CN202870284U - Active shimming system used for magnetic resonance imaging permanent magnet - Google Patents
Active shimming system used for magnetic resonance imaging permanent magnet Download PDFInfo
- Publication number
- CN202870284U CN202870284U CN 201220365508 CN201220365508U CN202870284U CN 202870284 U CN202870284 U CN 202870284U CN 201220365508 CN201220365508 CN 201220365508 CN 201220365508 U CN201220365508 U CN 201220365508U CN 202870284 U CN202870284 U CN 202870284U
- Authority
- CN
- China
- Prior art keywords
- coil
- group
- shim
- shim coil
- resonance imaging
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Images
Landscapes
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
The utility model relates to an active shimming system used for a magnetic resonance imaging permanent magnet. The active shimming system is characterized by comprising: a pair of active shimming coils which are respectively arranged on a surface of an upper magnetic pole and on a surface of a lower magnetic pole of the magnetic resonance imaging permanent magnet; a shimming coil current controller which is connected with the active shimming coils and is used for providing DC steady current sources for the active shimming coils; and a computer control system which is connected with the shimming coil current controller, is used for radio frequency excitation for a human body or a water model in an imaging static magnetic field through a radio frequency coil in a magnetic resonance imaging system, and is also used for calculating a current value that needs to be applied to the active shimming coils based on FID (Free Induction Decay) signal strength obtained by a receiving coil in the magnetic resonance imaging system. Compared with the prior art, the active shimming system is capable of correcting an imaging magnetic field of the magnetic resonance imaging permanent magnet, allows non-uniform components of an imaging main magnetic field to be eliminated by a generated additional correction magnetic field, and enables MRI quality to be improved.
Description
Technical field
The utility model relates to a kind of active shimming system for the magnetic resonance imaging permanent magnet.
Background technology
Magnetic resonance imaging (Magnetic Resonance Imaging, MRI) can provide high spatial resolution, unlimited penetration depth and very good soft tissue contrast, and dissection location, splendid space, so magnetic resonance imaging has the incomparable advantage of other Imaging Technology.In the MRI system, require image magnet that the static magnetic field of high evenness can be provided, this is the basic guarantee that obtains high-quality MRI image.For the permanent-magnet type magnet, because the problems such as magnetic material, machining precision, edge effect, so that the initial magnetic field that produces is difficult to reach the uniformity coefficient of imaging requirements, so need to compensate correction to magnetic field.Mainly adopt the passive shimming method of pasting little magnetic sheet to proofread and correct for the permanent-magnet type magnet at present, uniformity of magnetic field can reach imaging requirements behind the shimming, but because permanent magnet is very responsive to temperature variation, the magnetic field of having adjusted homogeneity when temperature changes also can change thereupon, the phenomenons such as time drift in magnetic field also can occur in addition.
The utility model content
Technical problem to be solved in the utility model is to provide a kind of active shimming system for the magnetic resonance imaging permanent magnet for above-mentioned prior art, this active shimming system can carry out effectively proofreading and correct in real time to the magnetic field that the magnetic resonance imaging permanent magnet produces, thus the imaging magnetic field that makes application have the magnetic resonance imaging permanent magnet of this active shimming system to have high evenness and high stability.
The utility model solves the problems of the technologies described above the technical scheme that adopts: should be used for the active shimming system of magnetic resonance imaging permanent magnet, and it is characterized in that comprising:
The active shimming coil, mounted in pairs is magnetic pole surfaces about the magnetic resonance imaging permanent magnet;
The shim coil current controller links to each other with described active shimming coil, for described active shimming coil provides direct current permanent steady current source;
Computer control system, link to each other with described shim coil current controller, by radio-frequency coil in the magnetic resonance imaging system human body in the imaging static magnetic field or water mould are carried out radio-frequency (RF) excited, FID (FreeInductionDecay) signal intensity that obtains according to receiving coil in the magnetic resonance imaging system calculates the current value that need to be applied on the described active shimming coil.
Described shim coil includes:
Be installed in a Z13 shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described Z13 shim coil comprises the concentrically ringed A group coil of coiled and the concentrically ringed B group of coiled coil, A group coil is concentric with B group coil, and A group coil is arranged on outside the B group coil;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd Z13 shim coil, the 2nd Z13 shim coil is identical with a Z13 shim coil structure, in the 2nd Z13 shim coil electric current of A group coil identical with the size of current of A group coil in the Z13 shim coil, flow on the contrary, the electric current of B group coil, the flow direction identical with the size of current of B group coil in the Z13 shim coil is on the contrary in the 2nd Z13 shim coil.
Described active shimming coil also includes:
Be installed in a Z24 shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described Z24 shim coil comprises the concentrically ringed C group coil of coiled and the concentrically ringed D group of coiled coil, C group coil is concentric with D group coil, and C group coil is arranged on outside the D group coil;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd Z24 shim coil, the 2nd Z24 shim coil is identical with a Z24 shim coil structure, in the 2nd Z24 shim coil electric current of C group coil identical with the size of current of C group coil in the Z24 shim coil, flow to identical, in the 2nd Z24 shim coil in the electric current of D group coil and the Z24 shim coil D organize the size of current of coil identical, flow to identical.
Described active shimming coil also includes:
Be installed in an X shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described X shim coil comprises E group coil and the arc F group coil of coiled that coiled is arc, E organizes coil and F group coil is symmetrical on the Y-axis both sides, and E group coil is identical with the size of current that F group coil accesses, the flow direction is opposite;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd X shim coil, the 2nd X shim coil is identical with an X shim coil structure, in the 2nd X shim coil electric current of E group coil identical with the size of current of E group coil in the X shim coil, flow to identical, in the 2nd X shim coil in the electric current of F group coil and the X shim coil F organize the size of current of coil identical, flow to identical.
Described active shimming coil also includes:
Be installed in a Y shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described Y shim coil comprises G group coil and the arc H group coil of coiled that coiled is arc, G organizes coil and H group coil is symmetrical on the X-axis both sides, and G group coil is identical with the size of current that H group coil accesses, the flow direction is opposite;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd Y shim coil, the 2nd Y shim coil is identical with a Y shim coil structure, in the 2nd Y shim coil electric current of G group coil identical with the size of current of G group coil in the Y shim coil, flow to identical, in the 2nd Y shim coil in the electric current of H group coil and the Y shim coil H organize the size of current of coil identical, flow to identical.
Described shim coil also includes:
Be installed in an x of magnetic pole surfaces on the magnetic resonance imaging permanent magnet
2-y
2Shim coil, a described x
2-y
2Shim coil comprises K group coil and the fan-shaped L group coil of coiled that coiled fan-shaped I group coil, coiled fan-shaped J group coil, coiled are fan-shaped, I group coil and J group coil are symmetrical on the X-axis both sides, K group coil and L group coil are symmetrical on the Y-axis both sides, and I group coil is identical with the size of current that J group coil accesses, it is identical to flow to, the size of current of K group coil and the access of L group coil is identical, it is identical to flow to, but the size of current of I group coil and the access of K group coil is identical, the flow direction on the contrary;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd x
2-y
2Shim coil, the 2nd x
2-y
2Shim coil and an x
2-y
2The shim coil structure is identical, the 2nd x
2-y
2In the shim coil electric current of I group line, J group coil, K group coil and L group coil respectively with an x
2-y
2In the shim coil size of current of I group line, J group coil, K group coil and L group coil identical, flow to identical.
Described shim coil also includes:
Be installed in an XY shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described x
2-y
2Shim coil is rotated counterclockwise 45 degree can obtain an XY coil;
Be installed in the 2nd XY shim coil on magnetic resonance imaging permanent magnet lower magnetic pole surface, described the 2nd x
2-y
2Shim coil is rotated counterclockwise 45 degree can obtain the 2nd XY coil.
Described shim coil also includes:
Be installed in an XZ shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described XZ shim coil comprises M group coil and the arc N group coil of coiled that coiled is arc, M organizes coil and N group coil is symmetrical on the Y-axis both sides, and M group coil is identical with the size of current that N group coil accesses, the flow direction is opposite;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd XZ shim coil, the 2nd XZ shim coil is identical with an XZ shim coil structure, in the 2nd XZ shim coil electric current of M group coil identical with the size of current of M group coil in the XZ shim coil, flow on the contrary, the electric current of N group coil, the flow direction identical with the size of current of N group coil in the XZ shim coil is on the contrary in the 2nd XZ shim coil.
Described shim coil also includes:
Be installed in a YZ shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described XZ shim coil is rotated counterclockwise 90 degree can obtain a YZ coil;
Be installed in the 2nd YZ shim coil on magnetic resonance imaging permanent magnet lower magnetic pole surface, described the 2nd XZ shim coil is rotated counterclockwise 90 degree can obtain the 2nd YZ coil.
Compared with prior art, the utility model has the advantage of: by in the upper and lower magnetic pole surfaces of image magnet active shim coil being set, the magnetic-field component that produces different directions by the electric current of control in the shim coil is added on the main field, realization is to the correction of imaging magnetic field, make to produce the non-homogeneous component that the imaging main field is eliminated in additive correction magnetic field, improve the MRI image quality.
Description of drawings
Fig. 1 is the structural representation that is used for the permanent-magnet of magnetic resonance imaging system among the utility model embodiment;
Fig. 2 is the structural representation of a Z13 shim coil among the utility model embodiment;
Fig. 3 is the structural representation of a Z24 shim coil among the utility model embodiment;
Fig. 4 is the structural representation of an X shim coil among the utility model embodiment;
Fig. 5 is the structural representation of a Y shim coil among the utility model embodiment;
Fig. 6 is an x among the utility model embodiment
2-y
2The structural representation of shim coil;
Fig. 7 is the structural representation of an XY shim coil among the utility model embodiment;
Fig. 8 is the structural representation of an XZ shim coil among the utility model embodiment;
Fig. 9 is the structural representation of a YZ shim coil among the utility model embodiment.
Embodiment
Embodiment is described in further detail the utility model below in conjunction with accompanying drawing.
The permanent-magnet that is used for magnetic resonance imaging system as shown in Figure 1, comprise hollow yoke 1, hollow yoke 1 inside surface one side is provided with the upper magnetic pole 2 of being made by the permanent magnetism material, hollow yoke 1 inside surface opposite side is symmetrically arranged with the lower magnetic pole 3 of being made by the permanent magnetism material, upper magnetic pole 2 and lower magnetic pole 3 corresponding inner surfaces are provided with active shimming coil 4, in the present embodiment, described active shimming coil 4 comprises eight groups, is respectively a Z13 shim coil, the 2nd Z13 shim coil, the one Z24 shim coil, the 2nd Z24 shim coil, the one X shim coil, the 2nd X shim coil, the one Y shim coil, the 2nd Y shim coil, the one x
2-y
2Shim coil, the 2nd x
2-y
2Shim coil, an XY shim coil, the 2nd XY shim coil, an XZ shim coil, the 2nd XZ shim coil, a YZ shim coil, the 2nd YZ shim coil, these eight groups of shim coil mounted in pairs are on the corresponding inner surface of upper magnetic pole, lower magnetic pole, the shim current values of above-mentioned eight groups of shim coils of flowing through is calculated in real time by computer control system, then be transferred to the shim coil current controller, provide independently shim current by the shim coil current controller to each group coil, above-mentioned eight groups of shim coils can produce z, z
2, z
3, z
4, x, y, x
2-y
2, xy, yz, ten direction magnetic-field components of xz magnetic field for correcting.
In the present embodiment:
The one Z13 shim coil is installed in described upper magnetic pole 2 inner surfaces, a described Z13 shim coil comprises the concentrically ringed A group coil of coiled and the concentrically ringed B group of coiled coil, A group coil is concentric with B group coil, and A group coil is arranged on outside the B group coil, referring to shown in Figure 2;
The 2nd Z13 shim coil is installed in described lower magnetic pole inner surface, the 2nd Z13 shim coil is identical with a Z13 shim coil structure, in the 2nd Z13 shim coil electric current of A group coil identical with the size of current of A group coil in the Z13 shim coil, flow on the contrary, the electric current of B group coil, the flow direction identical with the size of current of B group coil in the Z13 shim coil is on the contrary in the 2nd Z13 shim coil;
The one Z24 shim coil is installed in described upper magnetic pole inner surface, a described Z24 shim coil comprises the concentrically ringed C group coil of coiled and the concentrically ringed D group of coiled coil, C group coil is concentric with D group coil, and C group coil is arranged on outside the D group coil, referring to shown in Figure 3;
The 2nd Z24 shim coil is installed in described lower magnetic pole inner surface, the 2nd Z24 shim coil is identical with a Z24 shim coil structure, in the 2nd Z24 shim coil electric current of C group coil identical with the size of current of C group coil in the Z24 shim coil, flow to identical, in the 2nd Z24 shim coil in the electric current of D group coil and the Z24 shim coil D organize the size of current of coil identical, flow to identical;
The one X shim coil is installed in described upper magnetic pole inner surface, a described X shim coil comprises E group coil and the arc F group coil of coiled that coiled is arc, E group coil and F group coil are symmetrical on the Y-axis both sides, and E group coil is identical with the size of current that F group coil accesses, the flow direction is opposite, referring to shown in Figure 4;
The 2nd X shim coil is installed in described lower magnetic pole inner surface, the 2nd X shim coil is identical with an X shim coil structure, in the 2nd X shim coil electric current of E group coil identical with the size of current of E group coil in the X shim coil, flow to identical, in the 2nd X shim coil in the electric current of F group coil and the X shim coil F organize the size of current of coil identical, flow to identical;
The one Y shim coil is installed in described upper magnetic pole inner surface, a described Y shim coil comprises G group coil and the arc H group coil of coiled that coiled is arc, G group coil and H group coil are symmetrical on the X-axis both sides, and G group coil is identical with the size of current that H group coil accesses, the flow direction is opposite, referring to shown in Figure 5;
The 2nd Y shim coil is installed in described lower magnetic pole inner surface, the 2nd Y shim coil is identical with a Y shim coil structure, in the 2nd Y shim coil electric current of G group coil identical with the size of current of G group coil in the Y shim coil, flow to identical, in the 2nd Y shim coil in the electric current of H group coil and the Y shim coil H organize the size of current of coil identical, flow to identical.
The one x
2-y
2Shim coil is installed in described upper magnetic pole inner surface, a described x
2-y
2Shim coil comprises K group coil and the fan-shaped L group coil of coiled that coiled fan-shaped I group coil, coiled fan-shaped J group coil, coiled are fan-shaped, I group coil and J group coil are symmetrical on the X-axis both sides, K group coil and L group coil are symmetrical on the Y-axis both sides, and I group coil leads to, flows to identical with the size of current of J group coil access, K group coil is identical with the current direction that L organizes the coil access, but I group coil is identical with the size of current that K organizes the coil access, the flow direction is opposite;
The 2nd x
2-y
2Shim coil is installed in described lower magnetic pole inner surface, the 2nd x
2-y
2Shim coil and an x
2-y
2The shim coil structure is identical, the 2nd x
2-y
2In the shim coil electric current of I group line, J group coil, K group coil and L group coil respectively with an x
2-y
2In the shim coil size of current of I group line, J group coil, K group coil and L group coil identical, flow to identical.
The one XY shim coil is installed in described upper magnetic pole inner surface, a described x
2-y
2Shim coil is rotated counterclockwise 45 degree can obtain an XY coil, referring to shown in Figure 7;
The 2nd XY shim coil is installed in described lower magnetic pole inner surface, described the 2nd x
2-y
2Shim coil is rotated counterclockwise 45 degree can obtain the 2nd XY coil;
The one XZ shim coil is installed in described upper magnetic pole inner surface, a described XZ shim coil comprises M group coil and the arc N group coil of coiled that coiled is arc, M group coil and N group coil are symmetrical on the Y-axis both sides, and M group coil is identical with the size of current that N group coil accesses, the flow direction is opposite, referring to shown in Figure 8;
The 2nd XZ shim coil is installed in described lower magnetic pole inner surface, the 2nd XZ shim coil is identical with an XZ shim coil structure, in the 2nd XZ shim coil electric current of M group coil identical with the size of current of M group coil in the XZ shim coil, flow on the contrary, the electric current of N group coil, the flow direction identical with the size of current of N group coil in the XZ shim coil is on the contrary in the 2nd XZ shim coil;
The one YZ shim coil is installed in described upper magnetic pole inner surface, and a described XZ shim coil is rotated counterclockwise 90 degree can obtain a YZ coil, referring to shown in Figure 9;
The 2nd YZ shim coil is installed in described lower magnetic pole inner surface, and described the 2nd XZ shim coil is rotated counterclockwise 90 degree can obtain the 2nd YZ coil.
In above-mentioned eight groups of coils, the meaning that current direction is identical refers to all according to clockwise direction or all according to counterclockwise; And the opposite meaning of current direction refer to one according to clockwise direction another according to counterclockwise.
The shim coil current controller adopts Single-chip Controlling No. 10 constant-current supply modules, link to each other with described eight groups of shim coils respectively, for eight groups of shim coils provide separately-10A ~+the 10A permanent surely current source of direct current independently.
Computer control system, link to each other with described shim coil current controller, by the radio-frequency coil in the MRI system human body in the imaging static magnetic field or water mould are carried out radio-frequency (RF) excited, the FID signal intensity that obtains according to receiving coil in the MRI system calculates needs and is applied to current value on the described shim coil, described computer control system is when calculating the current value that need to be applied on the described shim coil, and its calculation procedure is as follows:
(1), measures initial FID intensity: with the electric current zero setting of all shim coils, the water apperance product of imaging space are applied radiofrequency signal encourage, by the FID signal intensity of receiving coil measuring system, with this initial reference value as the shimming effect;
(2), determine the shim current direction: establishing described shim coil has the n group, to i group shim coil, determines that by applying measuring current I0 the shim current of this group coil is adjusted direction;
(3), electric current step-length control: to i group shim coil, take measuring current as starting point, adjusting direction along it progressively increases shim current;
(4) if the FID signal intensity no longer increases or shim current exceeds span, then should the group shim current calculate end, forward (2) to and go on foot the shim current of calculating next group shim coil;
(5), after the shim current of all shim coils is calculated, iterative computation finishes;
(6), repeat (2)～(5), until system's FID intensity no longer increases, the shim current of respectively organizing shim coil this moment is final needs and is applied to current value on every group of shim coil.
Claims (9)
1. active shimming system that is used for the magnetic resonance imaging permanent magnet is characterized in that comprising:
The active shimming coil, mounted in pairs is magnetic pole surfaces about the magnetic resonance imaging permanent magnet;
The shim coil current controller links to each other with described active shimming coil, for described active shimming coil provides direct current permanent steady current source;
Computer control system, link to each other with described shim coil current controller, by radio-frequency coil in the magnetic resonance imaging system human body in the imaging static magnetic field or water mould are carried out radio-frequency (RF) excited, the FID signal intensity that obtains according to receiving coil in the magnetic resonance imaging system calculates needs and is applied to current value on the described active shimming coil.
2. the active shimming system for the magnetic resonance imaging permanent magnet according to claim 1, it is characterized in that: described shim coil includes:
Be installed in a Z13 shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described Z13 shim coil comprises the concentrically ringed A group coil of coiled and the concentrically ringed B group of coiled coil, A group coil is concentric with B group coil, and A group coil is arranged on outside the B group coil;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd Z13 shim coil, the 2nd Z13 shim coil is identical with a Z13 shim coil structure, in the 2nd Z13 shim coil electric current of A group coil identical with the size of current of A group coil in the Z13 shim coil, flow on the contrary, the electric current of B group coil, the flow direction identical with the size of current of B group coil in the Z13 shim coil is on the contrary in the 2nd Z13 shim coil.
3. the active shimming system for the magnetic resonance imaging permanent magnet according to claim 1, it is characterized in that: described shim coil includes:
Be installed in a Z24 shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described Z24 shim coil comprises the concentrically ringed C group coil of coiled and the concentrically ringed D group of coiled coil, C group coil is concentric with D group coil, and C group coil is arranged on outside the D group coil;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd Z24 shim coil, the 2nd Z24 shim coil is identical with a Z24 shim coil structure, in the 2nd Z24 shim coil electric current of C group coil identical with the size of current of C group coil in the Z24 shim coil, flow to identical, in the 2nd Z24 shim coil in the electric current of D group coil and the Z24 shim coil D organize the size of current of coil identical, flow to identical.
4. the active shimming system for the magnetic resonance imaging permanent magnet according to claim 1, it is characterized in that: described shim coil includes:
Be installed in an X shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described X shim coil comprises E group coil and the arc F group coil of coiled that coiled is arc, E organizes coil and F group coil is symmetrical on the Y-axis both sides, and E group coil is identical with the size of current that F group coil accesses, the flow direction is opposite;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd X shim coil, the 2nd X shim coil is identical with an X shim coil structure, in the 2nd X shim coil electric current of E group coil identical with the size of current of E group coil in the X shim coil, flow to identical, in the 2nd X shim coil in the electric current of F group coil and the X shim coil F organize the size of current of coil identical, flow to identical.
5. the active shimming system for the magnetic resonance imaging permanent magnet according to claim 1, it is characterized in that: described shim coil includes:
Be installed in a Y shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described Y shim coil comprises G group coil and the arc H group coil of coiled that coiled is arc, G organizes coil and H group coil is symmetrical on the X-axis both sides, and G group coil is identical with the size of current that H group coil accesses, the flow direction is opposite;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd Y shim coil, the 2nd Y shim coil is identical with a Y shim coil structure, in the 2nd Y shim coil electric current of G group coil identical with the size of current of G group coil in the Y shim coil, flow to identical, in the 2nd Y shim coil in the electric current of H group coil and the Y shim coil H organize the size of current of coil identical, flow to identical.
6. the active shimming system for the magnetic resonance imaging permanent magnet according to claim 1, it is characterized in that: described shim coil includes:
Be installed in an x of magnetic pole surfaces on the magnetic resonance imaging permanent magnet
2-y
2Shim coil, a described x
2-y
2Shim coil comprises K group coil and the fan-shaped L group coil of coiled that coiled fan-shaped I group coil, coiled fan-shaped J group coil, coiled are fan-shaped, I group coil and J group coil are symmetrical on the X-axis both sides, K group coil and L group coil are symmetrical on the Y-axis both sides, and I group coil is identical with the size of current that J group coil accesses, it is identical to flow to, the size of current of K group coil and the access of L group coil is identical, it is identical to flow to, but the size of current of I group coil and the access of K group coil is identical, the flow direction on the contrary;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd x
2-y
2Shim coil, the 2nd x
2-y
2Shim coil and an x
2-y
2The shim coil structure is identical, the 2nd x
2-y
2In the shim coil electric current of I group line, J group coil, K group coil and L group coil respectively with an x
2-y
2In the shim coil size of current of I group line, J group coil, K group coil and L group coil identical, flow to identical.
7. the active shimming system for the magnetic resonance imaging permanent magnet according to claim 6, it is characterized in that: described shim coil includes:
Be installed in an XY shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described x
2-y
2Shim coil is rotated counterclockwise 45 degree can obtain an XY coil;
Be installed in the 2nd XY shim coil on magnetic resonance imaging permanent magnet lower magnetic pole surface, described the 2nd x
2-y
2Shim coil is rotated counterclockwise 45 degree can obtain the 2nd XY coil.
8. the active shimming system for the magnetic resonance imaging permanent magnet according to claim 1, it is characterized in that: described shim coil includes:
Be installed in an XZ shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described XZ shim coil comprises M group coil and the arc N group coil of coiled that coiled is arc, M organizes coil and N group coil is symmetrical on the Y-axis both sides, and M group coil is identical with the size of current that N group coil accesses, the flow direction is opposite;
Be installed in magnetic resonance imaging permanent magnet lower magnetic pole surface the 2nd XZ shim coil, the 2nd XZ shim coil is identical with an XZ shim coil structure, in the 2nd XZ shim coil electric current of M group coil identical with the size of current of M group coil in the XZ shim coil, flow on the contrary, the electric current of N group coil, the flow direction identical with the size of current of N group coil in the XZ shim coil is on the contrary in the 2nd XZ shim coil.
9. the active shimming system for the magnetic resonance imaging permanent magnet according to claim 8, it is characterized in that: described shim coil includes:
Be installed in a YZ shim coil of magnetic pole surfaces on the magnetic resonance imaging permanent magnet, a described XZ shim coil is rotated counterclockwise 90 degree can obtain a YZ coil;
Be installed in the 2nd YZ shim coil on magnetic resonance imaging permanent magnet lower magnetic pole surface, described the 2nd XZ shim coil is rotated counterclockwise 90 degree can obtain the 2nd YZ coil.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 201220365508 CN202870284U (en) | 2012-07-26 | 2012-07-26 | Active shimming system used for magnetic resonance imaging permanent magnet |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 201220365508 CN202870284U (en) | 2012-07-26 | 2012-07-26 | Active shimming system used for magnetic resonance imaging permanent magnet |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN202870284U true CN202870284U (en) | 2013-04-10 |
Family
ID=48036993
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN 201220365508 Expired - Lifetime CN202870284U (en) | 2012-07-26 | 2012-07-26 | Active shimming system used for magnetic resonance imaging permanent magnet |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN202870284U (en) |
Cited By (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104635187A (en) * | 2015-02-28 | 2015-05-20 | 深圳先进技术研究院 | Adaptive active automatic shimming method and system of magnetic resonance system |
| CN104730475A (en) * | 2013-12-23 | 2015-06-24 | Ge医疗系统环球技术有限公司 | Magnetic field adjusting system |
| CN105022011A (en) * | 2015-07-02 | 2015-11-04 | 江苏美时医疗技术有限公司 | Magnetic-resonance permanent magnet magnetic field compensation device and using method thereof |
| CN105403846A (en) * | 2015-12-02 | 2016-03-16 | 江苏美时医疗技术有限公司 | Shimming assembly of permanent magnet |
| CN108896941A (en) * | 2018-05-09 | 2018-11-27 | 安徽锐捷信息科技有限公司 | A kind of gradient shimming method and device |
| CN109073681A (en) * | 2016-03-22 | 2018-12-21 | 海珀菲纳研究股份有限公司 | Method and apparatus for magnetic field shimming |
| EP3403577A4 (en) * | 2016-01-21 | 2019-01-16 | Samsung Electronics Co., Ltd. | Magnetic resonance imaging apparatus and method for shimming of magnetic resonance imaging apparatus |
| CN109407022A (en) * | 2018-10-25 | 2019-03-01 | 上海联影医疗科技有限公司 | Control method, device and the storage medium of magnetic field drift |
| CN109613111A (en) * | 2018-11-12 | 2019-04-12 | 南京航空航天大学 | A kind of gradient spiral vortex detection coil and its detection method |
| CN110927642A (en) * | 2019-12-05 | 2020-03-27 | 湖南迈太科医疗科技有限公司 | Shimming control method, device and system for magnetic resonance imaging |
| CN111103561A (en) * | 2019-12-10 | 2020-05-05 | 厦门大学 | Design and manufacturing method of permanent magnet shimming coil for compensating magnetic susceptibility |
| CN111133326A (en) * | 2017-09-28 | 2020-05-08 | 西达-赛奈医疗中心 | Magnetic resonance coil for simultaneous imaging and B0 shimming |
| CN111781549A (en) * | 2020-06-22 | 2020-10-16 | 上海交通大学 | Vertical type magnetic resonance imaging device capable of moving up and down |
-
2012
- 2012-07-26 CN CN 201220365508 patent/CN202870284U/en not_active Expired - Lifetime
Cited By (24)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104730475A (en) * | 2013-12-23 | 2015-06-24 | Ge医疗系统环球技术有限公司 | Magnetic field adjusting system |
| CN104730475B (en) * | 2013-12-23 | 2020-07-07 | Ge医疗系统环球技术有限公司 | Magnetic field adjusting system and method and magnetic resonance imaging system |
| CN104635187A (en) * | 2015-02-28 | 2015-05-20 | 深圳先进技术研究院 | Adaptive active automatic shimming method and system of magnetic resonance system |
| CN104635187B (en) * | 2015-02-28 | 2017-07-07 | 深圳先进技术研究院 | The adaptive active automatic shimming method and system of magnetic resonance system |
| CN105022011A (en) * | 2015-07-02 | 2015-11-04 | 江苏美时医疗技术有限公司 | Magnetic-resonance permanent magnet magnetic field compensation device and using method thereof |
| CN105403846A (en) * | 2015-12-02 | 2016-03-16 | 江苏美时医疗技术有限公司 | Shimming assembly of permanent magnet |
| EP3403577A4 (en) * | 2016-01-21 | 2019-01-16 | Samsung Electronics Co., Ltd. | Magnetic resonance imaging apparatus and method for shimming of magnetic resonance imaging apparatus |
| US11740302B2 (en) | 2016-03-22 | 2023-08-29 | Hyperfine Operations, Inc. | Methods and apparatus for magnetic field shimming |
| CN109073681A (en) * | 2016-03-22 | 2018-12-21 | 海珀菲纳研究股份有限公司 | Method and apparatus for magnetic field shimming |
| US11294006B2 (en) | 2016-03-22 | 2022-04-05 | Hyperfine Operations, Inc. | Methods and apparatus for magnetic field shimming |
| US10794974B2 (en) | 2016-03-22 | 2020-10-06 | Hyperfine Research, Inc. | Methods and apparatus for magnetic field shimming |
| US10788550B2 (en) | 2016-03-22 | 2020-09-29 | Hyperfine Research, Inc. | Methods and apparatus for magnetic field shimming |
| CN111133326A (en) * | 2017-09-28 | 2020-05-08 | 西达-赛奈医疗中心 | Magnetic resonance coil for simultaneous imaging and B0 shimming |
| CN108896941B (en) * | 2018-05-09 | 2020-11-06 | 安徽福晴医疗科技有限公司 | Gradient shimming method and device |
| CN108896941A (en) * | 2018-05-09 | 2018-11-27 | 安徽锐捷信息科技有限公司 | A kind of gradient shimming method and device |
| CN109407022A (en) * | 2018-10-25 | 2019-03-01 | 上海联影医疗科技有限公司 | Control method, device and the storage medium of magnetic field drift |
| CN109613111A (en) * | 2018-11-12 | 2019-04-12 | 南京航空航天大学 | A kind of gradient spiral vortex detection coil and its detection method |
| CN109613111B (en) * | 2018-11-12 | 2022-07-08 | 南京航空航天大学 | Gradient spiral eddy current detection coil and detection method thereof |
| CN110927642A (en) * | 2019-12-05 | 2020-03-27 | 湖南迈太科医疗科技有限公司 | Shimming control method, device and system for magnetic resonance imaging |
| CN110927642B (en) * | 2019-12-05 | 2021-09-10 | 湖南迈太科医疗科技有限公司 | Shimming control method, device and system for magnetic resonance imaging |
| CN111103561A (en) * | 2019-12-10 | 2020-05-05 | 厦门大学 | Design and manufacturing method of permanent magnet shimming coil for compensating magnetic susceptibility |
| CN111103561B (en) * | 2019-12-10 | 2021-01-05 | 厦门大学 | Design and manufacturing method of permanent magnet shimming coil for compensating magnetic susceptibility |
| CN111781549A (en) * | 2020-06-22 | 2020-10-16 | 上海交通大学 | Vertical type magnetic resonance imaging device capable of moving up and down |
| CN111781549B (en) * | 2020-06-22 | 2022-04-26 | 上海交通大学 | Vertical type magnetic resonance imaging device capable of moving up and down |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN202870284U (en) | Active shimming system used for magnetic resonance imaging permanent magnet | |
| CA2928850C (en) | System and method for electromagnet coil construction and operation | |
| CN106443535B (en) | The system of imaging magnetic field measurement and correction in magnetic resonance device | |
| CN101435857A (en) | Cylinder surface even field coil of magnetic nuclear resonance spectrometer and design method thereof | |
| CN108387857B (en) | Local shimming system and shimming method for magnetic resonance imaging | |
| Restrepo et al. | A comparative study of the magnetic field homogeneity for circular, square and equilateral triangular helmholtz coils | |
| US7541811B2 (en) | Apparatus for electron spin resonance CT | |
| Zhang et al. | An optimized target-field method for MRI transverse biplanar gradient coil design | |
| CN110162926A (en) | A method of for low-field nuclear magnetic resonance plane type gradient coil design | |
| Liu et al. | Target-field method for MRI biplanar gradient coil design | |
| CN105676155A (en) | Magnetic field inhomogeneity value acquisition method and distortion correction method for magnetic resonance imaging system | |
| CN106772683A (en) | A kind of method of component quadrature coil intercept in ordinary surveying vector magnetic meter | |
| JP4040930B2 (en) | Magnetic field homogenization method and apparatus | |
| CN108182329A (en) | A kind of radio frequency coil designs method and loop construction using particle cluster algorithm | |
| CN109765509A (en) | The method for shimming of superconducting magnetic resonance imaging equipment | |
| CN102651043B (en) | Hybrid design method for radio frequency coil | |
| CN108882498A (en) | A kind of high-intensity magnetic field synchrocyclotron and its magnet field shim method | |
| JP2014236868A (en) | Magnetic resonance imaging apparatus and method for adjusting uniformity of high-frequency magnetic field | |
| CN105223527B (en) | A method of shimming being carried out to Hall Bach's magnet using first coil array | |
| WO2008126895A1 (en) | Superconducting magnet apparatus, magnetic resonance imaging device, and magnetic field inhomogeneity compensation method | |
| US9778334B2 (en) | Magnetic shimming and magnet arrangements | |
| McDowell et al. | Thin high-order shims for small dipole NMR magnets | |
| US20120153952A1 (en) | Method and system for gradient linear correction | |
| Alvarez et al. | Analysis of the magnetic field homogeneity for an equilateral triangular helmholtz coil | |
| You et al. | Biplanar shim coil design for 1.5 T permanent magnet of in vivo animal MRI |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| C56 | Change in the name or address of the patentee |
Owner name: XINGAOYI MEDICAL EQUIPMENT CO., LTD. Free format text: FORMER NAME: NINGBO XINGAOYI MAGNETIC MATERIAL CO., LTD. |
|
| CP03 | Change of name, title or address |
Address after: 315400 No. 555 smelting Road, Yuyao City, Zhejiang Province Patentee after: XINGAOYI MEDICAL EQUIPMENT Co.,Ltd. Address before: 315400 No. 777 Tan Xi Road, Yuyao, Zhejiang Patentee before: Ningbo Xingaoyi Magnetic Material Co.,Ltd. |
|
| CX01 | Expiry of patent term | ||
| CX01 | Expiry of patent term |
Granted publication date: 20130410 |