Shielding coil, transmitting and receiving integrated coil, magnetic resonance scanning equipment and magnetic resonance system

Abstract

The invention relates to a shielding coil, a receiving and transmitting integrated coil, magnetic resonance scanning equipment and a magnetic resonance system, the shielding coil is applied to the magnetic resonance scanning equipment, and a first diode is arranged on the shielding coil; the first diode disconnects the access of the shielding coil under the condition that the receiving coil in the magnetic resonance scanning equipment is in a working state, so that the shielding coil is in a non-working state; and when the receiving coil is in a non-working state, the access of the shielding coil is conducted, so that the shielding coil is in a working state. The shielding coil provided by the invention can reduce the image of the receiving coil and improve the signal-to-noise ratio of the receiving coil.

Description

Technical Field

[0001] The present application relates to the field of magnetic resonance technology, and in particular to a shielding coil, a transceiver-integrated coil, a magnetic resonance scanning device and a magnetic resonance system. Background Art

[0002] In magnetic resonance systems, as the field strength increases, the wavelength becomes shorter and shorter, and it becomes increasingly difficult to obtain a uniform radio frequency field within a larger field of view (FOV). Therefore, local transceiver coils are increasingly used under high field strength. Transceiver coils include a transmitting coil, a receiving coil, and a shielding coil. The transmitting coil is used to generate a transmitting field, the receiving coil is used to receive magnetic resonance signals, and the shielding coil is used to shield the influence of the transmitting field generated by the transmitting coil on external devices.

[0003] In order to improve the practicality of the transceiver coil, it is necessary to reduce the volume and weight of the transceiver coil as much as possible while ensuring the clinical requirements for FOV. To reduce the volume of the transceiver coil, it is necessary to reduce the distance between the shielding coil, the receiving coil and the transmitting coil.

[0004] However, when the distance between the shielding coil and the receiving coil is reduced, the shielding coil will affect the receiving coil, resulting in a decrease in the signal-to-noise ratio of the receiving coil. Summary of the invention

[0005] Based on this, it is necessary to provide a shielding coil, a transceiver coil, a magnetic resonance scanning device and a magnetic resonance system that can reduce the impact of the shielding coil on the receiving coil in order to address the above technical problems.

[0006] In a first aspect, the present application provides a shielding coil, the shielding coil is applied to a magnetic resonance scanning device, and a first diode is arranged on the shielding coil;

[0007] The first diode disconnects the path of the shielding coil when the receiving coil in the magnetic resonance scanning device is in the working state, so that the shielding coil is in the non-working state; and connects the path of the shielding coil when the receiving coil is in the non-working state, so that the shielding coil is in the working state.

[0008] In one of the embodiments, the shielding coil further includes a first inductor component and a second inductor component;

[0009] One end of the first inductor component is connected to the first end of the first diode, and one end of the second inductor component is connected to the second end of the first diode;

[0010] The other end of the first inductance component is connected to a control device in the magnetic resonance scanning device, and the other end of the second inductance component is connected to the control device.

[0011] In one embodiment, the shielding coil further includes a first capacitor component and a third inductor component, and the first capacitor component, the third inductor component and the first diode are connected in parallel.

[0012] In one embodiment, the first diode is connected to a control device in the magnetic resonance scanning apparatus, and the control device is used to control the first diode to be disconnected when the receiving coil is in an operating state, and to control the first diode to be turned on when the receiving coil is in a non-operating state.

[0013] In the second aspect, an embodiment of the present application provides an integrated transceiver coil, which includes a transmitting coil, a receiving coil and a shielding coil as provided in the first aspect above, and the transmitting coil is arranged between the shielding coil and the receiving coil; the transmitting coil is a coil of a birdcage structure; and the receiving coil is composed of multiple phase array coils.

[0014] In one embodiment, a plurality of second capacitor components are disposed on the transmitting coil, and a second diode is disposed on the end ring of the transmitting coil.

[0015] In one embodiment, each phase array coil includes a third capacitor component and a high resistance circuit, the third capacitor component is connected in series to the phase array coil, and the high resistance circuit is connected in parallel to the third capacitor component.

[0016] In one embodiment, the high resistance circuit includes a third diode and a fourth inductor component;

[0017] The first end of the third diode is connected to the first end of the fourth inductor component, the second end of the third diode is connected to the first end of the third capacitor component, and the second end of the fourth inductor component is connected to the second end of the third capacitor component.

[0018] In a third aspect, an embodiment of the present application provides a magnetic resonance scanning device, including a control device and a transceiver coil as provided in the second aspect above;

[0019] The control device is used to control the working state of the transceiver coil.

[0020] In a fourth aspect, an embodiment of the present application provides a magnetic resonance system, comprising a processing device and a magnetic resonance scanning device as provided in the third aspect above.

[0021] The embodiment of the present application provides a shielding coil, a transceiver integrated coil, a magnetic resonance scanning device and a magnetic resonance system. The shielding coil is applied to the magnetic resonance scanning device, and the shielding coil is provided with a first diode; the first diode disconnects the path of the shielding coil when the receiving coil in the magnetic resonance scanning device is in a working state, so that the shielding coil is in a non-working state; the path of the shielding coil is turned on when the receiving coil is in a non-working state, so that the shielding coil is in a working state. In this embodiment, when the receiving coil is in a working state, that is, when receiving a magnetic resonance signal, the shielding coil is in a non-working state, so that the shielding coil will not affect the magnetic resonance signal received by the receiving coil, thereby improving the signal-to-noise ratio of the receiving coil. Moreover, when the receiving coil is in a non-working state, that is, when the transmitting coil is in a working state, the shielding coil is in a working state, which can shield the influence of the transmitting field generated by the transmitting coil on the external device, and the influence of the external device on the receiving coil and the transmitting coil. In this way, the radio frequency safety of the coil in the magnetic resonance scanning device can be improved, and the practicality and reliability of the magnetic resonance scanning device can be improved. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] Figure 1 A schematic diagram of the effect of a shielding coil in one embodiment;

[0023] Figure 2 A schematic diagram of the structure of a shielding coil in one embodiment;

[0024] Figure 3 This is a schematic diagram of the structure of a transceiver integrated coil in one embodiment;

[0025] Figure 4 A schematic diagram of the structure of a shielding coil in another embodiment;

[0026] Figure 5 A schematic diagram of the structure of a shielding coil in another embodiment;

[0027] Figure 6 A schematic diagram of the structure of a transmitting coil in one embodiment;

[0028] Figure 7 A schematic diagram of the structure of a receiving coil in one embodiment;

[0029] Figure 8 It is a schematic diagram of the structure of a transmitting coil in another embodiment;

[0030] Fig. 9 It is a schematic diagram of the structure of a transmitting coil in another embodiment;

[0031] Fig.10 is a schematic diagram of an end ring of a transmitting coil in one embodiment;

[0032] Fig.11It is a schematic diagram of the structure of a receiving coil in another embodiment;

[0033] Fig.12 is a schematic structural diagram of a magnetic resonance scanning device in one embodiment;

[0034] Fig.13 is a schematic structural diagram of a magnetic resonance system in one embodiment;

[0035] Fig.14 A schematic diagram of a simulation of the effect of a shielding coil in one embodiment;

[0036] Fig.15 Schematic diagram of the signal-to-noise ratio of a single-turn coil in the absence of metal copper in one embodiment;

[0037] Fig.16 FIG. 1 is a schematic diagram of the signal-to-noise ratio of a single-turn coil in the presence of metallic copper in one embodiment.

[0038] Description of reference numerals:

[0039] 10. Magnetic resonance scanning equipment; 11. Transceiver coil; 12. Control device; 20. Magnetic resonance system; 21. Processing equipment; 100. Shielding coil; 101. First diode; 102. First inductor component; 103. Second inductor component; 104. First capacitor component; 105. Third inductor component; 200. Receiving coil; 201. Phased array coil; 202. Third capacitor component; 203. High resistance circuit; 204. Third diode; 205. Fourth inductor component; 300. Transmitting coil; 301. Second capacitor component. DETAILED DESCRIPTION

[0040] In order to make the purpose, technical solution and advantages of the present application more clearly understood, the present application is further described in detail below in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain the present application and are not used to limit the present application.

[0041] The serial numbers assigned to the components herein, such as "first", "second", etc., are only used to distinguish the objects described and do not have any order or technical meaning. The "connection" and "coupling" mentioned in this application, unless otherwise specified, include direct and indirect connections (couplings). In the description of this application, it should be understood that the orientation or position relationship indicated by the terms "upper", "lower", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside", "clockwise", "counterclockwise", etc. are based on the orientation or position relationship shown in the accompanying drawings, which is only for the convenience of describing this application and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore cannot be understood as a limitation to this application.

[0042] In the present application, unless otherwise clearly specified and limited, a first feature being “above” or “below” a second feature may mean that the first and second features are in direct contact, or the first and second features are in indirect contact through an intermediate medium. Moreover, a first feature being “above”, “above”, and “above” a 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. A first feature being “below”, “below”, and “below” a second feature may mean that the first feature is directly below or obliquely below the second feature, or simply means that the first feature is lower in level than the second feature.

[0043] First of all, before specifically introducing the technical solution of the embodiment of the present application, the technical background or technical evolution context on which the embodiment of the present application is based is introduced. In a magnetic resonance system, as the number of scenes increases, the wavelength becomes shorter and shorter, and it becomes increasingly difficult to obtain a uniform radio frequency field within a larger field of view (FOV). Therefore, local transceiver coils are increasingly used under high field strengths. The transceiver coil includes a transmitting coil, a receiving coil, and a shielding coil. The transmitting coil is used to generate a transmitting field, which causes the protons of the object to be scanned to flip under the transmitting field, and the signal of proton relaxation recovery (i.e., the magnetic resonance signal) is received by the receiving coil. The shielding coil is used to shield the influence of the transmitting field generated by the transmitting coil on external devices, as well as the influence of external devices on the transmitting field generated by the transmitting coil.

[0044] Integrating the transmitting coil, receiving coil and shielding coil into one whole will make the whole transmitting and receiving coil bulky and heavy, which is inconvenient for clinical use. In order to improve the practicality of the transmitting and receiving coil, it is necessary to reduce the volume and weight of the transmitting and receiving coil as much as possible while ensuring the clinical requirements for FOV. To reduce the volume of the transmitting and receiving coil, it is necessary to reduce the distance between the shielding coil, receiving coil and transmitting coil. However, if Figure 1 As shown, when the receiving coil receives the magnetic resonance signal, if the shielding coil is not disconnected, the shielding coil is equivalent to a grounding component, and the current of the receiving coil itself will generate an "image current". The direction of this image current is opposite to the direction of the receiving coil current, so that the current of the receiving coil is offset, resulting in a decrease in the signal-to-noise ratio of the receiving coil. Therefore, a reasonable design is required to ensure that the shielding coil has the least effect on the receiving coil, thereby obtaining a higher signal-to-noise ratio and field uniformity, and ensuring the RF safety of the transceiver coil. In response to this, the present application provides a shielding coil.

[0045] The technical solution of the present application and how the technical solution of the present application solves the technical problem are described in detail below with specific embodiments. The following specific embodiments can be combined with each other, and the same or similar concepts or processes may not be repeated in some embodiments. The embodiments of the present application will be described below in conjunction with the accompanying drawings.

[0046] See also Figure 2 An embodiment of the present application provides a shielding coil 100 , which is applied to a magnetic resonance scanning device. A first diode 101 is disposed on the shielding coil 100 .

[0047] The magnetic resonance scanning device includes a shielding coil 100, a receiving coil and a transmitting coil. The transmitting coil is used to generate a transmitting field, the receiving coil is used to receive magnetic resonance signals, and the shielding coil 100 is used to shield the influence of the transmitting field generated by the transmitting coil on external equipment, and the influence of external equipment on the receiving coil and the transmitting coil.

[0048] In an optional embodiment, the magnetic resonance scanning device includes a transceiver integrated coil 11 composed of a shielding coil 100, a receiving coil 200 and a transmitting coil 300. The structure of the transceiver integrated coil 11 is as follows: Figure 3 As shown, the transmitting coil 300 is located between the receiving coil 200 and the shielding coil 100. In other words, the receiving coil 200, the transmitting coil 300 and the shielding coil 100 are arranged in sequence from the inside to the outside. Optionally, the receiving coil 200, the transmitting coil 300 and the shielding coil 100 can be arranged on a substrate (not shown); the receiving coil 200, the transmitting coil 300 and the shielding coil 100 are arranged in a coaxial structure. The substrate can include two cylindrical insulators, which are spaced between the receiving coil 200, the transmitting coil 300 and the shielding coil 100. The substrate is provided with slots / openings that penetrate in the axial direction and the radial direction.

[0049] The shielding coil 100 is provided with a first diode 101, that is, the first diode 101 is connected in series in the shielding coil 100. The number of the first diodes 101 provided on the shielding coil 100 may be one or more, and this embodiment does not limit this, as long as its function can be achieved. The structure of the shielding coil 100 may be a full circular shield or an irregular partial shield. This embodiment does not limit the specific structure of the shielding coil 100, as long as its function can be achieved.

[0050] like Figure 2As shown, the structure of the shielding coil 100 is a circular shield with an open slot design, which can prevent eddy currents. Capacitor components are also included at the two ports of the shielding coil 100. The capacitor components and the first diode 101 are connected in series to the shielding coil 100. The normal operation of the shielding coil 100 can be ensured by the capacitor components and the first diode 101. At least two capacitor components and two first diodes 101 are arranged on one port of the shielding coil 100.

[0051] The first diode 101 disconnects the path of the shielding coil 100 when the receiving coil 200 in the magnetic resonance scanning device is in the working state, so that the shielding coil 100 is in the non-working state; and conducts the path of the shielding coil 100 when the receiving coil 200 is in the non-working state, so that the shielding coil 100 is in the working state.

[0052] The first diode 101 is a device with two electrodes that only allows current to flow in a single direction. When the receiving coil 200 in the magnetic resonance scanning device is in a working state, that is, the receiving coil 200 receives the magnetic resonance signal and the transmitting coil 300 does not generate a transmitting field, the first diode 101 is in a disconnected state. At this time, the path of the shielding coil 100 is disconnected by the first diode 101, so that the shielding coil 100 is in a non-working state. The first diode 101 is in a disconnected state when a current in a reverse direction is input to the first diode 101, that is, the current flows from the cathode to the anode of the first diode 101.

[0053] When the receiving coil 200 in the magnetic resonance scanning device is in a non-working state, that is, the receiving coil 200 does not receive a magnetic resonance signal, and the transmitting coil 300 generates a transmitting field, the first diode 101 is in a conducting state, and at this time, the path of the shielding coil 100 is conducted by the first diode 101, so that the shielding coil 100 is in a working state. The first diode 101 being in a conducting state may be that a forward current is input to the first diode 101, that is, the current flows from the positive electrode of the first diode 101 to the negative electrode.

[0054] In this embodiment, the working principle of the shielding coil 100 is as follows:

[0055] When the magnetic resonance scanning device is used to scan the object to be scanned, the transmitting coil 300 in the magnetic resonance scanning device is controlled to generate a transmitting field, and the receiving coil 200 in the magnetic resonance scanning device is controlled to receive magnetic resonance signals under the transmitting field, and at the same time, the first diode 101 in the shielding coil 100 is controlled to be in a disconnected state, so as to disconnect the path of the shielding coil 100 and put the shielding coil 100 in a non-working state; while the receiving coil 200 is controlled not to receive the magnetic resonance signal, the first diode 101 in the shielding coil 100 is controlled to be in a conducting state, so as to conduct the path of the shielding coil 100 and put the shielding coil 100 in a working state. That is to say, when the receiving coil 200 is in a working state, the shielding coil 100 is in a non-working state, and when the receiving coil 200 is in a non-working state, the shielding coil 100 is in a working state.

[0056] The shielding coil 100 provided in this embodiment is applied to a magnetic resonance scanning device, and the shielding coil 100 is provided with a first diode 101; the first diode 101 disconnects the path of the shielding coil 100 when the receiving coil 200 in the magnetic resonance scanning device is in the working state, so that the shielding coil 100 is in the non-working state; the path of the shielding coil 100 is turned on when the receiving coil 200 is in the non-working state, so that the shielding coil 100 is in the working state. In this embodiment, when the receiving coil 200 is in the working state, that is, when receiving magnetic resonance signals, the shielding coil 100 is in the non-working state, so that the shielding coil 100 will not affect the magnetic resonance signals received by the receiving coil 200, thereby improving the signal-to-noise ratio of the receiving coil 200. In addition, when the receiving coil 200 is in the non-working state, that is, when the transmitting coil 300 is in the working state, the shielding coil 100 is in the working state, and can shield the influence of the transmission field generated by the transmitting coil 300 on the external device, and the influence of the external device on the receiving coil 200 and the transmitting coil 300. This can improve the radio frequency safety of the coil in the magnetic resonance scanning device, and improve the practicality and reliability of the magnetic resonance scanning device.

[0057] In one embodiment, Figure 4 As shown, the shielding coil 100 also includes a first inductor component 102 and a second inductor component 103. The first inductor component 102 may include one inductor or multiple inductors; similarly, the second inductor component 103 may include one inductor or multiple inductors. The structures of the first inductor component 102 and the second inductor component 103 may be the same or different, and this embodiment does not limit this, as long as the functions can be achieved.

[0058] One end of the first inductor component 102 is connected to the first end of the first diode 101 , and one end of the second inductor component 103 is connected to the second end of the first diode 101 .

[0059] The other end of the first inductance component 102 is connected to the control device 12 in the magnetic resonance scanning device, and the other end of the second inductance component 103 is connected to the control device 12 .

[0060] The magnetic resonance scanning device includes a control device 12 , which is used to control the working states of the shielding coil 100 , the receiving coil 200 and the transmitting coil 300 .

[0061] One end of the first inductor component 102 is connected to the first end of the first diode 101, and the other end of the first inductor component 102 is connected to the control device 12; one end of the second inductor component 103 is connected to the second end of the first diode 101, and the other end of the second inductor component 103 is connected to the control device 12. In other words, the control device 12 is connected to the first diode 101 through the first inductor component 102 and the second inductor component 103. Specifically, when the control device 12 is connected to the first diode 101, it includes two connection ports, one connection port is connected to the first end of the first diode 101 through the first inductor component 102; the other connection port is connected to the second end of the first diode 101 through the second inductor component 103. The control device 12 inputs a forward current or a reverse current to the first diode 101 through the first inductor component 102 and the second inductor component 103 to control the on and off of the first diode 101.

[0062] In this embodiment, the shielding coil 100 also includes a first inductance component 102 and a second inductance component 103. The first inductance component 102 and the second inductance component 103 conduct direct current and block alternating current. The control device 12 in the magnetic resonance scanning device is connected to the first diode 101 through the first inductance component 102 and the second inductance component 103. In this way, the influence of the alternating current generated by the control device 12 on the first diode 101 can be avoided, and the first diode 101 can be protected, thereby improving the practicality of the shielding coil 100.

[0063] In one embodiment, Figure 5 As shown, the shielding coil 100 further includes a first capacitor component 104 and a third inductor component 105 . The first capacitor component 104 , the third inductor component 105 are connected in parallel with the first diode 101 .

[0064] The first capacitor component 104 may include one capacitor or multiple capacitors. The third inductor component 105 may include one inductor or multiple inductors. This embodiment does not limit the specific structures of the first capacitor component 104 and the third inductor component 105, as long as their functions can be achieved.

[0065] The first capacitor component 104 is connected in parallel with the first diode 101, and the third inductor component 105 is also connected in parallel with the first diode 101. In other words, one end of the first capacitor component 104 is connected to the first end of the first diode 101, and the other end of the first capacitor component 104 is connected to the second end of the first diode 101; one end of the third inductor component 105 is connected to the first end of the first diode 101, and the other end of the third inductor component 105 is connected to the second end of the first diode 101.

[0066] In this embodiment, the first diode 101, the first capacitor component 104, and the third inductor component 105 in the shielding coil 100 are connected in parallel to form a high-resistance loop. In this way, when the receiving coil 200 in the magnetic resonance scanning device is in working state, the shielding coil 100 can be disconnected more thoroughly, thereby further reducing the impact of the shielding coil 100 on the receiving coil 200, thereby improving the signal-to-noise ratio of the receiving coil 200.

[0067] In one embodiment, the first diode 101 is connected to a control device 12 in a magnetic resonance scanning device, and the control device 12 is used to control the first diode 101 to be disconnected when the receiving coil 200 is in a working state, and to control the first diode 101 to be turned on when the receiving coil 200 is in a non-working state.

[0068] When the receiving coil 200 is in the working state, the control device 12 controls the first diode 101 to be in the disconnected state by inputting a reverse current into the first diode 101, so as to disconnect the path of the shielding coil 100 and put the shielding coil 100 in the non-working state. When the receiving coil 200 is in the non-working state, the control device 12 controls the first diode 101 to be in the conducting state by inputting a forward current into the first diode 101, so as to conduct the path of the shielding coil 100 and put the shielding coil 100 in the working state.

[0069] In an optional embodiment, the control device 12 supplies 150MA of forward power to the first diode 101 to turn on the first diode 101 ; the control device 12 supplies 30V of reverse power to the first diode 101 to turn on the first diode 101 .

[0070] In this embodiment, the first diode 101 is controlled to be disconnected or turned on by the control device 12, so the control method is convenient and fast.

[0071] In one embodiment, assuming that the first end of the first diode 101 is the positive electrode, the second end of the first diode 101 is the negative electrode, one end of the first inductor component 102 is connected to the positive electrode of the first diode 101; one end of the second inductor component 103 is connected to the negative electrode of the first diode 101. The control device 12 provides a current flowing from the positive electrode to the negative electrode to the first diode 101 through the first inductor component 102 and the second inductor component 103, so that the first diode 101 is turned on; the control device 12 provides a current flowing from the negative electrode to the positive electrode to the first diode 101 through the first inductor component 102 and the second inductor component 103, so that the first diode 101 is turned off.

[0072] Please continue to see Figure 3 An embodiment of the present application provides a transceiver integrated coil 11, which includes a transmitting coil 300, a receiving coil 200 and a shielding coil 100 as provided in the above embodiment. The transmitting coil 300 is disposed between the shielding coil 100 and the receiving coil 200.

[0073] For the description of the transmitting coil 300 , the receiving coil 200 and the shielding coil 100 in the transceiver integrated coil 11 , reference may be made to the specific description in the above embodiments, which will not be repeated here.

[0074] The transmitting coil 300 is a coil of a birdcage structure. The structure of the transmitting coil 300 is as follows: Figure 6 As shown, the transmitting coil 300 includes two end rings and a plurality of wires (legs) distributed between the two end rings. The end rings and the plurality of wires form a birdcage structure.

[0075] The receiving coil 200 is composed of a plurality of phase array coils 201. The structure of the receiving coil 200 is as follows: Figure 7 As shown, adjacent phase array coils 201 in the receiving coil 200 are decoupled by using any one of partial overlap, capacitive decoupling and inductive decoupling.

[0076] The transceiver-in-one coil 11 provided in this embodiment includes the shielding coil 100 provided in the above embodiment, so the transceiver-in-one coil 11 has all the beneficial effects of the shielding coil 100, which will not be described in detail here.

[0077] In one embodiment, Figure 6 As shown, a plurality of second capacitor components 301 are arranged on the transmitting coil 300 , and a second diode is arranged on the end ring of the transmitting coil 300 .

[0078] The second capacitor component 301 may include one capacitor or multiple capacitors. The multiple second capacitor components 301 may be distributed on the end rings in the transmitting coil 300, or distributed on multiple wires between two end rings. This embodiment does not limit the structure of the second capacitor component 301 and the specific positions where the multiple second capacitor components 310 are arranged in the transmitting coil 300. Figure 6 The capacitors C1 - C32 in FIG. 3 are the second capacitor component 301 arranged on the transmitting coil 300 .

[0079] like Figure 6 In the transmitting coil 300 shown in the figure, the plurality of second capacitor components 301 are all arranged on the end ring of the transmitting coil 300. The transmitting coil 300 formed in this way is a high-pass birdcage structure coil. The plurality of second capacitor components 301 can also be arranged on a plurality of wires between the two end rings of the transmitting coil 300, such as Figure 8 As shown, the transmitting coil 300 thus formed is a low-pass birdcage structure coil. The plurality of second capacitor components 301 can be simultaneously arranged on the two end rings of the transmitting coil 300 and the plurality of wires between the two end rings, such as Fig. 9 As shown, the transmitting coil 300 thus constructed is a bandpass birdcage structure coil.

[0080] A second diode (not shown) is provided on the end ring of the transmitting coil 300. By controlling the on-off of the second diode, the working state of the transmitting coil 300 can be controlled, that is, the transmitting coil 300 is placed in a tuned state or a detuned state by controlling the on-off of the second diode.

[0081] In addition, if Fig.10 As shown, two feeding ports port1 and port2 are provided on the end ring of the transmitting coil 300. The feeding ports are located on two orthogonal capacitors in the end ring, and RF signals with the same amplitude and a phase difference of 90 degrees are input through coaxial lines respectively, thereby forming a transmitting field (circularly polarized B1 field).

[0082] In an optional embodiment, the second diode is controlled to be turned on and off by a control device 12 in the magnetic resonance scanning apparatus.

[0083] In this embodiment, a plurality of second capacitors and resistors 301 are disposed on the transmitting coil 300 , and a second diode is disposed on the end ring of the transmitting coil 300 . Such a transmitting coil 300 has a simple structure.

[0084] In one embodiment, Fig.11 As shown, each phase array coil 201 includes a third capacitor component 202 and a high resistance circuit 203 . The third capacitor component 202 is connected in series to the phase array coil 201 , and the high resistance circuit 203 is connected in parallel to the third capacitor component 202 .

[0085] The third capacitor component 202 may include one capacitor or multiple capacitors. The third capacitor component 202 is connected in series in each phase array coil 201 in the receiving coil 200. The high resistance circuit 203 is connected in parallel with the third capacitor component 202. This embodiment does not limit the specific structure of the high resistance circuit 203, as long as its function can be achieved.

[0086] The working process of the high resistance circuit 203 is as follows:

[0087] By controlling the high-resistance circuit 203 to be in the working state, the receiving coil 200 is disconnected and in the detuned state, and the transmitting coil 300 is in the working state. By controlling the high-resistance circuit 203 to be in the non-working state, the receiving coil 200 has a complete path and is in the tuned state to receive the magnetic resonance signal, and the transmitting coil 300 is in the non-working state.

[0088] In this embodiment, a third capacitor component 202 is connected in series in each phase array coil 201 of the receiving coil 200, and a high resistance circuit 203 is connected in parallel with the third capacitor component 202. Such a receiving coil 200 has a simple structure and is easy to control.

[0089] Please continue to see Fig.11 In one embodiment, the high resistance circuit 203 includes a third diode 204 and a fourth inductor component 205. The fourth inductor component 205 may include one inductor or multiple inductors, which is not limited in this embodiment as long as its function can be achieved.

[0090] A first end of the third diode 204 is connected to a first end of the fourth inductor component 205 , a second end of the third diode 204 is connected to a first end of the third capacitor component 202 , and a second end of the fourth inductor component 205 is connected to a second end of the third capacitor component 202 .

[0091] The third diode 204 is connected in series with the fourth inductor component 205, and then connected in parallel with the third capacitor component 202 in the phase array coil 201. That is, the third diode 204 includes a first end and a second end, and the fourth inductor component 205 includes a first end and a second end. The first end of the third diode 204 is connected to the first end of the fourth inductor component 205, the second end of the third diode 204 is connected to the first end of the third capacitor component 202, and the second end of the fourth inductor component 205 is connected to the second end of the third capacitor component 202.

[0092] In this embodiment, the high resistance circuit 203 includes a third diode 204 and a fourth inductor component 205. Such a high resistance circuit 203 has a simple structure, and the third diode 204 and the fourth inductor component 205 are easy to obtain and have a low cost.

[0093] See also Fig.12 An embodiment of the present application provides a magnetic resonance scanning device 10, which includes a control device 12 and a transceiver coil 11 as provided in the above embodiment.

[0094] The control device 12 is used to control the working state of the transceiver coil 11 .

[0095] Specifically, the control device 12 can control the tuning state or detuning state of the transmitting coil 300 by controlling the on-off of the second diode in the transmitting coil 300 in the transceiver integrated coil 11. The control device 12 can control the on-off of the first diode 101 in the shielding coil 100 so that when the receiving coil 200 is in the working state, the shielding coil 100 is in the non-working state; when the receiving coil 200 is in the non-working state, the shielding coil 100 is in the working state. The control device 12 can control the on-off of the third diode 204 in the receiving coil 200 so that the receiving coil 200 is in the tuning state or the detuning state.

[0096] The magnetic resonance scanning device 10 provided in this embodiment includes the transceiver-in-one coil 11 provided in the above embodiment, and the magnetic resonance scanning device 10 has all the beneficial effects of the transceiver-in-one coil 11 provided in the above embodiment, which will not be described in detail here.

[0097] See also Fig.13 An embodiment of the present application provides a magnetic resonance system 20, which includes a processing device 21 and a magnetic resonance scanning device 10 as provided in the above embodiment.

[0098] The processing device 21 may be a computer device, which may be, but is not limited to, an industrial computer, a tablet computer, a control chip, and the like.

[0099] The processing device 21 is used to send a control signal to the control device 12 in the magnetic resonance scanning device 10 so that the control device 12 controls the working state of the transceiver coil 11. The processing device 21 is also used to receive the magnetic resonance signal received by the receiving coil 200 in the transceiver coil 11, and reconstruct the magnetic resonance signal to obtain a magnetic resonance image.

[0100] The magnetic resonance system 20 provided in this embodiment includes the magnetic resonance scanning device 10 , and the magnetic resonance system 20 has all the beneficial effects of the magnetic resonance scanning device 10 , which will not be described in detail herein.

[0101] In an optional embodiment, the shielding coil 100 may be simulated by simulation, such as Fig.14As shown in the figure, a single-turn coil with a size of 12cm*12cm and a resonant frequency of 128MHz is used as an example. The signal-to-noise ratio of the single-turn coil when no metal copper is placed 2.8cm above the single-turn coil is Fig.15 As shown in the figure, the signal-to-noise ratio of a single-turn coil when a metal copper is placed 2.8 cm above the single-turn coil is Fig.16 Compare Fig.15 and Fig.16 It can be seen that when metal copper is provided on the single-turn coil, the signal-to-noise ratio of the single-turn coil is reduced by about 35%. The closer the distance between the metal copper and the single-turn coil is, the more serious the deterioration of the signal-to-noise ratio is.

[0102] The technical features of the above embodiments may be combined arbitrarily. To make the description concise, 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.

[0103] The above-described embodiments only express several implementation methods of the present application, and the descriptions thereof are relatively specific and detailed, but they cannot be construed as limiting the scope of the present application. It should be noted that, for a person of ordinary skill in the art, several modifications and improvements can be made without departing from the concept of the present application, and these all belong to the protection scope of the present application. Therefore, the protection scope of the present application shall be subject to the attached claims.

Claims

1. A shielding coil, characterized in that: The shielding coil (100) is applied to a magnetic resonance scanning device (10), and a first diode (101) is arranged on the shielding coil (100); The first diode (101) disconnects the path of the shielding coil (100) when the receiving coil (200) in the magnetic resonance scanning device (10) is in an operating state, so that the shielding coil (100) is in a non-operating state; and conducts the path of the shielding coil (100) when the receiving coil (200) is in a non-operating state, so that the shielding coil (100) is in an operating state.

2. The shielding coil according to claim 1, characterized in that: The shielding coil (100) further comprises a first inductance component (102) and a second inductance component (103); One end of the first inductor component (102) is connected to the first end of the first diode (101), and one end of the second inductor component (103) is connected to the second end of the first diode (101); The other end of the first inductance component (102) is connected to a control device (12) in the magnetic resonance scanning device (10), and the other end of the second inductance component (103) is connected to the control device (12).

3. The shielding coil according to claim 2, characterized in that: The shielding coil (100) further comprises a first capacitor component (104) and a third inductor component (105), wherein the first capacitor component (104), the third inductor component (105) and the first diode (101) are connected in parallel.

4. The shielding coil according to any one of claims 1 to 3, characterized in that: The first diode (101) is connected to a control device (12) in the magnetic resonance scanning device (10), and the control device (12) is used to control the first diode (101) to be disconnected when the receiving coil (200) is in an operating state, and to control the first diode (101) to be turned on when the receiving coil (200) is in a non-operating state.

5. A transceiver integrated coil, characterized in that: The transceiver integrated coil (11) comprises a transmitting coil (300), a receiving coil (200) and a shielding coil (100) as described in any one of claims 1 to 4, wherein the transmitting coil (300) is arranged between the shielding coil (100) and the receiving coil (200); the transmitting coil (300) is a coil with a birdcage structure; and the receiving coil (200) is composed of a plurality of phase array coils (201).

6. The transceiver integrated coil according to claim 5, characterized in that: A plurality of second capacitor components (301) are arranged on the transmitting coil (300), and a second diode is arranged on the end ring of the transmitting coil (300).

7. The transceiver-in-one coil according to claim 5 or 6, characterized in that: Each of the phased array coils (201) comprises a third capacitor component (202) and a high resistance circuit (203); the third capacitor component (202) is connected in series to the phased array coil (201), and the high resistance circuit (203) is connected in parallel to the third capacitor component (202).

8. The transceiver integrated coil according to claim 7, characterized in that: The high resistance circuit (203) comprises a third diode (204) and a fourth inductor component (205); The first end of the third diode (204) is connected to the first end of the fourth inductor component (205), the second end of the third diode (204) is connected to the first end of the third capacitor component (202), and the second end of the fourth inductor component (205) is connected to the second end of the third capacitor component (202).

9. A magnetic resonance scanning device, characterized in that: The magnetic resonance scanning device (10) comprises a control device (12) and a transceiver coil (11) as claimed in any one of claims 5 to 8; The control device (12) is used to control the working state of the transceiver coil (11).

10. A magnetic resonance system, characterized in that: The magnetic resonance system (20) comprises a processing device (21) and a magnetic resonance scanning device (10) according to claim 9.

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