CN215641772U

CN215641772U - Magnetic resonance coil assembly and magnetic resonance system

Info

Publication number: CN215641772U
Application number: CN202121485171.XU
Authority: CN
Inventors: 陈莲; 王振; 陆海; 范贤文
Original assignee: Shanghai United Imaging Healthcare Co Ltd
Current assignee: Shanghai United Imaging Healthcare Co Ltd
Priority date: 2021-06-30
Filing date: 2021-06-30
Publication date: 2022-01-25
Anticipated expiration: 2031-06-30

Abstract

The present application relates to a magnetic resonance coil assembly and a magnetic resonance system. The magnetic resonance coil assembly includes a housing, a plurality of local coils, at least one junction box, and one or more first transmission coil assemblies. The shell comprises a first end part and a second end part, and all or part of the shell between the first end part and the second end part can be bent to form a set shape. A plurality of local coils are disposed inside the housing. At least one junction box is disposed at the first end or the second end, the junction box extending along an edge of the first end or an edge of the second end. One or more first transmission coil assemblies are disposed within the connection box, the first transmission coil assemblies being connected with at least one of the plurality of local coils to enable wireless communication of the magnetic resonance coil assembly with the outside. The magnetic resonance coil assembly performs signal transmission in a wireless communication mode, so that the overall weight of the magnetic resonance coil assembly is reduced, the use is more convenient, and the number of channels is not limited by cables.

Description

Magnetic resonance coil assembly and magnetic resonance system

Technical Field

The present application relates to the field of magnetic resonance technology, and in particular, to a magnetic resonance coil assembly and a magnetic resonance system.

Background

Magnetic Resonance Imaging (MRI) has been widely used for diagnosis of diseases and observation of therapeutic effects. When magnetic resonance is used for scanning, a local coil is used for scanning in order to improve the signal-to-noise ratio and obtain high-quality images. However, during use of local coils, different corresponding coils are used to scan different detection sites. When the local coil is connected with the magnetic resonance system, the local coil is connected through a connector in a plugging mode. The location of the connector to the local coil may have a long hybrid transmission line, resulting in a heavy coil itself. And the local coil is provided with a mixed wire, so that the use is inconvenient.

SUMMERY OF THE UTILITY MODEL

In view of the above, there is a need for a magnetic resonance coil assembly and a magnetic resonance system.

A magnetic resonance coil assembly includes a housing, a plurality of local coils, at least one connection box, and one or more first transmission coil assemblies. The shell comprises a first end part and a second end part, and all or part of the shell between the first end part and the second end part can be bent to form a set shape. A plurality of local coils are disposed inside the housing. At least one connection box is disposed at the first end or the second end, and the connection box extends along an edge of the first end or an edge of the second end. One or more first transmission coil assemblies disposed in the connection box and connected with at least one of the plurality of local coils to realize wireless communication between the magnetic resonance coil assembly and the outside.

In one embodiment, the connection box is provided at the first end portion and the second end portion, respectively.

In one embodiment, a plurality of the first transmission coil assemblies are arranged in the connecting box, and the plurality of the first transmission coil assemblies are arranged at intervals along the extending direction of the connecting box.

In one embodiment, the housing is made of a flexible material, the connection box is made of a hard material, and the connection box clamps the edge of the housing.

In one embodiment, the first transmission coil assemblies are arranged in one-to-one correspondence with the local coils, and the size of the first transmission coil assemblies is smaller than that of the local coils.

In one embodiment, the present application provides a magnetic resonance system. The magnetic resonance system comprises a magnetic resonance coil assembly and a patient bed. The magnetic resonance coil assembly comprises a shell and a plurality of local coils arranged inside the shell, the shell comprises a first end part and a second end part, a connecting box is arranged at the first end part and/or the second end part, and one or a plurality of first transmission coil assemblies are arranged in the connecting box. The sickbed is used for bearing the magnetic resonance coil assembly, a plurality of second transmission coil assemblies are arranged on one side edge or two side edges of the sickbed, and the first transmission coil assemblies are matched with the second transmission coil assemblies to realize wireless communication between the magnetic resonance coil assemblies and the sickbed.

In one embodiment, the connection box is arranged at the edge of the patient bed in an adhesion manner, the magnetic resonance coil assembly can be bent to form a set shape, and the bent magnetic resonance coil assembly can be fixed on the patient bed through the connection box.

In one embodiment, a plurality of the second transmission coil assemblies are arranged at intervals along the length direction of the patient bed, and the number of the first transmission coil assemblies is smaller than that of the second transmission coil assemblies.

In one embodiment, an auxiliary mark is arranged on the connecting box, and the auxiliary mark is used for assisting the first transmission coil assembly and the second transmission coil assembly in the connecting box to be arranged in a matched mode.

In one embodiment, the magnetic resonance coil assembly is an abdominal coil, the housing is made of a flexible material, the connection box is made of a hard material, and the connection box is clamped at the edge of the housing.

In one embodiment, a power supply connection end is arranged on the connection box, a metal contactor is arranged on the hospital bed, and the power supply connection end is matched with the metal contactor to supply power to the magnetic resonance coil assembly by the hospital bed.

In the magnetic resonance coil assembly, a plurality of the local coils form a receiving array, and high-quality images can be provided. The first transmission coil assembly is connected with at least one of the plurality of local coils, and is configured to receive the magnetic resonance signal and transmit the magnetic resonance signal to the outside. The wireless communication method may be an electromagnetic coupling method. Carry out signal transmission through the electromagnetic coupling mode, replaced traditional mixed dress line and carried out signal transmission, and then cancelled traditional mixed dress line and plug. The magnetic resonance coil assembly performs signal transmission in a wireless communication mode, so that the overall weight of the magnetic resonance coil assembly is reduced, and the magnetic resonance coil assembly is convenient to use. Meanwhile, the magnetic resonance coil assembly adopts a wireless communication mode to transmit signals, so that the number of channels is not limited by cables, and the number of units can be set according to clinical image requirements.

Drawings

In order to more clearly illustrate the technical solutions in the embodiments or the conventional technologies of the present application, the drawings used in the descriptions of the embodiments or the conventional technologies will be briefly introduced below, it is obvious that the drawings in the following descriptions are only some embodiments of the present application, and for those skilled in the art, other drawings can be obtained according to the drawings without creative efforts.

Figure 1 is a schematic circuit diagram of a magnetic resonance coil assembly in one embodiment provided by the present application.

Fig. 2 is a schematic diagram of a connection structure of a local coil and a first transmission coil assembly according to an embodiment of the present application.

Fig. 3 is a schematic diagram of the overall structure of the housing and the connection box in one embodiment provided in the present application.

Figure 4 is a schematic view of a connection structure of a magnetic resonance coil assembly and a patient bed according to an embodiment of the present invention.

FIG. 5 is a schematic illustration of patient testing in one embodiment provided herein.

Fig. 6 is a schematic circuit diagram of a first transmission coil assembly and a second transmission coil assembly according to an embodiment of the present disclosure.

Fig. 7 is a schematic circuit diagram of a local coil according to an embodiment of the present disclosure.

Figure 8 is a schematic circuit diagram of a magnetic resonance coil assembly in one embodiment provided by the present application.

Fig. 9 is a schematic connection diagram of a power supply connection terminal and a power supply connection structure in an embodiment provided by the present application.

Description of reference numerals:

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

Detailed Description

To facilitate an understanding of the present application, the present application will now be described more fully with reference to the accompanying drawings. Embodiments of the present application are set forth in the accompanying drawings. This application may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete.

Unless defined otherwise, 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 in the description of the present application is for the purpose of describing particular embodiments only and is not intended to be limiting of the application.

It will be understood that, as used herein, the terms "first," "second," and the like may be used herein 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, a first resistance may be referred to as a second resistance, and similarly, a second resistance may be referred to as a first resistance, without departing from the scope of the present application. The first resistance and the second resistance are both resistances, but they are not the same resistance.

It is to be understood that "connection" in the following embodiments is to be understood as "electrical connection", "communication connection", and the like if the connected circuits, modules, units, and the like have communication of electrical signals or data with each other.

As used herein, the singular forms "a", "an" and "the" may include the plural forms as well, unless the context clearly indicates otherwise. It will be further understood that the terms "comprises/comprising," "includes" or "including," etc., specify the presence of stated features, integers, steps, operations, components, parts, or combinations thereof, but do not preclude the presence or addition of one or more other features, integers, steps, operations, components, parts, or combinations thereof. Also, as used in this specification, the term "and/or" includes any and all combinations of the associated listed items.

Referring to fig. 1, a magnetic resonance coil assembly 100 is provided. 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 the examination site. Each of the first transmission coil assemblies 20 is connected to an output terminal of each of the local coils 10 for transmitting the magnetic resonance signal. Each of the second transmission coil assemblies 30 is wirelessly connected with each of the first transmission coil assemblies 20 for transmitting the magnetic resonance signal. The local coil 10 may be a loop coil, a rectangular coil, a butterfly coil, a saddle coil, etc. The detection part can be a head part, an abdomen part, a chest part or a leg part. A plurality of the local coils 10 form a receiving array, which can provide high quality images. One of the first transmission coil assemblies 20 is connected to an output of one of the local coils 10 for receiving and transmitting the magnetic resonance signals.

One of the second transmission coil assemblies 30 is wirelessly connected to one of the first transmission coil assemblies 20 for receiving and transmitting the magnetic resonance signal. The wireless connection may be electromagnetic coupling. The second transmission coil assembly 30 and the first transmission coil assembly 20 perform signal transmission in an electromagnetic coupling manner, so that the traditional mixed line is replaced for signal transmission, and the traditional mixed line and a plug are eliminated. Furthermore, the second transmission coil assembly 30 and the first transmission coil assembly 20 perform signal transmission through electromagnetic coupling, so that the overall weight of the magnetic resonance coil assembly 100 is reduced, and the use is convenient. Meanwhile, the magnetic resonance coil assembly 100 performs signal transmission in a wireless connection mode, so that the number of channels is not limited by cables and plugs on a hospital bed, and the number of units can be set according to clinical image requirements.

Referring to fig. 2 and 3, in one embodiment, the magnetic resonance coil assembly 100 further includes a housing 101. The material of the housing 101 may be a flexible material or a hard material. The flexible material may be, for example, one of a leather material, a cloth material, or a plastic. Alternatively, the flexible material may be made of cloth such as cotton wool, chemical fiber, woolen cloth, or fiber cloth, or plastic such as soft glue. The hard material may be a hard plastic such as modified polystyrene plastic (ABS), Polyoxymethylene (POM), polystyrene Plastic (PS), polymethyl methacrylate (PMMA), or modified polycarbonate material (PC).

In one embodiment, the housing 101 is made of flexible material, the connection box 102 is made of hard material, and the connection box 102 holds the edge of the housing. The material of the junction box 102 may be a rigid plastic with a molded plastic material.

When the patient wears the magnetic resonance coil assembly 100, the shell 101 is light and flexible, so that the magnetic resonance coil assembly can better fit the human body and the receiving sensitivity of the magnetic resonance coil assembly 100 is improved; the detection part of the patient is more comfortable, the cooperation examination is more facilitated, and the mood of the patient is relieved. The plurality of local coils 10 may be evenly distributed within the housing 101 for receiving magnetic resonance signals generated at a detection site of a patient. The connection box 102 is made of hard materials, so that the connection box is convenient to mount and fix from two sides and is firmer and more stable.

In one embodiment, the housing 101 includes a first end and a second end, and all or a portion of the housing 101 between the first end and the second end can be bent to form a set shape. All or part of the shell 101 can be bent to form a set shape, and can be adapted to different detection parts of a patient. The bending shape can be changed according to the body shapes of different patients. The plurality of local coils 10 are disposed inside the housing 101.

The magnetic resonance coil assembly 100 further comprises at least one connection box 102, the connection box 102 being arranged at the first end or the second end. The connection box 102 is electrically connected to a circuit structure, an electronic device, a partial coil, and the like provided inside the housing 101. And the connection box 102 extends along an edge of the first end or an edge of the second end.

One or more of the first transmission coil assemblies 20 are disposed within the junction box 102. And the first transmission coil assembly 20 is connected with at least one of the plurality of local coils 10 to enable wireless communication of the magnetic resonance coil assembly 100 with the outside. A plurality of the local coils 10 form a receiving array, which can provide high quality images. The first transmission coil assembly 20 is connected to at least one of the plurality of local coils 10, and receives the magnetic resonance signal and transmits the magnetic resonance signal to the outside. The wireless connection may be electromagnetic coupling. Carry out signal transmission through the electromagnetic coupling mode, replaced traditional mixed dress line and carried out signal transmission, and then cancelled traditional mixed dress line and plug. The magnetic resonance coil assembly 100 performs signal transmission in an electromagnetic coupling manner, so that the overall weight of the magnetic resonance coil assembly 100 is reduced, and the use is convenient. Meanwhile, the magnetic resonance coil assembly 100 performs signal transmission in a wireless communication mode, so that the number of channels is not limited by cables, and the number of units can be set according to clinical image requirements.

In one embodiment, the magnetic resonance coil assembly 100 includes two connection boxes 102. The connection box 102 is provided at the first end and the second end, respectively. It is also understood that two connection boxes 102 are respectively disposed on two sides of the housing 101. It will also be appreciated that the connection box 102 is clamped to the edge of the housing 101. The two connection boxes 102 are electrically connected to a circuit structure, an electronic device, a partial coil, and the like provided inside the housing 101. The plurality of first transmission coil assemblies 20 are disposed in the junction box 102.

Each of the first transmission coil assemblies 20 is led out from an output end 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 dispersed at both sides, and are uniformly disposed in the two connection boxes 102, for performing wireless transmission on the magnetic resonance signal. The magnetic resonance coil assembly 100 employs the connection box 102 to facilitate mounting and fixing from both sides.

In one embodiment, a plurality of the first transmission coil assemblies 20 are disposed within the junction box 102. And a plurality of the first transmission coil assemblies 20 are arranged side by side at intervals along the extending direction of the connecting box 102. The connection box 102 extends along an edge of the first end or an edge of the second end. Furthermore, a plurality of the first transmission coil assemblies 20 are arranged in the connecting box 102 at intervals, and are arranged side by side at intervals along the extending direction of the first end portion or the second end portion. It is also understood that the plurality of first transmission coil assemblies 20 are respectively disposed at one side or both sides of the plurality of partial coils 10 in a side-by-side spaced manner.

Referring to fig. 4, in one embodiment, the plurality of second transmission coil assemblies 30 are disposed at intervals on two sides of a patient bed 40 of the magnetic resonance system. It is understood that the plurality of second transmission coil assemblies 30 are spaced apart from each other on both sides of the patient bed 40 along the extension direction of the patient body. The plurality of first transmission coil assemblies 20 are arranged at intervals and movably arranged at two sides of the patient bed 40. It is understood that the plurality of first transmission coil assemblies 20 are spaced apart and can move along both sides of the patient bed 40. The plurality of first transmission coil assemblies 20 are respectively connected to the plurality of local coils 10. The plurality of first transmission coil assemblies 20 move along the two sides of the hospital bed 40, so that different parts of the body of a patient can be detected, and the flexibility is higher.

When each of the first transmission coil assemblies 20 overlaps each of the second transmission coil assemblies 30 and the resonance frequency of each of the first transmission coil assemblies 20 and each of the second transmission coil assemblies 30 is the same as the operating frequency of the magnetic resonance system, each of the second transmission coil assemblies 30 and each of the first transmission coil assemblies 20 transmit the magnetic resonance signal.

According to the near field communication principle, when the first transmission coil assembly 20 overlaps the second transmission coil assembly 30 and the resonant frequency is the same as the operating frequency of the magnetic resonance system, the first transmission coil assembly 20 is strongly coupled with the second transmission coil assembly 30, so that the magnetic resonance signal can be transmitted. The first transmission coil assembly 20 and the second transmission coil assembly 30 transmit signals in a wireless manner without depending on a mixed wire for signal transmission. By the first transmission coil assembly 20 and the second transmission coil assembly 30, a conventional hybrid wire and plug can be eliminated, so that the overall weight of the magnetic resonance coil assembly 100 is reduced and the use is convenient.

In one embodiment, the connection box 102 is adhesively disposed at the edge of the patient bed 40. 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 on the patient bed 40 by the connection box 102. The adhesion manner may be achieved by, for example, providing velcro tapes on the surfaces of the connection box 102 and the hospital bed 40, or providing an adhesive on the surfaces of the connection box 102 and the hospital bed 40.

In one embodiment, the first transmission coil assemblies 20 are disposed in one-to-one correspondence with the local coils 10. And the size of the first transmission coil assembly 20 is smaller than that of the local coil 10. The plurality of first transmission coil assemblies 20 are connected to the output ends of the plurality of local coils 10 in a one-to-one correspondence. The plurality of second transmission coil assemblies 30 are disposed at both sides of the patient bed 40. When the magnetic resonance coil assembly 100 is in operation, one of the first transmission coil assemblies 20 and one of the second transmission coil assemblies 30 are correspondingly and completely overlapped, and the patient bed 40 and the local coil 10 transmit signals through a coupling pair, so that a wireless transmission function is realized.

In one embodiment, when one of the first transmission coil assemblies 20 and one of the second transmission coil assemblies 30 are completely overlapped, the connection box 102 is disposed between the first transmission coil assembly 20 and the second transmission coil assembly 30, so that the first transmission coil assembly 20 and the second transmission coil assembly 30 can keep a distance to avoid interference caused by contact therebetween.

Referring to fig. 4 and 5, in one embodiment, the local coils 10 are covered on the detection site of the patient. The plurality of first transmission coil assemblies 20 are disposed at both sides of the plurality of partial coils 10 at intervals. The plurality of second transmission coil assemblies 30 are fixed at intervals on both sides of the patient bed 40. It is understood that the plurality of second transmission coil assemblies 30 are fixedly arranged at two sides of the patient bed 40 along the extending direction of the patient body. It is also understood that a plurality of second transmission coil assemblies 30 are spaced along the length of the patient bed 40.

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 butted one by one. The local coils 10 and the patient bed 40 surround to form a detection space 410 for detecting a detection site. The patient may lie flat on the patient bed 40. The detection space 410 varies depending on the detection site. The patient lies flat within the detection space 410.

When the abdomen of the patient needs to be detected, the first transmission coil assemblies 20 are moved to drive the local coils 10 to move, so that the detection space 410 moves to the abdomen of the patient. The magnetic resonance signals are transmitted between the plurality of local coils 10 and the patient bed 40 through the plurality of first transmission coil assemblies 20 and the plurality of second transmission coil assemblies 30.

In one embodiment, the patient bed 40 is provided with moving grooves 430 at both sides along the extension direction of the patient body. The plurality of second transmission coil assemblies 30 are disposed at intervals in the moving slot 430. The moving groove 430 extends along the extension direction of the patient's body and extends to the whole patient bed 40. The plurality of first transmission coil assemblies 20 are disposed in the two junction boxes 102. The two connection boxes 102 are slidably disposed in the moving slot 430. By moving the positions of the two connection boxes 102, the local coils 10 are driven to move, and thus, detection of different parts is realized. The magnetic resonance coil assembly 100 can be moved on the patient bed 40 to accommodate different patient sizes and to improve patient comfort.

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.

The plurality of second transmission coil assemblies 30 are disposed on two sides of the patient bed 40 along the extension direction of the patient body. The plurality of local coils 10 cover a detection site of a patient. The output ends 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 two sides of the patient bed 40, and then drive the plurality of local coils 10 to move along the extending direction of the patient body. The number of the second transmission coil assemblies 30 is greater than that of the first transmission coil assemblies 20, so that the magnetic resonance coil assembly 100 can detect different parts of a patient, and local detection is realized. When the plurality of first transmission coil assemblies 20 are respectively overlapped with a part of the second transmission coil assemblies 30 in the plurality of second transmission coil assemblies 30 in a one-to-one correspondence manner and have the same operating frequency as the magnetic resonance system, signal transmission is performed between the first transmission coil assemblies 20 and the corresponding second transmission coil assemblies 30.

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 requirements.

In one embodiment, the magnetic resonance coil assembly 100 includes a 24-channel coil. As can be seen from fig. 2, one of the first transmission coil assemblies 20 forms a channel coil with one of the local coils 10. The plurality of first transmission coil assemblies 20 are distributed at both sides of the plurality of local coils 10.

In one embodiment, the second transmission coil assemblies 30 are spaced apart by a distance equal to the first transmission coil assemblies 20. Each of the second transmission coil assemblies 30 is identical to each of the first transmission coil assemblies 20. The second transmission coil assembly 30 has the same resonance frequency as the first transmission coil assembly 20. The second transmission coil assembly 30 is also the same size as the first transmission coil assembly 20. The distance between two adjacent second transmission coil assemblies 30 is equal to the distance between two adjacent first transmission coil assemblies 20, which is favorable for the second transmission coil assemblies 30 to correspondingly overlap with the first transmission coil assemblies 20. The second transmission coil assembly 30 is overlapped with the first transmission coil assembly 20, so that the transmission efficiency can be improved.

In one embodiment, two adjacent second transmission coil assemblies 30 are spaced apart by a distance no greater than the radius of the second transmission coil assemblies 30. The spacing distance between two adjacent first transmission coil assemblies 20 is not more than the radius of the first transmission coil assemblies 20. The plurality of second transmission coil assemblies 30 are disposed at equal intervals. The plurality of first transmission coil assemblies 20 are disposed at equal intervals. By setting the spacing distance between two adjacent second transmission coil assemblies 30 and the spacing distance between two adjacent first transmission coil assemblies 20, the coupling interference phenomenon between the adjacent transmission coil assemblies can be avoided.

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

Referring to fig. 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 capacitance and inductance. In this embodiment, the first matching circuit 220 includes a capacitive device cf1 and an inductive device 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 capacitance and inductance. In this embodiment, the second matching circuit 320 includes a capacitive device cf2 and an inductive device L7.

The first transmission coil assembly 20 forms a resonant tank. The second transmission coil assembly 30 forms a resonant tank. 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 combined in a pairing manner, so that signal transmission with different frequencies can be realized. The magnetic resonance coil assembly 100 eliminates the conventional mix-up wires and plugs, making the coil lightweight.

Referring to fig. 7, in one embodiment, each of the local coils 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 of the coil body 110 for adjusting the resonant frequency of the resonant tank of the local coil 10. The first passive detuning circuit 130 is connected in parallel with the coil body 110 for controlling the resonance 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 line coil assembly 20.

The coil body 110 may be bent into one or several geometric shapes. The coil body 110 may extend along a set direction to form a ring shape, a rectangular shape, a square shape, a butterfly shape, a saddle shape, etc. The coil body 110 is used to receive the magnetic resonance signals. The matching circuit 120 comprises a capacitance or an inductance or a combination of a capacitance and an inductance. The matching circuit 120 is connected to the output of the coil body 110 for adjusting the resonant frequency of the resonant tank of the local coil 10. When a tuning frequency needs to be selected, the resonant frequency of the resonant tank of the local coil 10 can be adjusted by adjusting the capacitance and the inductance of the matching circuit 120, so as to receive the magnetic resonance signal, and output the magnetic resonance signal through the output end of the amplifier 150. The first passive detuning circuit 130 is used to adjust the resonance state of the local coil 10. When the transmitting coil works, the first passive detuning circuit 130 controls the local coil 10 to be in a detuned state, so that the resonance frequency deviation of the resonance loop where the local coil is located changes, the magnetic resonance signal cannot be received, and the phenomenon of coupling interference between the coils is avoided.

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 the first end of the coil body 110. The other end of the capacitive circuit 131 is connected to the second end of the coil body 110. And the first end and the second end are oppositely arranged. One end of the switch 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.

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. Wherein: the first diode D1 and the second diode D2 form a switch circuit 132; the first inductance L1 constitutes the inductive circuit 133. The first capacitor C1 and the second capacitor C2 constitute a capacitive circuit 131.

One end of the capacitive circuit 131 is connected to the first end of the coil body 110, the other end of the capacitive circuit 131 is connected to the second end of the coil body 110, and the first end and the second end are opposite to each other. One terminal of the switching circuit 132 is connected to the first terminal. The other end of the switching circuit 132 is connected to an inductive circuit 133, and the inductive circuit 133 is connected to a second end. The switching circuit 132 is configured to be turned off when no induced current is generated in the coil body 110. The switch circuit 132 is also used to conduct when the coil body 110 generates an induced current.

When the coil body 110 is within the magnetic field generated by the main magnet, the coil body 110 generates an induced current due to the time-varying radio frequency field generated by the transmit coil. Current will flow 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. The inductive circuit 133 has a current flowing therethrough, and the capacitive circuit 131 and the inductive circuit 133 are connected in parallel to the first end and the second end of the coil body 110. The first passive detuning circuit 130 is parallel resonant and in 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, i.e., the local coil 10 is in a detuned state.

The first diode D1 is used to conduct when a current in a first direction (counterclockwise) is generated in the coil body 110. The second diode D2 is used to conduct when a current in a second (clockwise) direction is generated in the coil body 110. The first direction is opposite to the second direction.

When the transmitting coil works, the magnetic field generated by the transmitting coil is a variable magnetic field. The current generated by the coil body 110 in the local coil 10 is also a current with a direction change. That is, the induced current in the coil body 110 may alternately flow in the first direction and the second direction.

When the induction in the coil body 110 flows in 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 in the first direction. The first diode D1 is connected in series with the first inductor L1. The branch of the first diode D1 connected in series with the first inductor L1 resonates in parallel with the capacitive circuit 131 to form 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, i.e., the local coil 10 is in a detuned state.

When the induction in the coil body 110 flows in the second direction, the second diode D2 is turned on, the first diode D1 is turned off, and the current in the first inductor L1 flows in the second direction. A second diode D2 is connected in series with the first inductor L1 and resonates in parallel with the capacitive circuit 131 to form 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, i.e., the local coil 10 is in a detuned state.

When the transmitting coil is not operated, the first diode D1 and the second diode D2 are both in an off state, and no current flows in the first inductor L1. The capacitive circuit 131 is not in parallel resonance with the inductive circuit 133. No current flows inside the coil body 110, and the coil body 110 mainly generates a detection signal by means of resonance with human tissues.

The first diode D1 is connected in anti-parallel with the second diode D2. Due to the ac operating environment, one of the first diode D1 and the second diode D2 is turned on when the transmitting coil is in operation. Further, the first inductor L1 is connected in parallel with the capacitive circuit 131, so that the deviation of the resonant frequency of the resonant tank changes, and the resonant tank is in a high-impedance state, thereby achieving a detuning effect.

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 the first output end of the coil body 110, and the other end of the capacitor Cm is connected to the second output end of the coil body 110. One end of the second inductor L2 is connected to the first output end of the coil body 110. The other end of the second inductor L2 is connected to the first input terminal of the amplifier 150. A second input of the amplifier 150 is connected to a second output of the coil body 110.

The amplifier 150 receives the magnetic resonance signal and amplifies the magnetic resonance signal. And outputting radio frequency signals to the first transmission coil assembly 20 through the output end of the amplifier 150 for signal transmission.

Referring to fig. 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. Wherein: the third diode D3 and the fourth diode D4 form a switch circuit (not shown); the fourth inductor L4 constitutes an inductive circuit (not shown); the third capacitor C3 and the fourth capacitor C4 form a capacitive circuit (not shown).

One end of the capacitive circuit is connected to the first end of the first transmission line coil body 210, the other end of the capacitive circuit is connected to the second end of the first transmission line coil body 210, and the first end and the second end are opposite to each other. One end of the switch circuit is connected with the first end. The other end of the switch circuit is connected with one end of the inductive circuit, and the other end of the inductive circuit is connected with the second end. The switching circuit is used for switching off when no induced current is generated in the first transmission coil body 210. The switching circuit is also used for conducting when the first transmission coil body 210 generates an induced current.

When the first transmission coil body 210 is within the magnetic field generated by the main magnet, the first transmission coil body 210 generates an induced current due to the time-varying radio frequency field generated by the transmit coil. Current will flow into the second passive detuning circuit 230. The switching circuit is also used for conducting when an induced current is generated in the first transmission coil body 210. The inductive circuit has current flowing therethrough, and the capacitive circuit and the inductive circuit are connected in parallel to the first end and the second end of the first transmission coil body 210. The second passive detuning circuit 230 is in parallel resonance and is in 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, and does not transmit signals.

The third diode D3 is used to conduct when a current in a first direction (counterclockwise) is generated in the first transmission coil body 210. The fourth diode D4 is used to conduct when a current in the second direction (clockwise) is generated in the first transmission coil body 210. The first direction is opposite to the second direction.

When the transmitting coil works, the magnetic field generated by the transmitting coil is a variable 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 direction change. The induced current in the first transmission coil body 210 may alternately flow in the first direction and the second direction.

When the induction in the first transmission coil body 210 flows in the first direction, the third diode D3 is turned on, the fourth diode D4 is turned off, and the current in the fourth inductor L4 flows in the first direction. The third diode D3 is connected in series with the fourth inductor L4. The branch of the third diode D3 connected in series with the fourth inductor L4 resonates in parallel with the capacitive circuit to form 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, i.e., the first transmission coil assembly 20 is in a detuned state.

When the induction in the first transmission coil body 210 flows in the second direction, the fourth diode D4 is turned on, the third diode D3 is turned off, and the current in the fourth inductor L4 flows in the second direction. A fourth diode D4 is connected in series with the fourth inductor L4 and resonates in parallel with the capacitive circuit to form 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, i.e., the first transmission coil assembly 20 is in a detuned state.

When the transmitting coil does not work, the third diode D3 and the fourth diode D4 are both in an off state, and no current flows in the fourth inductor L4. The capacitive circuit is not in parallel resonance with the inductive circuit. No current flows inside the first transmission coil body 210, and the first transmission coil body 210 is used for transmitting the magnetic resonance signal received by the local coil 10.

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. Wherein: the fifth diode D5 and the sixth diode D6 form a switch circuit (not shown); the fifth inductor L5 constitutes an inductive circuit (not shown); the fifth capacitor C5 and the sixth capacitor C6 form a capacitive circuit (not shown).

One end of the capacitive circuit is connected to the first end of the second transmission coil body 310, the other end of the capacitive circuit is connected to the second end of the second transmission coil body 310, and the first end and the second end are opposite to each other. One end of the switch circuit is connected with the first end. The other end of the switch circuit is connected with one end of the inductive circuit, and the other end of the inductive circuit is connected with the second end. The switching circuit is configured to be turned off when no induced current is generated in the second transmission coil body 310. The switching circuit is also used for conducting when the second transmission coil body 310 generates an induced current.

When the second transmission coil body 310 is within the magnetic field generated by the main magnet, the second transmission coil body 310 generates an induced current due to the time varying radio frequency field generated by the transmit coil. Current will flow into the third passive detuning circuit 330. The switching circuit is also used to be turned on when an induced current is generated in the second transmission coil body 310. An inductive circuit through which current flows, and a capacitive circuit connected in parallel with the inductive circuit to the first and second ends 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 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 and does not transmit signals.

The fifth diode D5 is used to conduct when a current in the first direction (counterclockwise) is generated in the second transmission coil body 310. The sixth diode D6 is used to conduct when a current in the second direction (clockwise) is generated in the second transmission coil body 310. The first direction is opposite to the second direction.

When the transmitting coil works, the magnetic field generated by the transmitting coil is a variable magnetic field. The current generated by the second transmission coil body 310 in the second transmission coil assembly 30 is also a current with a direction change. The induced current in the second transmission coil body 310 may alternately flow in the first direction and the second direction.

When the induction in the second transmission coil body 310 flows in the first direction, the fifth diode D5 is turned on, the sixth diode D6 is turned off, and the current in the fifth inductor L5 flows in the first direction. A fifth diode D5 is connected in series with the fifth inductor L5. The branch of the fifth diode D5 connected in series with the fifth inductor L5 resonates in parallel with the capacitive circuit to form 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, i.e., the second transmission coil assembly 30 is in a detuned state.

When the induction in the second transmission coil body 310 flows in the second direction, the sixth diode D6 is turned on, the fifth diode D5 is turned off, and the current in the fifth inductor L5 flows in the second direction. A sixth diode D6 is connected in series with the fifth inductor L5 and resonates in parallel with the capacitive circuit to form 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, i.e., the second transmission coil assembly 30 is in a detuned state.

When the transmitting coil does not work, the fifth diode D5 and the sixth diode D6 are both in an off state, and no current flows in the fifth inductor L5. The capacitive circuit is not in parallel resonance with the inductive circuit. No current flows inside the second transmission coil body 310, and the second transmission coil body 310 is used for transmitting the magnetic resonance signal.

In one embodiment, the first passive detuning circuit 130, the second passive detuning circuit 230, and the third passive detuning circuit 330 may be integrated on a circuit board to form a modular structure. The modular structure can be directly connected in series with the middle position of the coil body. The first passive detuning circuit 130, the second passive detuning circuit 230, and the third passive detuning circuit 330 may be integrated on a circuit board, and occupy a small space without causing trouble to the volume and weight of the magnetic resonance coil assembly 100.

Referring to fig. 9, in one embodiment, the power supply terminals of a plurality of amplifiers 150 are connected to the power supply connection structure 420 of the patient bed 40.

The power supply terminals of a plurality of said amplifiers 150 are connected, leading to a power supply connection terminal 151. The power supply connection terminal 151 is led out from one side of the plurality of first transmission line coil assemblies 20. When the first transmission coil assemblies 20 are movably disposed on the patient bed 40, the power supply connection end 151 is connected to the power supply connection structure 420 of the patient bed 40, so as to supply power to the amplifiers 150. When the power supply connection end 151 is correspondingly connected to the power supply connection structure 420, the plurality of first transmission line coil assemblies 20 can be aligned and fixed, and a positioning function is realized.

The power supply connection structure 420 may be a metal contactor. After the plurality of first transmission coil assemblies 20 are placed on two sides of the patient bed 40, the power supply connection end 151 is connected to the power supply connection structure 420, so as to supply power to the plurality of amplifiers 150. Since the power supply terminals of a plurality of amplifiers 150 are connected to lead out a power supply connection terminal 151, the power supply connection structure 420 can realize parallel power supply to the plurality of amplifiers 150. A power supply signal may simultaneously power the plurality of amplifiers 150.

Optionally, an auxiliary mark is provided on the junction box 102, and the auxiliary mark is used for assisting the first transmission coil assembly 20 and the second transmission coil assembly 30 in the junction box 102 to be arranged in a matching manner. In one embodiment, a plurality of the power supply connection structures 420 are disposed on both sides of the patient bed 40. The plurality of first transmission coil assemblies 20 are movably disposed at two sides of the patient bed 40, and each side of the first transmission coil assemblies is provided with a power supply connection end 151 used as an auxiliary identifier for connecting with the power supply connection structures 420 at two sides of the patient bed 40. When the plurality of first transmission coil assemblies 20 move, the power supply connection ends 151 may correspond to the power supply connection structures 420 at both sides of the patient bed 40 and assist in positioning and aligning.

In one embodiment, the power supply connection terminal 151 is disposed on the connection box 102, a metal contactor is disposed on the patient bed 40, and the power supply connection terminal 151 is matched with the metal contactor to supply power to the magnetic resonance coil assembly 100 through the patient bed 40.

In one embodiment, the amplifiers 150 of every 12 local coils 10 share one supply connection 151.

In one embodiment, the present application provides a magnetic resonance system. The magnetic resonance system comprises 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 at the examination site. Each of the first transmission coil assemblies 20 is connected to an output of each of the local coils 10 for transmitting the magnetic resonance signal. Each of the second transmission coil assemblies 30 is wirelessly connected with each of the first transmission coil assemblies 20 for transmitting the magnetic resonance signal. The signal processing unit 50 is connected to the plurality of second transmission coil assemblies 30, and is configured to receive the magnetic resonance signals and process the magnetic resonance signals.

The local coil 10 receives the magnetic resonance signal and transmits the magnetic resonance signal to the signal processing unit 50 through 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/digital converter, and the like, and is configured to acquire the magnetic resonance signal received by the local coil 10 and perform data processing to generate spectral data, so as to perform medical imaging on the patient.

The magnetic resonance system further comprises a superconducting magnet unit, a gradient coil unit, a controller unit, an examination table, a display unit and the like. The magnetic resonance system may also be used in medical imaging systems for imaging human subjects, and may also include veterinary or non-medical systems for imaging non-human subjects, baggage, and the like.

In one embodiment, the present application provides a magnetic resonance system. The magnetic resonance system comprises the magnetic resonance coil assembly 100 and the patient bed 40. The magnetic resonance coil assembly 100 comprises a housing 101, a plurality of local coils 10 arranged 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 junction box 102. The patient bed 40 is used for carrying the magnetic resonance coil assembly 100, a plurality of second transmission coil assemblies 30 are arranged on one side edge or two side edges of the patient bed 40, and the first transmission coil assembly 20 is matched with the second transmission coil assemblies 30 to realize wireless communication between the magnetic resonance coil assembly 100 and the patient bed 40. The description of the magnetic resonance coil assembly 100 and the patient bed 40 can refer to the description related to the above embodiments.

In the description herein, references to the description of "some embodiments," "other embodiments," "desired embodiments," etc., mean that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the application. In this specification, a schematic description of the above terminology may not necessarily refer to the same embodiment or example.

The technical features of the embodiments described above may be arbitrarily combined, and for the sake of brevity, all possible combinations of the technical features in the embodiments described above are not described, but should be considered as being within the scope of the present specification as long as there is no contradiction between the combinations of the technical features.

The above-mentioned embodiments only express several embodiments of the present application, and the description thereof is more specific and detailed, but not construed as limiting the claims. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the concept of the present application, which falls within the scope of protection of the present application. Therefore, the protection scope of the present patent shall be subject to the appended claims.

Claims

1. A magnetic resonance coil assembly, comprising:

the shell comprises a first end part and a second end part, and all or part of the shell between the first end part and the second end part can be bent to form a set shape;

a plurality of local coils disposed inside the housing;

at least one connection box disposed at the first end or the second end and extending along an edge of the first end or an edge of the second end;

one or more first transmission coil assemblies disposed in the connection box and connected with at least one of the plurality of local coils to realize wireless communication between the magnetic resonance coil assembly and the outside.

2. The magnetic resonance coil assembly as set forth in claim 1, wherein the connection box is provided at the first end portion and the second end portion, respectively.

3. A magnetic resonance coil assembly according to claim 1 or 2, wherein a plurality of the first transmission coil assemblies are provided in the connection box and are spaced apart in the direction of extension of the connection box.

4. The mr coil assembly of claim 1 wherein the housing is formed of a flexible material, the connection box is formed of a rigid material, and the connection box clamps an edge of the housing.

5. The mr coil assembly of claim 2 wherein the first transmission coil assemblies are arranged in a one-to-one correspondence with the local coils and wherein the first transmission coil assemblies are smaller in size than the local coils.

6. A magnetic resonance system, comprising:

a magnetic resonance coil assembly comprising a housing, a plurality of local coils disposed inside the housing, the housing comprising a first end and a second end, a connection box disposed at the first end and/or the second end, one or more first transmission coil assemblies disposed within the connection box;

the sickbed is used for bearing the magnetic resonance coil assembly, a plurality of second transmission coil assemblies are arranged on one side edge or two side edges of the sickbed, and the first transmission coil assemblies are matched with the second transmission coil assemblies to realize wireless communication between the magnetic resonance coil assemblies and the sickbed.

7. The MRS of claim 6, wherein said connection box is adhered to the edge of said patient's bed, said MRL can be bent to form a predetermined shape, and said bent MRL can be fixed on said patient's bed by said connection box.

8. The MR system according to claim 6 or 7, wherein a plurality of the second transmission coil assemblies are spaced apart along a length of the patient bed, and a number of the first transmission coil assemblies is less than a number of the second transmission coil assemblies.

9. A magnetic resonance system according to claim 6 or 7, wherein the connection box is provided with an auxiliary marker for assisting the first transmission coil assembly and the second transmission coil assembly in the connection box to be arranged in cooperation.

10. The MR system according to claim 6, wherein the connection box is provided with a power supply connection end, the patient bed is provided with a metal contactor, and the power supply connection end is matched with the metal contactor to supply power to the MR coil assembly through the patient bed.