Cooling structure and magnetic resonance system

Abstract

The application relates to a cooling structure and a magnetic resonance system. The cooling structure comprises a cooling channel for thermal coupling with a gradient coil and an electrically conductive shielding unit covering the outer circumferential surface of the cooling channel, the electrically conductive shielding unit being used for generating a shielding magnetic field under the action of a radio frequency field of a radio frequency coil; the electrically conductive shielding unit has at least one disconnection area. The electrically conductive shielding unit generates a shielding magnetic field under the action of the radio frequency field, inhibits the radio frequency field from transmitting energy to a cooling medium in the external cooling channel, so that the cooling medium cannot be excited, the possibility of interaction between the radio frequency field and the cooling medium is reduced, the uniformity of the radio frequency field is maintained, hydrogen atomic nuclei in a diagnostic object body are stably excited and uniform magnetic resonance signals are generated, and the possibility of abnormal signals and image artifacts is reduced. The disconnection area blocks the generation of a current loop, avoids the generation of an additional magnetic field by the current loop, and causes interference to the radio frequency field and a gradient field, thereby guaranteeing image quality, guaranteeing the accuracy and reliability of clinical diagnosis.

Description

Technical Field

[0001] This application relates to the field of magnetic resonance technology, and in particular to cooling structures and magnetic resonance systems. Background Technology

[0002] Magnetic resonance imaging (MRI) devices are widely used in medical diagnostics. Their basic principle involves using a main magnet to generate a uniform, strong magnetic field. With the assistance of a gradient coil generating a specific gradient field, hydrogen atoms within the patient's body are polarized. Then, a radio frequency (RF) coil emits radio pulses to excite the hydrogen nuclei, causing nuclear resonance and energy absorption. After the RF pulses cease, the hydrogen nuclei emit radio signals at a specific frequency, releasing the absorbed energy. This released signal is captured by an external receiver and processed by a computer to obtain an image.

[0003] Because multiple coil components generate a lot of heat during operation, especially the gradient coil, a cooling medium is typically introduced to cool the gradient coil in order to ensure image quality and user experience.

[0004] Because the cooling medium has a certain degree of conductivity, it will interact with the magnetic resonance system, causing abnormalities in the magnetic resonance signal. These abnormal signals will result in artifacts in the final image, affecting the accuracy and reliability of clinical diagnosis. Utility Model Content

[0005] Therefore, it is necessary to provide a cooling structure and magnetic resonance system to address the artifact problem in existing magnetic resonance images.

[0006] A cooling structure is applied to a magnetic resonance system, the magnetic resonance system including a gradient coil and a radio frequency coil disposed inside the gradient coil, the cooling structure comprising:

[0007] Cooling channels are used for thermal coupling with the gradient coil;

[0008] A conductive shielding unit covers the outer peripheral surface of the cooling channel; the conductive shielding unit is used to generate a shielding magnetic field under the action of the radio frequency field of the radio frequency coil; wherein, the conductive shielding unit has at least one disconnection region.

[0009] In one embodiment, the conductive shielding unit includes a first conductive layer and a second conductive layer, with the disconnection region between the first conductive layer and the second conductive layer.

[0010] In one embodiment, a portion of the second conductive layer is radially spaced from the first conductive layer along the cooling channel;

[0011] A first insulating layer is disposed between the second conductive layer and the first conductive layer.

[0012] In one embodiment, the second conductive layer includes a first diameter segment and a second diameter segment, wherein the inner diameter of the first diameter segment is larger than the inner diameter of the second diameter segment;

[0013] The first diameter segment and the first conductive layer are arranged radially apart along the cooling channel;

[0014] The second diameter segment and the first conductive layer are spaced apart along the flow direction of the cooling medium.

[0015] In one embodiment, the first conductive layer and the second conductive layer are spaced apart along the flow direction of the cooling medium;

[0016] The conductive shielding unit further includes a third conductive layer, a portion of which is disposed around the outside of the first conductive layer, and another portion of which is disposed around the outside of the second conductive layer.

[0017] In one embodiment, the conductive shielding unit further includes a second insulating layer, a first portion of which is located between the first conductive layer and the third conductive layer, and a second portion of which is located between the second conductive layer and the third conductive layer.

[0018] In one embodiment, the cooling inlet and the cooling outlet of the cooling channel are spaced apart.

[0019] In one embodiment, the cooling structure is spirally connected to the inner wall of the gradient coil.

[0020] In one embodiment, the cooling structure further includes a fixed cylinder, and the cooling channel is connected to the outside of the fixed cylinder.

[0021] A cooling structure is applied to a magnetic resonance system, the magnetic resonance system including gradient coils, the cooling structure comprising:

[0022] A non-metallic tube, including a nylon tube or a PU tube, wherein the nylon tube or PU tube extends along a set direction and forms a cooling channel for thermal coupling with the gradient coil;

[0023] A conductive material is applied to the outer circumferential surface of the nylon tube or PU tube. The conductive material has at least one break zone along the predetermined direction. The conductive material is a non-ferromagnetic conductive material.

[0024] In one embodiment, the non-ferromagnetic conductive material forms at least two conductive layers along the predetermined direction, the two conductive layers have a partially overlapping region, and an insulating layer is disposed between the overlapping regions of the two conductive layers.

[0025] A magnetic resonance system, comprising:

[0026] Gradient coils are used to generate gradient fields;

[0027] A radio frequency coil, disposed inside the gradient coil, is used to transmit radio frequency pulses; and

[0028] The cooling structure includes a cooling channel and a conductive shielding unit, wherein the cooling channel is used for thermal coupling with the gradient coil;

[0029] The conductive shielding unit covers the outer peripheral surface of the cooling channel; the conductive shielding unit can generate a shielding magnetic field under the action of the radio frequency field of the radio frequency coil; wherein, the conductive shielding unit is intermittently provided with multiple conductive layers along the extension direction of the cooling channel.

[0030] The aforementioned cooling structure and magnetic resonance system, due to the alternating electromagnetic field of the radio frequency (RF) field, will generate an induced electromotive force (EMF) in the conductive shielding unit under the influence of the RF field, according to the principle of electromagnetic induction. This EMF will then form an induced current. According to Lenz's law, this induced current will generate a shielding magnetic field to resist changes in the RF field's magnetic flux, thereby suppressing the transfer of energy from the RF field to the cooling medium in the external cooling channel. This prevents the cooling medium from being excited, reduces the possibility of interaction between the RF field and the cooling medium, maintains the uniformity of the RF field, and ensures that the hydrogen nuclei in the patient are stably excited to generate a uniform magnetic resonance signal, reducing the possibility of abnormal signals and image artifacts. Simultaneously, because the conductive shielding unit has a disconnect region (i.e., it is not a closed structure), it can block the generation of current loops, preventing the current loops from generating additional magnetic fields that could interfere with the RF field and gradient field. This ensures the uniformity and stability of the magnetic field, thereby guaranteeing image quality and ensuring the accuracy and reliability of clinical diagnosis. Attached Figure Description

[0031] To more clearly illustrate the technical solutions in the embodiments or exemplary embodiments of this application, the drawings used in the description of the embodiments or exemplary embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0032] Figure 1 This is a schematic diagram of a cooling structure provided in an embodiment of this application applied to a magnetic resonance system.

[0033] Figure 2 for Figure 1 A three-dimensional schematic diagram of the cooling structure shown.

[0034] Figure 3This is a longitudinal cross-sectional view of a cooling structure provided in an embodiment of this application.

[0035] Figure 4 A longitudinal cross-sectional view of a cooling structure provided in another embodiment of this application.

[0036] Figure 5 This is a cross-sectional view of a cooling structure provided in an embodiment of this application.

[0037] Reference numerals: 100, Cooling structure; 110, Cooling channel; 111, Cooling inlet; 112, Cooling outlet; 120, Conductive shielding unit; 121, First conductive layer; 122, Second conductive layer; 1221, First diameter segment; 1222, Second diameter segment; 123, Disconnection zone; 124, First insulating layer; 125, Third conductive layer; 126, Second insulating layer; 130, Insulating unit; 140, Fixing cylinder; 200, Gradient coil; 300, Radio frequency coil. Detailed Implementation

[0038] To make the above-mentioned objectives, features, and advantages of this application more apparent and understandable, the specific embodiments of this application are described in detail below with reference to the accompanying drawings. Many specific details are set forth in the following description to provide a thorough understanding of this application. However, this application can be implemented in many other ways different from those described herein, and those skilled in the art can make similar modifications without departing from the spirit of this application. Therefore, this application is not limited to the specific embodiments disclosed below.

[0039] In the description of this application, it should be understood that if terms such as "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential" appear, these terms indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this application.

[0040] Furthermore, where the terms "first" and "second" appear, these terms are for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined with "first" or "second" may explicitly or implicitly include at least one of that feature. In the description of this application, where the term "multiple" appears, "multiple" means at least two, such as two, three, etc., unless otherwise explicitly specified.

[0041] In this application, unless otherwise expressly specified and limited, the terms "installation," "connection," "joining," and "fixing," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components, unless otherwise expressly limited. Those skilled in the art can understand the specific meaning of the above terms in this application based on the specific circumstances.

[0042] In this application, unless otherwise expressly specified and limited, the use of descriptions such as "above" or "below" the second feature indicates that the first and second features are in direct contact or indirect contact via an intermediate medium. Furthermore, "above," "on top of," and "over" the second feature can mean that the first feature is directly above or diagonally above the second feature, or simply that the first feature is at a higher horizontal level than the second feature. Similarly, "below," "below," and "under" the second feature can mean that the first feature is directly below or diagonally below the second feature, or simply that the first feature is at a lower horizontal level than the second feature.

[0043] It should be noted that if an element is referred to as being "fixed to" or "set on" another element, it can be directly on the other element or there may be an intervening element. If an element is considered to be "connected to" another element, it can be directly connected to the other element or there may be an intervening element. If so, the terms "vertical," "horizontal," "upper," "lower," "left," "right," and similar expressions used in this application are for illustrative purposes only and do not represent the only possible implementation.

[0044] As mentioned in the background section, components primarily composed of gradient coils generate significant heat during operation. To prevent this heat from affecting the performance of the gradient coils, ensuring image quality, and extending the lifespan of components such as gradient coils, a cooling medium is needed to cool the gradient coils. The inventors of this application discovered that, due to the conductivity of the cooling medium and the alternating magnetic field of the radio frequency (RF) field, the magnetic field strength and direction change continuously over time. According to the law of electromagnetic induction, the cooling medium generates an induced electromotive force under the influence of the alternating magnetic field, thus forming a current. This current generates its own electromagnetic field, which superimposes on the original RF field, interfering with and affecting the uniformity of the RF field. This leads to abnormalities in the magnetic resonance signal excited by the RF field, such as signal attenuation or localized signal enhancement. During subsequent image processing, these abnormal signals cause artifacts in the presented image, interfering with the doctor's accurate interpretation of the image and affecting the accuracy and reliability of clinical diagnosis.

[0045] Based on this, one embodiment of this application provides a cooling structure applied to a magnetic resonance system. This structure can suppress the interaction between the radio frequency field and the cooling medium, and while maintaining the cooling effect of the cooling medium, significantly reduce the impact of artifacts on the image, thereby improving the imaging quality of the magnetic resonance system. The cooling structure provided in one embodiment of this application will now be described in detail with reference to the accompanying drawings.

[0046] See Figures 1 to 4 As shown, a cooling structure 100 provided in one embodiment of this application is applied to a magnetic resonance system. The magnetic resonance system includes a gradient coil 200 and a radio frequency coil 300 disposed inside the gradient coil 200. The cooling structure 100 includes a cooling channel 110 for thermal coupling with the gradient coil 200 and a conductive shielding unit 120 covering the outer peripheral surface of the cooling channel 110. The conductive shielding unit 120 is used to generate a shielding magnetic field under the action of the radio frequency field of the radio frequency coil 300. The conductive shielding unit 120 has at least one disconnection region 123.

[0047] As mentioned earlier, since the radio frequency (RF) field is an alternating electromagnetic field, the conductive shielding unit 120 will generate an induced electromotive force under the action of the RF field, thereby forming an induced current. According to Lenz's law, this induced current will generate a shielding magnetic field to resist the change in the magnetic flux of the RF field, thus suppressing the transfer of energy from the RF field to the cooling medium in the external cooling channel 110. This prevents the cooling medium from being excited, reduces the possibility of interaction between the RF field and the cooling medium, maintains the uniformity of the RF field, and allows the hydrogen nuclei in the diagnostic subject to be stably excited and generate a uniform magnetic resonance signal, reducing the possibility of abnormal signals and image artifacts. At the same time, since the conductive shielding unit 120 has a disconnection region 123, that is, the conductive shielding unit 120 is not a closed structure, it can block the generation of current loops, avoid the current loops generating additional magnetic fields that would interfere with the RF field and gradient field, ensure the uniformity and stability of the magnetic field, and thus ensure image quality, ensuring the accuracy and reliability of clinical diagnosis. Compared with directly setting magnetic components to interfere with the imaging magnetic field, setting the conductive shielding unit 120 can avoid introducing additional magnetic field interference, ensure the uniformity of the imaging magnetic field, and thus ensure image quality.

[0048] The cooling structure 100 effectively dissipates heat from the gradient coil 200, enabling it to maintain stable performance. The gradient magnetic field it generates meets imaging requirements in terms of intensity, direction, and uniformity, avoiding gradient magnetic field fluctuations caused by temperature changes. This reduces problems such as image artifacts, inaccurate spatial positioning, and reduced resolution during imaging, resulting in more stable and reliable magnetic resonance images each time they are acquired, which is more conducive to doctors making accurate clinical diagnoses.

[0049] In some embodiments, the cooling channel 110 can be a circular tubular structure. In other embodiments, the cooling channel 110 can also be a flat tubular structure with a rectangular cross-section or other cross-sectional shapes. In some embodiments, the cooling channel 110 is made of a non-metallic material, which is less likely to interfere with the imaging magnetic field. In some embodiments, the cooling channel 110 can be made of polyamide (PA), which has high local tensile strength, good wear resistance, and good toughness. In some embodiments, the cooling channel 110 can be made of polyurethane (PU), which has good wear resistance and flexibility. In some embodiments, the cooling medium can be a liquid with good flowability, such as water.

[0050] See Figure 3 or Figure 4 As shown, in one embodiment, the conductive shielding unit 120 includes a first conductive layer 121 and a second conductive layer 122, with a disconnection region 123 between the first conductive layer 121 and the second conductive layer 122. By providing the disconnection region 123 between the first conductive layer 121 and the second conductive layer 122, at least two regions of the conductive shielding unit 120 are physically disconnected, thereby preventing the formation of a current loop during the operation of the gradient coil 200 and thus avoiding the generation of additional magnetic field interference. At the same time, the first conductive layer 121 and the second conductive layer 122 can also form the aforementioned shielding magnetic field to suppress the interaction between the cooling medium and the radio frequency field, ensuring image quality.

[0051] See Figure 3 As shown, in one embodiment, a portion of the second conductive layer 122 is radially spaced from the first conductive layer 121 along the cooling channel 110; a first insulating layer 124 is disposed between the second conductive layer 122 and the first conductive layer 121. For example, in the embodiment shown in the figures, with reference to the flow direction of the cooling medium, the first end of the second conductive layer 122 is located outside the first conductive layer 121, and the two have an overlapping area. This arrangement ensures that the area where the conductive shielding unit 120 is disposed can completely cover the cooling channel 110, avoiding the possibility of interaction between the cooling medium and the radio frequency field in the uncovered area. The portion of the second conductive layer 122 near its head is spaced apart from the head of the first conductive layer 121, forming a disconnection region 123. A first insulating layer 124 is also provided between the head of the first conductive layer 121 and the head of the second conductive layer 122 to prevent the head of the first conductive layer 121 from being electrically connected to the head of the second conductive layer 122. This prevents the first conductive layer 121 and the second conductive layer 122 from forming a current loop, thus avoiding the generation of an additional magnetic field that could interfere with the radio frequency field and gradient field. This ensures the uniformity and stability of the magnetic field, thereby guaranteeing image quality and ensuring the accuracy and reliability of clinical diagnosis.

[0052] See Figure 3As shown, in one embodiment, the second conductive layer 122 includes a first diameter segment 1221 and a second diameter segment 1222. The inner diameter of the first diameter segment 1221 is larger than the inner diameter of the second diameter segment 1222. The first diameter segment 1221 and the first conductive layer 121 are radially spaced apart along the cooling channel 110; the second diameter segment 1222 and the first conductive layer 121 are spaced apart along the flow direction of the cooling medium. That is, the second conductive layer 122 can be a variable diameter structure, allowing the first end of the second conductive layer 122 to be fitted over the outside of the first insulating layer 124 and the first conductive layer 121 through the first diameter segment 1221. In other embodiments, the second conductive layer 122 may not have a variable diameter structure. Since the size of the cooling channel 110 is small, reaching the millimeter level, the second conductive layer 122 can be fitted over the outside of the first conductive layer 121 through its own slight deformation.

[0053] See Figure 3 As shown, in one embodiment, the first conductive layer 121 and the second conductive layer 122 are spaced apart along the flow direction of the cooling medium; correspondingly, the conductive shielding unit 120 also includes a third conductive layer 125, a portion of which is disposed around the outside of the first conductive layer 121, and another portion of which is disposed around the outside of the second conductive layer 122.

[0054] By setting a third conductive layer 125, the conductive shielding unit 120 completely covers the outer periphery of the cooling channel 110, avoiding the possibility of interaction between the cooling medium and the radio frequency field in the uncovered area. The first conductive layer 121 and the second conductive layer 122 are spaced apart along the flow direction of the cooling medium, thereby forming a break zone 123 at the interval. This prevents the formation of a current loop under the action of the gradient coil 200, avoiding the generation of an additional magnetic field that could interfere with the radio frequency field and gradient field, ensuring the uniformity and stability of the magnetic field, and thus guaranteeing image quality and the accuracy and reliability of clinical diagnosis.

[0055] See Figure 3 As shown, in one embodiment, the conductive shielding unit 120 further includes a second insulating layer 126. A first portion of the second insulating layer 126 is located between the first conductive layer 121 and the third conductive layer 125, and a second portion of the second insulating layer 126 is located between the second conductive layer 122 and the third conductive layer 125. The third insulating layer isolates the first conductive layer 121 and the second conductive layer 122 from the third insulating layer, preventing the formation of current loops under the action of the gradient coil 200. This prevents the current loops from generating additional magnetic fields that could interfere with the radio frequency field and gradient field, ensuring the uniformity and stability of the magnetic field, thereby guaranteeing image quality and the accuracy and reliability of clinical diagnosis.

[0056] Understandably, the first conductive layer 121 and the second conductive layer 122 can be located in the middle region of the conductive shielding unit 120 or in the end region of the conductive shielding unit 120. As long as they can achieve the effect of disconnecting the interface, the specific location is not limited.

[0057] In some embodiments, the aforementioned first conductive layer 121, second conductive layer 122, and third conductive layer 125 can be made of non-ferromagnetic conductive materials, such as metals like copper (Cu), aluminum (Al), zinc (Zn), lead (Pb), and tin (Sn), or non-ferromagnetic alloys, such as nickel-chromium alloys, copper alloys, and aluminum alloys. The conductive shielding unit, made of non-ferromagnetic conductive materials, does not introduce additional magnetic field interference, achieving good electromagnetic shielding while maintaining the uniformity and stability of the magnetic field in the magnetic resonance system, ensuring high-quality imaging. In some embodiments, the aforementioned first insulating layer 124 and second insulating layer 126 can be made of polytetrafluoroethylene, polyimide, silicone rubber, etc.

[0058] In addition to setting a disconnection zone 123 in the middle or end region of the conductive shielding unit 120 to avoid current loops, spatial isolation or insulation isolation can also be provided in the cooling inlet 111 and cooling outlet 112 of the cooling channel 110.

[0059] See Figure 2 As shown, in one embodiment, the cooling inlet 111 and the cooling outlet 112 of the cooling channel 110 are spaced apart. For example, in the embodiment shown in the attached figure, the left end of the cooling channel 110 is the cooling inlet 111, and the right end of the cooling channel 110 is the cooling outlet 112. Of course, the cooling inlet 111 and the cooling outlet 112 can also be interchanged, that is, the right end of the cooling channel 110 is the cooling inlet 111, and the left end of the cooling channel 110 is the cooling outlet 112.

[0060] Since the cooling inlet 111 and the cooling outlet 112 are separated, the beginning and end of the conductive shielding unit 120 covering the outside of the cooling channel 110 are spatially isolated, that is, a disconnection zone is formed between the beginning and end of the conductive shielding unit 120, thereby avoiding the possibility of generating an additional magnetic field due to the current loop, thus maintaining the uniformity and stability of the radio frequency field and gradient field, and ensuring that the imaging quality is not interfered with by the current loop.

[0061] See Figure 2As shown, in one embodiment, the cooling structure 100 is spiral-shaped and connected to the inner wall of the gradient coil 200. That is, the cooling channel 110 and the conductive shielding unit 120 can be spiral tubular structures. Spiraling the cooling channel 110 to the inner wall of the gradient coil 200 not only ensures a tight fit between the two but also increases the contact area between the cooling channel 110 and the RF coil 300, allowing the cooling medium to more fully absorb the heat generated by the RF coil 300 and improving heat dissipation efficiency. Simultaneously, the spirally arranged cooling pipes can be more evenly distributed inside the gradient coil 200, avoiding localized overheating and ensuring the performance and lifespan of the gradient coil 200. Furthermore, the spirally arranged cooling pipes can utilize space more effectively, avoiding excessive space occupation.

[0062] In other embodiments, the cooling structure 100 may also be U-shaped and connected to the inner wall of the gradient coil 200. For example, the cooling structure 100 includes two parallel segments and one arc segment. The two parallel segments may extend along different parts of the inner wall of the gradient coil, while the arc segment may fit at the corresponding corner, thereby achieving effective coverage of a specific area and facilitating the more uniform flow of the cooling medium within it, ensuring balanced heat dissipation.

[0063] In other embodiments, the cooling structure 100 may also be fingerprint-shaped, with many curved, swirling and interconnected fine textures, which can increase the contact area between the cooling structure 100 and the inner wall of the gradient coil 200, so that there are more contact points and contact areas between the cooling structure 100 and the inner wall of the gradient coil 200, better conforming to the shape changes of the inner wall of the gradient coil 200, thereby improving heat dissipation efficiency and more comprehensively removing the heat generated by the gradient coil.

[0064] like Figure 2 As shown, in one embodiment, the cooling structure 100 further includes a fixing cylinder 140, and the cooling channel 110 is connected to the outside of the fixing cylinder 140. Since the cooling channel 110 is generally a long and thin tubular structure, by setting the fixing cylinder 140 to fix the cooling channel 110, the cooling channel 110 is limited between the fixing cylinder 140 and the gradient coil 200, ensuring the reliability of the fixing of the cooling channel 110, and thus ensuring the reliability of its cooling performance.

[0065] In some embodiments, the influence on the imaging magnetic field can be improved by selecting a cooling medium with low conductivity. Low-conductivity cooling media have relatively few internal free charges, resulting in a weaker ability to generate current based on electromagnetic induction when facing the alternating magnetic field of the radio frequency field. This reduces the interaction between the cooling medium and the radio frequency field caused by secondary electromagnetic fields generated by the current.

[0066] In some embodiments, the influence on the imaging magnetic field can be improved by selecting a cooling medium with low magnetic susceptibility, such as heavy water, so that the resonant frequency of the cooling medium is different from the resonant frequency of water in the human body. Cooling media with low magnetic susceptibility are less susceptible to external magnetic fields and do not generate their own additional magnetic fields, nor do they interfere with the original magnetic field distribution of the radio frequency field. This avoids the interaction between the cooling medium and the radio frequency field due to the cooling medium's own magnetism, ensuring that the radio frequency field can operate in a relatively stable and interference-free environment.

[0067] In some embodiments, an insulating unit 130 may also be provided between the cooling channel 110 and the conductive shielding unit 120 to insulate and isolate the cooling channel 110 and the conductive shielding unit 120, thereby preventing the formation of a current loop between the cooling channel 110 and the conductive shielding unit 120.

[0068] The aforementioned cooling structure 100, through the conductive shielding unit 120, generates an induced electromotive force under the action of the radio frequency field, thereby forming an induced current and generating a shielding magnetic field to resist changes in the magnetic flux of the radio frequency field. This suppresses the transfer of energy from the radio frequency field to the cooling medium within the external cooling channel 110, preventing the cooling medium from being excited. This reduces the possibility of interaction between the radio frequency field and the cooling medium, maintains the uniformity of the radio frequency field, and allows the hydrogen nuclei in the diagnostic subject to be stably excited, generating a uniform magnetic resonance signal, reducing the possibility of abnormal signals and image artifacts. Simultaneously, because the conductive shielding unit 120 has a disconnection region 123, meaning it is not a closed structure, it can block the generation of current loops, preventing the current loops from generating additional magnetic fields that could interfere with the radio frequency field and gradient field. This ensures the uniformity and stability of the magnetic field, thereby guaranteeing image quality and the accuracy and reliability of clinical diagnosis. Compared to directly setting magnetic components to interfere with the imaging magnetic field, using the conductive shielding unit 120 avoids introducing additional magnetic field interference, ensuring the uniformity of the imaging magnetic field and thus guaranteeing image quality.

[0069] One embodiment of this application also provides a cooling structure 100 applied to a magnetic resonance system. The magnetic resonance system includes a gradient coil 200. The cooling structure 100 includes a non-metallic tube and a conductive material. The non-metallic tube includes a nylon tube or a PU tube, which extends along a predetermined direction and forms a cooling channel 110. The nylon tube or PU tube is used for thermal coupling with the gradient coil 200. The conductive material covers the outer peripheral surface of the nylon tube or PU tube and has at least one break region 123 along the predetermined direction. The conductive material is a non-ferromagnetic conductive material.

[0070] In this way, the non-ferromagnetic conductive material can generate a shielding magnetic field, reducing the possibility of interaction between the cooling medium and the radio frequency field within the cooling channel 110. This allows the cooling structure 100 to effectively dissipate heat from the gradient coil 200, helping it maintain stable performance and preventing gradient magnetic field fluctuations caused by temperature changes. Consequently, it reduces problems such as image artifacts, inaccurate spatial positioning, and reduced resolution during imaging. The nylon or PU tube is a non-metallic material, making it less likely to interfere with the imaging magnetic field. Furthermore, because the non-ferromagnetic conductive material has an open region 123 (i.e., it is not a closed structure), it can block the generation of current loops, preventing the current loops from generating additional magnetic fields that could interfere with the gradient field. This ensures the uniformity and stability of the magnetic field, thereby guaranteeing image quality and the accuracy and reliability of clinical diagnosis.

[0071] In one embodiment, a non-ferromagnetic conductive material forms at least two conductive layers along a predetermined direction, the two conductive layers have a partially overlapping region, and an insulating layer is disposed between the overlapping regions of the two conductive layers.

[0072] Because the two conductive layers partially overlap, the area where the non-ferromagnetic conductive material is placed can completely cover the cooling channel 110, reducing the possibility of interaction between the cooling medium and the radio frequency field. An insulating layer is also placed between the overlapping areas of the two conductive layers to reduce the possibility of electrical connection between them, thus preventing the formation of current loops. This avoids the generation of additional magnetic fields by current loops that could interfere with the gradient field, ensuring the uniformity and stability of the magnetic field, thereby guaranteeing image quality and ensuring the accuracy and reliability of clinical diagnosis.

[0073] Furthermore, such as Figure 1 As shown, one embodiment of this application also provides a magnetic resonance system, including a gradient coil 200, a radio frequency coil 300, and a cooling structure 100. The gradient coil 200 is used to generate a gradient field to encode spatial positions, facilitating precise location of the specific part of the human tissue that generates magnetic resonance signals. It also helps to improve the uniformity of the magnetic field and assists in the execution of different imaging sequences to obtain high-quality images. The radio frequency coil 300 is disposed inside the gradient coil 200 and is used to emit radio frequency pulses to excite the atomic nuclei in the human tissue to generate magnetic resonance phenomena. The cooling structure 100 includes a cooling channel 110 and a conductive shielding unit 120. The cooling channel 110 is used for thermal coupling with the gradient coil 200. The conductive shielding unit 120 covers the outer peripheral surface of the cooling channel 110. The conductive shielding unit 120 can generate a shielding magnetic field under the action of the radio frequency field of the radio frequency coil 300. The conductive shielding unit 120 is provided with multiple conductive layers intermittently along the extension direction of the cooling channel 110.

[0074] Understandably, this magnetic resonance system also includes a superconducting magnet to generate a main magnetic field, causing atomic nuclei, such as hydrogen nuclei, within human tissue to align in a specific direction, creating conditions for subsequent magnetic resonance phenomena. In some embodiments, the radio frequency coil, gradient coil, and superconducting magnet can all be toroidal cylindrical structures, and the three are essentially coaxial. Specifically: the radio frequency coil is the innermost layer, the gradient coil is the outermost layer, and the superconducting magnet is the outermost layer. The cavity inside the radio frequency coil is the detection space, i.e., the patient channel.

[0075] The cooling structure can be any of the cooling structures mentioned in the above embodiments, and will not be described again here. Because this magnetic resonance system includes the aforementioned cooling structure, it can significantly reduce the impact of artifacts on the image without affecting the cooling effect, thereby improving the imaging quality of the magnetic resonance system.

[0076] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0077] The above embodiments merely illustrate several implementation methods of this application, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the patent application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this patent application should be determined by the appended claims.

Claims

1. A cooling structure applied to a magnetic resonance system, the magnetic resonance system comprising a gradient coil (200) and a radio frequency coil (300) disposed inside the gradient coil (200), characterized in that, The cooling structure includes: Cooling channel (110) for thermal coupling with the gradient coil (200); A conductive shielding unit (120) covers the outer peripheral surface of the cooling channel (110); the conductive shielding unit (120) is used to generate a shielding magnetic field under the action of the radio frequency field of the radio frequency coil (300); wherein the conductive shielding unit (120) has at least one disconnection region (123).

2. The cooling structure according to claim 1, characterized in that, The conductive shielding unit (120) includes a first conductive layer (121) and a second conductive layer (122), and there is a disconnection region (123) between the first conductive layer (121) and the second conductive layer (122).

3. The cooling structure according to claim 2, characterized in that, A portion of the second conductive layer (122) is disposed radially from the first conductive layer (121) along the cooling channel (110); A first insulating layer (124) is provided between the second conductive layer (122) and the first conductive layer (121).

4. The cooling structure according to claim 3, characterized in that, The second conductive layer (122) includes a first diameter segment (1221) and a second diameter segment (1222), wherein the inner diameter of the first diameter segment (1221) is larger than the inner diameter of the second diameter segment (1222); The first radial segment (1221) and the first conductive layer (121) are arranged radially apart along the cooling channel (110); The second diameter segment (1222) and the first conductive layer (121) are spaced apart along the flow direction of the cooling medium.

5. The cooling structure according to claim 2, characterized in that, The first conductive layer (121) and the second conductive layer (122) are spaced apart along the flow direction of the cooling medium; The conductive shielding unit (120) further includes a third conductive layer (125), a portion of which is disposed around the outside of the first conductive layer (121), and another portion of which is disposed around the outside of the second conductive layer (122).

6. The cooling structure according to claim 5, characterized in that, The conductive shielding unit (120) further includes a second insulating layer (126), a first portion of which is located between the first conductive layer (121) and the third conductive layer (125), and a second portion of which is located between the second conductive layer (122) and the third conductive layer (125).

7. The cooling structure according to any one of claims 1 to 5, characterized in that, The cooling structure also includes a fixed cylinder (140), and the cooling channel (110) is connected to the outside of the fixed cylinder (140).

8. A cooling structure for use in a magnetic resonance system, the magnetic resonance system comprising gradient coils (200), characterized in that, The cooling structure includes: The non-metallic tube, including nylon tube or PU tube, extends along a set direction and forms a cooling channel (110) for thermal coupling with the gradient coil (200); A conductive material is applied to the outer periphery of the nylon tube or PU tube. The conductive material has at least one break zone (123) along the set direction. The conductive material is a non-ferromagnetic conductive material.

9. The cooling structure according to claim 8, characterized in that, The non-ferromagnetic conductive material forms at least two conductive layers along the predetermined direction, with the two conductive layers having a partial overlap area, and an insulating layer is disposed between the overlap areas of the two conductive layers.

10. A magnetic resonance system, characterized in that, include: Gradient coil (200) is used to generate a gradient field; A radio frequency coil (300), disposed inside the gradient coil (200), is used to transmit radio frequency pulses; and, The cooling structure includes a cooling channel (110) and a conductive shielding unit (120), wherein the cooling channel (110) is used for thermal coupling with the gradient coil (200); The conductive shielding unit (120) covers the outer peripheral surface of the cooling channel (110); the conductive shielding unit (120) can generate a shielding magnetic field under the action of the radio frequency field of the radio frequency coil (300); wherein, the conductive shielding unit (120) is intermittently provided with multiple conductive layers along the extension direction of the cooling channel (110).

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