CN212872865U

CN212872865U - Gradient coil system for special nuclear magnetic resonance equipment for mammary gland

Info

Publication number: CN212872865U
Application number: CN202021824634.6U
Authority: CN
Inventors: 陈博; 白易民; 刘艳华; 陈豪; 曲绪凯; 李明闯; 祁建军
Original assignee: Shandong Aoluorui Medical Technology Co Ltd
Current assignee: Shandong Aoluorui Medical Technology Co Ltd
Priority date: 2020-08-27
Filing date: 2020-08-27
Publication date: 2021-04-02
Anticipated expiration: 2030-08-27

Abstract

The utility model belongs to the technical field of nuclear magnetic resonance uses, especially, relate to a gradient coil system for special nuclear magnetic resonance equipment of mammary gland. Including main gradient coil layer, shielding coil layer and the shimming layer of setting between main gradient coil layer and shielding coil layer, main gradient coil layer includes GX coil, GY coil or GZ coil, the shielding coil layer includes the SX coil, SY coil or SZ coil, compares with prior art, the utility model has the advantages of and positive effect lie in, the utility model provides a gradient coil system for special nuclear magnetic resonance equipment of mammary gland makes the improvement through structure and overall arrangement to current gradient coil to reach the intensity that increases the main field in Z axle direction, and then conveniently accomplish the detection of changing to the mammary gland, simultaneously, the utility model discloses rationally distributed, simple structure, processing convenience are fit for using widely on a large scale.

Description

Gradient coil system for special nuclear magnetic resonance equipment for mammary gland

Technical Field

The utility model belongs to the technical field of nuclear magnetic resonance uses, especially, relate to a gradient coil system for special nuclear magnetic resonance equipment of mammary gland.

Background

Magnetic Resonance Imaging (MRI) is an important technique in the field of medical imaging. The device puts a person to be detected in a special magnetic field, excites hydrogen atomic nuclei in a human body by using radio frequency pulse, causes the hydrogen atomic nuclei to resonate, and absorbs energy. After the radio frequency pulse is stopped, the hydrogen atomic nucleus sends out radio signals according to specific frequency, releases absorbed energy, is recorded by a receiver outside the body, and is processed by an electronic computer to obtain an image. Self-shielded gradient coils are an important component of magnetic resonance imaging apparatus for spatial localization, including phase and frequency encoding. The gradient field generated by the gradient coil can be processed to define any position in space.

Scientific research in the fields of magnetic resonance imaging and applications places ever-increasing demands on gradient performance. In the magnetic resonance system, the traditional gradient coil comprises three groups of main gradient coils GX, GY and GZ and three groups of shielding gradient coils SX, SY and SZ, a gradient power amplifier drives the three groups of main gradient coils GX, GY and GZ so as to generate gradient magnetic fields in X, Y and Z three directions and meet the imaging requirement of the magnetic resonance system, and the three groups of shielding gradient coils SX, SY and SZ are respectively the shielding gradient coils in X, Y and Z three directions. Wherein X, Y coil is fingerprint coil, and Z coil is spiral tubular coil. The six sets of coils are fabricated as cylindrical structures and assembled coaxially, and then packaged together to form a cylindrical gradient coil.

The existing gradient coil used by nuclear magnetic resonance lacks a special gradient coil aiming at the aspect of mammary gland, so that the existing detection of the aspect of mammary gland has the technical problems of nonuniform imaging, long scanning time and large image slice thickness.

SUMMERY OF THE UTILITY MODEL

The utility model discloses to the technical problem that foretell mammary gland is convenient nuclear magnetic resonance detected to exist, provide a reasonable in design, method is simple, processing is convenient and can realize that the scanning time is short, the even and image slice thickness of formation of image is little the gradient coil system who is used for special nuclear magnetic resonance equipment of mammary gland.

In order to achieve the above purpose, the technical scheme adopted by the utility model is that the utility model provides a gradient coil system for special nuclear magnetic resonance equipment for mammary gland, which comprises a main gradient coil layer, a shielding coil layer and a shimming layer arranged between the main gradient coil layer and the shielding coil layer, the main gradient coil layer comprises a GX coil, a GY coil or a GZ coil, the shielding coil layer comprises an SX coil, a SY coil or an SZ coil, the main gradient coil layer, the shielding coil layer and the shimming layer are arranged in 13 layers, the main gradient coil layer or the shielding coil layer comprises four GX coils, GY coils, GZ coils, SX coils, SY coils or SZ coils which are arranged in the same layout along the axial direction of the cylinder and are mutually connected, wherein the main gradient coil layer comprises at least 7 coil layers and the shield coil layer comprises at most 5 coil layers.

Preferably, the main gradient coils include three layers of GZ coils, two layers of GY coils, and one layer of GX coils.

Preferably, the shield coil layer includes two layers of SZ coils, two layers of SY coils, and one layer of SX wire.

Preferably, the GZ coil includes a first GZ coil, a second GZ coil, and a third GZ coil of three different layouts, the second GZ coil has a pitch of spiral at least twice as large as that of the first GZ coil or the third GZ coil, and the second GZ coil is disposed between the first GZ coil and the third GZ coil.

Compared with the prior art, the utility model has the advantages and positive effects that,

1. the utility model provides a gradient coil system for special nuclear magnetic resonance equipment of mammary gland makes the improvement through structure and overall arrangement to current gradient coil to reach the intensity that increases the main field in Z axle direction, and then the detection of change is accomplished to the mammary gland to the convenience, simultaneously, the utility model discloses rationally distributed, simple structure, processing are convenient, are fit for using widely on a large scale.

Drawings

In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the drawings required to be used in the description of the embodiments are briefly introduced below, and it is obvious that the drawings in the following description are some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to these drawings without inventive labor.

Fig. 1 is a schematic diagram of a coil placement of a gradient coil system for a mammary gland-dedicated nuclear magnetic resonance apparatus provided in example 1;

fig. 2 is a schematic structural diagram of a first GZ coil provided in embodiment 1;

fig. 3 is a schematic structural diagram of a second GZ coil provided in embodiment 1;

fig. 4 is a schematic structural diagram of a third GZ coil provided in embodiment 1

In the above figures, 1 denotes a coil.

Detailed Description

In order to make the above objects, features and advantages of the present invention more clearly understood, the present invention will be further described with reference to the accompanying drawings and examples. It should be noted that the embodiments and features of the embodiments of the present application may be combined with each other without conflict.

In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present invention, however, the present invention may be practiced in other ways than those specifically described herein, and therefore the present invention is not limited to the limitations of the specific embodiments of the present disclosure.

Embodiment 1, as shown in fig. 1 to 4, this embodiment is directed to providing a gradient coil system for nuclear magnetic resonance of a breast, in consideration of characteristics of a female breast, if a Z axis is taken from a head to a step of a patient, an X axis represents the left and right of the patient, and a Y axis represents the front and back of a human body, and in consideration of that a gradient coil mainly generates a magnetic field which is weak relative to a main magnetic field and changes in a spatial position, and is superimposed on the main magnetic field. For this reason, in order to achieve the purpose of targeting at the breast, the gradient coil system for the special nuclear magnetic resonance device for the breast provided by this embodiment includes a main gradient coil layer, a shielding coil layer, and a shimming layer disposed between the main gradient coil layer and the shielding coil layer, specifically, the main gradient coil layer is disposed on the inner side of the shielding coil layer, the main gradient coil layer includes a GX coil, a GY coil, or a GZ coil, and the shielding coil layer includes an SX coil, a SY coil, or an SZ coil, which are the common structures in the prior art, so in this embodiment, detailed description is not added.

In order to increase the influence speed of the coil, in the present embodiment, the main gradient coil layer or the shielding coil layer includes four GX coils, GY coils, GZ coils, SX coils, SY coils or SZ coils which are arranged in the same layout and connected with each other along the axial direction of the column, that is, the coils used in the same layer must be the same distributed coils, for example, if this coil is a GX coil, the whole layer is a GX coil and is a GX coil with the same layout. Therefore, the whole gradient coil is divided into four parts along the axial direction of the cylinder, and the corresponding speed of the gradient coil is further improved, so that the aim of quick imaging is fulfilled.

In order to increase the high linearity of the gradient coil, in the present embodiment, the main gradient coil layer, the shielding coil layer and the shim layer are arranged in 13 layers, wherein the shim layer is a single layer, for this purpose, the main gradient coil layer and the shielding coil layer are 12 layers, for the purpose of improving the gradient strength, the main gradient coil layer comprises at least 7 coil layers, and the shielding coil layer comprises at most 5 coil layers. In this embodiment, the main gradient coil layer is 7 layers, and the shield coil layer is 5 layers.

In order to achieve a more accurate observation of the mammary gland, the main gradient coil includes three layers of GZ coils, two layers of GY coils, and one layer of GX coils. Therefore, the gradient strength in the Z-axis direction is better, the linearity is better, and the purposes of improving the imaging and reducing the slice thickness are further achieved.

In order to achieve the purpose of shielding the eddy current linearity, in the present embodiment, the shielding coil layer includes two layers of SZ coils, two layers of SY coils, and one layer of SX wire.

The layout mode of odd layers also enables the coupling superposition of the generated gradient fields to realize the gradient strength which is 1.5-2 times higher than that of a single-layer coil under the condition of the same current, so that the magnetic resonance imaging method can be used for some high-level sequence applications of magnetic resonance imaging, and the imaging effect is improved.

In order to enable the shielding coil layer to achieve the shielding effect, in this embodiment, the GZ coil includes a first GZ coil, a second GZ coil and a third GZ coil with three different layouts, the spiral pitch of the second GZ coil is at least twice of that of the first GZ coil or the third GZ coil, and the second GZ coil is disposed between the first GZ coil and the third GZ coil.

The above description is only a preferred embodiment of the present invention, and is not intended to limit the present invention in other forms, and any person skilled in the art may use the above-mentioned technical contents to change or modify the equivalent embodiment into equivalent changes and apply to other fields, but any simple modification, equivalent change and modification made to the above embodiments according to the technical matters of the present invention will still fall within the protection scope of the technical solution of the present invention.

Claims

1. The utility model provides a gradient coil system for special nuclear magnetic resonance equipment of mammary gland, includes main gradient coil layer, shielding coil layer and sets up the shim layer between main gradient coil layer and shielding coil layer, main gradient coil layer includes GX coil, GY coil or GZ coil, the shielding coil layer includes SX coil, SY coil or SZ coil, its characterized in that, main gradient coil layer, shielding coil layer and shim layer divide 13 layers setting altogether, main gradient coil layer or shielding coil layer include along the section of thick bamboo post axial direction set up four the same overall arrangement and GX coil, GY coil, GZ coil, SX coil, SY coil or SZ coil that link up each other, wherein, main gradient coil layer includes 7 at least coil layers, the shielding coil layer includes 5 layers of coil layers at most.

2. Gradient coil system for a magnetic resonance apparatus dedicated for the breast according to claim 1, characterized in that the main gradient coil comprises a three-layer GZ coil, a two-layer GY coil and a one-layer GX coil.

3. The gradient coil system for a nuclear magnetic resonance apparatus dedicated to the breast as set forth in claim 2, wherein the shield coil layer includes two layers of SZ coil, two layers of SY coil, and one layer of SX wire.

4. The gradient coil system for a mammary gland-dedicated nuclear magnetic resonance apparatus according to claim 3, wherein the GZ coil includes a first GZ coil, a second GZ coil and a third GZ coil of three different layouts, the spiral pitch of the second GZ coil is at least twice that of the first GZ coil or the third GZ coil, and the second GZ coil is arranged between the first GZ coil and the third GZ coil.