WO2023159864A1 - 磁共振设备 - Google Patents

磁共振设备 Download PDF

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Publication number
WO2023159864A1
WO2023159864A1 PCT/CN2022/107100 CN2022107100W WO2023159864A1 WO 2023159864 A1 WO2023159864 A1 WO 2023159864A1 CN 2022107100 W CN2022107100 W CN 2022107100W WO 2023159864 A1 WO2023159864 A1 WO 2023159864A1
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WO
WIPO (PCT)
Prior art keywords
housing
magnetic resonance
resonance apparatus
casing
assembly
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PCT/CN2022/107100
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English (en)
French (fr)
Inventor
赵华炜
王鹏
虞维兴
Original Assignee
合肥泽璞医疗系统有限公司
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Publication of WO2023159864A1 publication Critical patent/WO2023159864A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves  involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/24—Arrangements or instruments for measuring magnetic variables involving magnetic resonance for measuring direction or magnitude of magnetic fields or magnetic flux

Definitions

  • the present disclosure relates to the technical field of medical equipment, in particular to a magnetic resonance equipment.
  • Magnetic Resonance Imaging occupies an important position in the field of in vitro diagnostics, and it also brings a lot of help to medical progress.
  • the noise during the operation of the magnetic resonance equipment is relatively large, which is not conducive to improving the detection experience of the detected person.
  • An embodiment of the present disclosure provides a magnetic resonance device, which can effectively reduce noise during operation and improve the detection experience of a detected person.
  • a magnetic resonance apparatus including a housing assembly, a radio frequency coil, a gradient coil, and a magnet component for generating a magnetic field.
  • the side of the housing assembly is provided with a detection chamber, the detection chamber is provided with an inlet and outlet, and the inner space of the housing assembly is provided with a first accommodating chamber arranged around the detection chamber from the circumferential outside of the detection chamber, and from the A second accommodating chamber is disposed around the first accommodating chamber on the outside of the first accommodating chamber in the circumferential direction, and the second accommodating chamber and the first accommodating chamber are isolated from each other via a vacuum chamber.
  • At least part of the radio frequency coil is disposed in the first accommodation cavity and surrounds the first accommodation cavity.
  • the gradient coil is arranged in the second containing chamber and surrounds the second containing chamber.
  • the magnet part is arranged in the second accommodation cavity, and is arranged around the gradient coil from the circumferential outer side of the gradient coil; wherein, the gradient coil is arranged between the magnet part and the radio frequency coil.
  • the gradient coil is subjected to the Lorentz force in the magnetic field generated by the magnet component, which causes vibration, thereby generating running noise.
  • the running noise is isolated by the vacuum chamber, which blocks the noise transmission path, making it difficult for the running noise to spread outward from the shell assembly, so the noise of the magnetic resonance equipment can be effectively reduced.
  • the shell assembly at least includes a first shell, a second shell and a third shell.
  • the first casing is arranged around the gradient coil and the radio frequency coil
  • the second casing is arranged around the outer side of the magnet part
  • the third casing is arranged at the end of the axial side for sealing connection with the first casing body and the second housing.
  • a second accommodating chamber is formed between the first housing and the second housing, and the inner space of the second housing forms the first accommodating chamber.
  • each of the housings is provided with an inner wall and an outer wall, and the inner wall and the outer wall are arranged at intervals to form a channel, and the first housing and the second housing are sealed and connected through a third housing, The channels of the first housing, the second housing and the third housing are communicated to form the vacuum chamber.
  • each of said housings comprises at least two housing parts sealedly connected to form said housing.
  • the inner wall and the outer wall of each of the at least two housing parts are arranged at intervals to form a sub-channel, and based on the sealed connection of the at least two housing parts, two adjacent housing parts The sub-channels are spliced and sealed to form the channels of each of the shells.
  • the third casing is sealingly connected to the first casing and the second casing, comprising: the third casing is provided with a plug-in portion; the first casing is connected to the second casing; The second shells are respectively provided with socket parts; the third shells are respectively inserted into the socket parts of the first shell and the second shell through the socket parts, and the third shell realizes The first housing and the second housing are sealingly connected.
  • the at least two housing parts at least include: a first housing part provided with an insertion part; a second housing part provided with a socket part; the at least two housing parts are sealed Connecting to form the housing, including: inserting the first housing part into the sleeve part of the second housing part through the plug-in part, so as to realize the sealing connection between the first housing part and the first housing part Two body parts.
  • At least one of the first casing and the second casing is connected to the third casing with a sealing layer, and the sealing layer is used to seal the first At least one of the housing and the second housing is in sealing connection with the third housing.
  • the sealing layer is interposed between the side wall of the socket part of at least one of the first housing and the second housing and the side wall of the third housing. between the side walls of the socket.
  • a sound-absorbing layer is further provided between the junction of at least one of the first shell and the second shell and the third shell, and the sound-absorbing layer is used to At least one of the first housing and the second housing is sealed with the third housing and absorbs vibration noise.
  • the sound-absorbing layer is disposed between the sleeve portion and the insertion portion.
  • a sealing layer is further provided at the joint between the first housing part and the second housing part, and the sealing layer is used for sealingly connecting the first housing part and the second housing part. shell pieces.
  • the sealing layer is interposed between the side wall of the socket part of the first housing part and the side wall of the socket part of the second housing part.
  • a sound-absorbing layer is further provided at the joint between the first casing part and the second casing part, and the sound-absorbing layer is used for sealingly connecting the first casing part and the second casing part.
  • the sound-absorbing layer is disposed between the insertion part and the socket part.
  • the insertion part is provided with a card part
  • the socket part is provided with a buckle part
  • the insertion part is inserted into the socket part, and the clip part and the buckle part Snap fastening.
  • the magnet component includes one of a permanent magnet or a superconducting magnet.
  • the magnetic resonance apparatus further includes shim coils for improving the uniformity of the magnetic field; the shim coils are arranged between the gradient coils and the magnet components; and/or the Shimming coils are integrated inside the gradient coils.
  • the magnetic resonance equipment further includes a support component and a first connecting member, a part of the support component is disposed outside the housing assembly, a part of the support component is disposed in the second accommodation cavity, and is fixedly connected with the magnet component , the first connecting piece is disposed in the second accommodating cavity, and is used for connecting the magnet component and the housing assembly.
  • the magnetic resonance equipment further includes a second connection piece, and the gradient coil is fixedly connected to the magnet component through the second connection piece.
  • the magnetic resonance equipment further includes an electrical connector and a vibration-damping pad
  • the electrical connector is fixed to the shell assembly through the vibration-damping pad
  • one end of the electrical connector is electrically connected to the gradient coil
  • the electrical connector The other end forms an electrical connection on the outside of the housing assembly.
  • Fig. 1 is a schematic structural diagram of a magnetic resonance apparatus shown in an embodiment.
  • FIG. 2 is a schematic cross-sectional view of the magnetic resonance equipment shown in FIG. 1 along the XZ plane.
  • FIG. 3 is a schematic structural diagram of a shielding assembly in the magnetic resonance equipment shown in FIG. 2 .
  • Fig. 4 is a partial structural schematic diagram of a housing assembly in an embodiment.
  • Fig. 5 is a schematic diagram of a partial structure of a housing in an embodiment.
  • 150 shell; 150-1, first shell; 150-2, second shell; 150-3, third shell;
  • the first housing part 1502. The second housing part;
  • 1501-1 the inner wall of the first shell part; 1501-2, the outer wall of the first shell part;
  • 1502-1 the inner wall of the second housing part
  • 1502-2 the outer wall of the second housing part
  • magnetic resonance equipment occupies an important position in the field of in vitro diagnostics and has also brought a lot of help to medical progress.
  • magnetic resonance equipment products with similar functions or performances the smaller the operating noise of the magnetic resonance equipment, the calmer and more comfortable the subject's mood during the testing process, and the better the testing experience, which in turn makes the magnetic resonance equipment better.
  • Gradient coils are one of the core components of magnetic resonance equipment. Its main function is to convert electrical energy into magnetic energy and provide the encoding magnetic field required for scanning by the magnetic resonance system. During the scanning process, the gradient coils vibrate due to the Lorentz force in the magnetic field, which will generate a lot of noise, which is the main noise source of the magnetic resonance equipment.
  • three methods of passive noise reduction, active noise reduction and noise masking are usually adopted. However, in the specific implementation process, the noise during the operation of the magnetic resonance equipment is still relatively large.
  • the present disclosure provides a magnetic resonance device, which can effectively reduce the noise during operation and improve the detection experience of the detected person.
  • FIG. 1 to FIG. 5 they are structural views of magnetic resonance equipment in some embodiments.
  • FIG. 1 is a schematic structural diagram of a magnetic resonance device shown in an embodiment.
  • FIG. 2 is a schematic cross-sectional view of the magnetic resonance equipment shown in FIG. 1 along the XZ plane.
  • FIG. 3 is a schematic structural diagram of a shielding assembly in the magnetic resonance equipment shown in FIG. 2 .
  • Fig. 4 is a schematic diagram of a partial structure of a casing assembly in an embodiment
  • Fig. 5 is a schematic diagram of a partial structure of a casing in an embodiment.
  • a magnetic resonance apparatus 10 including a housing assembly 100 , a radio frequency coil 200 , a gradient coil 300 and a magnet component 400 for generating a magnetic field.
  • the side of the housing assembly 100 is provided with a detection chamber 110, the detection chamber 110 is provided with an inlet and outlet 111, and the inner space of the housing assembly 100 is provided with a first accommodating chamber arranged around the detection chamber 110 from the circumferential outer side of the detection chamber 120 .
  • a second accommodation chamber 140 disposed around the first accommodation chamber 120 from a circumferential outer side of the first accommodation chamber 120 . Wherein, the second accommodation chamber 140 and the first accommodation chamber 120 are isolated from each other via the vacuum chamber 130 .
  • At least part of the radio frequency coil 200 is disposed in the first accommodation cavity 120 and is disposed around the first accommodation cavity 120 .
  • the gradient coil 300 is disposed in the second containing chamber 140 and is disposed around the second containing chamber 140 .
  • the magnet component 400 is disposed in the second accommodation cavity 140 and is disposed around the gradient coil 300 from the circumferential outer side of the gradient coil 300 .
  • the gradient coil 300 is disposed between the magnet part 400 and the radio frequency coil 200 .
  • the gradient coil 300 is subjected to the Lorentz force in the magnetic field generated by the magnet part 400 to cause vibration, thereby generating running noise.
  • the operating noise is isolated by the vacuum cavity 130 , that is, the vacuum cavity 130 blocks the noise transmission path, making it difficult for the operating noise to spread outward from the shell assembly 100 , thereby greatly reducing the noise of the magnetic resonance apparatus 10 .
  • disposing the magnet part 400 and the gradient coil 300 in the second accommodation cavity 140 facilitates the modular assembly of the two, and facilitates the assembly of the entire magnetic resonance equipment.
  • the first housing chamber 120 and the second housing chamber 140 are separated from each other by the vacuum chamber 130, so that the noise generated by the magnet part 400 and the gradient coil 300 can be isolated by the vacuum chamber 130, which blocks the noise transmission path and can effectively reduce the Operating noise of the magnetic resonance system 10 .
  • the magnet component 400 may be realized in various ways, including but not limited to any one of the permanent magnet 400 or the superconducting magnet 400 , as long as it can generate a magnetic field.
  • the magnet component 400 can be used to generate the main magnetic field (ie, the B0 field) along the axial direction of the detection cavity 110 (such as the Z direction in FIG. 1 ).
  • the gradient coil 300 may be implemented in various ways, and it only needs to be used to sample the sample to be tested.
  • the gradient coil 300 is used to sample the measured sample at different positions, phases and frequencies in the three-dimensional space, and finally form the gradient space data.
  • radio frequency coil 200 may be implemented in various ways, and it only needs to be used for transmitting energy and detecting signals.
  • the radio frequency coil 200 includes a radio frequency receiving coil and a radio frequency transmitting coil, the radio frequency transmitting coil is disposed in the first accommodating cavity 120 , and the radio frequency receiving coil is disposed on the sample to be tested.
  • the radio frequency coil 200 may have dual functions of transmitting and receiving, so that the tested sample does not need to wear a radio frequency receiving coil.
  • the radio frequency transmitting coils include but not limited to Helmholtz, optimized Maxwell, solenoid and other types of radio frequency transmitting coils.
  • the magnetic resonance apparatus 10 may further include a shim coil 500 for improving the uniformity of the magnetic field.
  • the shim coil 500 can be disposed on the radially outer peripheral side of the gradient coil 300 , and the magnet component 400 can be disposed on the radially outer peripheral side of the shim coil 500 ; the shim coil 500 can also be integrated inside the gradient coil.
  • the magnet component 400 can be a permanent magnet arranged oppositely for generating a main magnetic field in a vertical (such as Y direction) direction or a horizontal (such as X direction), and the radio frequency coil 200 is used to generate a B1 magnetic field perpendicular to the direction of the main magnetic field.
  • the magnet component 400 can be a superconducting magnet, which is used to generate a main magnetic field along the axial direction (such as the Z direction) of the detection cavity 110, and the radio frequency coil 200 is used to generate a magnetic field perpendicular to the main magnetic field. direction of the B1 magnetic field.
  • the embodiments of the present disclosure are not limited thereto.
  • the magnetic resonance apparatus 10 may further include a shielding assembly 600 as shown in FIG. 3 .
  • the shielding assembly 600 can be disposed on the shell assembly 100 and disposed between the gradient coil 300 and the radio frequency coil 200 . In this way, using the shielding assembly 600 can improve the performance of the magnetic resonance imaging equipment and improve the image quality.
  • the shielding assembly 600 includes at least one shielding ring 610-1, 610-2 (hereinafter collectively referred to as the shielding ring 610), and each shielding ring 610 is provided with at least one An axial slot 612 and at least one annular slot 611 perpendicular to the axial direction, the axial slot 612 runs through both ends of the at least one shielding ring 610 .
  • the number of annular slits 611 opened on the shielding ring 610 can be one or more, and the number of axial slits 612 opened can also be one or more. In the example shown in FIG. 3 , there are multiple annular slits 611 and one axial slit 612 on one shielding ring 610 , but the embodiments of the present disclosure are not limited thereto.
  • the shielding ring 610 may be made of non-magnetic metals, including copper, aluminum, magnesium, zinc, and the like.
  • the shielding assembly 600 When the shielding assembly 600 is applied to a magnetic resonance imaging device, at least one shielding ring 610 is disposed between the radio frequency coil 200 and the gradient coil 300 .
  • the eddy current circuit of the gradient coil 300 can be cut off by using the annular gap 611 to reduce the eddy current generated by the gradient coil 300 .
  • the axial slit 612 can also be used to change the direction of the induced current generated by the radio frequency coil 200 on the corresponding shielding ring 610, so that the current on the shielding ring 610 is in the same direction as the current in the corresponding radio frequency coil 200, thereby enhancing the internal strength of the radio frequency coil 200.
  • the intensity of the magnetic field can avoid the attenuation of the intensity of the magnetic field inside the radio frequency coil 200 . In this way, the shielding component 600 has a good shielding effect and can enhance the performance of the radio frequency coil 200 .
  • the magnetic resonance imaging device integrated with the shielding assembly 600 does not need to increase the transmission power of the radio frequency coil 200 to improve the efficiency of the radio frequency coil 200, which can reduce the manufacturing cost and operating cost of the magnetic resonance imaging device.
  • the "annular gap 611" includes, but is not limited to, circular, elliptical, wave-shaped and so on. It can also be set in combination with the shapes of the radio frequency coil 200 and the gradient coil 300 .
  • the "axial slot 612" includes but not limited to straight, curved, arc, stepped and so on.
  • the straight axial slit 612 can reduce the R&D and design cost of the shielding assembly 600 , facilitate processing and manufacturing, and further help reduce the manufacturing cost of the magnetic resonance imaging equipment.
  • At least one shielding ring 610 may include 1, 2 or 3 or more shielding rings 610 .
  • the number of shielding rings 610 specifically included in the shielding assembly 600 may be set according to actual needs.
  • insulation can be provided between two adjacent shielding rings 610 .
  • FIG. 3 herein uses two shielding rings 610 as an example for description, but embodiments of the present disclosure are not limited thereto.
  • the shielding assembly 600 includes at least two shielding rings 610 , and the at least two shielding rings 610 can be arranged around one another in order to improve the shielding effect.
  • the positions of the slots opened on the at least two shielding rings 610 may correspond to each other, or their positions may not correspond to each other, which is not limited in this embodiment of the present disclosure.
  • Fig. 3 shows a schematic structural diagram of a shielding assembly 600 provided by some embodiments of the present disclosure. Wherein, description is made by taking the shielding assembly 600 including two shielding rings 610 as an example, but the embodiment of the present disclosure is not limited thereto.
  • the shielding assembly 600 includes a first shielding ring 610-1 and a second shielding ring 610-2 insulated from the first shielding ring 610-1.
  • the first shielding ring 610 - 1 may be disposed radially inside the second shielding ring 610 - 2 , so as to be closer to the radio frequency coil 200 .
  • the embodiment of the present disclosure does not limit the mutual positional relationship between the first shielding ring 610-1 and the second shielding ring 610-2.
  • first shielding ring 610-1 and the second shielding ring 610-2 there are many ways to insulate the first shielding ring 610-1 and the second shielding ring 610-2 from each other, including but not limited to disposing an insulating ring between them, or applying insulating materials.
  • the housing assembly 100 may at least include a first housing 150-1, a second housing 150-2 and a third housing 150- 3.
  • the first casing 150-1 is arranged around the gradient coil 300 and the radio frequency coil 200;
  • the second casing 150-2 is arranged around the outer side of the magnet part 400;
  • the third casing 150-3 is arranged At the end of the axial side of the magnetic resonance apparatus 10, it is used for sealingly connecting the first housing 150-1 and the second housing 150-2.
  • the second housing chamber 140 is formed between the first housing 150 - 1 and the second housing 150 - 2 , and the inner space of the second housing 150 - 2 forms the first housing chamber 120 .
  • Each housing 150 is provided with an inner wall and an outer wall, and the inner wall and the outer wall are spaced apart to form a channel 151 .
  • the first housing 150-1 and the second housing 150-2 are packaged via the third housing 150-3, so that the channels 151 of the housings communicate with each other. In this way, the vacuum cavity 130 can be formed by vacuuming only one air hole provided on the shell assembly 100 .
  • the third housing 150-3 is provided with a socket part 152
  • the first housing 150-1 and the second housing 150-2 are respectively provided with socket parts 153
  • the third housing 150-3 is respectively inserted into the first housing 150-1 and the second housing 150-1 through the insertion part 152.
  • the sealing connection between the first housing 150-1 and the second housing 150-2 is realized through the third housing 150-3.
  • first shell 150-1, second shell 150-2 and third shell 150-3's insertion portion 152 and sleeve portion 153 is just an example.
  • the third housing 150-3 may also be provided with a socket portion 153, and the first housing 150-1 and the second housing 150-2 may be respectively provided with an insertion portion 152, or in other ways
  • the insertion portion 152 and the socket portion 153 are arranged in any manner, which is not limited in the present disclosure.
  • each housing 150 can be formed by connecting at least two housing parts (for example, a first housing part 1501 and a second housing part 1502), and the inner wall and the outer wall of each housing part A sub-channel is formed at intervals, and based on the sealing connection of the at least two shell parts, two adjacent sub-channels are spliced and sealed to form the channel 151 of each of the shells 150 .
  • the first housing part 1501 and the second housing part 1502 are spliced to form at least part of the first housing 150-1, so that the hollow sub-channels of the two communicate to form the At least part of the channel 151 corresponding to the first housing 150-1.
  • Both the second shell 150-2 and the third shell 150-3 can be spliced by corresponding shell parts through a similar process. Furthermore, the first housing 150 - 1 and the second housing 150 - 2 are packaged and connected via the third housing 150 - 3 , so that the channels 151 of the housings 150 communicate with each other. In this way, the flexibility of forming the vacuum cavity 130 can be improved, thereby reducing the production cost of the magnetic resonance apparatus 10 .
  • the inner and outer walls of each of the at least two housing parts 1501, 1502 are connected to each other.
  • the inner wall 1501 - 1 of the first housing part 1501 and the inner wall 1502 - 1 of the second housing part 1502 are connected to each other to form at least part of the inner wall of the housing 150 .
  • the outer wall 1501-2 of the first housing part 1501 and the outer wall 1502-2 of the second housing part 1502 are connected to each other to form at least part of the outer wall of the housing 150.
  • the first housing 150 - 1 , the second housing 150 - 2 and the third housing 150 - 3 can be formed by splicing at least two housing parts. Each housing is sealed by splicing corresponding housing parts, so that the sub-channels of the housing parts communicate with each other to form the channel 151 of the housing 150 .
  • the first housing 150-1 and the second housing 150-2 are packaged and connected through the third housing 150-3, so that the channels 151 of the housings 150 communicate with each other, and through a drawer provided on the housing assembly 100 Vacuuming the pores can form the vacuum cavity 130 .
  • the vacuum cavity 130 is formed by modularly assembling the shells 150 , which is beneficial to further improve the assembly efficiency of the magnetic resonance apparatus 10 .
  • the vacuum chamber 130 may be in the shape of a ring, although the above-mentioned shells 150 are formed by connecting two shell parts to each other, and the shells 150 are hermetically connected to each other, so that the passages 151 of the shells 150 are communicated and sealed.
  • the vacuum cavity 130 is formed as an example, but those skilled in the art should understand that the present disclosure is not intended to limit the number of housing parts. In fact, each housing 150 can also be formed by four, five, or six or even more housing parts that are spliced together and then sealed.
  • the first shell part 1501 may be provided with an insertion part 152
  • the second shell part 1502 may be provided with A socket portion 153 may be provided, and the insertion portion 152 is inserted into the socket portion 153 and fixedly connected.
  • the first housing part 1501 and the second housing part 1502 are socketed and fixedly connected by the socket part 152 and the sleeve part 153 for easy assembly, which is beneficial to improve the assembly efficiency of the magnetic resonance apparatus 10 .
  • the housing assembly 100 may further include a sealing layer 160 , and the sealing layer 160 is sandwiched between the side wall of the insertion portion 152 of the third housing 150 - 3 and the first between the side wall of the socket portion 153 of at least one of the housing 150-1 and the second housing 150-2; and/or, the housing assembly 100 may further include a sound-absorbing layer 170 disposed on the first housing Between the sleeve portion 153 of at least one of the body 150-1 and the second housing 150-2 and the insertion portion 152 of the third housing 150-3. In this way, using the sealing layer 160 and/or the sound-absorbing layer 170 to further form the sealed and reliable vacuum cavity 130 can reduce the noise generated by the magnetic resonance equipment 10 from spreading outward, and further reduce the operating noise of the magnetic resonance equipment 10 .
  • the sealing layer 160 may be ring-shaped and sheathed on the outside of the insertion portion 152 , and the sound-absorbing layer 170 may be disposed between the free end of the sleeve portion 153 and the insertion portion 152 .
  • the sealed and reliable vacuum cavity 130 is further formed by using the sealing layer 160 and the sound-absorbing layer 170.
  • the sound-absorbing layer 170 can be used to passively absorb the noise generated by the magnetic resonance equipment 10, further reducing the operating noise of the magnetic resonance equipment 10, and improving the health of the subject. Test experience.
  • the above-mentioned socket part 152 can be provided with a card part 154, and the above-mentioned socket part 153 can be provided with a buckle part 155, and the socket part 152 can be inserted into the socket part 153, and The buckle part 154 and the buckle part 155 are buckled and fixed.
  • the fixed connection between the plug part 152 and the sleeve part 153 is realized by using the clamp part 154 and the buckle part 155.
  • the sealing layer 160 can be used to improve the sealing performance of the connection between the shells, and the sound-absorbing layer 170 can be used to improve the sealing performance. Noise reduction effect.
  • the casing may further include a sealing layer 160, and the sealing layer 160 is disposed in the connection gap of the casing parts (for example, the above-mentioned first casing part 1501 and the above-mentioned second casing part 1502).
  • the housing further includes a sound-absorbing layer 170 , and the sound-absorbing layer 170 is disposed in a connection gap between the housing parts (eg, the first housing part 1501 and the second housing part 1502 ). In this way, the noise reduction effect of the magnetic resonance apparatus 10 can be further improved by using the sound-absorbing layer 170 arranged at the joint of the shell parts.
  • sealing layer 160 may be implemented in various ways, including but not limited to silica gel, rubber, and the like. There are many specific ways to realize the sound-absorbing layer 170, including but not limited to sound-absorbing cotton and the like.
  • the magnetic resonance apparatus 10 may further include a supporting component 800 and a first connecting member 180 .
  • the support component 800 can be partially disposed outside the housing assembly 100 , and partially disposed in the second accommodating cavity 140 , and can be fixedly connected with the magnet component 400 .
  • the first connecting piece 180 is disposed in the second receiving chamber 140 for connecting the magnet part 400 and the housing assembly 100 .
  • a part of the supporting component 800 is disposed outside the casing assembly 100 to form a supporting foot, and further supports the magnet component 400 , so that the magnet component 400 hovers reliably in the second accommodating cavity 140 .
  • the housing assembly 100 and the magnet component 400 can be connected by using the first connecting piece 180 , so that the housing assembly 100 can reliably support the magnet component 400 through the first connecting piece 180 .
  • the support member 800 is sealingly engaged with the housing assembly 100 .
  • support member 800 there may be various specific implementation manners of the support member 800, including but not limited to pins, support rods, support seats and the like.
  • the magnetic resonance apparatus 10 may further include a second connecting piece 190, and the gradient coil 300 may be fixedly connected to the magnet component 400 through the second connecting piece 190.
  • the second connecting member 190 can be used to support the magnet component 400 , reducing the contact area between the gradient coil 300 and the magnet component 400 , thereby reducing the vibration transmitted from the gradient coil 300 to the magnet component 400 .
  • first connecting member 180 and the second connecting member 190 there may be various specific implementation manners of the first connecting member 180 and the second connecting member 190 , including but not limited to a fixing rod, a fixing plate, and the like.
  • the magnetic resonance device 10 may further include an electrical connector 101 and a vibration damping pad 102 .
  • the electrical connector 101 is fixed on the housing assembly 100 through the shock absorbing pad 102 , and one end of the electrical connector 101 is electrically connected to the gradient coil 300 , and the other end forms an electrical connection part outside the housing assembly 100 .
  • the vibration damping pad 102 to cooperate with the electrical connector 101 , the vibration energy generated when the gradient coil 300 is running can be absorbed by the vibration damping pad 102 , thereby reducing the vibration of the housing assembly 100 .
  • components such as gradient power amplifiers can be disposed outside the casing assembly 100 by using the electrical connector 101 , and the external components and the gradient coil 300 can be connected by the electrical connector 101 .
  • the electrical connector 101 can be implemented in various ways, and it only needs to be able to realize the electrical connection between components such as gradient power amplifiers and the gradient coil 300 .
  • the electrical connector 101 may include, but is not limited to: electrical connectors such as electrical plugs, Type-A connectors, Type-B connectors, Type-C connectors, and Lightning connectors; or Type-A interfaces, Type-B interfaces, Type-C interfaces, An electrical interface such as a Lightning interface; or a cable such as a coaxial cable.
  • the magnetic resonance apparatus 10 may further include a bearing assembly 700 .
  • the bearing assembly 700 includes a bed board 710 that can move relative to the housing assembly 100 .
  • the subject to be tested may lie on the bed board 710 and then be sent into the detection chamber 110 for detection as the bed board 710 moves.
  • the bearing assembly 700 may also have a lifting assembly capable of driving the bed board 710 up and down.
  • the lifting component can be realized by electronically controlled lifting equipment, and can also be realized by manual lifting equipment, and there are no too many restrictions here.
  • the movement of the bed board 710 and the carrying assembly 700 can also be realized by means of electronically controlled moving equipment or manual moving equipment, and there are no too many restrictions here.
  • first”, “second”, etc. are used for descriptive purposes only, and should not be interpreted as indicating or implying relative importance or implicitly specifying the quantity of the indicated technical features. Thus, a feature defined with “first”, “second”, etc. may expressly or implicitly include at least one of that feature.
  • “plurality” means at least two, such as two, three, etc., unless otherwise specifically defined.
  • a first feature being “on” or “under” a second feature may mean that the first and second features are in direct contact, or that the first and second features are indirect through an intermediary. touch.
  • “above”, “above” and “above” the first feature on the second feature may mean that the first feature is directly above or obliquely above the second feature, or simply means that the first feature is higher in level than the second feature.
  • “Below”, “beneath” and “beneath” the first feature may mean that the first feature is directly below or obliquely below the second feature, or simply means that the first feature is less horizontally than the second feature.

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Abstract

本申请提供一种磁共振设备。该磁共振设备包括壳体组件、射频线圈、梯度线圈以及用于产生磁场的磁体部件。壳体组件的侧部设有检测腔，检测腔设有进出口，壳体组件的内部空间设有从检测腔的周向外侧环绕所述检测腔设置的第一容纳腔、从所述第一容纳腔的周向外侧环绕所述第一容纳腔设置的第二容纳腔，第二容纳腔与第一容纳腔经由真空腔相互隔绝设置。射频线圈的至少部分设置于第一容纳腔内，并环绕检测腔设置。梯度线圈设置于第二容纳腔内。磁体部件设置于第二容纳腔内，并环绕梯度线圈设置；其中，梯度线圈设置于磁体部件与射频线圈之间。

Description

磁共振设备 技术领域
本公开涉及医疗设备技术领域，特别是涉及一种磁共振设备。
背景技术
磁共振设备(Magnetic Resonance Imaging，MRI)作为一种医疗影像设备，在体外诊断领域中占据着重要位置，也为医疗进步带来诸多帮助。在相关技术中，磁共振设备运行过程中的噪音较大，不利于提高被检测者的检测体验。
发明内容
本公开实施例提供一种磁共振设备，能够有效降低运行过程中的噪音，提高被检测者的检测体验。
根据本公开实施例的第一方面，提供一种磁共振设备，包括壳体组件、射频线圈、梯度线圈以及用于产生磁场的磁体部件。壳体组件的侧部设有检测腔，检测腔设有进出口，壳体组件的内部空间设有从所述检测腔的周向外侧环绕所述检测腔设置的第一容纳腔、从所述第一容纳腔的周向外侧环绕所述第一容纳腔设置的第二容纳腔，所述第二容纳腔与所述第一容纳腔经由真空腔相互隔绝设置。射频线圈的至少部分设置于第一容纳腔内，并环绕所述第一容纳腔设置。梯度线圈设置于第二容纳腔内，并环绕所述第二容纳腔设置。磁体部件设置于第二容纳腔内，并从梯度线圈的周向外侧环绕所述梯度线圈设置；其中，梯度线圈设置于磁体部件与射频线圈之间。
该磁共振设备在扫描过程中，梯度线圈在磁体部件产生的磁场中受到洛伦兹力的作用而引起振动，进而产生运行噪音。而该运行噪音受到真空腔的隔绝，真空腔阻断了噪音传播途径，使得该运行噪音不易从壳体组件向外扩散，因此可以有效降低磁共振设备的噪音。
在其中一个实施例中，壳体组件至少包括第一壳体、第二壳体以及第三壳体。第一壳体环绕设置于梯度线圈与射频线圈之间，第二壳体环绕设置于磁体部件的周向外侧，第三壳体设置于轴向侧面端部，用于密封连接所述第一壳体与所述第二壳体。其中，第一壳体与第二壳体之间形成第二容纳腔，第二壳体的内部空间形成第一容纳腔。
在其中一个实施例中，各所述壳体均设置有内壁和外壁，且内壁和外壁间隔设置并形成通道，通过第三壳体密封连接所述第一壳体与所述第二壳体，使得所述第一壳体、所述第二壳体与所述第三壳体各自的通道连通，形成所述真空腔。
在一些实施例中，每个所述壳体包括至少两个壳体件，所述至少两个壳体件密封连接，用于形成所述壳体。
在其中一个实施例中，所述至少两个壳体件中每一个壳体件的内壁和外壁间隔设置形成一个子通道，基于所述至少两个壳体件密封连接，使相邻两个所述子通道拼接密封，用于形成各所述壳体的通道。
在其中一个实施例中，所述第三壳体密封连接所述第一壳体与所述第二壳体，包括：所述第三壳体设有插接部；所述第一壳体与所述第二壳体分别设有套接部；所述第三壳体通过插接部分别插入所述第一壳体与第二壳体的套接部中，以所述第三壳体实现密封连接所述第一壳体与所述第二壳体。
在一些实施例中，所述至少两个壳体件至少包括：第一壳体件，设有插接部；第二壳体件，设有套接部；所述至少两个壳体件密封连接，形成所述壳体，包括：所述第一壳体件通过插接部插入所述第二壳体件的套接部中，以实现密封连接所述第一壳体件与所述第二壳体件。
在其中一个实施例中，所述第一壳体和第二壳体中的至少之一与所述第三壳体的连接处还设置有密封层，所述密封层用于将所述第一壳体和第二壳体中的至少之一与所述第三壳体密封连接。
在其中一个实施例中，所述密封层夹设于所述第一壳体和所述第二壳体中的至少之一的所述套接部的侧壁与所述第三壳体的所述插接部的侧壁之间。
在一些实施例中，所述第一壳体和第二壳体中的至少之一的连接处与所述第三壳体之间还设置有吸音层，所述吸音层用于将所述第一壳体和所述第二壳体中的至少之一与所述第三壳体密封连接，并吸收振动噪音。
在一个实施例中，所述吸音层设置于所述套接部与所述插接部之间。
在一个实施例中，所述第一壳体件与所述第二壳体件的连接处还设置有密封层，所述密封层用于密封连接所述第一壳体件与所述第二壳体件。
在其中一个实施例中，所述密封层夹设于所述第一壳体件的插接部的侧壁与所述第二壳体件的套接部的侧壁之间。
在其中一些实施例中，所述第一壳体件与所述第二壳体件的连接处还设置有吸音层，所述吸音层用于密封连接所述第一壳体件与所述第二壳体件，并吸收振动噪音。
在其中一个实施例中，所述吸音层设置于所述插接部与所述套接部之间。
在一些实施例中，所述插接部设有卡部，所述套接部设有扣部，所述插接部插入所述套接部中，并使所述卡部与所述扣部卡扣固定。
在上述任一实施例中，所述磁体部件包括永磁体或超导磁体中的一种。
在上述任一实施例中，所述磁共振设备还包括用于改进磁场均匀性的匀场线圈；所述匀场线圈设置于所述梯度线圈与所述磁体部件之间；和/或所述匀场线圈集成在所述梯 度线圈的内部。
在上述任一实施例中，磁共振设备还包括支撑部件以及第一连接件，支撑部件的部分设置于壳体组件的外部，支撑部件的部分设置于第二容纳腔，并与磁体部件固定连接，第一连接件设置于第二容纳腔内，用于连接磁体部件以及壳体组件。
在上述任一实施例中，磁共振设备还包括第二连接件，梯度线圈通过第二连接件与磁体部件固定连接。
在其中一个实施例中，磁共振设备还包括电连接器以及减振垫，电连接器通过减振垫固设于壳体组件，且电连接器的一端与梯度线圈电连接，电连接器的另一端在壳体组件的外侧形成电连接部。
应当理解的是，以上的一般描述和后文的细节描述仅是示例性和解释性的，并不能限制本公开。
附图说明
附图说明构成本公开的一部分的附图用来提供对本公开的进一步理解，本公开的示意性实施例及其说明用于解释本公开，并不构成对本公开的不当限定。
为了更清楚地说明本公开实施例中的技术方案，下面将对实施例描述中所需要使用的附图作简单地介绍，显而易见地，下面描述中的附图仅仅是本公开的一些实施例，对于本领域普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图获得其他的附图。
图1为一实施例中所示的磁共振设备的结构示意图。
图2为图1所示的磁共振设备沿XZ平面的剖视示意图。
图3为图2所示的磁共振设备中屏蔽组件的结构示意图。
图4为一实施例中的壳体组件的局部结构示意图。
图5为一实施例中的壳体的局部结构示意图。
附图标记说明：
10、磁共振设备；
100、壳体组件；
110、检测腔；        111、进出口；
120、第一容纳腔；
130、真空腔；
140、第二容纳腔；
150、壳体；    150-1、第一壳体；150-2、第二壳体；150-3、第三壳体；
1501、第一壳体件；                1502、第二壳体件；
1501-1、第一壳体件的内壁；       1501-2、第一壳体件的外壁；
1502-1、第二壳体件的内壁；       1502-2、第二壳体件的外壁；
151、通道；
1511、第一子通道；         1512、第二子通道
152、插接部；             153、套接部；
154、卡部；                155、扣部；
160、密封层；
170、吸音层；
180、第一连接件；
190、第二连接件；
101、电连接器；        102、减振垫；
200、射频线圈；
300、梯度线圈；
400、磁体部件；
500、匀场线圈；
600、屏蔽组件；
610、屏蔽环；
610-1、第一屏蔽环；           610-2、第二屏蔽环；
611、环形缝隙；           612、轴向缝隙；
700、承载组件；
710、床板；
800、支撑部件。
具体实施方式
为使本公开的目的、技术方案及优点更加清楚明白，以下结合附图及具体实施方式，对本公开进行进一步的详细说明。应当理解的是，此处所描述的具体实施方式仅用以解释本公开，并不限定本公开的保护范围。
除非另有定义，本文所使用的技术和科学术语与本领域技术人员通常理解的含义相同。本文中所使用的术语只是为了描述具体的实施方式，不是旨在于限制本公开。
磁共振设备作为一种常用的医疗影像设备，在体外诊断领域中占据着重要位置，也为医疗进步带来诸多帮助。在功能或性能相近的磁共振设备产品中，磁共振设备的运行噪音越小，被检测者在检测过程中的心情会越平缓、舒服，被检测体验也越好，进而使得该磁共振设备越能获得医院和/或体检机构的青睐。因此如何降低磁共振设备的运行噪音，成了磁共振设备厂家越来越重视的问题。
梯度线圈是磁共振设备的核心部件之一，它的主要作用是将电能转化为磁能，提供磁共振系统扫描所需的编码磁场。在扫描过程中，由于梯度线圈在磁场中受到洛伦兹力的作用引起振动，会产生很大的噪音，是磁共振设备的主要噪声源。在相关技术中，为解决磁共振设备运行过程中噪音问题，通常采用被动降噪、主动降噪和噪声遮蔽三种方法。但具体实现过程中，磁共振设备运行过程中的噪音仍然较大。
基于此，本公开提供一种磁共振设备，能够有效降低运行过程中的噪音，提高被检测者的检测体验。
为了更好地理解本公开的磁共振设备，下面结合附图进行进一步阐述说明。
如图1至图5所示，为一些实施例中磁共振设备的结构视图。其中，图1为一实施例中所示的磁共振设备的结构示意图。图2为图1所示的磁共振设备沿XZ平面的剖视示意图。图3为图2所示的磁共振设备中屏蔽组件的结构示意图。图4为一实施例中的壳体组件的局部结构示意图，图5为一实施例中的壳体的局部结构示意图。
如图1以及图2所示，提供一种磁共振设备10，包括壳体组件100、射频线圈200、梯度线圈300以及用于产生磁场的磁体部件400。壳体组件100的侧部设有检测腔110，检测腔110设有进出口111，壳体组件100的内部空间设有从所述检测腔的周向外侧环绕检测腔110设置的第一容纳腔120、从所述第一容纳腔120的周向外侧环绕第一容纳腔120设置的第二容纳腔140。其中，所述第二容纳腔140与第一容纳腔120经由真空腔130实现了相互隔绝设置。射频线圈200的至少部分设置于第一容纳腔120内，并环绕第一容纳腔120设置。梯度线圈300设置于第二容纳腔140内，并环绕第二容纳腔140设置。磁体部件400设置于第二容纳腔140内，并从所述梯度线圈300的周向外侧环绕梯度线圈300设置。梯度线圈300设置于磁体部件400与射频线圈200之间。
该磁共振设备10在扫描过程中，梯度线圈300在磁体部件400产生的磁场中受到洛伦兹力的作用而引起振动，进而产生运行噪音。而该运行噪音受到真空腔130的隔绝，即该真空腔130阻断了噪音传播途径，使得该运行噪音不易从壳体组件100向外扩散，进而会极大降低磁共振设备10的噪音。
此外，可以理解地，将磁体部件400与梯度线圈300设置于第二容纳腔140，易于二者的模块化组装，更易于整个磁共振设备的装配。同时，利用真空腔130将第一容纳 腔120与第二容纳腔140相互隔开，使得磁体部件400以及梯度线圈300产生的噪音能够被真空腔130隔绝，阻断了噪音传播途径，可以有效降低磁共振设备10的运行噪音。
需要说明的是，磁体部件400的具体实现方式可以有多种，包括但不限于永磁体400或超导磁体400中的任一种，能够产生磁场即可。
一些实施例中，磁体部件400可用于产生沿着检测腔110轴向方向(如图1中Z方向)的主磁场(也即B0场)。
需要说明的是，梯度线圈300的具体实现方式可以有多种，能够用于对被测样本进行采样即可。
一些实施例中，梯度线圈300用于实现对被测样本在三维空间中不同位置、位相和频率进行采样并最终构成梯度空间数据。
需要说明的是，射频线圈200的具体实现方式可以有多种，能够用于发射能量和检测信号即可。
在一些实施例中，射频线圈200包括射频接收线圈以及射频发射线圈，射频发射线圈设置于第一容纳腔120内，射频接收线圈设置在被测样本上。
另一些实施例中，射频线圈200可具有发射以及接收双重功能，使得被测样本无需佩戴射频接收线圈。
在本公开实施例中，射频发射线圈包括但不限于亥姆霍兹、优化的麦克斯韦以及螺线管等类型的射频发射线圈。
在上述任一实施例的基础上，如图2所示，一些实施例中，磁共振设备10还可包括用于改进磁场均匀性的匀场线圈500。匀场线圈500可以设置于梯度线圈300的径向外周侧，磁体部件400设置于匀场线圈500的径向外周侧；匀场线圈500也可以集成在梯度线圈内部。在此对匀场线圈500的设置不做过多限制。
在一实施例中，如图1以及图2所示，磁体部件400可以为相对设置的永磁体，用于产生竖直(如Y方向)方向或水平(如X方向)的主磁场，射频线圈200用于产生垂直于主磁场方向的B1磁场。而另一实施例中，如图1所示，磁体部件400可以为超导磁体，用于产生沿检测腔110轴向(如Z方向)的主磁场，射频线圈200用于产生垂直于主磁场方向的B1磁场。但本公开实施例不限于此。
为了提升磁共振成像设备的性能并改善图像质量，梯度线圈300和射频线圈200之间的相互干扰或影响通常越小越好。在上述任一实施例的基础上，磁共振设备10还可以包括如图3所示的屏蔽组件600。具体地，该屏蔽组件600可设置于壳体组件100上，并设置于梯度线圈300与射频线圈200之间。如此，利用屏蔽组件600可以提升磁共振成像设备的性能并改善图像质量。
如图3所示，一些实施例中，屏蔽组件600包括至少一个屏蔽环610-1、610-2(以下可统称为屏蔽环610)，每个屏蔽环610上开设有沿着轴向的至少一个轴向缝隙612以及垂直于轴向的至少一个环形缝隙611，轴向缝隙612贯穿所述至少一个屏蔽环610的两端。
屏蔽环610上开设的环形缝隙611的数量可以为一个或多个，开设的轴向缝隙612的数量也可以为一个或多个。在图3所示的例子中，一个屏蔽环610上开设的环形缝隙611的数量为多个，而开设的轴向缝隙612的数量为一个，但本公开实施例不限于此。
在一些实施例中，屏蔽环610的材质可以为非磁性金属，包括铜、铝、镁、锌、等。
该屏蔽组件600应用于磁共振成像设备时，至少一个屏蔽环610设置于射频线圈200与梯度线圈300之间。这样，可利用环形缝隙611切断梯度线圈300的涡流回路，减少梯度线圈300产生的涡流。还可利用轴向缝隙612改变射频线圈200在对应屏蔽环610上产生的感应电流的方向，使屏蔽环610上的电流与相应的射频线圈200中的电流同向，进而可以增强射频线圈200内部的磁场强度，从而能够避免射频线圈200内部的磁场强度的衰减。如此，屏蔽组件600具有良好的屏蔽效果，且能够增强射频线圈200的性能。
进一步地，集成有屏蔽组件600的磁共振成像设备无需增加射频线圈200的发射功率来提高射频线圈200的效率，能够降低磁共振成像设备的制造成本以及运行成本。
在本公开实施例中，“环形缝隙611”包括但不仅限于圆形、椭圆形、波浪环形等等。也可以结合射频线圈200以及梯度线圈300的形状进行设置。
在本公开实施例中，“轴向缝隙612”包括但不仅限于直条形、曲线形、弧形、阶梯形等等。其中，直条状的轴向缝隙612可以降低屏蔽组件600的研发设计成本，方便加工制造，进而有利于降低磁共振成像设备的制造成本。
在本公开实施例中，至少一个屏蔽环610可以包括1个、2个或3个及更多屏蔽环610。实施时，屏蔽组件600具体包括的屏蔽环610的数量，可以根据实际需要进行设置。此外，相邻两个屏蔽环610之间可绝缘设置。为了便于理解，本文图3以两个屏蔽环610为例进行描述，但本公开实施例不限于此。
在一些实施例中，屏蔽组件600包括至少两个屏蔽环610，该至少两个屏蔽环610可以依次环绕设置，以提高屏蔽效果。其中，该至少两个屏蔽环610上开设的缝隙可以位置对应，或者位置不对应，本公开实施例对此不做限定。图3示出了本公开一些实施例提供的屏蔽组件600的结构示意图。其中，以屏蔽组件600包括两个屏蔽环610为例进行描述，但本公开实施例不限于此。
如图3所示，屏蔽组件600包括第一屏蔽环610-1以及与第一屏蔽环610-1绝缘设置的第二屏蔽环610-2。其中，第一屏蔽环610-1可以设置于第二屏蔽环610-2的径向内侧，从而更靠近射频线圈200。然而，本公开实施例对第一屏蔽环610-1和第二屏蔽环 610-2的相互位置关系不做限定。
使第一屏蔽环610-1与第二屏蔽环610-2相互绝缘设置的方式可以有多种，包括但不限于在两者之间设置绝缘环，或者涂抹绝缘材料等。
在上述任一实施例的基础上，如图4所示，一些实施例中，壳体组件100可至少包括第一壳体150-1、第二壳体150-2以及第三壳体150-3，第一壳体150-1环绕设置于梯度线圈300与所述射频线圈200之间；第二壳体150-2环绕设置于磁体部件400的周向外侧；第三壳体150-3设置于磁共振设备10的轴向侧面端部，用于密封连接所述第一壳体150-1与所述第二壳体150-2。第一壳体150-1与第二壳体150-2之间形成所述第二容纳腔140，所述第二壳体150-2的内部空间形成所述第一容纳腔120。每个壳体150均设置有内壁和外壁，且内壁和外壁间隔设置，并形成通道151。组装时，第一壳体150-1、第二壳体150-2经由第三壳体150-3封装，使各所述壳体的通道151相互连通。这样，只需在壳体组件100上开设的一处抽气孔进行抽真空操作，即可形成真空腔130。
在一些可能的实施例中，第一壳体150-1、第二壳体150-2经由第三壳体150-3封装时，可采用以下方式：第三壳体150-3设有插接部152，第一壳体150-1与第二壳体150-2分别设有套接部153，第三壳体150-3通过插接部152分别插入第一壳体150-1与第二壳体150-2的套接部153中，从而实现通过第三壳体150-3密封连接所述第一壳体150-1与所述第二壳体150-2。本领域技术人员应能理解，上述第一壳体150-1、第二壳体150-2与第三壳体150-3的插接部152与套接部153的设置方式仅为一种示例，在一些实施例中，还可以是第三壳体150-3设有套接部153，第一壳体150-1、第二壳体150-2分别设有插接部152，或以其它任意方式设置插接部152与套接部153，本公开对此不作限制。
在一些可能的实施例中，每个壳体150可由至少两个壳体件(例如第一壳体件1501、第二壳体件1502)相互连接而成，每个壳体件的内壁和外壁间隔设置形成一个子通道，基于所述至少两个壳体件密封连接，使相邻两个子通道拼接密封，用于形成各所述壳体150的通道151。具体地，在一个示例中，如图5所示，第一壳体件1501和第二壳体件1502拼接形成至少部分第一壳体150-1，使得两者的中空子通道连通而形成所述第一壳体150-1对应的通道151的至少部分。第二壳体150-2与第三壳体150-3均可以通过相似的过程由对应的壳体件拼接而成。进而将第一壳体150-1、第二壳体150-2经由第三壳体150-3封装连接，使各所述壳体150的通道151相互连通。如此，可以提高真空腔130形成的灵活度，进而降低磁共振设备10的生产成本。
需要说明的是，“至少两个壳体件相互连接”的具体实现方式可以有多种，包括但不限于螺接、铆接、焊接、卡扣等等。
一示例中，至少两个壳体件1501、1502中的每一个壳体件的内壁和外壁均相互连接。如图5所示，第一壳体件1501的内壁1501-1和第二壳体件1502的内壁1502-1相互连接，形成壳体150的至少部分内壁。同时，第一壳体件1501的外壁1501-2和第二壳体 件1502的外壁1502-2相互连接，形成壳体150的至少部分外壁。
如图2以及图5所示，一些实施例中，第一壳体150-1、第二壳体150-2以及第三壳体150-3均可以由至少两个壳体件拼接形成。各壳体通过对应的壳体件拼接密封，使得壳体件的子通道相互连通形成所述壳体150的通道151。第一壳体150-1、第二壳体150-2通过第三壳体150-3封装连接，使得各所述壳体150的通道151相互连通，并通过壳体组件100上开设的一个抽气孔抽真空即可形成真空腔130。如此，通过模块化组装各壳体150来形成真空腔130，有利于进一步提高磁共振设备10的装配效率。
一示例中，真空腔130可以呈圆环状，尽管上述以两个壳体件相互连接来形成各壳体150，各壳体150相互密封连接，使各所述壳体150的通道151连通密封进而形成真空腔130作为示例，但本领域技术人员应能理解，本公开无意限定壳体件的数量。实际上，每个壳体150也可由四个、五个、或六个甚至更多个壳体件相互拼接后密封形成。
进一步地，如图5所示，一些实施例中，相互拼接密封的两个壳体件1501、1502中，第一壳体件1501上可设有插接部152，第二壳体件1502上可设有套接部153，插接部152插入套接部153中，并固定连接。如此，利用插接部152与套接部153套接固定连接第一壳体件1501及第二壳体件1502易于组装，有利于提高磁共振设备10的装配效率。
更进一步地，如图4所示，一些实施例中，壳体组件100还可以包括密封层160，密封层160夹设于第三壳体150-3的插接部152的侧壁与第一壳体150-1与第二壳体150-2至少之一的套接部153的侧壁之间；和/或，壳体组件100还可以包括吸音层170，吸音层170设置于第一壳体150-1与第二壳体150-2至少之一的套接部153与第三壳体150-3的插接部152之间。如此，利用密封层160和/或吸音层170进一步形成密封可靠的真空腔130，可减少磁共振设备10产生的噪音向外扩散，进一步降低磁共振设备10的运行噪音。
一示例中，密封层160可以呈环形，并套设于插接部152的外侧，吸音层170可设置于套接部153的自由端与插接部152之间。如此，利用密封层160和吸音层170进一步形成密封可靠地真空腔130，同时利用吸音层170可以被动吸收磁共振设备10产生的噪音，进一步降低磁共振设备10的运行噪音，提高被检测者的检测体验。
需要说明的是，“拼接密封的两个壳体件”的具体实现方式可以有多种，包括不限于螺接密封、铆接密封、焊接密封、卡扣密封等等。
如图4及图5所示，一些实施例中，上述插接部152可设有卡部154，上述套接部153可设有扣部155，插接部152插入套接部153中，并使卡部154与扣部155卡扣固定。如此，利用卡部154与扣部155固定连接，实现插接部152与套接部153的固定连接，同时利用密封层160可以提高壳体之间连接的密封性，并利用吸音层170来提高降噪效果。当然了，在其他实施例中，壳体还可包括密封层160，密封层160设置于壳体 件的连接缝隙中(例如上述第一壳体件1501与上述第二壳体件1502)。如此，亦可以提高真空腔130的密封可靠性，有利于保证真空腔130的真空度。和/或，一些实施例中，壳体还包括吸音层170，吸音层170设置于壳体件(例如上述第一壳体件1501与上述第二壳体件1502)的连接缝隙中。如此，利用设置在壳体件连接处的吸音层170可进一步提升磁共振设备10的降噪效果。
需要说明的是，密封层160的具体实现方式可以有多种，包括但不限于硅胶、橡胶等。吸音层170的具体实现方式可以有多种，包括但不限于吸音棉等。
在上述任一实施例的基础上，如图2所示，一些实施例中，磁共振设备10还可以包括支撑部件800以及第一连接件180。支撑部件800可部分设置于壳体组件100的外部，部分设置于第二容纳腔140，并可与磁体部件400固定连接。第一连接件180设置于第二容纳腔140内，用于连接磁体部件400以及壳体组件100。如此，支撑部件800的部分设置于壳体组件100的外部形成支撑脚，进而支撑磁体部件400，使得磁体部件400可靠地悬停在第二容纳腔140内。同时可利用第一连接件180连接壳体组件100以及磁体部件400，使得壳体组件100可以通过第一连接件180对磁体部件400进行可靠支撑。
可选地，支撑部件800与壳体组件100密封配合。
需要说明的是，支撑部件800的具体实现方式可以有多种，包括但不限于引脚、支撑杆以及支撑座等等。
在上述任一实施例的基础上，如图2所示，一些实施例中，磁共振设备10还可以包括第二连接件190，梯度线圈300可通过第二连接件190与磁体部件400固定连接。如此，可以利用第二连接件190对磁体部件400进行支撑，减少梯度线圈300与磁体部件400的接触面积，从而可以减少梯度线圈300将振动传递给磁体部件400。
需要说明的是，第一连接件180以及第二连接件190的具体实现方式可以有多种，包括但不限于固定杆、固定板等。
在上述任一实施例的基础上，如图2所示，一些实施例中，磁共振设备10还可以包括电连接器101以及减振垫102。电连接器101通过减振垫102固设于壳体组件100，且电连接器101的一端与梯度线圈300电连接，另一端在壳体组件100的外侧形成电连接部。利用减振垫102与电连接器101配合，使梯度线圈300运行时产生的振动能量能够被减振垫102吸收，从而可以减少壳体组件100的振动。同时，利用电连接器101可以将梯度功率放大器等元件设置于壳体组件100的外部，并利用电连接器101连接外部元件与梯度线圈300。
需要说明的是，电连接器101的具体实现方式可以有多种，能够实现梯度功率放大器等元件与梯度线圈300的电连接即可。电连接器101可以包括但不限于：电插头、Type-A接头、Type-B接头、Type-C接头、Lightning接头等电接头；或者Type-A接口、Type-B接口、Type-C接口、Lightning接口等电接口；或者，同轴线缆等线缆。
如图1所示，一些实施例中，磁共振设备10还可以包括承载组件700，承载组件700包括可相对于壳体组件100移动的床板710，床板710通过进出口111进出检测腔110。示例中，被检测者可以躺在床板710上，然后随床板710移动而送入检测腔110中进行检测。
需要说明的是，承载组件700的具体实现方式可以参照多种相关技术中的扫描床设备实现。一些实施例中，承载组件700还可以具有能够实现带动床板710升降的升降组件。该升降组件可以采用电控升降设备实现，也可以采用手动升降设备实现，在此不做过多限制。
此外，床板710以及承载组件700的移动，也可以采用电控移动设备或手动移动设备等方式实现，在此不做过多限制。
在本公开的描述中，需要理解的是，术语“中心”、“纵向”、“横向”、“长度”、“宽度”、“厚度”、“上”、“下”、“前”、“后”、“左”、“右”、“竖直”、“水平”、“顶”、“底”、“内”、“外”、“顺时针”、“逆时针”、“轴向”、“径向”、“周向”等指示的方位或位置关系为基于附图所示的方位或位置关系，仅是为了便于描述本公开和简化描述，而不是指示或暗示所指的装置或元件必须具有特定的方位、以特定的方位构造和操作，因此不能理解为对本公开的限制。
此外，术语“第一”、“第二”等仅用于描述目的，而不能理解为指示或暗示相对重要性或者隐含指明所指示的技术特征的数量。由此，限定有“第一”、“第二”等的特征可以明示或者隐含地包括至少一个该特征。在本公开的描述中，“多个”的含义是至少两个，例如两个，三个等，除非另有明确具体的限定。
在本公开中，除非另有明确的规定和限定，术语“安装”、“相连”、“连接”、“固定”等术语应做广义理解，例如，可以是固定连接，也可以是可去除连接，或成一体；可以是机械连接，也可以是电连接；可以是直接相连，也可以通过中间媒介间接相连，可以是两个元件内部的连通或两个元件的相互作用关系，除非另有明确的限定。对于本领域的普通技术人员而言，可以根据具体情况理解上述术语在本公开中的具体含义。
在本公开中，除非另有明确的规定和限定，第一特征在第二特征“上”或“下”可以是第一和第二特征直接接触，或第一和第二特征通过中间媒介间接接触。而且，第一特征在第二特征“之上”、“上方”和“上面”可是第一特征在第二特征正上方或斜上方，或仅仅表示第一特征水平高度高于第二特征。第一特征在第二特征“之下”、“下方”和“下面”可以是第一特征在第二特征正下方或斜下方，或仅仅表示第一特征水平高度小于第二特征。
需要说明的是，当元件被称为“固定于”、“设置于”、“固设于”或“安设于”另一个元件，它可以直接在另一个元件上或者也可以存在居中的元件。当一个元件被认为是“连接”另一个元件，它可以是直接连接到另一个元件或者可能同时存在居中元件。
以上实施例的各技术特征可以进行任意的组合，为使描述简洁，未对上述实施例中 的各个技术特征所有可能的组合都进行描述，然而，只要这些技术特征的组合不存在矛盾，都应当认为是本说明书记载的范围。
以上实施例仅表达了本公开的几种实施方式，其描述较为具体和详细，但并不能因此而理解为对公开专利范围的限制。应当指出的是，对于本领域的普通技术人员来说，在不脱离本公开构思的前提下，还可以做出若干变形和改进，这些都属于本公开的保护范围。

Claims (21)

  1. 一种磁共振设备，其特征在于，包括：
    壳体组件，所述壳体组件的侧部设有检测腔，所述检测腔设有进出口，所述壳体组件的内部空间设有从所述检测腔的周向外侧环绕所述检测腔设置的第一容纳腔、从所述第一容纳腔的周向外侧环绕所述第一容纳腔设置的第二容纳腔，所述第二容纳腔与所述第一容纳腔经由真空腔相互隔绝设置；
    射频线圈，所述射频线圈的至少部分设置于所述第一容纳腔内，并环绕所述第一容纳腔设置；
    梯度线圈，设置于所述第二容纳腔内，并环绕所述第二容纳腔设置；以及
    磁体部件，用于产生磁场，所述磁体部件设置于所述第二容纳腔内，并从所述梯度线圈的周向外侧环绕所述梯度线圈设置。
  2. 根据权利要求1所述的磁共振设备，其特征在于，所述壳体组件至少包括：
    第一壳体，环绕设置于所述梯度线圈与所述射频线圈之间；
    第二壳体，环绕设置于所述磁体部件的周向外侧；
    第三壳体，设置于轴向侧面端部，用于密封连接所述第一壳体与所述第二壳体；
    其中，所述第一壳体与所述第二壳体之间形成所述第二容纳腔，所述第二壳体的内部空间形成所述第一容纳腔。
  3. 根据权利要求2所述的磁共振设备，其特征在于，各所述壳体均设置有内壁和外壁，且内壁和外壁间隔设置并形成通道；
    通过第三壳体密封连接所述第一壳体与所述第二壳体，使得所述第一壳体、所述第二壳体与所述第三壳体各自的通道连通，形成所述真空腔。
  4. 根据权利要求2或3所述的磁共振设备，其特征在于，每个所述壳体包括至少两个壳体件，所述至少两个壳体件密封连接，用于形成所述壳体。
  5. 根据权利要求4所述的磁共振设备，其特征在于，所述至少两个壳体件中每一个壳体件的内壁和外壁间隔设置形成一个子通道，基于所述至少两个壳体件密封连接，使相邻两个所述子通道拼接密封，用于形成各所述壳体的通道。
  6. 根据权利要求2或3所述的磁共振设备，其特征在于，所述第三壳体密封连接所述第一壳体与所述第二壳体，包括：
    所述第三壳体设有插接部；
    所述第一壳体与所述第二壳体分别设有套接部；
    所述第三壳体通过插接部分别插入所述第一壳体与第二壳体的套接部中，以所述第三壳体实现密封连接所述第一壳体与所述第二壳体。
  7. 根据权利要求4或5所述的磁共振设备，其特征在于，所述至少两个壳体件至少包括：
    第一壳体件，设有插接部；
    第二壳体件，设有套接部；
    所述至少两个壳体件密封连接，形成所述壳体，包括：
    所述第一壳体件通过插接部插入所述第二壳体件的套接部中，以实现密封连接所述第一壳体件与所述第二壳体件。
  8. 根据权利要求6所述的磁共振设备，其特征在于，所述第一壳体和第二壳体中的至少之一与所述第三壳体的连接处还设置有密封层，所述密封层用于将所述第一壳体和第二壳体中的至少之一与所述第三壳体密封连接。
  9. 根据权利要求8所述的磁共振设备，其特征在于，所述密封层夹设于所述第一壳体和所述第二壳体中的至少之一的所述套接部的侧壁与所述第三壳体的所述插接部的侧壁之间。
  10. 根据权利要求6或9所述的磁共振设备，其特征在于，所述第一壳体和第二壳体中的至少之一的连接处与所述第三壳体之间还设置有吸音层，所述吸音层用于将所述第一壳体和所述第二壳体中的至少之一与所述第三壳体密封连接，并吸收振动噪音。
  11. 根据权利要求10所述的磁共振设备，其特征在于，所述吸音层设置于所述套接部与所述插接部之间。
  12. 根据权利要求7所述的磁共振设备，其特征在于，所述第一壳体件与所述第二壳体件的连接处还设置有密封层，所述密封层用于密封连接所述第一壳体件与所述第二壳体件。
  13. 根据权利要求12所述的磁共振设备，其特征在于，所述密封层夹设于所述第一壳体件的插接部的侧壁与所述第二壳体件的套接部的侧壁之间。
  14. 根据权利要求7或13所述的磁共振设备，其特征在于，所述第一壳体件与所述第二壳体件的连接处还设置有吸音层，所述吸音层用于密封连接所述第一壳体件与所述第二壳体件，并吸收振动噪音。
  15. 根据权利要求14所述的磁共振设备，其特征在于，所述吸音层设置于所述插接部与所述套接部之间。
  16. 根据权利要求6-15任一项所述的磁共振设备，其特征在于，所述插接部设有卡部，所述套接部设有扣部，所述插接部插入所述套接部中，并使所述卡部与所述扣部卡扣固定。
  17. 根据权利要求1-16任一项所述的磁共振设备，其特征在于，所述磁体部件包括永磁体或超导磁体中的一种。
  18. 根据权利要求1-17任一项所述的磁共振设备，其特征在于，所述磁共振设备还包括用于改进磁场均匀性的匀场线圈；
    所述匀场线圈设置于所述梯度线圈与所述磁体部件之间；和/或
    所述匀场线圈集成在所述梯度线圈的内部。
  19. 根据权利要求1-18任一项所述的磁共振设备，其特征在于，所述磁共振设备还包括支撑部件以及第一连接件，所述支撑部件的部分设置于所述壳体组件的外部，所述支撑部件的部分设置于所述第二容纳腔，并与所述磁体部件固定连接；
    所述第一连接件设置于所述第二容纳腔内，用于连接所述磁体部件以及所述壳体组件。
  20. 根据权利要求1-19任一项所述的磁共振设备，其特征在于，所述磁共振设备还包括第二连接件，所述梯度线圈通过所述第二连接件与所述磁体部件固定连接。
  21. 根据权利要求1-20任一项所述的磁共振设备，其特征在于，所述磁共振设备还包括电连接器以及减振垫，所述电连接器通过所述减振垫固设于所述壳体组件，且所述电连接器的一端与所述梯度线圈电连接，所述电连接器的另一端在所述壳体组件的外侧形成电连接部。
PCT/CN2022/107100 2022-02-28 2022-07-21 磁共振设备 WO2023159864A1 (zh)

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