Magnetic resonance coil assembly

Abstract

The application relates to a magnetic resonance coil assembly. The magnetic resonance coil assembly comprises a first coil structure and a second coil structure, the first coil structure is provided with a first accommodating cavity for accommodating a scanning part of a detected object; the second coil structure is surrounded outside the first coil structure and has a gap with the first coil structure, the size of the first coil structure can be matched with the size of the scanning part, so that the first coil structure is closer to and fits the scanning part, and thus the magnetic resonance signal emitted by the tissue can be more efficiently received, and a higher image signal-to-noise ratio can be obtained; the second coil structure is arranged outside the first coil structure and has a certain gap with the first coil structure, that is, the size of the second coil structure can be larger, which can not only adapt to more detected objects of different body sizes and improve the proportion of applicable people, but also can relieve the problem of claustrophobia of the detected object, improve the comfort of the detected object, and be more convenient to use.

Description

Technical Field

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

[0002] Medical imaging is the technology and process of acquiring images of internal tissues of the human body or a part of the human body in a non-invasive manner for medical or medical research purposes. It has become a widely used and important medical diagnostic technology for all parts of the human body. Magnetic resonance imaging (MRI) systems employing medical imaging technology apply a magnetic field within a cylindrical measurement space containing the scanned object. Local coils are widely used in MRI systems to receive magnetic resonance signals. These local coils are positioned directly close to the scanned object, and compared to other acquisition devices that are spaced apart from the scanned object and used to receive magnetic resonance signals, such as body coils, local coils offer a higher image signal-to-noise ratio.

[0003] Taking the combination of local coils into a head coil and its application to the head as an example, in order for the head coil to be applicable to most people, the cavity used by the head coil to accommodate the head of the subject cannot be made too large. Otherwise, when applied to subjects with small heads, the image signal-to-noise ratio will be poor and the image quality will decrease. On the other hand, the cavity used by the head coil to accommodate the head cannot be made too small. Otherwise, it will reduce the proportion of applicable people and affect the user experience of scanning subjects with claustrophobia. Therefore, existing magnetic resonance coils have the problem of inconvenience in use. Summary of the Invention

[0004] Therefore, it is necessary to provide a magnetic resonance coil assembly to address the inconvenience of using existing magnetic resonance coils.

[0005] A magnetic resonance coil assembly, the magnetic resonance coil assembly comprising:

[0006] The first coil structure is provided with a first receiving cavity, the cavity wall of the first receiving cavity can fit against the scanning part of the object being detected, and the first coil structure is used to receive the magnetic resonance signal of the scanning part;

[0007] A second coil structure surrounds the outside of the first coil structure, and there is a gap between the second coil structure and the first coil structure; the second coil structure is used to couple and acquire the magnetic resonance signal of the first coil structure.

[0008] In one embodiment, the first coil structure includes a plurality of first coil units; the second coil structure includes a plurality of second coil units;

[0009] Each of the first coil units is provided in a one-to-one correspondence with a second coil unit.

[0010] In one embodiment, each of the second coil units is located in the direction of extension of the magnetic field lines of the corresponding first coil unit.

[0011] In one embodiment, the first coil unit has no preamplifier and is tuned to the system frequency using a passive detuning method.

[0012] In one embodiment, the second coil unit is connected to the preamplifier via a transmission cable and is tuned to the system frequency using an active detuning method.

[0013] In one embodiment, the first coil structure includes a plurality of first coil units; the second coil structure includes a plurality of second coil units; and the number of first coil units is greater than the number of second coil units; the second coil units are sequentially connected to a matching network and a preamplifier, and the second coil units are tuned to the system frequency using an active detuning method.

[0014] In one embodiment, the first coil structure is a wearable coil structure, which can be adapted to scanning parts of various sizes or shapes, and the inner surface of the wearable coil structure can fit the scanning part when worn.

[0015] In one embodiment, the first coil structure includes a plurality of first coil modules, which are sequentially spliced ​​together to form a cylindrical wearable coil structure, wherein adjacent first coil modules have overlapping areas.

[0016] In one embodiment, the magnetic resonance coil assembly is a head coil assembly, a breast coil assembly, an elbow joint coil assembly, a wrist joint coil assembly, an ankle joint coil assembly, or a knee joint coil assembly.

[0017] In one embodiment, the magnetic resonance coil assembly further includes a cable, one end of which is electrically connected to the second coil structure;

[0018] The magnetic resonance coil assembly also includes an amplifier electrically connected to the other end of the cable.

[0019] The aforementioned magnetic resonance coil assembly includes a first coil structure and a second coil structure. The size of the first coil structure can be adapted to the size of the scanning area, thus getting closer and closer to the scanning area, thereby receiving the magnetic resonance signals emitted by the tissue more efficiently and obtaining a higher image signal-to-noise ratio. The second coil structure is located outside the first coil structure and has a certain gap with the first coil structure, that is, the size of the second coil structure can be made larger. This not only accommodates a wider range of body types of subjects, increasing the proportion of applicable people, but also alleviates the claustrophobia of subjects, improves their comfort, and makes it more convenient to use. Attached Figure Description

[0020] Figure 1 This is a schematic diagram of a magnetic resonance coil assembly provided in the first embodiment of this application.

[0021] Figure 2 for Figure 1 A simplified diagram of the magnetic resonance coil assembly shown.

[0022] Figure 3 for Figure 1 The diagram shows the application of the first coil structure in the magnetic resonance coil assembly.

[0023] Figure 4 This is a schematic diagram of a magnetic resonance coil assembly provided in the second embodiment of this application.

[0024] Figure 5 for Figure 4 The diagram shows an exploded view of the magnetic resonance coil assembly.

[0025] Figure 6 for Figure 4 The diagram shows an application schematic of the magnetic resonance coil assembly.

[0026] Figure 7 This is a schematic diagram of a magnetic resonance coil assembly provided in the third embodiment of this application.

[0027] Figure 8 for Figure 7 The diagram shows an exploded view of the magnetic resonance coil assembly.

[0028] Figure 9 for Figure 7 The diagram shows an application schematic of the magnetic resonance coil assembly.

[0029] Figure 10 This is a schematic diagram of the first coil module in the magnetic resonance coil assembly provided in the fourth embodiment of this application.

[0030] Figure 11 for Figure 10 A schematic diagram of the first coil structure in the magnetic resonance coil assembly shown.

[0031] Figure 12A An equivalent circuit diagram of the first coil unit included in the first coil structure provided in an embodiment of this application.

[0032] Figure 12B for Figure 12A The diagram shows the observation results.

[0033] Figure 12C An equivalent circuit diagram of the second coil unit included in the second coil structure provided in an embodiment of this application.

[0034] Figure 12D for Figure 12C The diagram shows the observation curves.

[0035] Figure 12E A schematic diagram of the observation curve of the second coil unit provided in another embodiment of this application.

[0036] Figure 13A An equivalent circuit diagram of the second coil unit included in the second coil structure provided in another embodiment of this application.

[0037] Reference numerals in the attached figures: 110, first coil structure; 111, first receiving cavity; 112, first coil unit; 113, first coil module; 114, overlapping area; 120, second coil structure; 121, gap; 122, second coil unit; 1000, object to be detected. Detailed Implementation

[0038] To make the above-mentioned objectives, features, and advantages of this application more apparent and understandable, the specific embodiments of this application are described in detail below with reference to the accompanying drawings. Many specific details are set forth in the following description to provide a thorough understanding of this application. However, this application can be implemented in many other ways different from those described herein, and those skilled in the art can make similar modifications without departing from the spirit of this application. Therefore, this application is not limited to the specific embodiments disclosed below.

[0039] In the description of this application, it should be understood that if terms such as "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential" appear, these terms indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this application.

[0040] Furthermore, where the terms "first" and "second" appear, these terms are for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined with "first" or "second" may explicitly or implicitly include at least one of that feature. In the description of this application, where the term "multiple" appears, "multiple" means at least two, such as two, three, etc., unless otherwise explicitly specified.

[0041] In this application, unless otherwise expressly specified and limited, the terms "installation," "connection," "joining," and "fixing," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components, unless otherwise expressly limited. Those skilled in the art can understand the specific meaning of the above terms in this application based on the specific circumstances.

[0042] In this application, unless otherwise expressly specified and limited, the use of descriptions such as "above" or "below" the second feature indicates that the first and second features are in direct contact or indirect contact via an intermediate medium. Furthermore, "above," "on top of," and "over" the second feature can mean that the first feature is directly above or diagonally above the second feature, or simply that the first feature is at a higher horizontal level than the second feature. Similarly, "below," "below," and "under" the second feature can mean that the first feature is directly below or diagonally below the second feature, or simply that the first feature is at a lower horizontal level than the second feature.

[0043] It should be noted that if an element is referred to as being "fixed to" or "set on" another element, it can be directly on the other element or there may be an intervening element. If an element is considered to be "connected to" another element, it can be directly connected to the other element or there may be an intervening element. If so, the terms "vertical," "horizontal," "upper," "lower," "left," "right," and similar expressions used in this application are for illustrative purposes only and do not represent the only possible implementation.

[0044] See Figure 1As shown, an embodiment of this application provides a magnetic resonance coil assembly including a first coil structure 110 and a second coil structure 120. The first coil structure 110 is provided with a first receiving cavity 111. The size of the first receiving cavity 111 is adapted to the scanning part of the object being detected 1000, that is, the cavity wall of the first receiving cavity 111 can be fitted and connected to the scanning part. The first coil structure 110 is used to receive magnetic resonance signals from the scanning part. The second coil structure 120 surrounds the outside of the first coil structure 110, that is, the first coil structure 110 is located in the three-dimensional space formed by the second coil structure 120, and there is a gap 121 between the second coil structure 120 and the first coil structure 110. The second coil structure 120 is used to couple and acquire the magnetic resonance signal of the first coil structure 110. For example, the second coil structure 120 and the first coil structure 110 are coupled and acquired by magnetic field coupling.

[0045] In the aforementioned magnetic resonance coil assembly, the size of the first coil structure 110 can be adapted to the size of the scanning area, thus getting closer and more closely fitting the scanning area. This allows for more efficient reception of magnetic resonance signals emitted by the tissue. Furthermore, the second coil structure 120 acquires the magnetic resonance signal from the first coil structure 110 through coupling, thereby improving the penetration depth of the magnetic resonance coil assembly, achieving a higher image signal-to-noise ratio, and realizing better scanning results. The second coil structure 120 is located outside the first coil structure 110 and has a certain gap 121 between them. In other words, the size of the second coil structure 120 can be made larger, which not only accommodates a wider range of body types of subjects 1000, increasing the proportion of applicable people, but also alleviates the claustrophobia of subjects 1000, improving their comfort and making it more convenient to use.

[0046] like Figure 1 As shown, in one embodiment, the first coil structure 110 may be worn and disposed within the second coil structure 120. The first coil structure 110 is not connected by a cable. The second coil structure 120 acquires the magnetic resonance signal of the first coil structure 110 through coupling, and after being amplified by an amplifier (e.g., a low-noise amplifier or a preamplifier), it is connected to a receiver or a coil channel selector via a cable or connector.

[0047] like Figure 4As shown, in one embodiment, the first coil structure 110 includes a plurality of first coil units 112, which are arranged in an array to form a coil array; wherein, two adjacent first coil units 112 overlap each other. This arrangement is beneficial to improving the coverage effect of the coil units, so that the entire first coil structure 110 can receive the nuclear magnetic resonance signals from all tissues in the scanned area.

[0048] Furthermore, such as Figure 4 As shown, the second coil structure 120 includes a plurality of arrayed second coil units 122; each first coil unit 112 is arranged in a one-to-one correspondence with a second coil unit 122. That is, the coil density of the first coil unit 112 is the same as the coil density of the second coil unit 122, so that the first coil unit 112 and the second coil unit 122 have a certain magnetic coupling, and reduce the coupling interference between multiple adjacent and second adjacent first coil units 112 in the first coil structure 110, and reduce the coupling interference between multiple adjacent and second adjacent second coil units 122 in the second coil structure 120.

[0049] like Figure 12A As shown, in one embodiment, when the first coil unit 112 and the second coil unit 122 are arranged in a one-to-one correspondence, the first coil unit 112 has no preamplifier, and the tuning circuit uses passive detuning mode to control the second coil unit 122 to tune to the system frequency, wherein: C14 is the equivalent capacitance of the first coil unit 112; C11 is the tuning capacitor; C13 is the matching capacitor; C12, L11, and two forward and reverse diodes constitute the passive detuning circuit. Figure 12B As shown, by using the dual-pickup method, the resonant frequency of the first coil unit 112 can be detected as the system frequency f0 of the magnetic resonance scanning device.

[0050] like Figure 12C As shown, in one embodiment, the second coil unit 122 is connected to the preamplifier via a transmission cable, and the tuning circuit uses an active detuning method to control the second coil unit 122 to tune to the system frequency. Wherein: C23 is the equivalent capacitance of the second coil unit 122; C21 is the tuning capacitor; C22, the inductor connected to it, and the diode constitute the active detuning circuit; the second coil unit 122 is located at the equivalent impedance Z of the preamplifier. in Preamplifier Z that meets the requirements of connection via transmission cable preamp Noise matching requirements. For example... Figure 12D As shown, using a dual-pickup method, the resonant frequency of the second coil unit 122 can be detected as the system frequency f0 of the magnetic resonance scanning device. Figure 12EAs shown, in another embodiment, the second coil unit 122, which is not connected to the preamplifier, will have a frequency offset relative to the system frequency f0.

[0051] In one embodiment, the first coil unit 112 and the second coil unit 122 have an inductive coupling relationship. Specifically, each second coil unit 122 is located in the extension direction of the magnetic field lines of the corresponding first coil unit 112, so that the first coil unit 112 and the second coil unit 122 have very strong magnetic coupling, thereby reducing the coupling between two adjacent first coil units 112. The operating frequency of the first coil structure 110 is consistent with the Larmor frequency of the magnetic resonance scanning device. When the second coil structure 120 is adjusted individually, by changing the inductance or capacitance of the second coil unit 122, the operating frequency of the second coil structure 120 can be made to deviate from the Larmor frequency. Therefore, when the first coil structure 110 and the second coil structure 120 are coupled, the coupling interference between different coil units belonging to the same coil structure can be reduced.

[0052] like Figure 13A As shown, in one embodiment, when the first coil unit 112 and the second coil unit 122 are not arranged in a one-to-one correspondence, the second coil unit 122 is connected to a matching network and then to a preamplifier, and the tuning circuit uses an active detuning method to control the second coil unit 122 to tune to the system frequency. Wherein: C33 is the equivalent capacitance of the second coil unit 122; C31 is the tuning capacitor; C32, the inductor connected to it, and the diode form an active detuning circuit; Cm is the matching capacitor; the second coil unit 122 and the matching network are connected at the equivalent impedance Z of the preamplifier. in Satisfy the Z of the preamplifier preamp Noise matching requirements.

[0053] like Figure 4As shown, in one embodiment, the gap 121 between the second coil unit 122 and the corresponding first coil unit 112 is not greater than the outer diameter of the first coil unit 112. Specifically, the gap 121 between the second coil unit 122 and the corresponding first coil unit 112 is greater than 1.5 cm. If the gap 121 between the second coil unit 122 and the corresponding first coil unit 112 is too small, it will cause coupling interference between the coil units belonging to the same coil structure and the first coil unit 112. At the same time, if the gap 121 between the second coil unit 122 and the corresponding first coil unit 112 is too large, it will also cause the second coil unit 122 to deviate from the magnetic field of the first coil unit 112, resulting in a weakening of the magnetic coupling between the two. Therefore, by setting the gap 121 between the second coil unit 122 and the first coil unit 112 to be no greater than the outer diameter of the first coil unit 112, the coupling effect between the two is ensured.

[0054] In one embodiment, the first coil structure 110 further includes a first detuning circuit (not shown) for detuning control of the first coil unit 112. This first detuning circuit can be a passive detuning circuit. The passive detuning circuit resonates at a specific frequency by selecting appropriate inductance and capacitance values. When radio frequency signal transmission or reception is not required, the frequency of the radio frequency signal is the same as or close to the resonant frequency of the passive detuning circuit, automatically putting the circuit in a detuned state. In the detuned state, the impedance of the radio frequency circuit becomes very high, effectively isolating it from the system and reducing electromagnetic interference. When radio frequency signal transmission or reception is required, the frequency of the radio frequency signal differs from the resonant frequency of the passive detuning circuit, restoring the circuit to normal operation. In the restored state, the impedance of the radio frequency circuit returns to its normal value, ensuring effective signal transmission and reception.

[0055] Furthermore, the second coil structure 120 also includes a second detuning circuit for detuning control of the second coil unit 122. This second detuning circuit can be an active detuning circuit and / or a passive detuning circuit. The first and second detuning circuits are used to eliminate the influence of the magnetic resonance coil assembly on the B1+ field (RF transmission field) of the volumetric transmitting coil. An active detuning circuit typically includes one or more electronic switches (such as PIN diodes, field-effect transistors, etc.). The state of the switches is controlled by a controller (such as a microprocessor or application-specific integrated circuit), which turns the switches on or off as needed. When RF signal transmission or reception is not required, the controller turns the switches on, putting the RF circuit in a detuned state. When RF signal transmission or reception is required, the controller turns the switches off, restoring the RF circuit to normal operation.

[0056] like Figure 1As shown, in one embodiment, since the first coil structure 110 and the second coil structure 120 are separately configured, the first coil structure 110 of different sizes can be replaced according to the size of the object being scanned, so that the first coil structure 110 can fit the scanning area, obtain a higher image signal-to-noise ratio, and achieve a better scanning effect.

[0057] In one embodiment, the magnetic resonance coil assembly further includes a cable, one end of which is electrically connected to the second coil structure 120; the magnetic resonance coil assembly also includes an external amplifier electrically connected to the other end of the cable. In other embodiments, the amplifier may also be built into the bedside of the magnetic resonance scanning device.

[0058] In another embodiment, the MRI scanner bed is equipped with a transmission interface; the MRI scanner also includes a receiver, and the transmission interface is connected to the receiver; the second coil structure 120 is connected to the transmission interface via a transmission cable to transmit the MRI signals received by the second coil structure 120 to the receiver. Optionally, the receiver can be integrated into the bed, and the second coil structure 120 can be directly connected to the transmission interface via a transmission cable. Alternatively, the receiver can be separated from the bed, the second coil structure 120 can be connected to the transmission interface via a transmission cable, and the MRI signals received by the second coil structure 120 can be further transmitted to the receiver via a transmission cable passing through the bed.

[0059] In another embodiment, the receiver can be integrated into the hospital bed. The second coil structure 120 is also connected to an amplifier, a filter, an analog-to-digital converter circuit, and a modulation and transmission unit. The amplifier, filter, analog-to-digital converter circuit, and modulation and transmission unit can all be integrated into the second coil structure 120. The second coil structure 120 wirelessly transmits the received magnetic resonance signal to the receiver. Specifically:

[0060] The second coil structure 120 acquires the magnetic resonance signal in real time and transmits it to an amplifier. The amplifier in the second coil structure 120 amplifies the coupled magnetic resonance signal and then transmits it to a filter. The filter filters the magnetic resonance signal and transmits it to an analog-to-digital converter (ADC). The ADC performs analog-to-digital conversion to obtain a digital magnetic resonance signal. The modulation and transmission unit modulates the digital magnetic resonance signal and wirelessly transmits the modulated signal.

[0061] Correspondingly, the receiver includes a wireless receiving module and a coherent demodulator. The wireless receiving module receives the modulated signal; the coherent demodulator, connected to the wireless receiving module, receives the modulated signal and demodulates it using a carrier wave to obtain a digital magnetic resonance signal. The coherent demodulator includes a bandpass filter, a mixer, a low-pass filter, and a carrier recovery unit. The bandpass filter, connected to the wireless receiving module, receives the modulated signal and filters out interference to obtain a filtered modulated signal; the carrier recovery unit, connected to the wireless receiving module, receives the modulated signal and obtains the carrier wave based on it; the mixer, connected to the bandpass filter and the carrier recovery unit, receives the filtered modulated signal and the carrier wave, and mixes them to obtain a mixed signal; the low-pass filter, connected to the first mixer, receives the mixed signal and filters out high-frequency signals to obtain the digital magnetic resonance signal.

[0062] like Figure 6 As shown, in one embodiment, the first coil structure 110 includes a flexible body and a flexible conductive wire disposed on the flexible body. The conductive wire is stretchable, meaning the first coil structure 110 is a wearable coil structure. This wearable coil structure can adapt to scanning areas of various sizes or shapes, and its inner surface can conform to the scanning area when worn. Thus, the first coil structure 110 can be worn by the subject 1000 to the relevant scanning area. After entering the scanning room, the subject only needs to lie on the bed and connect the cable, greatly reducing the complexity and time of the positioning process and improving examination efficiency.

[0063] like Figure 10 and Figure 11 As shown, in one embodiment, the first coil structure 110 includes multiple first coil modules 113, which are sequentially spliced ​​together to form a cylindrical wearable coil structure. By changing the number of first coil modules 113, the size of the space enclosed by the first coil structure 110 can be changed to accommodate different sizes of scanning areas, resulting in a better fit between the first coil structure 110 and the scanning area, thus improving the scanning imaging quality. Simultaneously, the first coil structure 110 can be manufactured in different models to adapt to different sizes of scanning areas, thereby ensuring imaging quality. Adjacent first coil modules 113 have an overlapping area 114. This improves the coverage effect of the coil, enabling the entire magnetic resonance coil assembly to receive MRI signals from all tissues in the scanning area.

[0064] In another embodiment, the first coil structure 110 can also be a flexible coil structure, including a flexible body. The first coil unit 112 is attached to the flexible body. The flexible body is made of a flexible and deformable material such as felt or PU, so that the first coil structure 110 can be unfolded into a planar structure for the object to be detected 1000 to wear; after being worn, it can be wound into a cylindrical structure, which can better adhere to the scanning area during use, improving the usability of the first coil structure 110. The first coil unit 112 in the first coil structure 110 is made of flexible conductive wire, which helps to improve the flexibility of the first coil structure 110.

[0065] like Figures 1 to 3 As shown, in one embodiment, the wearable coil structure is helmet-shaped when worn. The flexible body of the first coil structure 110 wraps around the head, and the shell of the second coil structure 120 is made of rigid material. The second coil structure 120 is helmet-shaped and supports the head.

[0066] In yet another embodiment, such as Figures 4 to 6 As shown, the wearable coil structure is cup-shaped when worn. The flexible body of the first coil structure 110 wraps around the mammary gland, and the shell of the second coil structure 120 is made of rigid material. The shell of the second coil structure 120 has a support surface and a receiving cavity. The support surface can support the object being detected, and the receiving cavity can accommodate the mammary gland after wearing the first coil structure 110.

[0067] like Figures 7 to 9 As shown, in another embodiment, the wearable coil structure is cylindrical when worn. The flexible body of the first coil structure 110 wraps around the upper or lower limb joint, and the second coil structure 120 is cylindrical along the axial direction of the cylinder. The size of the first coil structure 110 is smaller than the size of the second coil structure 120.

[0068] In other embodiments, the wearable coil structure may also be boot-shaped or shoulder-shaped when worn to better fit different scanning areas. For example, in one embodiment, the first coil structure 110 is boot-shaped when worn, and correspondingly, the second coil structure 120 is an ankle coil with a rigid shell.

[0069] Understandably, in another embodiment, the first coil structure 110 is scapular when worn, and correspondingly, the second coil structure 120 is a shoulder coil with a rigid shell.

[0070] like Figures 1 to 3As shown, in one embodiment, the magnetic resonance coil assembly can be a head coil assembly. When it is used as a head coil assembly, the first coil structure 110 can be used with multiple wearable head coils of different sizes, so that a higher image signal-to-noise ratio can be obtained when scanning heads of different sizes. At the same time, the second coil structure 120 can be made very large, which can solve the problem of claustrophobia and improve the comfort of the subject 1000 being tested.

[0071] like Figures 4 to 6 As shown, in one embodiment, the magnetic resonance coil assembly can be a breast coil assembly. When used as a breast coil assembly, the first coil structure 110 can be used with wearable bras of multiple sizes, enabling higher image signal-to-noise ratios when scanning breasts of different sizes, and accommodating scanning of a wider range of people.

[0072] like Figures 7 to 9 As shown, in one embodiment, the magnetic resonance coil assembly can be a knee joint coil assembly. The second coil structure 120 is arranged outside the first coil structure 110. The second coil unit 122 and the first coil unit 112 are radially spaced apart, and the coverage area of ​​the second coil unit 122 is larger than that of the first coil unit 112; that is, the size of the first coil unit 112 is generally smaller than the size of the second coil unit 122. Understandably, in other embodiments, the magnetic resonance coil assembly can be an elbow joint coil assembly, a wrist joint coil assembly, or an ankle joint coil assembly, etc. When the magnetic resonance coil assembly is applied to scanning areas such as the knee, elbow, wrist, or ankle joints, the first coil structure 110 can be composed of multiple first coil modules 113 spliced ​​together. By changing the number of first coil modules 113 spliced ​​together, the size of the space enclosed by the first coil structure 110 can be changed. Simultaneously, the first coil structure 110 can be manufactured in different models to adapt to different sizes of scanning areas, thereby ensuring imaging quality.

[0073] Furthermore, one embodiment of this application also provides a magnetic resonance scanning device, including a hospital bed (not shown), a scanner (not shown), and a magnetic resonance coil assembly. The hospital bed is used to support the object being examined. The magnetic resonance coil assembly includes a first coil structure 110 and a second coil structure 120. The first coil structure 110 has a flexible body and can be worn on the scanning area of ​​the object being examined. The hospital bed can support the object being examined. The second coil structure 120 is mounted on the hospital bed and can cover or wrap the scanning area corresponding to the first coil structure 110. The second coil structure 120 can be coupled with the first coil structure 110, for example, the second coil structure 120 can couple and acquire the magnetic resonance signal received by the first coil structure 110 through magnetic field coupling.

[0074] The scanner is used to perform scanning imaging operations on the object being inspected. It forms a second receiving cavity (not shown) to accommodate the object for scanning imaging. The scanner includes a main magnet (not shown), gradient coils (not shown), and a volumetric emission coil (not shown). The main magnet, which may be composed of superconducting coils, generates the main magnetic field (B0 field). The gradient coils include X-coil, Y-coil, and Z-coil, which generate X-coil, Y-coil, and Z-coil gradient fields, respectively, to generate corresponding spatially encoded signals for spatial localization of the magnetic resonance signal. The main magnet surrounds and forms the detection space. The gradient coils are positioned within the gaps formed by the main magnet, and the volumetric emission coil is located inside the detection space. In other words, the main magnet, gradient coils, and volumetric emission coil together form the second receiving cavity, which contains the detection space. The central portion of the second receiving cavity corresponds to the field of view (FOV).

[0075] Specifically, the hospital bed is coupled to the scanner, and the bed can move in or out of the second receiving cavity along its axial direction. A magnetic resonance coil assembly is disposed on the hospital bed and can move in or out of the second receiving cavity with the bed. The magnetic resonance coil assembly is used to receive magnetic resonance signals acquired from the human body.

[0076] In one embodiment, the magnetic resonance imaging (MRI) scanner includes a receiver integrated into or separated from the hospital bed, with the bed's transmission interface connected to the receiver. A second coil structure 120 is connected to the bed's transmission interface via a transmission cable to transmit the MRI signals received by the second coil structure 120 to the receiver.

[0077] In another embodiment, the receiver is integrated into the hospital bed. The second coil structure 120 wirelessly transmits the received magnetic resonance signals to the receiver.

[0078] In the above-mentioned magnetic resonance scanning device, the size of the first coil structure in the magnetic resonance coil assembly can be adapted to the size of the scanning area, so as to be closer to and fit the scanning area. Therefore, it can receive the magnetic resonance signal emitted by the tissue more efficiently and obtain a higher image signal-to-noise ratio. Moreover, it can alleviate the claustrophobia of the subject being examined, improve the comfort of the subject being examined, and make it more convenient to use.

[0079] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0080] The embodiments described above are merely illustrative of several implementation methods of this application, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the patent application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this patent application should be determined by the appended claims.

Claims

1. A magnetic resonance coil assembly, characterized in that, The magnetic resonance coil assembly includes: The first coil structure (110) can form a first receiving cavity (111), the cavity wall of the first receiving cavity (111) can fit with the scanning part of the object being tested (1000), and the first coil structure (110) is used to receive the magnetic resonance signal of the scanning part. The second coil structure (120) surrounds the outside of the first coil structure (110), and there is a gap (121) between the second coil structure (120) and the first coil structure (110); the second coil structure (120) is used to couple and acquire the magnetic resonance signal of the first coil structure (110).

2. The magnetic resonance coil assembly according to claim 1, characterized in that, The first coil structure (110) includes a plurality of first coil units (112); the second coil structure (120) includes a plurality of second coil units (122). Each of the first coil unit (112) is provided in a one-to-one correspondence with a second coil unit (122).

3. The magnetic resonance coil assembly according to claim 2, characterized in that, Each of the second coil units (122) is located in the direction of extension of the magnetic field lines of the corresponding first coil unit (112).

4. The magnetic resonance coil assembly according to claim 2, characterized in that, The first coil unit (112) has no preamplifier and is tuned to the system frequency using a passive detuning method.

5. The magnetic resonance coil assembly according to claim 4, characterized in that, The second coil unit (122) is connected to the preamplifier via a transmission cable and is tuned to the system frequency using an active detuning method.

6. The magnetic resonance coil assembly according to claim 1, characterized in that, The first coil structure (110) includes a plurality of first coil units (112); the second coil structure (120) includes a plurality of second coil units (122); and the number of the first coil units (112) is greater than the number of the second coil units (122); the second coil units (122) are connected in sequence to a matching network and a preamplifier, and the second coil units (122) are tuned to the system frequency by active detuning.

7. The magnetic resonance coil assembly according to claim 1, characterized in that, The first coil structure (110) is a wearable coil structure, which can be adapted to scanning parts of various sizes or shapes, and its inner surface can fit the scanning part when the wearable coil structure is worn.

8. The magnetic resonance coil assembly according to claim 7, characterized in that, The first coil structure (110) includes a plurality of first coil modules (113), which are sequentially spliced ​​together to form a cylindrical wearable coil structure, wherein two adjacent first coil modules (113) have an overlapping area (114).

9. The magnetic resonance coil assembly according to claim 1, characterized in that, The magnetic resonance coil assembly is a head coil assembly, a breast coil assembly, an elbow joint coil assembly, a wrist joint coil assembly, an ankle joint coil assembly, or a knee joint coil assembly.

10. The magnetic resonance coil assembly according to claim 1, characterized in that, The magnetic resonance coil assembly also includes a cable, one end of which is electrically connected to the second coil structure (120); The magnetic resonance coil assembly also includes an amplifier electrically connected to the other end of the cable.

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