CN212872867U

CN212872867U - Nuclear magnetic resonance gradient coil for mammary gland examination

Info

Publication number: CN212872867U
Application number: CN202021826624.6U
Authority: CN
Inventors: 陈博; 白易民; 刘艳华; 陈豪; 曲绪凯; 李明闯; 姚立兵
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 nuclear magnetic resonance gradient coil for mammary gland inspection. Including main gradient coil layer, shielding coil layer and set up the shimming 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 the SX coil, SY coil or SZ coil, the GZ coil includes that a plurality of is oval setting and interconnect's wire circle, the wire circle is from inside to outside and the inclination of the connecting wire of the guide ring in its outside is more and more littleer, the inlet wire end and the leading-out terminal of GZ coil are close to the setting. The utility model discloses rationally distributed, simple structure, processing convenience are fit for using widely on a large scale.

Description

Nuclear magnetic resonance gradient coil for mammary gland examination

Technical Field

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

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 small nuclear magnetic resonance gradient coil of image slice thickness of formation of image for the mammary gland inspection.

In order to achieve the above purpose, the technical scheme adopted by the utility model is that the utility model provides a nuclear magnetic resonance gradient coil for mammary gland examination, 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 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 GZ coil includes that a plurality of is oval setting and interconnect's wire circle, the wire circle is from inside to outside more and less little rather than the inclination of the connecting wire of the direction circle in the outside, the inlet wire end and the leading-out terminal of GZ coil are close to the setting.

Preferably, the main gradient coil layer, the shielding coil layer and the shimming layer are arranged in 13 layers.

Preferably, the main gradient coil layer and the shield coil layer are each provided with 6 layers.

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

1. the utility model provides a nuclear magnetic resonance gradient coil for mammary gland inspection 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 nuclear magnetic resonance gradient coil for breast examination provided in example 1;

fig. 2 is a schematic structural diagram of a 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 and 2, this embodiment is directed to providing a magnetic resonance gradient coil for breast examination, in consideration of the characteristics of female breast, if the Z axis is the axis from the head to the step of the patient, the X axis represents the left and right of the patient, and the Y axis represents the front and back of the human body, and in consideration of the fact that the gradient coil mainly uses the gradient coil to generate a weak magnetic field varying in spatial position with respect to the main magnetic field 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 obtain the ideal surface current intensity, in this embodiment, the GZ coil includes a plurality of wire loops that are elliptically arranged and are connected to each other, and the wire loop is from inside to outside with the inclination angle of the connecting wire of the guide loop outside it is getting smaller and smaller, can guarantee required gradient and coil size and reach ideal surface current intensity at the minimum energy criterion of coil design.

In order to facilitate connection of four adjacent GZ coils, in the present embodiment, the wire inlet end and the wire outlet end of the GZ coil are disposed close to each other.

In order to increase the high linearity of the gradient coil, in the embodiment, the main gradient coil layer, the shielding coil layer and the shimming layer are arranged in 13 layers, wherein the shimming layer is a single layer, for this reason, the main gradient coil layer and the shielding coil layer are arranged in 12 layers, and each GX coil, the GY coil, the GZ coil, the SX coil, the SY coil or the SZ coil is arranged in two layers, so that a double-layer conductor structure is formed, and the turn density of the coil can be effectively improved by more than one time. By adopting a double-layer conductor structure and coupling superposition of a gradient field generated by the double-layer conductor structure, the gradient intensity which is 1.5-2 times higher than that of a single-layer coil can be realized under the condition of the same current, so that the aims of short scanning time, uniform imaging and small image slice thickness are fulfilled.

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 nuclear magnetic resonance gradient coil for mammary gland inspection, includes main gradient coil layer, shielding coil layer and sets up the shimming 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, a serial communication port, 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 that link up each other, SY coil or SZ coil, wherein, the GZ coil includes that a plurality of is oval setting and interconnect's wire circle, the wire circle is from inside to outside less and less with the inclination of the connecting wire of the guide circle in its outside, the line terminal and the leading-out terminal of GZ coil are close to the setting.

2. The nuclear magnetic resonance gradient coil for mammary gland examination according to claim 1, wherein the main gradient coil layer, the shield coil layer and the shim layer are arranged in 13 layers.

3. The nuclear magnetic resonance gradient coil for breast examination according to claim 2, wherein 6 layers are provided for each of the main gradient coil layer and the shield coil layer.