Patent Grant
10969449
The present application relates to the field of magnetic resonance imaging technology, and more particularly to a local shimming system for magnetic resonance imaging and the shimming method thereof.
In a magnetic resonance imaging system, the magnet itself is generally capable of providing a relatively homogeneous static magnetic field B0 in a certain space. However, due to the difference in magnetic susceptibility of the tissue, local magnetic field changes are generated at the interface, causing image artifacts. Especially in single-shot spin Echo-planar imaging (EPI), geometric distortion, signal loss and image blur will occur. In general, increasing the number of shim coils can reduce the non-homogeneity of the magnetic field, thereby improving the quality of the image.
In general, shim coils mainly include two types: spherical harmonic function (SH) shim coils and multi-coil (MC) shim coils. The SH shim coil is generally used for the magnetic field non-homogeneity correction of the main magnet, while the SH shim coil of the commercial MRI system has the second order at most. In animal and human brain experiments, the magnetic field non-homogeneity at the junction of tissue and air is often as high as 5 orders, so the order of the SH shim coil needs to be increased to 5 orders to achieve a better shimming effect. However, increasing the order of the SH shim coils brings about practical problems, such as reduction of efficient space, poor efficiency of the coil. Moreover, an additional cooling system for shim coils and the need to increase the number of power amplifiers should be considered. Compared with the SH shim coil, the MC shim coil generates a relatively complex high-order magnetic field with a plurality of simple coil loops, obtaining a better shimming capability. Moreover, the inductance of the MC shim coil is relatively small, and is far away from the main magnet, without causing a large eddy current.
At present, in magnetic resonance imaging, the more is the number of the shimming multi-coil units, the higher is the order of the non-uniform magnetic field that can be compensated. However, the problem is that more power amplifiers are needed; moreover, in the shimming process, it is necessary to perform sensitivity field map collection for each channel coil unit, which takes long time.
For example, CN 201510629760 discloses a shim coil device that compensates for non-homogeneity of a main magnetic field in the process of performing medical magnetic resonance imaging of human chest. CN201210202891, CN201410414924 and CN201510173911 have also developed shimming systems for magnetic resonance imaging of human head and abdomen. The papers “Magnetic field modeling with a set of individual localized coils”, Journal of Magnetic Resonance, 2010, 204(2): 281-289 by Juchem C et al., and “Multicoil shimming of the mouse brain[J]. Magnetic resonance in medicine”, 2011, 66(3): 893-900 by Juchem C et al., describe a shim coil applied to magnetic resonance imaging in mouse brains, in which the number of channels is from 24 to 48, and the number of power amplifiers is also from 24 to 48, the cost is much higher and the system is more complicated.
In view of this, a local shimming system and a process capable of achieving a better shimming effect using a shim coil with a small number of channels should be developed.
In view of the deficiencies of the above techniques, it is an object of the present application to provide a magnetic resonance imaging system applicable to animals and the method thereof, meanwhile the system and method are applicable for magnetic resonance temperature imaging. The present application specifically provides a local shimming system that can be used for magnetic resonance imaging and a shimming method to reduce high-order non-uniform magnetic field shift and improve the homogeneity of the B0 magnetic field. The local shim coils are asymmetrically distributed with a smaller number of channels to solve the problem of non-homogeneity of the B0 magnetic field during the process of magnetic resonance imaging. The local shimming method of the present application uses a fast two-dimensional gradient echo sequence to collect the field mapping B0, which is relatively short in time and relatively simple.
In order to achieve the above object, in view of the deficiencies in the prior art, the present application provides a shimming method for magnetic resonance imaging, wherein the method comprises the steps of: collecting B0 field map information using a two-dimensional gradient echo; calculating and evaluating the homogeneity of B0; optimizing the current of each channel of the shim coil; determining whether the minimum standard deviation (SD) value of Δf is obtained; outputting an optimal current combination value and setting optimum current values corresponding to each channel shimming coil on the current control software; and testing and evaluating the homogeneity of B0 to achieve the shimming goal.
In some embodiments, the collecting comprises collecting the field map information with the pulse sequence echo number of 5, the pulse sequence repetition time of 25 ms, and the flip angle of 10°. The calculating comprises unwrapping five echo phase maps, and performing straight-line fitting of the pixel points at the same position of the five phase maps on the five corresponding echo times TE by using the least square method, wherein the slope value is the main magnetic field offset value, and the calculation formula is:
wherein Δφ is the phase difference between the two echoes, γ is the gyromagnetic ratio of the imaging nucleus, and ΔTE is the time difference between the two echoes.
In some embodiments, the step of optimizing the current values of the shim coil comprises linearly combining the main magnetic field offset value Δf0 and the sensitivity field map Δf0i of each channel shim coil to achieve the minimum standard deviation value of Δf, and the main magnetic field offset value Δf after the shimming current is applied is expressed as:
wherein I=1, 2, . . . , n, and n is the number of channels of the shim coil, Δf0 is the main magnetic field offset value without applying the shimming current, Δf0i is the sensitivity field map of the shim coil, and ai is the linear superposition factor of the shim coil sensitivity field map.
The present application further provides a local shimming system for magnetic resonance imaging, which comprises a multi-channel local shim coil unit, which is configured to be installed on an inspection table of the magnetic resonance imaging system, wherein the local shimming coil unit comprises a local multi-channel shimming coil and a radio frequency receiving coil for receiving magnetic resonance signals, and the radio frequency receiving coils are placed inside the local shim coil with a separated distance; a computer control system, which is configured to install and set the software controlled by the DC power and calculate field maps in the calculation and optimization processes; and a DC power system, which is communicatively connected to the computer control system to control the amount of current of each channel.
In some embodiments, the multi-channel local shim coil unit further comprises a housing, and the housing is provided with a plurality of holes for the tuning and matching of the radio frequency receiving coil. In some embodiments, the channel number of the local shim coil unit is 5, and the local shim coils are asymmetrically distributed.
In some embodiments, the local shim coil element is a circular loop with a diameter of 4 cm. In some embodiments, the bottom of the housing is further provided with a hole as a reserved channel for the ultrasound ablation treatment. In some embodiments, the hole has a diameter of 6 cm.
The local shimming system and the shimming method of the present application provide at least the following advantages:
a better shimming effect is achieved using a shim coil with a smaller number of channels, the system is simpler and the cost is relatively low;
the proposed shimming method is relatively simple and is relatively short in time; and
the system is applicable to magnetic resonance temperature imaging, improving the accuracy of temperature measurement.
These and other advantages of the present application will be understood by those skilled in the art upon reading the entire specification and claims.
The drawings described in the present application are intended to provide a further understanding of the present application and are not intended to limit the present application. In the drawing:
In the figures: 10 represents a local shim coil unit, 11 represents a magnetic resonance imaging system, 101 represents an operation room, 102 represents an equipment room, 103 represents a magnetic resonance laboratory, 104 represents a computer control system, 105 represents a network cable, 106 represents a DC power system, 107 represents a waveguide plate and a waveguide tube, 108 represents a DC power cord, 109 represents a local multi-channel shim coil, 110 represents an RF receiving coil.
Specific embodiments of the present application will be described below with reference to the accompanying drawings. In the specific embodiments of the present application described hereinafter, some very specific technical features are described for a better understanding of the present application, but it will be apparent to those skilled in the art that not all of the technical features are essential technical features for implementing the present application. Some specific embodiments of the present application described below are merely some exemplary embodiments of the present application and are not to be construed as limiting the present application.
and the formula Δω0=γ·ΔB0 of the main magnetic field offset, the calculation formula of this step can be obtained as follows:
wherein Δφ is the phase difference between the two echoes, γ is the gyromagnetic ratio of the imaging nucleus, ΔTE is the time difference between the two echoes, and Δω0 is the nuclear magnetic resonance angle frequency.
In step 303, the current of each channel shim coil element is optimized. In some embodiments, the main magnetic field offset value Δf0 and the sensitivity field map Δf0i (i=1, 2, . . . , n, wherein n is the channel number of the shim coil) of each channel shim coil element are linearly combined, which is expressed as:
wherein Δf0 is the main magnetic field offset value without applying the shimming current, Δf0i is the sensitivity field map of the shim coil, ai is the linear superposition factor of the sensitivity field map, and Δf is the main magnetic field offset value after the shimming current is applied; through the above process, with the goal of obtaining the minimum standard deviation value of Δf to optimize the current value of each channel coil, when the average value of the optimized Δf is smaller than the average value of Δf0 prior to optimization, it is effective shimming.
In step 304, it is determined whether a constraint condition is met. If not, operations 303-304 are repeated until the constraint condition is met. In step 305, an optimal current combination value is output, and optimum current values corresponding to every channel shim coil are set on the current control software. Finally, in step 306, the homogeneity of the main magnetic field B0 is tested and evaluated. The average value and the standard deviation value of the main magnetic field offset value are used as the evaluation index. The smaller the value is, the more uniform the main magnetic field B0 is, and the shimming goal is achieved.
The present application is experimentally verified on a Siemens 3T magnetic resonance imaging system, and a local shimming system and a shimming method are applied in magnetic resonance temperature measurement imaging.
The present application provides a 5-channel local shim coil for magnetic resonance temperature imaging, which compensates for a change in local magnetic field due to the difference in magnetic proton susceptibility between water and fat tissue, thereby improving the precision and accuracy of temperature measurement. The magnetic resonance shimming system and the shimming method of the embodiment of the present application achieve a better shimming effect using a shim coil with a smaller number of channels, and the system is simpler and the cost is relatively low; and the shimming method provided is relatively simple and is relatively short in time; at the same time, the system is applicable in magnetic resonance temperature imaging, which improves the accuracy of temperature measurement.
Although the present application has been described in terms of the preferred embodiments, modifications, replacements, and various alternatives are possible that fall within the scope of the present application. It should also be noted that there are many alternative ways of implementing the method and system of the present application. Accordingly, it is intended that the appended claims be interpreted as including all such modifications, replacements, and various alternatives that fall within the gist and scope of the present application.
This application is a continuation of International Patent Application No. PCT/CN2017/118275 with a filing date of Dec. 25, 2017, the content thereof is incorporated herein by reference.
| Number | Name | Date | Kind |
|---|---|---|---|
| 20120249137 | Witschey | Oct 2012 | A1 |
| 20150355306 | Stemmer | Dec 2015 | A1 |
| 20160274202 | Stemmer | Sep 2016 | A1 |
| Number | Date | Country |
|---|---|---|
| 1934458 | Mar 2007 | CN |
| 102830377 | Dec 2012 | CN |
| 104422915 | Mar 2015 | CN |
| 104502873 | Apr 2015 | CN |
| 105044636 | Nov 2015 | CN |
| 105467337 | Apr 2016 | CN |
| Entry |
|---|
| Juchem, C. et al., Magnetic Field Modeling with a Set of Individual Localized Coils, Journal of Magnetic Resonance, 2010, pp. 281-289, vol. 204, No. 2. |
| Juchem, C. et al., Multicoil Shimming of the Mouse Brain, Magnetic Resonance in Medicine, 2011, pp. 893-900, vol. 66, No. 3. |
| Number | Date | Country | |
|---|---|---|---|
| 20190195972 A1 | Jun 2019 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | PCT/CN2017/118275 | Dec 2017 | US |
| Child | 16261610 | US |
