CN212872866U

CN212872866U - Gradient coil for nuclear magnetic resonance mammary gland examination

Info

Publication number: CN212872866U
Application number: CN202021824673.6U
Authority: CN
Inventors: 陈博; 白易民; 刘艳华; 陈豪; 祁长银; 祁建军; 史守臣
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 is used in nuclear magnetic resonance mammary gland inspection. 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, the GX coil includes that a plurality of is the lead coil that the annular set up, parallel arrangement between the lead coil, interval between the lead coil is crescent to both sides from the middle part, the GY coil includes that a plurality of is the Y axle coil that the annular set up, the Y axle coil is including crisscross last parallel portion and the lower parallel portion that sets up, go up the parallel portion and be provided with the broken line portion down between the parallel portion, the inclination of broken line portion is crescent to both sides from the coil middle part, the utility model discloses rationally distributed, simple structure, processing convenience are fit for using widely on a large scale.

Description

Gradient coil for nuclear magnetic resonance mammary gland examination

Technical Field

The utility model belongs to the technical field of nuclear magnetic resonance uses, especially, relate to a gradient coil is used in nuclear magnetic resonance 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 nuclear magnetic resonance gradient coil for mammary gland inspection that the image slice thickness is little of imaging.

In order to achieve the above object, the present invention provides a gradient coil for nuclear magnetic resonance breast examination, comprising 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, wherein 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 GX coil comprises a plurality of conductive coils arranged in a ring shape, the conductive coils are arranged in parallel, the distance between the conductive coils is gradually increased from the middle to two sides, the GY coil comprises a plurality of Y-axis coils arranged in a ring shape, the Y-axis coil comprises an upper parallel portion and a lower parallel portion which are arranged in a staggered manner, a folding line portion is arranged between the upper parallel portion and the lower parallel portion, the inclination angle of the folding line portion is gradually increased from the middle to two sides of the coil, the interval between the Y axle coil reduces to both sides from the middle part gradually, the GZ coil includes that a plurality of is oval setting and interconnect's Z axle coil, Z axle coil is more and more littleer rather than the inclination of the connecting wire of the direction circle in the outside from inside to outside.

Preferably, 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.

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 gradient coil is used in nuclear magnetic resonance 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 the coil placement of the gradient coil for the magnetic resonance breast examination provided in example 1;

fig. 2 is a schematic structural diagram of the GX coil provided in embodiment 1;

fig. 3 is a schematic structural view of the GY coil provided in embodiment 1;

fig. 4 is a schematic structural diagram of the 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.

Example 1, as shown in fig. 1 to 4, this example aims to provide a gradient coil for a magnetic resonance breast examination, in consideration of the characteristics of a female breast, if the Z axis is the axis from the head to the step of a 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 magnetic field which is weak relative to a main magnetic field and changes in spatial position, and is superimposed on the main magnetic field. Meanwhile, the gradient coil system for the special nuclear magnetic resonance equipment for the mammary gland provided by the embodiment 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, specifically, the main gradient coil layer is arranged on the inner side of 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 above structures are conventional structures, and therefore, in the embodiment, detailed description is omitted.

The optimal design of the gradient coil considering the satisfaction of the magnetic resonance imaging comprises the following steps: has high current efficiency (defined as the ratio of gradient value of magnetic field to applied current), that is, the required gradient is obtained with the smallest current possible; the shorter switching time requires the coil to have a very small inductance; the gradient field has high linearity required by imaging in a large range; lower power consumption requires coils with low resistance to minimize the interaction caused by eddy currents. The GX coil that this embodiment provided includes that a plurality of is the lead coil that the annular set up, and parallel arrangement between the lead coil, interval between the lead coil is crescent to both sides from the middle part, GY coil then includes that a plurality of is the Y axle coil that the annular set up, and Y axle coil is including crisscross last parallel portion and the lower parallel portion that sets up, goes up the parallel portion and is provided with the broken line portion down between the parallel portion, and the inclination of broken line portion is crescent to both sides from the coil middle part, interval between the Y axle coil reduces to both sides from the middle part gradually, and the GZ coil includes that a plurality of is oval setting and interconnect's Z axle coil, and the Z axle coil is more and more littleer rather than the inclination of the lead coil's in the outside from inside. The structural design can ensure the required gradient and coil size and achieve the ideal surface current intensity on the minimum energy criterion of coil design. Thereby achieving the purpose of optimizing design.

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 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. A gradient coil for nuclear magnetic resonance breast examination 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, wherein 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, and the gradient coil is characterized in that the GX coil comprises a plurality of lead coils which are annularly arranged, the lead coils are arranged in parallel, the distance between the lead coils is gradually increased from the middle part to two sides, the GY coil comprises a plurality of Y-axis coils which are annularly arranged, the Y-axis coils comprise upper parallel parts and lower parallel parts which are staggered, a folded line part is arranged between the upper parallel parts and the lower parallel parts, the inclination angle of the folded line part is gradually increased from the middle part of the coil to two sides, the distance between the Y-axis coils is gradually reduced from the middle part to two sides, the GZ coil includes that a plurality of is oval setting and interconnect's Z axle coil, Z axle coil from inside to outside and the inclination of the connecting wire of the direction circle in its outside are more and more littleer.

2. The gradient coil for nuclear magnetic resonance breast examination as claimed in claim 1, wherein the main gradient coil layer or the shield coil layer includes four GX coils, GY coils, GZ coils, SX coils, SY coils or SZ coils arranged in the same layout in the axial direction of the column and engaged with each other.

3. The gradient coil for nuclear magnetic resonance breast examination of claim 2, wherein the main gradient coil layer, the shield coil layer and the shim layer are arranged in 13 layers.

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