Magnetic resonance coil assembly and magnetic resonance system

Abstract

The application relates to a magnetic resonance coil assembly and a magnetic resonance system. The magnetic resonance coil assembly comprises a plurality of local coils, a plurality of first transmission coil assemblies and a plurality of second transmission coil assemblies. The plurality of local coils are used for receiving magnetic resonance signals generated by a detection site. Each first transmission coil assembly is connected with an output end of each local coil and is used for transmitting the magnetic resonance signals. Each second transmission coil assembly is wirelessly connected with each first transmission coil assembly and is used for transmitting the magnetic resonance signals. The second transmission coil assembly and the first transmission coil assembly transmit signals through electromagnetic coupling, instead of a traditional mixed line for signal transmission, thereby canceling the traditional mixed line and a plug, so that the overall weight of the magnetic resonance coil assembly is reduced, the magnetic resonance coil assembly is convenient to use, and the number of channels is not controlled by a cable and a plug, and can be set according to clinical image requirements.

Description

Technical Field

[0001] This application relates to the field of magnetic resonance technology, and in particular to a magnetic resonance coil assembly and a magnetic resonance system. Background Technology

[0002] Magnetic Resonance Imaging (MRI) is widely used for disease diagnosis and monitoring of treatment outcomes. During MRI scans, local coils are used to improve the signal-to-noise ratio and obtain high-quality images. However, different local coils are used for different areas of the body being scanned. The local coils are connected to the MRI system via pluggable connectors. This connection between the connector and the local coil involves a long, mixed-signal transmission line, making the coil itself heavy. Furthermore, the presence of this mixed-signal line makes the local coil inconvenient to use. Summary of the Invention

[0003] Therefore, it is necessary to provide a magnetic resonance coil assembly and a magnetic resonance system.

[0004] This application provides a magnetic resonance coil assembly. The magnetic resonance coil assembly includes multiple local coils, multiple first transmission coil assemblies, and multiple second transmission coil assemblies. The multiple local coils are used to receive magnetic resonance signals generated at a detection site. Each first transmission coil assembly is connected to the output terminal of each local coil for transmitting the magnetic resonance signal. Each second transmission coil assembly is wirelessly connected to each first transmission coil assembly for transmitting the magnetic resonance signal.

[0005] In one embodiment, the plurality of second transmission coil assemblies are spaced apart and disposed on both sides of the bed of the magnetic resonance system. The plurality of first transmission coil assemblies are spaced apart and movably disposed on both sides of the bed.

[0006] In one embodiment, the plurality of first transmission coil assemblies are disposed on both sides of the plurality of local coils, and the plurality of local coils and the hospital bed surround a detection space for detecting the detection site.

[0007] In one embodiment, the number of the plurality of second transmission coil assemblies is greater than the number of the plurality of first transmission coil assemblies.

[0008] In one embodiment, the spacing between two adjacent second transmission coil assemblies is equal to the spacing between two adjacent first transmission coil assemblies, and each second transmission coil assembly is identical to each first transmission coil assembly.

[0009] In one embodiment, the spacing between two adjacent second transmission coil components is no greater than the radius of the second transmission coil component.

[0010] In one embodiment, each local coil includes a coil body, a matching circuit, a first passive detuning circuit, and an amplifier. The matching circuit is connected to the output terminal of the coil body and is used to adjust the resonant frequency of the resonant circuit of the local coil. The first passive detuning circuit is connected in parallel with the coil body and is used to control the resonant state of the local coil. The input terminal of the amplifier is connected to the output terminal of the matching circuit, and the output terminal of the amplifier is connected to the first transmission coil assembly.

[0011] In one embodiment, the first passive detuning circuit includes a capacitive circuit, a switching circuit, and an inductive circuit. One end of the capacitive circuit is connected to a first end of the coil body, and the other end of the capacitive circuit is connected to a second end of the coil body, with the first end and the second end positioned opposite each other. One end of the switching circuit is connected to the first end. One end of the inductive circuit is connected to the other end of the switching circuit, and the other end of the inductive circuit is connected to the second end.

[0012] In one embodiment, the power supply terminals of the plurality of amplifiers are connected and connected to the power supply connection structure of the hospital bed.

[0013] In one embodiment, this application provides a magnetic resonance system, which includes a plurality of local coils, a plurality of first transmission coil assemblies, a plurality of second transmission coil assemblies, and a signal processing unit. The plurality of local coils are used to receive magnetic resonance signals generated by a detection site. Each first transmission coil assembly is connected to the output terminal of each of the local coils for transmitting the magnetic resonance signals. Each second transmission coil assembly is wirelessly connected to each of the first transmission coil assemblies for transmitting the magnetic resonance signals. The signal processing unit is connected to the plurality of second transmission coil assemblies for receiving and processing the magnetic resonance signals.

[0014] In the aforementioned magnetic resonance coil assembly, one second transmission coil assembly is wirelessly connected to one first transmission coil assembly for receiving and transmitting the magnetic resonance signal. The wireless connection can be electromagnetic coupling. The second transmission coil assembly and the first transmission coil assembly transmit signals via electromagnetic coupling, replacing the traditional mixed-lay cable method and eliminating the need for traditional mixed-lay cables and plugs. Furthermore, the electromagnetic coupling method reduces the overall weight of the magnetic resonance coil assembly, making it more convenient to use. Simultaneously, the wireless connection method allows the number of channels to be independent of cables and plugs, enabling the number of units to be set according to clinical imaging needs. Attached Figure Description

[0015] To more clearly illustrate the technical solutions in the embodiments of this application or the conventional technology, the drawings used in the description of the embodiments or the conventional technology 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.

[0016] Figure 1 A circuit diagram of a magnetic resonance coil assembly provided in one embodiment of this application.

[0017] Figure 2 This is a schematic diagram of the connection structure between the local coil and the first transmission coil assembly in one embodiment of this application.

[0018] Figure 3 This is a schematic diagram of the overall structure of the outer shell and the connecting box in one embodiment of this application.

[0019] Figure 4 This is a schematic diagram of the connection structure between the magnetic resonance coil assembly and the hospital bed in one embodiment provided in this application.

[0020] Figure 5 A schematic diagram of patient testing is provided in one embodiment of this application.

[0021] Figure 6 A schematic diagram of the circuit structure of the first transmission coil assembly and the second transmission coil assembly in one embodiment provided in this application.

[0022] Figure 7 This is a schematic diagram of the circuit structure of a local coil in one embodiment of this application.

[0023] Figure 8 A circuit diagram of a magnetic resonance coil assembly provided in one embodiment of this application.

[0024] Figure 9 This is a schematic diagram of the connection between the power supply connection terminal and the power supply connection structure in one embodiment of this application.

[0025] Explanation of reference numerals in the attached figures:

[0026] Magnetic resonance coil assembly 100, local coil 10, housing 101, connection box 102, first transmission coil assembly 20, second transmission coil assembly 30, hospital bed 40, detection space 410, coil body 110, matching circuit 120, first passive detuning circuit 130, amplifier 150, power supply connection terminal 151, power supply connection structure 420, signal processing unit 50, second passive detuning circuit 230, and third passive detuning circuit 330. Detailed Implementation

[0027] To facilitate understanding of this application, a more complete description will be provided below with reference to the accompanying drawings, which illustrate embodiments of the present application. However, the present application can be implemented in many different forms and is not limited to the embodiments described herein. Rather, these embodiments are provided so that the disclosure of this application will be thorough and complete.

[0028] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the application.

[0029] It is understood that the terms "first," "second," etc., used herein may be used to describe various elements, but these elements are not limited by these terms. These terms are only used to distinguish one element from another. For example, without departing from the scope of this application, a first resistor may be referred to as a second resistor, and similarly, a second resistor may be referred to as a first resistor. Both the first resistor and the second resistor are resistors, but they are not the same resistor.

[0030] It is understood that the term "connection" in the following embodiments should be understood as "electrical connection," "communication connection," etc., if the connected circuits, modules, units, etc., have electrical signal or data transmission with each other.

[0031] When used herein, the singular forms of “a,” “an,” and “the” may also include the plural forms unless the context clearly indicates otherwise. It should also be understood that the terms “comprising / including” or “having,” etc., specify the presence of the stated features, wholes, steps, operations, components, parts, or combinations thereof, but do not preclude the possibility of the presence or addition of one or more other features, wholes, steps, operations, components, parts, or combinations thereof. Meanwhile, the term “and / or” as used in this specification includes any and all combinations of the associated listed items.

[0032] Please see Figure 1 This application provides a magnetic resonance coil assembly 100. The magnetic resonance coil assembly 100 includes a plurality of local coils 10, a plurality of first transmission coil assemblies 20, and a plurality of second transmission coil assemblies 30. The plurality of local coils 10 are used to receive magnetic resonance signals generated at a detection site. Each first transmission coil assembly 20 is connected to the output terminal of each local coil 10 for transmitting the magnetic resonance signal. Each second transmission coil assembly 30 is wirelessly connected to each first transmission coil assembly 20 for transmitting the magnetic resonance signal. The local coils 10 can be ring coils, rectangular coils, butterfly coils, saddle-shaped coils, etc. The detection site can be a head, abdomen, chest, or leg, etc. The plurality of local coils 10 form a receiving array, which can provide high-quality images. One first transmission coil assembly 20 is connected to the output terminal of one local coil 10 for receiving and transmitting the magnetic resonance signal.

[0033] A second transmission coil assembly 30 is wirelessly connected to a first transmission coil assembly 20 for receiving and transmitting the magnetic resonance signals. The wireless connection can be electromagnetic coupling. The second transmission coil assembly 30 and the first transmission coil assembly 20 transmit signals via electromagnetic coupling, replacing traditional mixed-layup cables and eliminating the need for traditional cables and plugs. Furthermore, the electromagnetic coupling between the second transmission coil assembly 30 and the first transmission coil assembly 20 reduces the overall weight of the magnetic resonance coil assembly 100, making it more convenient to use. Simultaneously, the wireless connection of the magnetic resonance coil assembly 100 eliminates the limitation on the number of channels caused by cables and plugs on the bedside table, allowing the number of units to be set according to clinical imaging needs.

[0034] Please see Figure 2 and Figure 3In one embodiment, the magnetic resonance coil assembly 100 further includes a housing 101. The housing 101 can be made of a flexible or rigid material. Flexible materials can be, for example, leather, fabric, or plastic. Alternatively, flexible materials can be made of fabrics such as cotton, synthetic fibers, wool, or fiber cloth, or plastics such as soft rubber. Rigid materials can be, for example, rigid plastics such as modified polystyrene (ABS), polyoxymethylene (POM), polystyrene (PS), polymethyl methacrylate (PMMA), or modified polycarbonate (PC).

[0035] In one embodiment, the outer shell 101 is made of a flexible material, the connecting box 102 is made of a rigid material, and the connecting box 102 clamps the edge of the outer shell. The material of the connecting box 102 can be a rigid plastic with mold-processing plasticity.

[0036] When worn by the patient, the outer shell 101 is lightweight and flexible, conforming better to the human body and improving the receiving sensitivity of the magnetic resonance coil assembly 100. This makes the patient's examination site more comfortable, facilitating cooperation during the examination and alleviating the patient's anxiety. The multiple local coils 10 can be evenly distributed within the outer shell 101 to receive the magnetic resonance signals generated by the patient's examination site. The connecting box 102 is made of rigid material, facilitating installation and fixation from both sides, resulting in a more secure and stable fit.

[0037] In one embodiment, the housing 101 includes a first end and a second end, and all or part of the housing 101 located between the first end and the second end can be bent to form a predetermined shape. The ability to bend all or part of the housing 101 to form a predetermined shape can adapt to different detection sites on the patient. The bending shape can vary according to the body shape of different patients. The plurality of local coils 10 are disposed inside the housing 101.

[0038] The magnetic resonance coil assembly 100 further includes at least one connecting box 102, which is disposed at the first end or the second end. The connecting box 102 is electrically connected to the circuit structure, electronic devices, local coils, etc. disposed inside the housing 101. The connecting box 102 extends along the edge of the first end or the edge of the second end.

[0039] One or more of the first transmission coil assemblies 20 are disposed within the connection box 102. The first transmission coil assembly 20 is connected to at least one of the plurality of local coils 10 to enable wireless communication between the magnetic resonance coil assembly 100 and the outside. The plurality of local coils 10 form a receiving array, which can provide high-quality images. The first transmission coil assembly 20, connected to at least one of the plurality of local coils 10, is used to receive the magnetic resonance signal and transmit the magnetic resonance signal to the outside. The wireless connection method can be electromagnetic coupling. Signal transmission via electromagnetic coupling replaces traditional mixed-lay cable signal transmission, thereby eliminating the need for traditional mixed-lay cables and plugs. The electromagnetic coupling method for signal transmission reduces the overall weight of the magnetic resonance coil assembly 100, making it more convenient to use. Simultaneously, the wireless communication method for signal transmission eliminates cable limitations on the number of channels, allowing the number of units to be set according to clinical imaging needs.

[0040] In one embodiment, the magnetic resonance coil assembly 100 includes two connecting boxes 102. The connecting boxes 102 are respectively disposed at the first end and the second end. Alternatively, the two connecting boxes 102 can be understood as being disposed on both sides of the outer casing 101. Alternatively, the connecting boxes 102 can be understood as being clamped to the edge of the outer casing 101. The two connecting boxes 102 are electrically connected to the circuit structures, electronic devices, local coils, etc., disposed inside the outer casing 101. The plurality of first transmission coil assemblies 20 are disposed within the connecting boxes 102.

[0041] Each of the first transmission coil assemblies 20 is led out from the output terminal of each of the local coils 10 and extends to both sides of the housing 101. The plurality of first transmission coil assemblies 20 are distributed on both sides and evenly arranged within the two connecting boxes 102 for wireless transmission of the magnetic resonance signal. The magnetic resonance coil assembly 100 uses the connecting box 102, which facilitates installation and fixation from both sides.

[0042] In one embodiment, a plurality of first transmission coil assemblies 20 are disposed within the connection box 102. The plurality of first transmission coil assemblies 20 are arranged side-by-side at intervals along the extending direction of the connection box 102. The connection box 102 extends along the edge of either the first end or the edge of the second end. Furthermore, the plurality of first transmission coil assemblies 20 are spaced apart within the connection box 102 and arranged side-by-side at intervals along the extending direction of either the first end or the second end. Alternatively, the plurality of first transmission coil assemblies 20 can be understood as being arranged side-by-side at intervals on one or both sides of the plurality of local coils 10.

[0043] Please see Figure 4In one embodiment, the plurality of second transmission coil assemblies 30 are spaced apart on both sides of the magnetic resonance imaging (MRI) system bed 40. This can be understood as the plurality of second transmission coil assemblies 30 being spaced apart on both sides of the bed 40 along the patient's body extension direction. The plurality of first transmission coil assemblies 20 are spaced apart and movably disposed on both sides of the bed 40. This can be understood as the plurality of first transmission coil assemblies 20 being spaced apart and movable along both sides of the bed 40. The plurality of first transmission coil assemblies 20 are respectively connected to the plurality of local coils 10. The movement of the plurality of first transmission coil assemblies 20 along both sides of the bed 40 allows for the detection of different parts of the patient's body, providing greater flexibility.

[0044] When each of the first transmission coil components 20 overlaps with each of the second transmission coil components 30, and the resonant frequency of each of the first transmission coil components 20 and each of the second transmission coil components 30 is the same as the operating frequency of the magnetic resonance system, each of the second transmission coil components 30 and each of the first transmission coil components 20 transmits the magnetic resonance signal.

[0045] According to the principle of near-field communication, when the first transmission coil assembly 20 and the second transmission coil assembly 30 overlap and their resonant frequencies are the same as the operating frequency of the magnetic resonance system, a strong coupling exists between them, enabling the transmission of the magnetic resonance signal. The first transmission coil assembly 20 and the second transmission coil assembly 30 transmit signals wirelessly, eliminating the need for a cross-connect cable. By using the first transmission coil assembly 20 and the second transmission coil assembly 30, traditional cross-connect cables and plugs can be eliminated, reducing the overall weight of the magnetic resonance coil assembly 100 and making it more convenient to use.

[0046] In one embodiment, the connecting box 102 is attached to the edge of the hospital bed 40 by adhesive bonding. The magnetic resonance coil assembly 100 can be bent to form a predetermined shape, and the bent magnetic resonance coil assembly 100 can be fixed to the hospital bed 40 by the connecting box 102. The adhesive bonding method can be achieved, for example, by providing Velcro to the surface of the connecting box 102 and the hospital bed 40, or by providing adhesive to the connecting box 102 and the hospital bed 40.

[0047] In one embodiment, the first transmission coil assembly 20 is arranged in a one-to-one correspondence with the local coil 10, and the size of the first transmission coil assembly 20 is smaller than the size of the local coil 10. The output terminals of the plurality of first transmission coil assemblies 20 are connected to the output terminals of the plurality of local coils 10 in a one-to-one correspondence. The plurality of second transmission coil assemblies 30 are arranged on both sides of the hospital bed 40. When the magnetic resonance coil assembly 100 is working, one first transmission coil assembly 20 and one second transmission coil assembly 30 completely overlap, and the hospital bed 40 and the local coil 10 transmit signals through coupling pairs, realizing wireless transmission function.

[0048] In one embodiment, when one of the first transmission coil components 20 and one of the second transmission coil components 30 completely overlap, the connection box 102 is provided between the first transmission coil component 20 and the second transmission coil component 30, which allows the first transmission coil component 20 and the second transmission coil component 30 to maintain a distance and avoid interference caused by contact between them.

[0049] Please see Figure 4 and Figure 5 In one embodiment, the plurality of local coils 10 cover the detection area of ​​the patient. The plurality of first transmission coil assemblies 20 are spaced apart on both sides of the plurality of local coils 10. The plurality of second transmission coil assemblies 30 are fixedly spaced apart on both sides of the hospital bed 40. This can be understood as the plurality of second transmission coil assemblies 30 being fixedly disposed on both sides of the hospital bed 40 along the patient's body extension direction. Alternatively, it can be understood as the plurality of second transmission coil assemblies 30 being spaced apart along the length direction of the hospital bed 40.

[0050] The plurality of first transmission coil assemblies 20 and the plurality of second transmission coil assemblies 30 on both sides of the plurality of local coils 10 are connected one-to-one. The plurality of local coils 10 and the hospital bed 40 surround to form a detection space 410 for detecting the detection site. The patient can lie flat on the hospital bed 40. The detection space 410 changes depending on the detection site. The patient lies flat within the detection space 410.

[0051] When an abdominal examination is required on a patient, the plurality of first transmission coil assemblies 20 are moved, causing the plurality of local coils 10 to move, thereby moving the detection space 410 to the patient's abdominal area. The magnetic resonance signal is transmitted between the plurality of local coils 10 and the bed 40 through the plurality of first transmission coil assemblies 20 and the plurality of second transmission coil assemblies 30.

[0052] In one embodiment, the hospital bed 40 is provided with movable slots 430 on both sides along the patient's body extension direction. The plurality of second transmission coil assemblies 30 are spaced apart within the movable slots 430. The movable slots 430 extend along the patient's body extension direction and extend to the entire hospital bed 40. The plurality of first transmission coil assemblies 20 are disposed within the two connecting boxes 102. The two connecting boxes 102 are slidably disposed within the movable slots 430. By moving the positions of the two connecting boxes 102, the plurality of local coils 10 are moved, thereby enabling detection of different body parts. The magnetic resonance coil assembly 100 can move on the hospital bed 40 to adapt to different patient body shapes and improve patient comfort.

[0053] In one embodiment, the number of the plurality of second transmission coil assemblies 30 is greater than the number of the plurality of first transmission coil assemblies 20.

[0054] The plurality of second transmission coil assemblies 30 are disposed on both sides of the bed 40 along the patient's body extension direction. The plurality of local coils 10 cover the patient's detection area. The output terminals of the plurality of local coils 10 are connected to the plurality of first transmission coil assemblies 20. The plurality of first transmission coil assemblies 20 move along both sides of the bed 40, thereby driving the plurality of local coils 10 to move along the patient's body extension direction. The number of the plurality of second transmission coil assemblies 30 is greater than the number of the plurality of first transmission coil assemblies 20, which allows the magnetic resonance coil assembly 100 to detect different parts of the patient, thereby achieving local detection. When the plurality of first transmission coil assemblies 20 overlap with a portion of the plurality of second transmission coil assemblies 30 in a one-to-one correspondence and are at the same operating frequency as the magnetic resonance system, signal transmission occurs between the first transmission coil assembly 20 and the corresponding second transmission coil assembly 30.

[0055] In one embodiment, the number of the plurality of second transmission coil assemblies 30 and the number of the plurality of first transmission coil assemblies 20 can be adjusted according to actual needs.

[0056] In one embodiment, the magnetic resonance coil assembly 100 includes 24-channel coils. Figure 2 As can be seen, one of the first transmission coil assemblies 20 and one of the local coils 10 form a channel coil. The plurality of first transmission coil assemblies 20 are distributed on both sides of the plurality of local coils 10.

[0057] In one embodiment, the spacing between two adjacent second transmission coil components 30 is equal to the spacing between two adjacent first transmission coil components 20. Each second transmission coil component 30 is identical to each first transmission coil component 20. The resonant frequencies of the second transmission coil components 30 and the first transmission coil components 20 are the same. The sizes of the second transmission coil components 30 and the first transmission coil components 20 are also the same. The equal spacing between two adjacent second transmission coil components 30 and the equal spacing between two adjacent first transmission coil components 20 facilitates the overlapping of the second transmission coil components 30 and the first transmission coil components 20. This overlapping of the second transmission coil components 30 and the first transmission coil components 20 can improve transmission efficiency.

[0058] In one embodiment, the spacing between two adjacent second transmission coil assemblies 30 is no greater than the radius of the second transmission coil assembly 30. The spacing between two adjacent first transmission coil assemblies 20 is no greater than the radius of the first transmission coil assembly 20. The plurality of second transmission coil assemblies 30 are arranged at equal intervals. The plurality of first transmission coil assemblies 20 are arranged at equal intervals. By setting the spacing between two adjacent second transmission coil assemblies 30 and the spacing between two adjacent first transmission coil assemblies 20, coupling interference between adjacent transmission coil assemblies can be avoided.

[0059] In one embodiment, the diameter of the second transmission coil assembly 30 is 30 mm to 50 mm. The diameter of the first transmission coil assembly 20 is 30 mm to 50 mm. The spacing between two adjacent second transmission coil assemblies 30 is 15 mm to 25 mm. The spacing between two adjacent first transmission coil assemblies 20 is 15 mm to 25 mm.

[0060] Please see Figure 6 In one embodiment, each of the first transmission coil assemblies 20 includes a first transmission coil body 210 and a first matching circuit 220. The first matching circuit 220 is connected in series with the first transmission coil body 210. The first matching circuit 220 may include one or more combinations of capacitors and inductors. In this embodiment, the first matching circuit 220 includes a capacitor cf1 and an inductor L6. Each of the second transmission coil assemblies 30 includes a second transmission coil body 310 and a second matching circuit 320. The second matching circuit 320 is connected in series with the second transmission coil body 310. The second matching circuit 320 may include one or more combinations of capacitors and inductors. In this embodiment, the second matching circuit 320 includes a capacitor cf2 and an inductor L7.

[0061] The first transmission coil assembly 20 forms a resonant circuit. The second transmission coil assembly 30 forms a resonant circuit. The resonant frequencies of the first transmission coil assembly 20 and the second transmission coil assembly 30 are adjustable. The first transmission coil assembly 20 and the second transmission coil assembly 30 are paired together to achieve signal transmission at different frequencies. The magnetic resonance coil assembly 100 eliminates the need for traditional mixed-wire cables and plugs, making the coil lighter and more portable.

[0062] Please see Figure 7 In one embodiment, each local coil 10 includes a coil body 110, a matching circuit 120, a first passive detuning circuit 130, and an amplifier 150. The matching circuit 120 is connected to the output terminal of the coil body 110 and is used to adjust the resonant frequency of the resonant circuit of the local coil 10. The first passive detuning circuit 130 is connected in parallel with the coil body 110 and is used to control the resonant state of the local coil 10. The input terminal of the amplifier 150 is connected to the output terminal of the matching circuit 120, and the output terminal of the amplifier 150 is connected to the first transmission coil assembly 20.

[0063] The coil body 110 can be bent into one or more geometric shapes. The coil body 110 can extend along a set direction to form shapes such as rings, rectangles, squares, butterflies, and saddles. The coil body 110 is used to receive the magnetic resonance signal. The matching circuit 120 includes a capacitor, an inductor, or a combination of both. The matching circuit 120 is connected to the output terminal of the coil body 110 and is used to adjust the resonant frequency of the resonant circuit of the local coil 10. When a tuning frequency needs to be selected, the resonant frequency of the resonant circuit of the local coil 10 can be adjusted by adjusting the capacitor and inductor of the matching circuit 120, thereby receiving the magnetic resonance signal and outputting it through the output terminal of the amplifier 150. The first passive detuning circuit 130 is used to adjust the resonant state of the local coil 10. When the transmitting coil is working, the first passive detuning circuit 130 controls the local coil 10 to be in a detuned state, causing the resonant frequency of its resonant circuit to deviate and change, making it unable to receive the magnetic resonance signal and avoiding coupling interference between coils.

[0064] In one embodiment, the first passive detuning circuit 130 includes a capacitive circuit 131, a switching circuit 132, and an inductive circuit 133. One end of the capacitive circuit 131 is connected to a first end of the coil body 110. The other end of the capacitive circuit 131 is connected to a second end of the coil body 110. The first end and the second end are positioned opposite each other. One end of the switching circuit 132 is connected to the first end. One end of the inductive circuit 133 is connected to the other end of the switching circuit 132. The other end of the inductive circuit 133 is connected to the second end.

[0065] The first passive detuning circuit 130 may include a first diode D1, a second diode D2, a first inductor L1, a first capacitor C1, and a second capacitor C2. Specifically: the first diode D1 and the second diode D2 form a switching circuit 132; the first inductor L1 forms an inductive circuit 133; and the first capacitor C1 and the second capacitor C2 form a capacitive circuit 131.

[0066] One end of the capacitive circuit 131 is connected to the first end of the coil body 110, and the other end of the capacitive circuit 131 is connected to the second end of the coil body 110, with the first end and the second end positioned opposite each other. One end of the switching circuit 132 is connected to the first end. The other end of the switching circuit 132 is connected to the inductive circuit 133, and the inductive circuit 133 is connected to the second end. The switching circuit 132 is used to disconnect when no induced current is generated in the coil body 110. The switching circuit 132 is also used to turn on when an induced current is generated in the coil body 110.

[0067] When the coil body 110 is within the magnetic field generated by the main magnet, an induced current is generated in the coil body 110 due to the time-varying radio frequency field generated by the transmitting coil. This current flows into the first passive detuning circuit 130. The switching circuit 132 is also used to conduct when an induced current is generated in the coil body 110. Current flows through the inductive circuit 133, and the capacitive circuit 131 is connected in parallel with the inductive circuit 133 to the first and second ends of the coil body 110. The first passive detuning circuit 130 resonates in parallel and is in a high-impedance state. The first passive detuning circuit 130 blocks the first and second ends of the coil body 110, putting the coil body 110 in an open-circuit state, i.e., the partial coil 10 is in a detuned state.

[0068] The first diode D1 is turned on when a current in a first direction (counterclockwise) is generated in the coil body 110. The second diode D2 is turned on when a current in a second direction (clockwise) is generated in the coil body 110. The first direction is opposite to the second direction.

[0069] When the transmitting coil is operating, the magnetic field it generates is a changing magnetic field. The current generated in the coil body 110 of the local coil 10 is also a current with a changing direction. That is, the induced current in the coil body 110 flows alternately along the first direction and the second direction.

[0070] When the induction in the coil body 110 flows along the first direction, the first diode D1 is turned on, the second diode D2 is turned off, and the current in the first inductor L1 flows along the first direction. The first diode D1 is connected in series with the first inductor L1. The branch after the first diode D1 and the first inductor L1 are connected in series resonates in parallel with the capacitive circuit 131, forming a high-impedance state. The first passive detuning circuit 130 blocks the first end and the second end of the coil body 110, so that the coil body 110 is in an open-circuit state, that is, the partial coil 10 is in a detuned state.

[0071] When the inductance in the coil body 110 flows in the second direction, the second diode D2 conducts, the first diode D1 is open, and the current in the first inductor L1 flows in the second direction. The second diode D2 is connected in series with the first inductor L1 and resonates in parallel with the capacitive circuit 131, forming a high-impedance state. The first passive detuning circuit 130 blocks the first and second ends of the coil body 110, putting the coil body 110 in an open-circuit state, that is, the local coil 10 is in a detuned state.

[0072] When the transmitting coil is not working, both the first diode D1 and the second diode D2 are in the open state, and no current flows through the first inductor L1. The capacitive circuit 131 and the inductive circuit 133 are not connected in parallel for resonance. No current flows inside the coil body 110, and the coil body 110 mainly generates the detection signal by resonating with human tissue.

[0073] The first diode D1 and the second diode D2 are connected in reverse parallel. Due to the AC operating environment, when the transmitting coil is working, one of the first diode D1 and the second diode D2 will conduct. Consequently, the first inductor L1 is connected in parallel with the capacitive circuit 131, causing the resonant frequency of the resonant circuit to deviate and change, resulting in a high-impedance state and achieving a detuning effect.

[0074] In one embodiment, the matching circuit 120 includes a second inductor L2 and a capacitor Cm. One end of the capacitor Cm is connected to a first output terminal of the coil body 110, and the other end of the capacitor Cm is connected to a second output terminal of the coil body 110. One end of the second inductor L2 is connected to the first output terminal of the coil body 110. The other end of the second inductor L2 is connected to a first input terminal of the amplifier 150. The second input terminal of the amplifier 150 is connected to a second output terminal of the coil body 110.

[0075] The amplifier 150 receives the magnetic resonance signal and amplifies it. A radio frequency signal is then output from the amplifier 150 to the first transmission coil assembly 20 for signal transmission.

[0076] Please see Figure 8 In one embodiment, each of the first transmission coil assemblies 20 further includes a second passive detuning circuit 230. The second passive detuning circuit 230 includes a third diode D3, a fourth diode D4, a fourth inductor L4, a third capacitor C3, and a fourth capacitor C4. Specifically: the third diode D3 and the fourth diode D4 form a switching circuit (not shown in the figure); the fourth inductor L4 forms an inductive circuit (not shown in the figure); and the third capacitor C3 and the fourth capacitor C4 form a capacitive circuit (not shown in the figure).

[0077] One end of the capacitive circuit is connected to the first end of the first transmission coil body 210, and the other end of the capacitive circuit is connected to the second end of the first transmission coil body 210, with the first end and the second end positioned opposite each other. One end of the switching circuit is connected to the first end. The other end of the switching circuit is connected to one end of the inductive circuit, and the other end of the inductive circuit is connected to the second end. The switching circuit is used to disconnect when no induced current is generated in the first transmission coil body 210. The switching circuit is also used to turn on when an induced current is generated in the first transmission coil body 210.

[0078] When the first transmission coil body 210 is within the magnetic field generated by the main magnet, an induced current is generated in the first transmission coil body 210 due to the time-varying radio frequency field generated by the transmitting coil. This current flows into the second passive detuning circuit 230. A switching circuit is also used to turn on when an induced current is generated in the first transmission coil body 210. Current flows through the inductive circuit, and the capacitive circuit is connected in parallel with the inductive circuit to the first and second terminals of the first transmission coil body 210. The second passive detuning circuit 230 resonates in parallel and is in a high-impedance state. The second passive detuning circuit 230 blocks the first and second terminals of the first transmission coil body 210, causing the first transmission coil body 210 to be in an open-circuit state, i.e., the first transmission coil assembly 20 is in a detuned state and does not transmit signals.

[0079] The third diode D3 is turned on when a current in a first direction (counterclockwise) is generated in the first transmission coil body 210. The fourth diode D4 is turned on when a current in a second direction (clockwise) is generated in the first transmission coil body 210. The first direction is opposite to the second direction.

[0080] When the transmitting coil is operational, the magnetic field it generates is a changing magnetic field. The current generated by the first transmission coil body 210 in the first transmission coil assembly 20 is also a current with a changing direction. The induced current in the first transmission coil body 210 flows alternately along the first direction and the second direction.

[0081] When the induction in the first transmission coil body 210 flows along the first direction, the third diode D3 conducts, the fourth diode D4 is open, and the current in the fourth inductor L4 flows along the first direction. The third diode D3 and the fourth inductor L4 are connected in series. The branch after the third diode D3 and the fourth inductor L4 are connected in parallel with the capacitive circuit and resonate, forming a high-impedance state. The second passive detuning circuit 230 blocks the first end and the second end of the first transmission coil body 210, so that the first transmission coil body 210 is in an open-circuit state, that is, the first transmission coil assembly 20 is in a detuned state.

[0082] When the inductance in the first transmission coil body 210 flows along the second direction, the fourth diode D4 conducts, the third diode D3 is open, and the current in the fourth inductor L4 flows along the second direction. The fourth diode D4 is connected in series with the fourth inductor L4 and resonates in parallel with the capacitive circuit, forming a high-impedance state. The second passive detuning circuit 230 blocks the first end and the second end of the first transmission coil body 210, putting the first transmission coil body 210 in an open-circuit state, that is, the first transmission coil assembly 20 is in a detuned state.

[0083] When the transmitting coil is not working, both the third diode D3 and the fourth diode D4 are in the off state, and no current flows through the fourth inductor L4. The capacitive circuit and the inductive circuit are not connected in parallel for resonance. No current flows inside the first transmission coil body 210, which is used to transmit the magnetic resonance signal received by the local coil 10.

[0084] Each of the second transmission coil assemblies 30 further includes a third passive detuning circuit 330. The third passive detuning circuit 330 includes a fifth diode D5, a sixth diode D6, a fifth inductor L5, a fifth capacitor C5, and a sixth capacitor C6. Specifically: the fifth diode D5 and the sixth diode D6 form a switching circuit (not shown in the figure); the fifth inductor L5 forms an inductive circuit (not shown in the figure); and the fifth capacitor C5 and the sixth capacitor C6 form a capacitive circuit (not shown in the figure).

[0085] One end of the capacitive circuit is connected to the first end of the second transmission coil body 310, and the other end of the capacitive circuit is connected to the second end of the second transmission coil body 310, with the first end and the second end positioned opposite each other. One end of the switching circuit is connected to the first end. The other end of the switching circuit is connected to one end of the inductive circuit, and the other end of the inductive circuit is connected to the second end. The switching circuit is used to disconnect when no induced current is generated in the second transmission coil body 310. The switching circuit is also used to turn on when an induced current is generated in the second transmission coil body 310.

[0086] When the second transmission coil body 310 is within the magnetic field generated by the main magnet, an induced current is generated in the second transmission coil body 310 due to the time-varying radio frequency field generated by the transmitting coil. This current flows into the third passive detuning circuit 330. A switching circuit is also used to turn on when an induced current is generated in the second transmission coil body 310. Current flows through the inductive circuit, and the capacitive circuit is connected in parallel with the inductive circuit to the first and second terminals of the second transmission coil body 310. The second transmission coil body 310 resonates in parallel and is in a high-impedance state. The third passive detuning circuit 330 blocks the first and second terminals of the second transmission coil body 310, putting the second transmission coil body 310 in an open-circuit state, i.e., the second transmission coil assembly 30 is in a detuned state and does not transmit signals.

[0087] The fifth diode D5 is turned on when a current in a first direction (counterclockwise) is generated in the second transmission coil body 310. The sixth diode D6 is turned on when a current in a second direction (clockwise) is generated in the second transmission coil body 310. The first direction is opposite to the second direction.

[0088] When the transmitting coil is operational, the magnetic field it generates is a changing magnetic field. The current generated by the second transmission coil body 310 in the second transmission coil assembly 30 is also a changing current. The induced current in the second transmission coil body 310 flows alternately along the first direction and the second direction.

[0089] When the induction in the second transmission coil body 310 flows along the first direction, the fifth diode D5 conducts, the sixth diode D6 is open, and the current in the fifth inductor L5 flows along the first direction. The fifth diode D5 and the fifth inductor L5 are connected in series. The branch after the fifth diode D5 and the fifth inductor L5 are connected in series resonates in parallel with the capacitive circuit, forming a high-impedance state. The third passive detuning circuit 330 blocks the first end and the second end of the second transmission coil body 310, so that the second transmission coil body 310 is in an open-circuit state, that is, the second transmission coil assembly 30 is in a detuned state.

[0090] When the inductance in the second transmission coil body 310 flows along the second direction, the sixth diode D6 conducts, the fifth diode D5 is open-circuited, and the current in the fifth inductor L5 flows along the second direction. The sixth diode D6 is connected in series with the fifth inductor L5 and resonates in parallel with the capacitive circuit, forming a high-impedance state. The third passive detuning circuit 330 blocks the first and second ends of the second transmission coil body 310, putting the second transmission coil body 310 in an open-circuit state, that is, the second transmission coil assembly 30 is in a detuned state.

[0091] When the transmitting coil is not operating, both the fifth diode D5 and the sixth diode D6 are in the open state, and no current flows through the fifth inductor L5. The capacitive circuit and the inductive circuit do not resonate in parallel. No current flows inside the second transmission coil body 310, which is used to transmit the magnetic resonance signal.

[0092] In one embodiment, the first passive detuning circuit 130, the second passive detuning circuit 230, and the third passive detuning circuit 330 can be integrated on a circuit board to form a modular structure. The modular structure can be directly connected in series at the middle of the coil body. The integration of the first passive detuning circuit 130, the second passive detuning circuit 230, and the third passive detuning circuit 330 onto the circuit board occupies less space and does not affect the size and weight of the magnetic resonance coil assembly 100.

[0093] Please see Figure 9 In one embodiment, the power supply terminals of the plurality of amplifiers 150 are connected and connected to the power supply connection structure 420 of the hospital bed 40.

[0094] The power supply terminals of multiple amplifiers 150 are connected to form a single power supply connection terminal 151. This power supply connection terminal 151 extends from one side of each of the multiple first transmission coil assemblies 20. When the multiple first transmission coil assemblies 20 are movably mounted on the hospital bed 40, the power supply connection terminal 151 connects to the power supply connection structure 420 of the hospital bed 40, thereby supplying power to the multiple amplifiers 150. When the power supply connection terminal 151 is correspondingly connected to the power supply connection structure 420, the multiple first transmission coil assemblies 20 can be aligned and fixed, achieving a positioning function.

[0095] The power supply connection structure 420 can be a metal contactor. After the plurality of first transmission coil assemblies 20 are placed on both sides of the hospital bed 40, the power supply connection terminal 151 is connected to the power supply connection structure 420 to supply power to the plurality of amplifiers 150. Since the power supply terminals of the plurality of amplifiers 150 are connected and a single power supply connection terminal 151 is led out, the power supply connection structure 420 can provide parallel power to the plurality of amplifiers 150. A single power supply signal can simultaneously power the plurality of amplifiers 150.

[0096] Optionally, the connection box 102 is provided with an auxiliary mark to assist in the arrangement of the first transmission coil assembly 20 and the second transmission coil assembly 30 within the connection box 102. In one embodiment, a plurality of power supply connection structures 420 are provided on both sides of the hospital bed 40. The plurality of first transmission coil assemblies 20 are movably disposed on both sides of the hospital bed 40, and each side is provided with a power supply connection end 151 serving as an auxiliary mark for connecting to the power supply connection structures 420 on both sides of the hospital bed 40. When the plurality of first transmission coil assemblies 20 move, the power supply connection end 151 can correspond to the power supply connection structures 420 on both sides of the hospital bed 40 and assist in positioning and alignment.

[0097] In one embodiment, the connection box 102 is provided with the power supply connection terminal 151, and the hospital bed 40 is provided with a metal contactor. The power supply connection terminal 151 cooperates with the metal contactor to enable the hospital bed 40 to supply power to the magnetic resonance coil assembly 100.

[0098] In one embodiment, every 12 of the local coils 10 and the amplifier 150 share a single power supply connection terminal 151.

[0099] In one embodiment, this application provides a magnetic resonance imaging (MRI) system. The MRI system includes a plurality of local coils 10, a plurality of first transmission coil assemblies 20, a plurality of second transmission coil assemblies 30, and a signal processing unit 50. The plurality of local coils 10 are used to receive magnetic resonance signals generated by a detection site. Each first transmission coil assembly 20 is connected to the output terminal of each local coil 10 for transmitting the magnetic resonance signal. Each second transmission coil assembly 30 is wirelessly connected to each first transmission coil assembly 20 for transmitting the magnetic resonance signal. The signal processing unit 50 is connected to the plurality of second transmission coil assemblies 30 for receiving the magnetic resonance signal and processing the magnetic resonance signal.

[0100] The local coil 10 receives the magnetic resonance signal and transmits it to the signal processing unit 50 via the first transmission coil assembly 20 and the second transmission coil assembly 30. The signal processing unit 50 may include a phase detector, an analog-to-digital converter, etc., for acquiring the magnetic resonance signal received by the local coil 10 and performing data processing to generate spectral data, thereby enabling medical imaging of the patient.

[0101] The magnetic resonance system also includes a superconducting magnet unit, a gradient coil unit, a controller unit, an examination table, and a display unit. The magnetic resonance system can also be used as a medical imaging system for imaging human subjects, and may also include veterinary or non-medical systems for imaging non-human subjects, luggage, etc.

[0102] In one embodiment, this application provides a magnetic resonance imaging (MRI) system. The MRI system includes a magnetic resonance coil assembly 100 and a hospital bed 40. The MRI coil assembly 100 includes a housing 101 and a plurality of local coils 10 disposed inside the housing 101. The housing 101 includes a first end and a second end. A connection box 102 is provided at the first end and / or the second end. One or more first transmission coil assemblies 20 are disposed within the connection box 102. The hospital bed 40 is used to support the MRI coil assembly 100. A plurality of second transmission coil assemblies 30 are disposed on one or both edges of the hospital bed 40. The first transmission coil assemblies 20 cooperate with the second transmission coil assemblies 30 to achieve wireless communication between the MRI coil assembly 100 and the hospital bed 40. A description of the MRI coil assembly 100 and the hospital bed 40 can be found in the relevant descriptions in the above embodiments.

[0103] In the description of this specification, the references to terms such as "some embodiments," "other embodiments," "ideal embodiments," etc., refer to specific features, structures, materials, or characteristics described in connection with that embodiment or example that are included in at least one embodiment or example of this application. In this specification, the illustrative descriptions of the above terms do not necessarily refer to the same embodiments or examples.

[0104] 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.

[0105] The embodiments described above are merely illustrative of 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 magnetic resonance coil assembly, characterized in that, include: The outer shell (101) includes a first end and a second end, the first end and the second end being movable along both sides of the bed (40) of the magnetic resonance system, and the outer shell (101) located between the first end and the second end is bent to form a predetermined shape; Multiple local coils (10) distributed within the outer shell (101) are used to receive magnetic resonance signals generated by the detection site. The multiple local coils (10) and the bed (40) surround and form a detection space (410). The connecting box (102) is disposed at the first end or the second end; A plurality of first transmission coil assemblies (20) spaced apart at the first end or the second end are disposed within the connection box (102), each first transmission coil assembly (20) being connected to the output end of each local coil (10) for transmitting the magnetic resonance signal; A plurality of second transmission coil assemblies (30) are spaced apart on both sides of the hospital bed (40). Each second transmission coil assembly (30) is used to transmit the magnetic resonance signal between each second transmission coil assembly when each first transmission coil assembly overlaps with each second transmission coil assembly based on an electromagnetic coupling connection with each first transmission coil assembly (20). The first transmission coil assembly (20) and the second transmission coil assembly (30) both form a resonant circuit. The resonant frequency of the first transmission coil assembly (20) and the resonant frequency of the second transmission coil assembly (30) can be adjusted. The first transmission coil assembly (20) and the second transmission coil assembly (30) are paired and combined to realize the transmission of signals at different frequencies.

2. The magnetic resonance coil assembly as claimed in claim 1, characterized in that, The plurality of first transmission coil assemblies (20) are disposed on both sides of the plurality of local coils (10), and the plurality of local coils (10) and the hospital bed (40) surround to form a detection space (410) for detecting the detection site.

3. The magnetic resonance coil assembly as described in claim 1, characterized in that, The number of the plurality of second transmission coil assemblies (30) is greater than the number of the plurality of first transmission coil assemblies (20).

4. The magnetic resonance coil assembly as claimed in claim 1, characterized in that, The spacing between two adjacent second transmission coil assemblies (30) is equal to the spacing between two adjacent first transmission coil assemblies (20), and each second transmission coil assembly (30) is the same as each first transmission coil assembly (20).

5. The magnetic resonance coil assembly as described in claim 3, characterized in that, The distance between two adjacent second transmission coil assemblies (30) is not greater than the radius of the second transmission coil assembly (30).

6. The magnetic resonance coil assembly as claimed in claim 1, characterized in that, Each of the local coils (10) includes: Coil body (110); A matching circuit (120) is connected to the output terminal of the coil body (110) and is used to adjust the resonant frequency of the resonant circuit of the local coil (10). The first passive detuning circuit (130) is connected in parallel with the coil body (110) and is used to control the resonance state of the local coil (10); An amplifier (150) is connected to the output of the matching circuit (120) and the output of the amplifier (150) is connected to the first transmission coil assembly (20).

7. The magnetic resonance coil assembly as claimed in claim 6, characterized in that, The first passive detuning circuit (130) includes: A capacitive circuit (131) is provided, one end of which is connected to the first end of the coil body (110), and the other end of which is connected to the second end of the coil body (110), with the first end and the second end being disposed opposite to each other. A switching circuit (132), one end of which is connected to the first end; An inductive circuit (133) is provided, one end of which is connected to the other end of the switching circuit (132), and the other end of which is connected to the second end.

8. The magnetic resonance coil assembly as claimed in claim 6, characterized in that, The power supply terminals of the plurality of amplifiers (150) are connected and connected to the power supply connection structure (420) of the hospital bed (40).

9. The magnetic resonance coil assembly as claimed in claim 1, characterized in that, The outer shell is made of flexible material to fit the detection area.

10. A magnetic resonance system, characterized in that, include: The outer shell (101) includes a first end and a second end, the first end and the second end being disposed on both sides of the bed (40) of the magnetic resonance system, and the outer shell (101) located between the first end and the second end is bent to form a predetermined shape; Multiple local coils (10) distributed within the outer shell (101) are used to receive magnetic resonance signals generated by the detection site. The multiple local coils (10) and the bed (40) surround and form a detection space (410). The connecting box (102) is disposed at the first end or the second end; A plurality of first transmission coil assemblies (20) spaced apart at the first end or the second end are disposed within the connection box (102), each first transmission coil assembly (20) being connected to the output end of each local coil (10) for transmitting the magnetic resonance signal; A plurality of second transmission coil assemblies (30) are spaced apart on both sides of the hospital bed (40). Each second transmission coil assembly (30) is used to transmit the magnetic resonance signal between each second transmission coil assembly when each first transmission coil assembly overlaps with each second transmission coil assembly based on an electromagnetic coupling connection with each first transmission coil assembly (20). A signal processing unit (50) is connected to the plurality of second transmission coil assemblies (30) for receiving the magnetic resonance signal and processing the magnetic resonance signal; The first transmission coil assembly (20) and the second transmission coil assembly (30) both form a resonant circuit. The resonant frequency of the first transmission coil assembly (20) and the resonant frequency of the second transmission coil assembly (30) can be adjusted. The first transmission coil assembly (20) and the second transmission coil assembly (30) are paired and combined to realize the transmission of signals at different frequencies.

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