed by the support 2. Here, in the description of the first embodiment, it is described as an example of the pipe 1 having two outlets, the first outlet 13 and the second outlet 15, but it is not limited to this, and multiple outlets may be provided along the pipe 1. Furthermore, the first outlet 13 is formed with a uniform cross-section without abrupt changes.

[0053] Therefore, the cross-section of the first row outlet 13 is uniform and without abrupt changes, and the pipe 1 is formed into a smooth arc that matches the shape of the platform 2, thereby reducing the air resistance and air consumption of the airflow passing through the branch 12 and ensuring uniform airflow.

[0054] The second guide section 14 is located downstream of the first outlet 13 and guides the air branched into a second direction by the branch section 12. Specifically, the second guide section 14 is formed into an arc with a small curvature between the first outlet 13 and the second outlet 15 (described later), thereby forming a shape that is in harmony with... Figure 1 The shape of the platform 2 shown matches a smooth arc. Here, the curvature of the branch 12 is different from the curvature of the second guide 14.

[0055] The second outlet 15 is located downstream of the first outlet 13, guiding the air branched into a second direction by the branch 12. The airflow entering from the first guide 11 is blown towards the test object from the first outlet 13 and the second outlet 15.

[0056] Alternatively, when there are three or more outlet pipes 1, the pipe 1 may have a first outlet 13 near the first guide part 11, a second outlet 15 located downstream of the first outlet 13, and one or more third outlets 16 located between the first outlet 13 and the second outlet.

[0057] In other words, the third outlet 16 is located between the first outlet 13 and the second outlet 15 in the direction in which air is guided, and discharges the air guided by the second guide 14 into the hole formed by the frame 2.

[0058] Furthermore, the multiple outlets, namely the first outlet 13, the second outlet 15, and one or more third outlets 16, may have the same shape. Alternatively, the cross-sectional area of ​​the first outlet 13 may be smaller than the cross-sectional area of ​​the second outlet 15. For example, the multiple outlets may be shaped as rectangular openings as shown in the figure. The cross-sectional areas of the multiple outlets will be described later.

[0059] In addition, the multiple exhaust outlets are configured to have variable orientations, so that the wind direction of the airflow exiting from the multiple exhaust outlets can be varied.

[0060] Alternatively, the number of branch sections 12 may match the number of multiple outlets, with each branch section 12 located inside the multiple outlets. Specifically, the branch section 12 may not be provided at the second outlet 15 located at the end of the pipe 1, but may only be provided at the first outlet 13 located upstream of the second outlet 15. That is, in the first embodiment, there is one branch section 12 matching the number of the first outlet 13, and the branch section 12 is located inside the first outlet 13.

[0061] In addition, pipe 1 also has a distribution port 17 and a baffle 18.

[0062] Reference Figure 4A , 4B The distribution port 17 is explained. Figure 4A This is a three-dimensional diagram representing the distribution port 17. Figure 4B This is a three-dimensional view of baffle 18.

[0063] like Figure 4A As shown, the distribution port 17 is located inside the discharge port. In addition, the distribution port 17 includes at least a proximal distribution port 17A located upstream and a distal distribution port 17B located downstream of the proximal distribution port 17A. The cross-sectional area of ​​the proximal distribution port 17A is smaller than the cross-sectional area of ​​the distal distribution port 17B.

[0064] This is because the airflow exiting from the second outlet 15 travels a longer path through duct 1 and encounters greater resistance compared to the airflow exiting from the first outlet 13. Therefore, by making the cross-sectional area of ​​the near-end distribution port 17A smaller than the cross-sectional area of ​​the far-end distribution port 17B, it can be ensured that the airflow volume is consistent when it reaches the first outlet 13 and the second outlet 15.

[0065] like Figure 4B As shown, the baffle 18 is located near the distribution port 17A and is quadrilateral in shape. Thus, by finely adjusting the air volume discharged from the first outlet 13 through the baffle 18, equal air volume can be achieved from multiple outlets.

[0066] Furthermore, the baffle 18 is not located at the second outlet 15, which is positioned downstream of the first outlet 13, but only at the first outlet 13. Therefore, since the airflow path from the first outlet 13 differs from that from the second outlet 15, adjusting the size of the baffle 18 ensures that the airflow volume is consistent when reaching both the first and second outlets, allowing for uniform and equal airflow distribution to multiple outlets.

[0067] This allows multiple outlets to provide a consistent blowing experience to the subject.

[0068] Therefore, with the magnetic resonance imaging apparatus 100 of the first embodiment of the present invention, since the conduit 1 is formed as an arc-shaped channel 121 that matches the shape of the stand 2, it is not necessary to make other components in the magnetic resonance imaging apparatus 100 avoid each other, and the sheet metal structure around it can be simplified.

[0069] Furthermore, by using the magnetic resonance imaging device 100, since multiple outlets are arranged along the pipe 1 formed to match the shape of the stand 2 without the use of tee joints and multiple branch pipes, support components for supporting tee joints and multiple branch pipes are not required, thus reducing the number of required components and achieving a more compact structure. In addition, it can also reduce the space occupied in the magnetic resonance imaging device, save on-site assembly time, and reduce costs.

[0070] In addition, in the magnetic resonance imaging device 100, the outlet includes a first outlet 13 and a second outlet 15 located downstream of the first outlet 13. Therefore, without increasing the number of components, airflow can be discharged from the subject through more outlets, which can improve the user experience of the subject.

[0071] Furthermore, in the magnetic resonance imaging device 100, airflow enters from the duct 1 and sequentially passes through the first guide section 11, the branch section 12, the first outlet 13, the second guide section 14, and the second outlet 15 before being discharged towards the subject. Moreover, before the airflow passes through the first guide section 11 and exits from the first outlet 13, the airflow volume is adjusted by passing through the distribution port 17 and the baffle 18 located at the first outlet 13.

[0072] Therefore, by using the magnetic resonance imaging device 100, the cross-section of the first outlet 13 is uniform and without abrupt changes, thereby reducing airflow resistance and air consumption, and ensuring uniform airflow. Furthermore, this airflow path allows for more uniform airflow distribution, reduces pressure loss in the airflow path, and improves airflow utilization efficiency. It also enables the uniform and equal discharge of airflow to multiple outlets.

[0073] In addition, since the first outlet 13 and the second outlet 15 have the same shape, the airflow discharged to the subject can be controlled by the magnetic resonance imaging device 100, so that multiple outlets can provide a consistent blowing experience to the subject.

[0074] In addition, by using the magnetic resonance imaging device 100 to make the cross-sectional area of ​​the proximal distribution port 17A smaller than the cross-sectional area of ​​the distal distribution port 17B, it is possible to ensure that the airflow volume is consistent when the airflow reaches the first outlet 13 and the second outlet 15, and further achieve uniform and equal discharge of airflow to multiple outlets.

[0075] (Second Implementation)

[0076] The following is for reference Figure 5 The magnetic resonance imaging apparatus 200 according to the second embodiment of the present invention will be described. Figure 5 This is a perspective view showing the magnetic resonance imaging apparatus 200 according to the second embodiment of the present invention. In the following description, only the differences between the magnetic resonance imaging apparatus 200 of the second embodiment and the magnetic resonance imaging apparatus 100 of the first embodiment will be described, and the description of the similarities will be omitted.

[0077] The difference between the magnetic resonance imaging device 200 of the second embodiment and the magnetic resonance imaging device 100 of the first embodiment is that the outlet of the magnetic resonance imaging device 200 includes a first outlet 13, a second outlet 15, a third outlet 16, and a fourth outlet 19. The third outlet 16 and the fourth outlet 19 are arranged between the first outlet 13 and the second outlet 15 in the direction in which air is guided, and discharge air into the hole formed by the stand 2.

[0078] Therefore, by providing multiple outlets (first outlet 13, second outlet 15, third outlet 16, and fourth outlet 19) through the pipe 1, airflow can be discharged evenly and equally to more than three outlets with fewer component points and a compact structure.

[0079] (Third Implementation)

[0080] The following is for reference Figure 6 The magnetic resonance imaging apparatus 300 according to the third embodiment of the present invention will be described. Figure 6 This is a perspective view showing the magnetic resonance imaging apparatus 300 according to the third embodiment of the present invention. In the following description, only the differences between the magnetic resonance imaging apparatus 300 of the third embodiment and the magnetic resonance imaging apparatus 100 of the first embodiment will be described, and the description of the similarities will be omitted.

[0081] The difference between the magnetic resonance imaging apparatus 300 of the third embodiment and the magnetic resonance imaging apparatus 100 of the first embodiment is that the magnetic resonance imaging apparatus 300 is provided with a rotating member 20 whose orientation can be adjusted at each of the multiple exhaust ports. The rotating member 20 is, for example, a component with a joint rotation structure, and the orientation of the airflow discharged from each exhaust port can be adjusted by adjusting the orientation of the rotating member 20.

[0082] Therefore, by providing rotating members 20 with adjustable orientation at each of the multiple outlets of the magnetic resonance imaging device 300, the orientation of the airflow discharged from each outlet can be freely adjusted, providing a more comfortable blowing experience to the subject.

[0083] (Airflow distribution method)

[0084] The following is for reference Figure 7 The airflow distribution method of the present invention will be described. Figure 7 This is a flowchart illustrating the flow of the airflow distribution method of the present invention.

[0085] Furthermore, in the following description, the airflow distribution method is described as being applicable to a pipe 1 with n outlets, but it is not limited thereto. The airflow distribution method of the present invention can be applied to the magnetic resonance imaging device 100 of the first embodiment of the present invention, the magnetic resonance imaging device 200 of the second embodiment, and the magnetic resonance imaging device 300 of the third embodiment, and can also be applied to other medical imaging examination devices other than magnetic resonance imaging devices that have the function of discharging airflow to the subject.

[0086] In step S1, the structural parameters are determined.

[0087] In step S1, structural parameters include, for example, the location, opening shape, and cross-sectional area of ​​each of the multiple outlets of pipe 1.

[0088] Specifically, suppose that pipe 1 has n outlets, and suppose that the airflow path from the nearest outlet (near-end outlet, such as the first outlet 13) to the farthest outlet (far-end outlet, such as the second outlet 15) of pipe 1 is airflow path 1, airflow path 2, ... airflow path x, ... airflow path n. Let the flow rate of the airflow discharged from each outlet be Q. Then, the flow rates of the airflow discharged from each outlet from airflow path 1 to airflow path n are Q1, Q2, ..., Qx, ..., Qn.

[0089] At this point, as shown in equation (1), the structural parameters are designed with the goal of making the flow rates Q1, Q2, ..., Qx, ..., Qn of the airflow discharged from each outlet the same.

[0090] Q1 = Q2 = ... = Qx =... = Q n Equation (1)

[0091] Here, as shown in Equation (2), based on fluid dynamics theory, the flow rate Q of each discharge port depends on the cross-sectional area A of each discharge port and the pipeline pressure loss ΔP (i.e., pipeline resistance) in the branch 12.

[0092]

[0093] Thus, through Equation (2), Equation (1) can be transformed into the following Equation (3).

[0094]

[0095] Among them, A1 to A x are the cross-sectional areas of the discharge ports of the air flow paths 1 to air flow path n, and ΔP1 to ΔP n are the pipeline pressure losses at the cross-sectional areas of the discharge ports.

[0096] Next, the air flow paths 1, air flow path 2... air flow path x,... air flow path n of the air flow discharged from each discharge port are divided into three cases: the air flow path 1 of the air flow discharged from the proximal discharge port of the pipeline ①, the air flow path of the air flow discharged from the distal discharge port of the pipeline 1 is successively the air flow path n, and the air flow path x (1 < x < n) of the air flow discharged from the discharge port (intermediate discharge port, such as the third discharge port 16 or the fourth discharge port 19) between the nearest end and the farthest end of the pipeline 1. Structural parameters are determined for the three cases respectively.

[0097] In the air flow path 1 of the air flow discharged from the proximal discharge port of the pipeline 1, the air flow only passes through the baffle 18 and does not pass through the pipeline path of the long pipeline 1. Therefore, only as shown in Equation (4), based on fluid dynamics theory, considering the local pressure loss, the pipeline pressure loss ΔP1 is calculated.

[0098]

[0099] Here, ζ1 represents the local resistance coefficient of the discharge port of the nearest air flow path 1, and can be calculated using the following Table (1).

[0100] Table (1)

[0101]

[0102] Among them, A1' represents the cross-sectional area in front of the baffle 18 of the discharge port of the nearest air flow path 1, and A1 represents the cross-sectional area behind the baffle 18 of the first discharge port 13.

[0103] In addition, in Equation (4), ρ represents the density of the gas (kg / m3 V1 represents the velocity (m / s) of the airflow exiting from the outlet of the nearest airflow path 1.

[0104] Furthermore, the relationship between the velocity V1 of the airflow discharged from the outlet of the nearest airflow path 1 and the flow rate Q and cross-sectional area A of each outlet is V1 = #1 / A1.

[0105] Furthermore, in the airflow path n of the airflow discharged from the far end of pipe 1, the airflow passes through a relatively long section of pipe 1 with a uniform cross-section. Moreover, no baffle 18 is installed at the far end of the outlet of pipe 1. Therefore, it is only necessary to calculate the pipe pressure loss ΔP based on the fluid dynamics theory, as shown in equation (5). n .

[0106]

[0107] Here, λ represents the range drag coefficient. The range drag coefficient λ is obtained through... Calculate, where ε represents the surface roughness of the pipe path of pipe 1, and d f This represents the equivalent diameter of the pipeline path for pipe 1. Equivalent diameter d f pass Calculate, where A f The area (m²) of the cross-section of pipe path 1. 3 )χ f This represents the perimeter (m) of the cross-section of the pipeline path of pipe 1.

[0108] In addition, in equation (5), ρ represents the density of the gas constituting the airflow (kg / m³). 3 v2~v n v represents the airflow velocity (m / s) within airflow paths 2 to n. x = (n-x+1)Q n / A f l2 represents the path length (m) between the outlet of airflow path 2 and the outlet of airflow path 1. n The length (m) between the outlet of airflow path n and the outlet of airflow path n-1 is expressed as l. x This represents the path length (m) between the outlet of airflow path x and the outlet of airflow path x-1.

[0109] In addition, in the gas flow path x (1 < x < n) of the gas flow discharged from the middle discharge port of the pipe 1, the gas flow passes through a pipeline path of the pipe 1 with a uniform cross-section, and a baffle 18 is provided at the middle discharge port of the pipe 1. The gas flow also passes through the baffle 18. Therefore, as shown in Equation (6), based on the fluid dynamics theory, the extended pressure loss and the local pressure loss need to be considered to calculate the pipeline pressure loss ΔP. n .

[0110]

[0111] Here, the part of l2 to l in Equation (6) represents the extended pressure loss, and the last part represents the local pressure loss. In Equation (6), v n represents the flow velocity (m / s) of the gas flow in the gas flow path x, and v x =(n - x + 1)Q x / A n , l f represents the path length (m) between the discharge port of the gas flow path x and the discharge port of the gas flow path x - 1, and ζ x represents the local resistance coefficient of the discharge port of the gas flow path x, and can be calculated using the following Table (2). x

[0112] Table (2)

[0113]

[0114] Furthermore, by substituting Equation (4), Equation (5), and Equation (6) into Equation (3) respectively, the following Equation (7) can be obtained.

[0115]

[0116] Furthermore, by simplifying Equation (7), the following Equation (8) is obtained.

[0117]

[0118] As described above, in Equation (8) above, only the cross-sectional area A of each discharge port is unknown, and the other parameters are all preset in advance based on the materials of the magnetic resonance imaging device, the selection, the cross-sectional dimensions and length dimensions of the pipeline path of the pipe 1, etc., and are therefore all known.

[0119] Thus, the cross-sectional area A of each discharge port of the pipe 1 can be calculated through Equation (8).

[0120] In addition, by changing the height of the baffle plate 18, the cross-sectional area A of each discharge port can be adjusted so that the cross-sectional area A is consistent with the calculated cross-sectional area. Therefore, through the cross-sectional area A of each discharge port, the height h of the baffle plate 18 can be calculated by the following Equation (9).

[0121] h x =(H·B-( x Formula (9) / B

[0122] Where H represents the total height of all outlets and B represents the total width of all outlets.

[0123] Thus, the step of determining the structural parameters is complete. Next, proceed to step S2.

[0124] In step S2, digital modeling is performed based on the structural parameters. Specifically, for the initial design, the shape of the magnetic resonance imaging device based on the determined structural parameters is drawn using digital modeling methods. Then, the process proceeds to step S3.

[0125] In step S3, the digital model is analyzed to simulate the airflow state. This yields the airflow state based on determined structural parameters. Then, steps S41-S43 are performed.

[0126] In step S41, data analysis is performed to adjust the shape of each outlet. Specifically, based on the analyzed airflow state according to structural parameters, the shape of the first outlet 13 is adjusted to ensure that airflow is discharged evenly and in equal amounts from each outlet, according to the airflow distribution method described above. Then, the process proceeds to step S5.

[0127] In step S42, data analysis is performed to adjust the cross-sectional area of ​​each outlet. Specifically, based on the analyzed airflow state according to structural parameters, the cross-sectional area of ​​each outlet is adjusted to ensure that airflow is discharged uniformly and equally from each outlet, based on the aforementioned airflow distribution method. Next, the process proceeds to step S5.

[0128] In step S43, data analysis is performed to adjust the cross-sectional area of ​​pipe 1. Specifically, based on the analyzed airflow blowing state based on structural parameters, the cross-sectional area of ​​pipe 1 is adjusted to ensure that airflow is discharged evenly and in equal amounts from each outlet, according to the aforementioned airflow distribution method. Next, the process proceeds to step S5.

[0129] In step S5, the model undergoes secondary analysis to adjust the parts sensitive to airflow. Specifically, the digital model after adjusting the shape and cross-sectional area of ​​each outlet and the cross-sectional area of ​​pipe 1 is analyzed again to adjust the parts sensitive to airflow, ensuring that airflow is discharged evenly and in equal amounts from each outlet. Then, proceed to step S6.

[0130] In step S6, experimental verification is conducted. Specifically, based on the above parameters such as material, selection, shape, and structural parameters, a prototype is constructed, and the actual effect of the exhaust airflow is verified through experiments. Then, the process ends.

[0131] Therefore, the airflow distribution method of the present invention can be used to design the structural parameters such as the position, opening shape and cross-sectional area of ​​the outlet in the pipeline of the magnetic resonance imaging device, so as to enable the airflow to be discharged uniformly and equally from each outlet.

[0132] Furthermore, using the airflow distribution method of the present invention, the airflow path 1 of the airflow discharged from the near-end outlet of pipe 1, the airflow path n of the airflow discharged from the far-end outlet of pipe 1, and the airflow path x(1) of the airflow discharged from the intermediate outlet between the nearest and farthest ends of pipe 1 are respectively airflow path n.

Claims

1. A magnetic resonance imaging device, characterized in that, have: Magnets generate magnetic fields; A stand, storing the magnet; and A pipe, installed on the platform, discharges air into an opening formed by the platform. The pipeline has the following features: The first guide section guides the inhaled airflow; A branch section that branches the airflow guided by the first guide section; The first outlet discharges air into the hole, which is branched into a first direction by the branch section; The second guide section is located downstream of the first outlet and guides the air branched into a second direction by the branch section. as well as The second outlet discharges air guided by the second guide into the hole.

2. The magnetic resonance imaging device according to claim 1, characterized in that, The curvature of the branch is different from the curvature of the second guide portion.

3. The magnetic resonance imaging device according to claim 1, characterized in that, The branch distributes the intake airflow to the first direction and the second direction with equal flow rates.

4. The magnetic resonance imaging device according to claim 1, characterized in that, The pipe has a third outlet, which is positioned between the first outlet and the second outlet in the direction in which the air is guided, and discharges air guided by the second guide into the hole.

5. The magnetic resonance imaging device according to claim 1, characterized in that, The cross-sectional area of ​​the first outlet is smaller than that of the second outlet.

6. The magnetic resonance imaging device according to claim 1, characterized in that: The second guide portion is formed into a smooth arc shape that matches the shape of the stand.

7. The magnetic resonance imaging device according to claim 1, characterized in that: The orientation of the first outlet and the second outlet can be changed.

8. The magnetic resonance imaging device according to claim 7, characterized in that: Rotating components capable of adjusting the orientation of the first and second outlets are respectively provided at the first outlet and the second outlet.

9. An airflow distribution method, characterized in that, Includes the following steps: Determine the structural parameters based on the shape and structure of the platform; Determine the number of exhaust outlets and the length of the airflow path; The cross-sectional area and pipeline pressure loss of each of the outlets are determined in such a way that the flow rates of the airflow discharged from each of the outlets are equal. The outlets include a near-end outlet located at the nearest end of the main pipeline, a far-end outlet located at the farthest end of the main pipeline and disposed at the end of the pipeline, and one or more intermediate outlets located between the nearest end and the farthest end of the main pipeline. Calculate the cross-sectional area of ​​each of the discharge outlets.

10. The airflow distribution method according to claim 9, characterized in that, The pipeline pressure loss at the near-end outlet includes local pressure loss. The pipeline pressure loss at the distal outlet includes pressure loss over distance. The pipeline pressure loss at the intermediate outlet includes the local pressure loss and the extended pressure loss.

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