WO2023082038A1 - 一种磁共振线圈 - Google Patents

一种磁共振线圈 Download PDF

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Publication number
WO2023082038A1
WO2023082038A1 PCT/CN2021/129477 CN2021129477W WO2023082038A1 WO 2023082038 A1 WO2023082038 A1 WO 2023082038A1 CN 2021129477 W CN2021129477 W CN 2021129477W WO 2023082038 A1 WO2023082038 A1 WO 2023082038A1
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capacitor
magnetic resonance
circuit
tuning
coil
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PCT/CN2021/129477
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English (en)
French (fr)
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李烨
莫智广
李楠
罗超
杜凤
陈巧燕
刘新
郑海荣
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深圳先进技术研究院
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Priority to PCT/CN2021/129477 priority Critical patent/WO2023082038A1/zh
Publication of WO2023082038A1 publication Critical patent/WO2023082038A1/zh

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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/05Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/055Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves  involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01RMEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00Arrangements or instruments for measuring magnetic variables
    • G01R33/20Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/32Excitation or detection systems, e.g. using radio frequency signals
    • G01R33/36Electrical details, e.g. matching or coupling of the coil to the receiver

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  • the present application belongs to the technical field of magnetic resonance imaging, and in particular relates to a magnetic resonance coil.
  • Magnetic resonance imaging has become an important imaging method for clinical diagnosis due to its advantages of non-invasive, non-radiation, high resolution, high contrast, and cross-sectional imaging in any orientation.
  • the magnetic resonance system When performing magnetic resonance imaging, the magnetic resonance system sends magnetic resonance signals to the human body through the transmitting coil, and the human tissue is excited by the signal, and the feedback electromagnetic signal is fed back to the magnetic resonance system through the receiving coil.
  • the signal strength received by the receiving coil determines the quality of the magnetic resonance imaging to a certain extent.
  • the surface coil since the signal will rapidly attenuate as the distance from the coil increases, it is difficult for the surface coil to obtain high imaging quality for imaging of organs located deep inside the body. Taking prostate imaging as an example, the rectal coil needs to be inserted into the patient's rectum to bring it closer to the prostate, so as to obtain a stronger signal and better image quality than surface coils.
  • the signal-to-noise ratio is the core parameter of coil design, and a high signal-to-noise ratio means higher resolution and higher contrast, which means better image quality.
  • the coils in the prior art usually only include one channel, and the signal-to-noise ratio is small, so it is difficult to meet the high-resolution imaging requirements.
  • the single-channel coil has a relatively high signal-to-noise ratio only in the direction perpendicular to it, while the signal-to-noise ratio in other directions is low. The image is blurry.
  • the present application provides a magnetic resonance coil, aiming to solve one of the above-mentioned technical problems in the prior art at least to a certain extent.
  • a magnetic resonance coil including a receiving coil, a support and a tuning and matching circuit
  • the receiving coil includes at least two circuit loops, the at least two circuit loops are respectively distributed on the support, and the at least two circuit loops overlap each other; the tuning and matching circuit is arranged at one end of the support , and is electrically connected to the receiving coil.
  • the technical solution adopted in the embodiment of the present application further includes: further comprising a coaxial cable and an amplifier, the tuning and matching circuit is connected to the amplifier through the coaxial cable, and the amplifier is connected to the magnetic resonance system.
  • the technical solution adopted in the embodiment of the present application further includes: the at least two circuit loops are mutually independent in circuit.
  • the technical solution adopted in the embodiment of the present application further includes: the at least two circuit loops respectively correspond to a port, and the tuning and matching circuit tunes, matches and decouples the corresponding circuit loop through the port.
  • the tuning and matching circuit includes the tuning and matching circuit including a first capacitor, a third capacitor, a fourth capacitor, a fifth capacitor, a sixth capacitor, a diode, a first inductor, and a first capacitor.
  • Two inductors; the fourth capacitor, the fifth capacitor, the third capacitor and the first capacitor are connected in series, and the at least two circuit loops are decoupled through the first capacitor; the sixth capacitor, the fifth capacitor, the diode and The first inductor is connected in series, and the third capacitor, the second inductor, and the diode are connected in series to form a parallel resonant circuit; when the diode is turned on, the parallel resonant circuit starts to work, so that the corresponding circuit loop It is in an off state; when the diode is off, the second inductor does not work, and the third capacitor works, so that the corresponding circuit loop is in the state of receiving signals.
  • the technical solution adopted in the embodiment of the present application also includes: the tuning and matching process of the tuning and matching circuit is specifically: after connecting the port to a vector network analyzer through a coaxial cable for calibration, testing the S11 parameter of the port , displayed as the Smith chart mode; add the adjustment mark point as the operating frequency point of the magnetic resonance system, and adjust the size of the third capacitor, the fourth capacitor, and the fifth capacitor by replacing or adjusting the capacitor, so that the mark point moves to Smith
  • the central position of the circular diagram completes the tuning and matching of the tuning and matching circuit.
  • the technical solution adopted in the embodiment of the present application further includes: the support member is a cylinder with a set diameter.
  • the beneficial effect of the embodiment of the present application lies in that the magnetic resonance coil of the embodiment of the present application adopts a multi-channel design mode, and multiple channels overlap each other, which reduces the mutual interference between channels.
  • the embodiment of the present application has higher resolution and higher contrast, improves the signal-to-noise ratio of the rectal coil, improves the imaging quality of the magnetic resonance system, and has a wider imaging coverage , so that the imaging area of the coil better covers the entire site to be measured.
  • Fig. 1 is a schematic structural diagram of a magnetic resonance coil according to an embodiment of the present application
  • Fig. 2 is a circuit connection diagram of the receiving coil 1 of the embodiment of the present application.
  • Fig. 3 is a flowchart of a magnetic resonance coil imaging method according to an embodiment of the present application.
  • FIG. 1 is a schematic structural diagram of a magnetic resonance coil according to an embodiment of the present application.
  • the magnetic resonance coil of the embodiment of the present application includes a receiving coil 1 , a support 2 , a tuning and matching circuit 3 , a coaxial cable 4 and an amplifier 5 .
  • the receiving coil 1 includes at least two circuit loops. In the embodiment of the present application, three circuit loops are taken as an example, which are respectively the first circuit loop 11, the second circuit loop 12 and the third circuit loop 13. The first circuit loop 11, the second circuit loop The second circuit loop 12 and the third circuit loop 13 are respectively distributed on the support member 2 .
  • the support member 2 is a cylinder with a set diameter (the set diameter is 25 mm in the embodiment of the present application, which can be set according to actual application), and is used to provide support for the receiving coil 1 .
  • the tuning and matching circuit 3 is arranged at one end of the support member 2 and is electrically connected to the receiving coil 1 for performing, tuning, matching and decoupling processing on the receiving coil 1 .
  • the tuning and matching circuit 3 is connected to the amplifier 5 through the coaxial cable 4, and the amplifier 5 is connected to the magnetic resonance system (not shown) through the cable.
  • FIG. 2 is a circuit connection diagram of the receiving coil 1 according to the embodiment of the present application.
  • the first circuit loop 11, the second circuit loop 12 and the third circuit loop 13 are independent of each other on the circuit, and the first circuit loop 11 and the second circuit loop 12, the second circuit loop 12 and the third circuit loop 13 alternate in pairs overlap to achieve the purpose of overlap decoupling.
  • the first capacitor C41 is used for decoupling between the first circuit loop 11 and the third circuit loop 13 , and the second capacitor C21 and the tuning and matching circuit of the second circuit loop 12 play a tuning role together.
  • the first circuit loop 11, the second circuit loop 12 and the third circuit loop 13 correspond to the first port, the second port and the third port respectively, and the tuning and matching circuit 3 passes through the first port, the second port and the third port respectively.
  • the third port adjusts the first circuit loop 11 , the second circuit loop 12 and the third circuit loop 13 to achieve the effects of tuning, matching and preamplifier decoupling.
  • the tuning and matching circuit structures of the first circuit loop 11, the second circuit loop 12 and the third circuit loop 13 are the same.
  • the circuit structure of the tuning and matching circuit 3 includes: the third capacitor C12, the fourth capacitor Cf1, the fifth capacitor Cp1, the sixth capacitor Cs1, the diode D1, the first inductor L11 and the second inductor L12; the fourth capacitor Cf1, the fifth capacitor Cp1, the third capacitor C12 and the first capacitor C41 are connected in series.
  • the six capacitors Cs1, the fifth capacitor Cp1, the diode D1 and the first inductor L11 are connected in series, and the third capacitor C12, the second inductor L12 and the diode D1 are connected in series to form a parallel resonant circuit; the diode D1 functions as a direct current, AC isolation; the fourth capacitor Cf1, the fifth capacitor Cp1 and the sixth capacitor Cs1 jointly determine the tuning and matching of the circuit.
  • the parallel resonant circuit composed of the third capacitor C12 and the second inductance L12 starts to work, and the first circuit loop 11 is in a disconnected state at this time, so as to avoid the excitation signal of the magnetic resonance system from damaging the circuit; when the diode D1 When disconnected, the second inductor L12 does not work, the third capacitor C12 works, and the first circuit loop 11 is in a normal state of receiving signals.
  • the tuning and matching circuit structures of the second circuit loop 12 and the third circuit loop 13 are the same as those of the first circuit loop 11 , and will not be repeated in this application.
  • the tuning and matching process of the tuning and matching circuit is specifically: after connecting the first port to a vector network analyzer through a coaxial cable for calibration, then testing the first port S11 parameter, displayed as Smith chart mode, add the adjustment mark point marker as the working frequency point of the magnetic resonance system, adjust the size of Cf1, Cp1 and Cs1 by replacing the capacitor or adjusting the adjustable capacitor, so that the marker point marker moves to Smith
  • the center position of the circular diagram completes the tuning and matching of the tuning matching circuit.
  • the tuning and matching processes of the second circuit loop 12 and the third circuit loop 13 are the same as those of the first circuit loop 11 , which will not be repeated in this application.
  • FIG. 3 is a flow chart of the magnetic resonance coil imaging method according to the embodiment of the present application.
  • the magnetic resonance coil imaging method of the embodiment of the present application includes the following steps:
  • the coil is inserted into the rectum of the subject to be tested.
  • S2 Detect whether the tuning, matching and cross-coupling of the receiving coil are normal, if not, go to S3; otherwise, go to S4;
  • S4 Connect the receiving coil to the magnetic resonance system, and perform magnetic resonance scanning imaging of the part to be measured through the magnetic resonance system.
  • the magnetic resonance coil of the embodiment of the present application adopts a multi-channel design mode, and multiple channels are overlapped in pairs to reduce mutual interference between channels.
  • the embodiment of the present application has higher resolution and higher contrast, improves the signal-to-noise ratio of the rectal coil, improves the imaging quality of the magnetic resonance system, and has a wider imaging coverage , so that the imaging area of the coil better covers the entire site to be measured.

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Abstract

一种磁共振线圈,磁共振线圈包括接收线圈(1)、支撑件(2)以及调谐匹配电路(3);接收线圈(1)包括至少两个电路回路(11,12,13),至少两个电路回路(11,12,13)分别分布在支撑件(2)上;调谐匹配电路(3)设于支撑件(2)的一端,并与接收线圈(1)电连接。本磁共振线圈采用多通道设计方式,且多个通道之间两两重叠,降低了通道与通道间的相互干扰。相对于单通道直肠线圈,本磁共振线圈具有更高的分辨率和更高的对比度,提高了直肠线圈的信噪比,并提高了磁共振***的成像质量,且拥有更宽的成像覆盖范围,使得线圈的成像区域更好的覆盖整个待测部位。

Description

一种磁共振线圈 技术领域
本申请属于磁共振成像技术领域,特别涉及一种磁共振线圈。
背景技术
磁共振成像技术由于其具有的无创伤、无辐射、高分辨率、高对比度以及任意方位截面成像等优点,已经成为临床诊断的重要成像手段。
当进行磁共振成像时,磁共振***通过发射线圈对人体发送磁共振信号,人体组织被该信号激励后将反馈的电磁信号经由接收线圈反馈回磁共振***。其中,接收线圈接收到的信号强度在一定程度上决定了磁共振成像质量。而由于信号会随着与线圈距离的增加而快速衰减,导致表面线圈对于处于身体内部较深处的器官成像难以获得较高的成像质量。以***成像为例,在使用时需要将直肠线圈***患者直肠,使其更加靠近***,从而获得相较于表面线圈更强的信号,并获得更好的图像质量。
信噪比是线圈设计的核心参数,信噪比高意味着更高的分辨率和更高的对比度,即意味着更好的图像质量。现有技术中的线圈通常只包含一个通道,信噪比较小,难以达到高分辨率的成像要求。此外,单通道线圈只有在与其垂直的方向上拥有相对较高的信噪比,而其他方向上的信噪比较低,假如线圈***时方向没有恰好对准检查器官,则会使部分器官的图像模糊。
发明内容
本申请提供了一种磁共振线圈,旨在至少在一定程度上解决现有技术中的 上述技术问题之一。
为了解决上述问题,本申请提供了如下技术方案:
一种磁共振线圈,包括接收线圈、支撑件以及调谐匹配电路;
所述接收线圈包括至少两个电路回路,所述至少两个电路回路分别分布在支撑件上,且所述至少两个电路回路之间两两重叠;所述调谐匹配电路设于支撑件的一端,并与接收线圈电连接。
本申请实施例采取的技术方案还包括:还包括同轴电缆及放大器,所述调谐匹配电路通过同轴电缆与放大器连接,所述放大器与磁共振***连接。
本申请实施例采取的技术方案还包括:所述至少两个电路回路在电路上相互独立。
本申请实施例采取的技术方案还包括:所述至少两个电路回路分别对应一个端口,所述调谐匹配电路通过端口对对应的电路回路进行调谐、匹配和去耦。
本申请实施例采取的技术方案还包括:所述调谐匹配电路包括所述调谐匹配电路包括第一电容、第三电容、第四电容、第五电容、第六电容、二极管、第一电感以及第二电感;第四电容、第五电容、第三电容以及第一电容通过串联方式连接,所述至少两个电路回路之间通过第一电容进行去耦;第六电容、第五电容、二极管以及第一电感通过串联方式连接,第三电容、第二电感以及二极管通过串联方式连接,组成并联谐振电路;当所述二极管导通时,所述并联谐振电路开始工作,使所述对应的电路回路处于断开状态;当二极管断开时,所述第二电感不工作,所述第三电容工作,使所述对应的电路回路处于接收信号状态。
本申请实施例采取的技术方案还包括:所述调谐匹配电路的调谐与匹配过程具体为:将所述端口通过同轴电缆连接到矢量网络分析仪上进行校准后, 测试所述端口的S11参数,显示为史密斯圆图模式;添加调节标记点为磁共振***的工作频点,通过更换电容或者调节电容的方式调节第三电容、第四电容以及第五电容的大小,使得标记点移动到史密斯圆图的中心位置,完成所述调谐匹配电路的调谐与匹配。
本申请实施例采取的技术方案还包括:所述支撑件为设定直径大小的圆柱体。
相对于现有技术,本申请实施例产生的有益效果在于:本申请实施例的磁共振线圈采用多通道设计方式,且多个通道之间两两重叠,降低了通道与通道间的相互干扰。相对于单通道直肠线圈,本申请实施例具有更高的分辨率和更高的对比度,提高了直肠线圈的信噪比,并提高了磁共振***的成像质量,且拥有更宽的成像覆盖范围,使得线圈的成像区域更好的覆盖整个待测部位。
附图说明
图1是本申请实施例的磁共振线圈结构示意图;
图2是本申请实施例的接收线圈1的电路连接关系图;
图3是本申请实施例的磁共振线圈成像方法流程图。
具体实施方式
为了使本申请的目的、技术方案及优点更加清楚明白,以下结合附图及实施例,对本申请进行进一步详细说明。应当理解,此处所描述的具体实施例仅用以解释本申请,并不用于限定本申请。
请参阅图1,是本申请实施例的磁共振线圈结构示意图。本申请实施例的磁共振线圈包括接收线圈1、支撑件2、调谐匹配电路3、同轴电缆4以及放 大器5。接收线圈1包括至少两个电路回路,本申请实施例中以三个电路回路为例,分别为第一电路回路11、第二电路回路12和第三电路回路13,第一电路回路11、第二电路回路12和第三电路回路13分别分布在支撑件2上。支撑件2为设定直径大小(本申请实施例中设定直径大小为25mm,具体可以根据实际应用进行设定)的圆柱体,用于为接收线圈1提供支撑作用。调谐匹配电路3设于支撑件2的一端,并与接收线圈1电连接,用于对接收线圈1进行、调谐、匹配以及去耦处理。调谐匹配电路3通过同轴电缆4与放大器5连接,放大器5通过电缆连接到磁共振***(图未示)上。
请参阅图2,是本申请实施例的接收线圈1的电路连接关系图。第一电路回路11、第二电路回路12和第三电路回路13在电路上相互独立,且第一电路回路11与第二电路回路12、第二电路回路12与第三电路回路13两两交叠,达到交叠去耦的目的。第一电路回路11和第三电路回路13之间通过第一电容C41进行去耦,第二电容C21与第二电路回路12的调谐匹配电路共同起到调谐作用。如图所示,第一电路回路11、第二电路回路12和第三电路回路13分别对应第一端口、第二端口和第三端口,调谐匹配电路3分别通过第一端口、第二端口和第三端口对第一电路回路11、第二电路回路12和第三电路回路13进行调整,以达到调谐、匹配和前放去耦的效果。第一电路回路11、第二电路回路12和第三电路回路13的调谐匹配电路结构相同,以第一电路回路11为例,调谐匹配电路3的电路结构包括:第三电容C12、第四电容Cf1、第五电容Cp1、第六电容Cs1、二极管D1、第一电感L11以及第二电感L12;第四电容Cf1、第五电容Cp1、第三电容C12以及第一电容C41通过串联方式连接,第六电容Cs1、第五电容Cp1、二极管D1以及第一电感L11通过串联方式连接,第三电容C12、第二电感L12以及二极管D1通过串联方式连接,组成并联谐 振电路;二极管D1起到通直流、隔交流的作用;第四电容Cf1、第五电容Cp1以及第六电容Cs1三者共同决定了电路的调谐与匹配。当二极管D1导通时,由第三电容C12与第二电感L12组成的并联谐振电路开始工作,此时第一电路回路11处于断开状态,避免磁共振***的激发信号损害电路;当二极管D1断开时,第二电感L12不工作,第三电容C12工作,第一电路回路11处于正常的接收信号状态。
第二电路回路12和第三电路回路13与第一电路回路11的调谐匹配电路结构相同,本申请将不再赘述。
本申请实施例中,以第一电路回路11为例,调谐匹配电路的调谐与匹配过程具体为:将第一端口通过同轴电缆连接到矢量网络分析仪上进行校准后,测试第一端口的S11参数,显示为史密斯圆图模式,添加调节标记点marker为磁共振***的工作频点,通过更换电容或者调节可调电容的方式调节Cf1、Cp1以及Cs1的大小,使得标记点marker移动到史密斯圆图的中心位置,完成调谐匹配电路的调谐与匹配。第二电路回路12和第三电路回路13与第一电路回路11的调谐及匹配过程相同,本申请将不再赘述。
请参阅图3,是本申请实施例的磁共振线圈成像方法流程图。本申请实施例的磁共振线圈成像方法包括以下步骤:
S1:将接收线圈置于被检测者的待测部位;
其中,以检测***为例,将线圈***被检测者的直肠。
S2:检测接收线圈的调谐、匹配和交叉耦合是否正常,如果不正常,执行S3;否则,执行S4;
S3:调节调谐匹配电路的电容大小,并重新执行S2;
S4:将接收线圈连接到磁共振***上,通过磁共振***对待测部位进行磁 共振扫描成像。
基于上述,本申请实施例的磁共振线圈采用多通道设计方式,且多个通道之间两两重叠,降低了通道与通道间的相互干扰。相对于单通道直肠线圈,本申请实施例具有更高的分辨率和更高的对比度,提高了直肠线圈的信噪比,并提高了磁共振***的成像质量,且拥有更宽的成像覆盖范围,使得线圈的成像区域更好的覆盖整个待测部位。
对所公开的实施例的上述说明,使本领域专业技术人员能够实现或使用本申请。对这些实施例的多种修改对本领域的专业技术人员来说将是显而易见的,本申请中所定义的一般原理可以在不脱离本申请的精神或范围的情况下,在其它实施例中实现。因此,本申请将不会被限制于本申请所示的这些实施例,而是要符合与本申请所公开的原理和新颖特点相一致的最宽的范围。

Claims (7)

  1. 一种磁共振线圈,其特征在于,包括接收线圈、支撑件以及调谐匹配电路;
    所述接收线圈包括至少两个电路回路,所述至少两个电路回路分别分布在支撑件上,且所述至少两个电路回路之间两两重叠;所述调谐匹配电路设于支撑件的一端,并与接收线圈电连接。
  2. 根据权利要求1所述的磁共振线圈,其特征在于,还包括同轴电缆及放大器,所述调谐匹配电路通过同轴电缆与放大器连接,所述放大器与磁共振***连接。
  3. 根据权利要求1所述的磁共振线圈,其特征在于,所述至少两个电路回路在电路上相互独立。
  4. 根据权利要求1至3任一项所述的磁共振线圈,其特征在于,所述至少两个电路回路分别对应一个端口,所述调谐匹配电路通过端口对对应的电路回路进行调谐、匹配和去耦。
  5. 根据权利要求4所述的磁共振线圈,其特征在于,所述调谐匹配电路包括第一电容、第三电容、第四电容、第五电容、第六电容、二极管、第一电感以及第二电感;第四电容、第五电容、第三电容以及第一电容通过串联方式连接,所述至少两个电路回路之间通过第一电容进行去耦;第六电容、第五电容、二极管以及第一电感通过串联方式连接,第三电容、第二电感以及二极管通过串联方式连接,组成并联谐振电路;当所述二极管导通时,所述并联谐振电路开始工作,使所述对应的电路回路处于断开状态;当二极管断开时,所述第二电感不工作,所述第三电容工作,使所述对应的电路回路处于接收信号状态。
  6. 根据权利要求5所述的磁共振线圈,其特征在于,所述调谐匹配电路的调谐与匹配过程具体为:将所述端口通过同轴电缆连接到矢量网络分析仪上进行校准后,测试所述端口的S11参数,显示为史密斯圆图模式;添加调节标记点为磁共振***的工作频点,通过更换电容或者调节电容的方式调节第三电容、第四电容以及第五电容的大小,使得标记点移动到史密斯圆图的中心位置,完成所述调谐匹配电路的调谐与匹配。
  7. 根据权利要求1所述的磁共振线圈,其特征在于,所述支撑件为设定直径大小的圆柱体。
PCT/CN2021/129477 2021-11-09 2021-11-09 一种磁共振线圈 WO2023082038A1 (zh)

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