A comprehensive multi-nuclear magnetic resonance imaging device and its imaging method

Abstract

The present application discloses a comprehensive multi-nuclear magnetic resonance imaging device and an imaging method thereof, relating to the technical field of nuclear magnetic resonance, including: a base, on which a housing is fixedly provided, the housing is coaxially sleeved with a main magnet for generating a stable static magnetic field, and a monitoring bed is arranged at the center of the housing; a control box, fixedly arranged outside the housing; a skeleton assembly, coaxially located inside the main magnet, and a gradient system is arranged on the skeleton assembly, the gradient system includes an X-gradient coil, a Y-gradient coil and a Z-gradient coil; a radio frequency assembly, arranged in multiple numbers, is arranged inside the skeleton assembly, and a receiving coil for receiving FID signals is also arranged at the center of the housing, and a control system for controlling the radio frequency assembly and the entire MRI scanning process is installed in the control box.

Description

Technical Field

[0001] This application relates to the field of nuclear magnetic resonance technology, and particularly relates to a comprehensive multi-nuclear magnetic resonance imaging device and an imaging method thereof. Background Art

[0002] A magnetic resonance imaging (MRI) device is a medical device that uses nuclear magnetic resonance phenomena to perform non-invasive and non-radioactive imaging of the internal structure of the human body. Its working principle is based on the nuclear magnetic resonance phenomenon of atomic nuclei (mainly hydrogen atomic nuclei, i.e., protons) in a strong magnetic field. The main factors for evaluating the quality of nuclear magnetic resonance imaging include signal-to-noise ratio, contrast, spatial resolution, and artifacts, etc. They are affected by imaging time, slice thickness, matrix, field of view, and the signal characteristics of the tissue itself.

[0003] Because hydrogen atoms are abundant in biomolecules and have a relatively large magnetic moment and are easy to detect, nuclear magnetic resonance focuses on the nuclear magnetic resonance signals of hydrogen atoms. In addition, multi-nuclear magnetic resonance technology can also detect the nuclear magnetic resonance signals of other nuclides. Multi-dimensional nuclear magnetic resonance technology constructs multi-dimensional spectra by combining the nuclear magnetic resonance signals of two or more nuclei, showing more molecular information, such as the spatial distance between nuclei, interactions, and dynamic processes inside the molecule, etc.

[0004] However, the principle of nuclear magnetic resonance imaging technology is complex, and there are many factors affecting the imaging quality. For example, MRI artifacts are incorrect signals that do not exist during the imaging process; they are recorded on the image data, resulting in a decrease in image quality or interference with the authenticity. Due to interference from the device itself and the outside world, the magnetic field changes, thereby generating artifacts; including non-uniform static magnetic fields or non-linearity of gradient magnetic fields, which will cause errors in the positioning of MR signals, resulting in irregular deformation of the image or abnormal changes in the signal, or distortion of spatial information encoding due to interference of the main magnetic field uniformity by various factors. In addition, in addition to the geometric and electrical characteristics of the radiofrequency micro-solenoid coil affecting the detection signal-to-noise ratio, due to different magnetic susceptibility coefficients of materials, the structure of the coil itself in the static magnetic field will also affect the uniform distribution of the internal static magnetic field.

[0005] Therefore, it is necessary to provide a comprehensive multi-nuclear magnetic resonance imaging device and an imaging method thereof to solve the problems raised in the above background art. Summary of the Invention

[0006] To achieve the above object, this application provides the following technical solution: A comprehensive multi-nuclear magnetic resonance imaging device, comprising:

[0007] A base, on which a housing is fixedly provided. The housing is coaxially sleeved with a main magnet for generating a stable static magnetic field, and a monitoring bed is arranged at the center of the housing.

[0008] The control box is fixedly arranged outside the housing;

[0009] The skeleton assembly is coaxially located inside the main magnet, and a gradient system is arranged on the skeleton assembly. The gradient system includes an X-gradient coil, a Y-gradient coil, and a Z-gradient coil;

[0010] The RF components are arranged in multiple numbers and are set inside the skeleton assembly. A receiving coil for receiving FID signals is also arranged at the center of the housing. A control system for controlling the RF components and the entire MRI scanning process is installed in the control box.

[0011] Further, as a preference, the skeleton assembly includes two semi-skeletons arranged symmetrically. A plurality of ribs are evenly distributed at intervals along the axis on the outer wall of the semi-skeleton, and a plurality of spacer blocks are also arranged outside the semi-skeleton.

[0012] Further, as a preference, the spacer blocks are distributed on the end face parallel to the axis of the semi-skeleton and on the outer surface of the semi-skeleton parallel to the axis, and the spacer blocks are arranged corresponding to the ribs.

[0013] Further, as a preference, a gap, namely a gap groove, is formed between the two semi-skeletons. An installation hole groove is arranged parallel to the axis on the inner wall of the semi-skeleton, and a plurality of arc-shaped tube bins are arranged at intervals on the inner wall of the semi-skeleton.

[0014] Further, as a preference, the RF component includes a tube sleeve. A plurality of RF wires are evenly distributed on the inner circumference of the tube sleeve. Adjusting bushings for sleeving the RF wires are arranged at positions close to the ends inside the tube sleeve, and a bearing for sleeving the RF wires is arranged at a position close to the middle inside the tube sleeve. A positioning groove for placing the RF wires is formed on the inner circumference of the bearing.

[0015] Further, as a preference, the RF wires are composed of different materials. Different material wires are also filled in the arc-shaped tube bins in a side-by-side manner, and the arrangement order corresponds to that of the RF wires. Gaps are maintained between the RF wires, and insulating materials are filled. The same is true for the arc-shaped tube bins.

[0016] Further, as a preference, an adjusting end cover is also arranged at the end of the tube sleeve, and the adjusting end cover is fixedly connected to the adjusting bushing, facilitating adjusting the rotation of the adjusting bushing and the position of the RF wires inside it through the adjusting end cover.

[0017] Further, as a preference, a contact slot is also formed on the inner wall of the tube sleeve. A connecting piece is arranged in the contact slot. By adjusting the rotation of the tube sleeve, the connecting piece is controlled to be connected to different wires in the arc-shaped tube bin, and by adjusting the rotation of the adjusting bushing, the connecting piece is controlled to be connected to different RF wires.

[0018] Further, as a preference, a catalyst pin is rotatably arranged at the center of the adjusting end cap, and the catalyst pin penetrates through the adjusting end cap. An extended contact that can contact the RF wire is arranged on the catalyst pin.

[0019] The present application also proposes a comprehensive multi-nuclear magnetic resonance imaging method, including:

[0020] Ⅰ. First, adjust the RF component, including adjusting the position of the tube sleeve and installing and fixing it, and adjusting and selecting a suitable RF wire to construct and adjust it into a complete RF coil, so as to provide a frequency consistent with the Larmor frequency of a specific atomic nucleus under the external magnetic field strength, facilitating the generation of resonance;

[0021] Ⅱ. Convey the target to be measured into the device through the bed to be monitored. At the same time, the device generates a stable static magnetic field through the main magnet, and then controls the X-gradient coil, Y-gradient coil, and Z-gradient coil in the gradient system to work through the control box, generating changing magnetic fields in different directions, so that protons at different positions have different resonance frequencies in space, facilitating subsequent encoding and decoding to achieve spatial positioning of the internal structure;

[0022] Ⅲ. Control the RF component to work through the control box, emit RF pulses with a specific frequency to excite the atomic nucleus to resonate, and then after stopping the RF pulses, the protons return to the equilibrium state and release magnetic resonance signals, which are received by the receiving coil;

[0023] Ⅳ. Process the received signals through the internal system of the control box and convert them into detailed images to display the internal structure of the human body.

[0024] Compared with the prior art, the present application provides a comprehensive multi-nuclear magnetic resonance imaging device and its imaging method, having the following beneficial effects:

[0025] In the present application, by controlling the installation angle of the tube sleeve, the connecting piece contacts the wire in the arc-shaped tube bin. Then, by rotating the adjusting end cap, the required RF wire can be controlled to contact the connecting piece, and by controlling the rotation of the catalyst pin, the extended contact contacts the required RF wire, thereby forming a circuit to construct an RF coil for generating an RF magnetic field to excite the atomic nucleus to generate a precessional force. The whole process can stably adjust the RF coil composed of metals with different magnetic susceptibilities to reduce the interference to the uniform distribution of the static magnetic field; moreover, under the support of the skeleton component, the RF coil is jointly adjusted with the RF component to ensure the accuracy and convenience of each adjustment result. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] By reading the detailed description of the non-limiting embodiments with reference to the following drawings, other features, objects, and advantages of the present application will become more obvious:

[0027] Figure 1Schematic diagram of the overall structure of a comprehensive multi-nuclear magnetic resonance imaging device;

[0028] Figure 2 Schematic diagram of the gradient system structure of a comprehensive multi-nuclear magnetic resonance imaging device;

[0029] Figure 3 Schematic diagram of the skeleton assembly structure of a comprehensive multi-nuclear magnetic resonance imaging device;

[0030] Figure 4 Schematic diagram of the overall structure of the radio frequency component of a comprehensive multi-nuclear magnetic resonance imaging device;

[0031] Figure 5 Schematic diagram of the internal structure of the radio frequency component of a comprehensive multi-nuclear magnetic resonance imaging device;

[0032] In the figure: 1, base; 2, housing; 3, monitoring bed; 4, control box; 5, skeleton assembly; 51, semi-skeleton; 52, spacer block; 53, rib; 54, placement hole groove; 55, arc tube bin; 56, clearance groove; 6, X-gradient coil; 7, Y-gradient coil; 8, Z-gradient coil; 9, radio frequency component; 91, tube sleeve; 92, radio frequency wire; 93, adjusting bushing; 94, bearing shell; 941, positioning groove; 95, adjusting end cover; 96, catalyst nail; 97, contact point groove. Detailed implementation manner

[0033] Please refer to Figures 1 - 5 , in the embodiment of the present application, a comprehensive multi-nuclear magnetic resonance imaging device includes:

[0034] Base 1, on which a housing 2 is fixedly provided, the housing 2 is coaxially sleeved with a main magnet for generating a stable static magnetic field, and a monitoring bed 3 is arranged at the center of the housing 2;

[0035] Control box 4, fixedly arranged outside the housing 2;

[0036] Skeleton assembly 5, coaxially located inside the main magnet, and a gradient system is arranged on the skeleton assembly 5, and the gradient system includes an X-gradient coil 6, a Y-gradient coil 7 and a Z-gradient coil 8;

[0037] Radio frequency components 9, arranged in multiple numbers, are arranged inside the skeleton assembly 5, and a receiving coil for receiving FID signals is also arranged at the center of the housing 2, and a control system for controlling the radio frequency components 9 and the entire MRI scanning process is installed in the control box 4.

[0038] It should be noted that in addition to the geometric and electrical characteristics of the radio frequency micro solenoid coil affecting the detection signal-to-noise ratio, due to the different magnetic susceptibility of materials, the structure of the coil itself in the static magnetic field will also affect the uniform distribution of the internal static magnetic field. One method is to select metals with different magnetic susceptibility to reduce the interference with the uniform distribution of the static magnetic field.

[0039] In this embodiment, as shown in the figure, the skeleton assembly 5 includes two half-skeletons 51 arranged symmetrically. A plurality of ribs 53 are evenly distributed at intervals along the axis on the outer wall of the half-skeleton 51, and a plurality of spacer blocks 52 are also provided outside the half-skeleton 51.

[0040] As a preferred embodiment, the spacer blocks 52 are distributed on the end face parallel to the axis of the half-skeleton 51 and on the outer surface of the half-skeleton 51 parallel to the axis. The spacer blocks 52 are arranged corresponding to the ribs 53. Specifically, the intervals between the ribs 53 and the intervals between the spacer blocks 52 are used to limit and position the installation of the X-gradient coil 6, Y-gradient coil 7, and Z-gradient coil 8.

[0041] As a preferred embodiment, a gap, namely a gap groove 56, is formed between the two half-skeletons 51. An installation hole groove 54 is provided on the inner wall of the half-skeleton 51 parallel to the axis, and a plurality of arc-shaped tube bins 55 are provided at intervals on the inner wall of the half-skeleton 51.

[0042] In this embodiment, as shown in the figure, the radio frequency assembly 9 includes a tube sleeve 91. A plurality of radio frequency wires 92 are evenly distributed on the inner circumference of the tube sleeve 91. An adjusting sleeve 93 for sleeving the radio frequency wires 92 is provided near the end of the tube sleeve 91. Specifically, the adjusting sleeve 93 drives the radio frequency wires 92 for adjustment. A bearing 94 for sleeving the radio frequency wires 92 is provided near the middle of the tube sleeve 91. A positioning groove 941 for placing the radio frequency wires 92 is provided on the inner wall circumference of the bearing 94. Specifically, it is used to support the radio frequency wires 92.

[0043] As a preferred embodiment, the radio frequency wires 92 are composed of different materials. Different material wires are also filled in the arc-shaped tube bins 55 in a side-by-side manner, and the arrangement order corresponds to that of the radio frequency wires 92. A gap is maintained between the radio frequency wires 92, and an insulating material is filled. The same is true for the arc-shaped tube bins 55.

[0044] As a preferred embodiment, an adjusting end cap 95 is further provided at the end of the tube sleeve 91, and the adjusting end cap 95 is fixedly connected to the adjusting sleeve 93, facilitating the adjustment of the rotation of the adjusting sleeve 93 and the position of the radio frequency wires 92 therein through the adjusting end cap 95.

[0045] As a preferred embodiment, a contact slot 97 is further formed in the inner wall of the sleeve 91, and a connecting piece is arranged in the contact slot 97. By adjusting the rotation of the sleeve 91, the connecting piece is controlled to communicate with different wire materials in the arc-shaped tube bin 55, and by adjusting the rotation of the adjusting sleeve 93, the connecting piece is controlled to communicate with different radio frequency wire materials 92.

[0046] As a preferred embodiment, a catalyst nail 96 is rotatably arranged at the center of the adjusting end cap 95, and the catalyst nail 96 penetrates through the adjusting end cap 95. An extended contact that can contact the radio frequency wire material 92 is arranged on the catalyst nail 96.

[0047] It should be explained that during the adjustment process, by controlling the installation angle of the sleeve 91, the connecting piece is made to contact the wire material in the arc-shaped tube bin 55. Then, by rotating the adjusting end cap 95, the required radio frequency wire material 92 can be controlled to contact the connecting piece, and by controlling the rotation of the catalyst nail 96, the extended contact is made to contact the required radio frequency wire material 92, thereby forming a circuit to construct a radio frequency coil for generating a radio frequency magnetic field to excite the atomic nucleus to generate a precessional force. The whole process can stably adjust the radio frequency coil composed of metals with different magnetization coefficients to reduce the interference to the uniform distribution of the static magnetic field;

[0048] Moreover, under the support of the skeleton assembly 5, the radio frequency assembly 9 is jointly adjusted to ensure the accuracy and convenience of each adjustment result.

[0049] In this embodiment, a comprehensive multi-nuclear magnetic resonance imaging method includes:

[0050] Ⅰ. First, adjust the radio frequency assembly 9, including adjusting the position of the sleeve 91 and installing and fixing it, and adjusting and selecting appropriate radio frequency wire materials 92 to construct and adjust into a complete radio frequency coil to provide a frequency consistent with the Larmor frequency of a specific atomic nucleus under the external magnetic field intensity to facilitate the generation of resonance;

[0051] Ⅱ. Convey the target to be measured into the device through the monitoring bed 3. At the same time, the device generates a stable static magnetic field through the main magnet, and then controls the X-gradient coil 6, Y-gradient coil 7, and Z-gradient coil 8 in the gradient system to work through the control box 4 to generate changing magnetic fields in different directions, so that protons at different positions have different resonance frequencies in space to facilitate subsequent encoding and decoding to achieve spatial positioning of the internal structure;

[0052] Ⅲ. Control the radio frequency assembly 9 to work through the control box 4, emit radio frequency pulses with a specific frequency to excite the atomic nucleus to resonate, and then after stopping the radio frequency pulses, the protons return to the equilibrium state and release magnetic resonance signals, which are received by the receiving coil;

[0053] Ⅳ. Process the received signals through the internal system of the control box 4 and convert them into detailed images to display the internal structure of the human body.

[0054] The above are only the preferred specific embodiments of the present application, but the protection scope of the present application is not limited thereto. Any person skilled in the art within the technical scope disclosed by the present application, according to the technical solution and the application concept of the present application, makes equivalent substitutions or changes, and should be covered within the protection scope of the present application.

Claims

1. A comprehensive multi-nuclear magnetic resonance imaging device, characterized in that: include: A base (1) on which a shell (2) is fixedly provided, wherein the shell (2) is coaxially sleeved with a main magnet for generating a stable static magnetic field, and a monitoring bed (3) is provided at the center of the shell (2); A control box (4) is fixedly arranged outside the housing (2); A skeleton component (5) is coaxially located inside the main magnet, and a gradient system is arranged on the skeleton component (5), wherein the gradient system comprises an X gradient coil (6), a Y gradient coil (7) and a Z gradient coil (8); A plurality of radio frequency components (9) are arranged inside the skeleton component (5), and a receiving coil for receiving FID signals is also arranged at the center of the shell (2). A control system for controlling the radio frequency components (9) and the entire MRI scanning process is installed in the control box (4); The skeleton assembly (5) comprises two symmetrically arranged half skeletons (51), the outer wall of the half skeleton (51) is provided with a plurality of ribs (53) spaced evenly along the axis, and a plurality of spacers (52) are also provided outside the half skeleton (51); A gap is formed by maintaining a distance between the two half-frames (51), namely a gap groove (56), and an inner wall of the half-frame (51) is provided with a placement hole groove (54) parallel to the axis, and a plurality of arc-shaped pipe bins (55) are arranged at intervals on the inner wall of the half-frame (51); The radio frequency component (9) comprises a sleeve (91), a plurality of radio frequency wires (92) are evenly distributed on the inner circumference of the sleeve (91), an adjusting sleeve (93) for sleeve-engaging the radio frequency wires (92) is arranged near the end of the sleeve (91), and a bearing (94) for sleeve-engaging the radio frequency wires (92) is arranged near the middle of the sleeve (91), and a positioning groove (941) for accommodating the radio frequency wires (92) is provided on the inner wall circumference of the bearing (94); The inner wall of the tube sleeve (91) is also provided with a contact groove (97), and a connecting piece is placed in the contact groove (97). By adjusting the rotation of the tube sleeve (91), the connecting piece is connected to different wires in the arc-shaped tube bin (55), and by adjusting the rotation of the adjustment shaft sleeve (93), the connecting piece is connected to different radio frequency wires (92).

2. A comprehensive multi-nuclear magnetic resonance imaging device according to claim 1, characterized in that: The spacers (52) are distributed on the end surface parallel to the axis of the semi-frame (51), and are distributed on the outer surface of the semi-frame (51) parallel to the axis, and the spacers (52) are arranged corresponding to the ribs (53).

3. A comprehensive multi-nuclear magnetic resonance imaging device according to claim 1, characterized in that: The radio frequency wires (92) are made of different materials, and the arc-shaped tube bin (55) is also filled with wires of different materials in a parallel manner, and the arrangement order corresponds to the radio frequency wires (92). Gaps are maintained between the radio frequency wires (92) and are filled with insulating materials. The same is true for the arc-shaped tube bin (55).

4. A comprehensive multi-nuclear magnetic resonance imaging device according to claim 1, characterized in that: The end of the tube sleeve (91) is also provided with an adjustment end cover (95), and the adjustment end cover (95) is fixedly connected to the adjustment shaft sleeve (93), so that the rotation of the adjustment shaft sleeve (93) and the position of the radio frequency wire (92) therein can be adjusted through the adjustment end cover (95).

5. A comprehensive multi-nuclear magnetic resonance imaging device according to claim 4, characterized in that: A catalyst nail (96) is rotatably arranged at the center of the adjustment end cover (95), and the catalyst nail (96) penetrates the adjustment end cover (95). An extended contact point capable of contacting the radio frequency wire (92) is arranged on the catalyst nail (96).

6. A comprehensive multi-nuclear magnetic resonance imaging method, using a comprehensive multi-nuclear magnetic resonance imaging device as claimed in any one of claims 1 to 5, characterized in that: The steps include: Ⅰ. Firstly, the radio frequency component (9) is adjusted, including adjusting the position of the tube sleeve (91) and installing and fixing it, and adjusting and selecting appropriate radio frequency wires (92) to construct and adjust a complete radio frequency coil, so as to provide a frequency consistent with the Larmor frequency of a specific atomic nucleus under the external magnetic field strength, so as to generate a resonance phenomenon; II. The target to be measured is transported into the device through the bed to be monitored (3). At the same time, the device generates a stable static magnetic field through the main magnet. Then, the control box (4) controls the X gradient coil (6), the Y gradient coil (7) and the Z gradient coil (8) in the gradient system to work, and generates a changing magnetic field in different directions, so that protons at different positions have different resonance frequencies in space, which is convenient for subsequent encoding and decoding to realize the spatial positioning of the internal structure; III. The radio frequency component (9) is controlled by the control box (4) to operate, and a radio frequency pulse of a specific frequency is emitted to excite the atomic nucleus to make it resonate. After the radio frequency pulse is stopped, the proton returns to a balanced state and releases a magnetic resonance signal, which is received by the receiving coil; IV. The received signal is processed by the internal system of the control box (4) and converted into a detailed image showing the internal structure of the human body.

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