US20020171425A1 - Active shield type of elliptic cylinder-shaped gradient coil for magnetic resonance imaging - Google Patents
Active shield type of elliptic cylinder-shaped gradient coil for magnetic resonance imaging Download PDFInfo
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- US20020171425A1 US20020171425A1 US09/863,007 US86300701A US2002171425A1 US 20020171425 A1 US20020171425 A1 US 20020171425A1 US 86300701 A US86300701 A US 86300701A US 2002171425 A1 US2002171425 A1 US 2002171425A1
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/42—Screening
- G01R33/421—Screening of main or gradient magnetic field
- G01R33/4215—Screening of main or gradient magnetic field of the gradient magnetic field, e.g. using passive or active shielding of the gradient magnetic field
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Abstract
Description
- 1. (Technical Field)
- The present invention relates to a gradient coil incorporated in a magnetic resonance imaging system in order to give magnetic field gradients to an examination space formed in a bore of the system, and in particular, to an active shield type of elliptic cylindrical gradient coil.
- 2. (Related Art)
- A medical MRI system uses a magnetic resonance phenomenon of nuclear spins within an object to acquire tomographic images or measure NMR spectrums.
- The MRI system has a gantry that has an examination space shaped into for example a substantial cylinder, into which an object to be examined is inserted. The gantry has a static magnet, which forms the examination space, for generating a magnetic static field, a gradient coil for generating magnetic field gradient pulses superposed on the static field, and an RF coil for transmitting and receiving RF pulse signals (including MR signals) to and from the object.
- A gradient amplifier, which is coupled with the gradient coil, is driven in response to instructions given from a sequencer to the gradient amplifier, so that the gradient coil creates magnetic filed gradient pulses. Currently, it is required that the magnetic field gradient pulses be switched at a switching time of less than 1 msec. Especially, in the case of ultra-fast imaging techniques that have drawn much attention, the switching time of less than 0.3 msec. is required. To realize this, it has been desired that a gradient coil assembly of higher energy efficiency be developed, together with a high-power gradient amplifier.
- Conventionally, for MRI systems of which magnetic static field is directed horizontally, cylindrical gradient coil assemblies have been used. To increase the energy efficiency of this cylindrical gradient coil assembly, a first measure is to reduce the coil radius. This is based on the nature that inductance that is a parameter to decide the switching time of coils is proportional to a coil radius to 5th power. However, this technique requires that the coil radius be lowered with an increase in energy efficiency. It was therefore difficult to obtain a radius of the examination space that permits the whole-body imaging for adults.
- One solution to this problem is proposed for example by U.S. Pat. No. 4,820,988. This publication discloses a gradient coil assembly of which coils are formed into an elliptic cylinder in place of a cylinder. The coil radius is shortened in the vertical direction (normally, in the Y-axis direction) in such a manner that a section perpendicular to the axis through the coils is formed into an elliptic shape. This makes it possible that a higher rate of energy efficiency is held and the whole-body examination for adults is performed. Practically, disclosed coil shapes include a coil shape in which a half cylinder is decentered in the Y-axis direction and placed face to lace and a second coil shape in which a cylindrical coil is flattened in a certain direction to the surface so as to form an elliptic cylindrical gradient coil.
- An alternative measure is proposed by Japanese Patent Laid-open 5-269100, in which disclosed are an elliptic gradient coil assembly formed into an elliptic cylindrical coil and a detailed design method of such coil assembly.
- One significant management item for the gradient coil assembly is to suppress eddy current that occurs in pulsating the assembly to a lower value of current. The eddy current occurs in transition manners when a time-dependent magnetic field penetrates a thermal shielding plate of the static magnet, thereby a magnetic eddy field being caused in a region necessary for imaging. This causes irregularities in intensity of an MR image, deeply deteriorating image quality. To prevent this problem, an active (self-) shielded type of gradient coil assembly (ASGC: Actively Shielded Gradient Coil) is used, as shown in for example U.S. Pat. No. 4,733, 189 and No. 4,737,716). In such coils, a shield coil is placed outside the gradient coil assembly to suppress or shield a magnetic field leaking out of the gradient coil serving as a main coil. The ASGC has coil assemblies in charge of generating magnetic fields in the individual X-, Y- and Z-channels of an MRI system, and each coil assembly is equipped with a main coil and a shield coil. This shield structure almost prevents, channel by channel, magnetic field gradients from leaking out
- Practical design techniques for an ASGC of which coils are formed into a cylindrical shape are proposed by Mansfield et al., “J. Phys. E. Sci. Inst. 19, 540-545 (1986),” Turner et al., “J. Phys. D: Appl. Phys. Vo.19, L147-L151,” and others.
- Thus, an elliptic cylindrical gradient coil should be an actively shielded type of coil. To meet this demand requires a design technique that permits magnetic field gradients to be generated at a higher accuracy. However, such a practical way of designing for the elliptic cylindrical gradient coil has yet to be proposed. There are therefore difficulties in designing an active shield type of elliptic cylindrical gradient coil in terms of such work as computation of a current distribution of shield coils and computation of a desired magnetic performance (such as a maximum gradient strength and linearity in the magnetic field). The active shield type of elliptic cylindrical gradient coil has not been put into practical uses.
- The present invention, which has been made with consideration of the above problem that the conventional techniques face, is directed to an object of proposing in detail how to design an active shield type of elliptic cylindrical gradient coil, thereby such coil being able to be put into practical uses.
- To realize this object, a gradient coil for magnetic resonance imaging (MRI) according to the present invention comprises a first coil forming an elliptic cylinder; and a second coil disposed coaxially to the first coil, wherein a coil wire of the second coil is positioned in winding so that a magnetic field created by the first coil outside the second coil is cancelled.
- Preferably, current density in a circumferential direction of each of the first and second coils is expressed by weighted even functions and weighted odd functions, ratios between weights for the second coil and weights for the first coil are determined by values based on the number of waves in a coil-axis direction and a flatness rate of an ellipse, and wound positions of the coil wire of the second coil are determined based on the values.
- More preferably, the second coil is located outside the first coil in a radial direction of the first coil. In this structure, the second coil is formed into an elliptic cylinder and an elliptic cylindrical plane formed by the second coil and an elliptic cylindrical plane formed by the first coil possess in common a focus located at almost the same position. By way of example, the second coil is formed into a cylinder.
- According to these structures, there can be provided how to design winding positions of an MRI gradient coil in which the elliptic-cylindrical or cylindrical second coil (shield coil) is disposed outside the elliptic cylindrical first coil (main coil) with the same center axis given. Thus, an active shield type of elliptic cylindrical gradient coil can be provided and put into a practical use, in which a higher rate of energy efficiency is kept, while still enabling the whole-body of an object to be imaged and eddy current to surely be suppressed to reduce artifacts.
- In addition, the present invention provides a magnetic resonance imaging system in which the above gradient coil is incorporated, a design technique for the gradient coil, and a computer-readable program preferable to the design.
- In the accompanying drawings:
- FIG. 1 is an outlined schematic view of a gantry of an MRI system according to embodiments of the present invention;
- FIG. 2 is a conceptual view illustrating wire arrangement of a Z-coil included in an elliptic cylindrical ASGC according to a first embodiment;
- FIGS. 3A and 3B show unrolled views of winding patterns of a symmetric type of Z-coil;
- FIGS. 4A and 4B stow unrolled views of winding patterns of an asymmetric type of Z-coil;
- FIGS. 5A and 5B show unrolled views of winding patterns of a symmetric type of X-coil;
- FIGS. 6A and 6B show unrolled views of winding patterns of an asymmetric type of X-coil;
- FIG. 7 is a view illustrating winding patterns of a Y-coil of an elliptic cylindrical gradient coil (non-shielded type) which is shown as a prior technique;
- FIG. 8 illustrates an elliptic coordinate;
- FIG. 9 is an outlined flowchart showing processing necessary for determining winding positions of the coils of the elliptic cylindrical ASGC; and
- FIG. 10 is a conceptual view illustrating wire arrangement of a Z-coil included in an elliptic cylindrical ASGC according to a second embodiment.
- Referring to the accompanying drawings, preferred embodiments of the present invention will now be described.
- (First Embodiment)
- Referring to FIGS.1 to 9, an MRI (magnetic resonance imaging) system according to a first embodiment will now be described.
- The MRI system has a
gantry 1 and animaging system 2. Thegantry 1 is equipped with a gradient coil, which is made up of an active (self-) shield type of gradient coil (ASGC: Actively Shielded Gradient Coil) of which section perpendicular to its axial direction is formed into an approximately ellipse. Hereafter, this gradient coil is referred to as an “elliptic cylindrical ASGC,” in which the term “cylinder” is used as a hollow type of cylinder. Theimaging system 2 has functions of applying an imaging pulse sequence, acquiring an MR signal, reconstructing an MR image, memorizing MR data, and conducting an interface to/from a user. - FIG. 1 outlines a section along the axial direction of the
gantry 1 of the MRI system. Thewhole gantry 1 is shaped into a cylinder of which inner bore serves as an examination space OP, in which an object to be examined P is placed during an examination. An orthogonal XYZ coordinate system is defined on condition that the axial direction of thegantry 1 is set to the Z-axis. - The
gantry 1 is provided with astatic magnet 11 shaped into an approximately cylinder actually providing the bore, an elliptic cylindrical ASGC (substantially cylindrical gradient coil) disposed within the bore of themagnet 11, ashim coil 13 attached for example on the outer surface of the ellipticcylindrical ASGC 12, and anRF coil 14 disposed within the bore of the ellipticcylindrical ASGC 12. With theRF coil 14 placed around the object, the object is laid on a not-shown tabletop and placed in the bore (examination space). - The
static magnet 11 is formed by a superconducting magnet that has an outer vacuum container in which a plurality of thermal-radiation shielded containers and a single liquid helium container are contained. Superconducing coils are wound and disposed within the liquid helium container. The outer vacuum container is covered on the outer surface by ametal casing 11A. - The elliptic
cylindrical ASGC 12 has a coil assembly for each of the X-, Y-, and Z-channels and each coil assembly is made into a shield structure that resists the leakage of a magnetic field created by itself into an outer space thereof. With such shielded states for all the channels, pulsed magnetic gradients are generated in each of the X-, Y- and Z-axis directions. - Practically, the elliptic
cylindrical ASGC 12 is produced into a structure in which an X-coil 12X, Y-coil 12Y and Z-coil 12Z of the X-, Y- and Z-channels are layered coil by coil with insulating members therebetween, thus a cylinder being provided of which section is generally a substantial ellipse. Each of the X-coil 12X, Y-coil 12Y and Z-coil 12Z includes a main coil (corresponding to the first coil of the present invention) that has a plurality of winding parts creating a magnetic gradient in each of the X-, Y- and Z-axis directions and a shield coil (corresponding to the second coil of the present invention) that has a plurality of shielding winding parts to reduce or suppress the magnetic gradient (pulsed) created by the winding parts of the main coil from leaking out. Each of thecoils 12X, 12Y and 12Z is connected to an individual gradient power supply channel by channel. - FIG. 2 outlines a pictorial configuration of the Z-
coil 12Z, which is a representative of the X-coil, Y-coil and Z-coil. A coordinate system is defined in the configuration such that the Z-axis is a center axis itself of the Z-coil 12Z and the X- and Y-axes are set as mutually-perpendicular two axes perpendicular to the Z-axis. - The Z-
coil 12Z, as illustrated in FIG. 2, includes amain coil 21 serving as the first coil and ashield coil 22 serving as the second coil, both of which are formed in a coaxial elliptic cylinder of double-layered coils. Winding a coil wire C1 around bobbin B1 (the first bobbin) of which section to the axial (Z-axis) direction is an ellipse forms themain coil 21. The coil wire C1 is for example a flat conductor. On the other hand, winding a coil wire C2 around a bobbin B2 (the second bobbin) larger in diameter than the bobbin B1 and of which section to the axial direction is an ellipse. Current is supplied to both the main coil and the shield coil so that currents passing through the coil wires C1 and C2 are opposite to each other. - Wigs.3A and 3A and FIGS. 4A and 4B exemplify winding patterns of the Z-coil (coil winding parts). Of these, FIGS. 3A and 3B show winding patterns (½-unrolled view) of the Z-coil of a symmetric type of elliptic cylindrical ASGC of which windings are symmetric with regard to the Z-axis direction. By contrast, FIGS. 4A and 4B show winding patterns (½-unrolled view) of the Z-coil of an asymmetric type of elliptic cylindrical ASGC of which windings are asymmetric with regard to the Z-axis direction. FIGS. 3A and 4A show the winding patterns of the main coils, while FIGS. 3B and 4B show the winding patterns of the shield coils.
- The X-coil12X includes, although not shown, a main coil and a shield coil each of which consists of for example a flat conductor and each coil has four saddle-type of winding patterns (winding parts) wound around a bobbin. In other words, in each of the main coil and the shield coil, two saddle-type of winding patterns arranged in the Z-axis direction and electrically connected in series are arranged face to face in the X-axis direction so as to form two sets of winding patterns. A total of eight winding parts in both the main coil and the shield coil are electrically connected in series and connected to, for example, a common gradient power supply. This connection is made to establish a current path that allows current to flow through the main and shield coils in the mutually opposite ways These current flows make it possible that magnetic field gradients are created linearly in the X-axis direction with the shield function maintained.
- FIGS. 5A and 5B and FIGS. 6A and 6B show examples of the winding patterns of the X-coil. Of these examples, FIGS. 5A and 5B illustrate winding patterns of the X-coil of a symmetric type of elliptic cylindrical ASGC (½-unrolled view), whilst FIGS. 6A and 6B do those of an asymmetric type of elliptic cylindrical ASGC (½-unrolled view). In addition, FIGS. 5A and 6A show the winding patterns of the main coil, while FIGS. 5B and 6B do those of the shield coil. The winding positions of the wires are analytically obtained on a desired distribution of magnetic flux.
- The Y-coil12Y employs winding patterns similar to those of the X-coil 12X, in which the winding patterns are arranged as if those for the X-coils 12X are rotated about the Z-axis.
- Though the foregoing Z-coil, X-coil and Y-coil have the winding patterns similar to those of the conventional cylindrical ASGC, spacings between winding positions of the wires are designed differently from the conventional in that, as will be described later, the wires are arranged around an elliptic cylindrical surface so as to obtain a magnetic field performance required for magnetic resonance imaging.
- As shown in FIG. 7, in the case of a conventionally known elliptic cylindrical gradient coil (non-shield type) disclosed by Japanese Patent Laid-open No. 5-269100, its one coil loop always includes an oppositely-wound loop. Similarly to FIG. 7 showing the Y-coil, each of the X-coil and the Z-coil includes such oppositely-wound loop. In contrast, for each coil of the elliptic cylindrical ASGC according to the present invention, such oppositely-wound loop is not necessarily required, with the result that the winding patterns according to the present invention also differs from those of the conventional.
- How to design the foregoing elliptic cylindrical ASGC will now be described in a quantitative manner. In other words, a technique for locating windings of coil wires of the elliptic cylindrical ASGC will now be detailed. The locations of the windings may be determined through processing executed by a host computer in the
imaging system 2 or by a not-shown universal type of computer. - An elliptic cylindrical surface around which coil wires of the main coil are wound is generally expressed by the following equations (1) that use the elliptic coordinate system (refer to FIG. 8).
- x=c cos h ξc cos η, y=c sin h ξc sin η (1),
- where (±c, 0) shows the coordinates of focuses of the ellipses. Further, an elliptic cylindrical surface around which the coil wires of the shield coil are wound can be expressed by the following equations (2) in the similar manner to the above.
- x=c cos h ξc cosη, y=c sin h ξc sin η (2)
- Incidentally, the main coil has the same focuses as those for the shield coil.
- Then, described will be how to determine winding positions of coil wires of the shield coil under the condition that the winding positions of wires of the main coils are given.
-
-
-
- is accomplished, because the gradient coil is formed into the ASGC. Hence the current density function for the shield coil can be calculated. Calculating equations (3) and (5) enables current density in the circumferential direction of each of the main coil and the shield coil to be expressed by weighted even functions and weighted odd functions. And ratios between weights for the shield coil and weights for the main coil are determined with the number of waves in the coil axial direction and a flatness rate of the ellipse.
- After calculating the current density function, a stream function is calculated on the current density function by a known technique, as will be described later. Based on the stream function, discrete winding positions of wires of the shield coil are determined. These relationships can be applied to all the X-, Y- and Z-coils as well.
-
-
-
-
-
- FIG. 9 shows a flow of coil-position determination processing and winding operations for manufacturing the elliptic cylindrical ASGC according to the present invention on the basis of the foregoing qualitative analysis. Practically, first, a current density function is given to the main coil, as shown in equation (3) (step S1), then a current density function of the shield coil that corresponds to that of the main coil is calculated based on equation (5) (step S2). Then, magnetic fields created by the main and shield coils are calculated on equation (7) and inductance values Lc, Ls and LASGC of the main and shield coils are calculated on equations (7) and (9) (steps S3 a and S3 b).
- These calculated results (the values of the magnetic fields and inductance) are inputted into a specified estimate function (step S4), then an estimate value of the estimate function is calculated (step S5). It is then determined whether or not the estimate value is minimized (step S6). If the determination is NO, the processing is returned to step S1 to alter the current density function. The altered current density function is again subject to processing at steps S2 to S6. In cases where it has been determined at step S6 that the estimate value reaches its minimum (YES), the current density distributions of both the main and shield coils are calculated, and then subjected to processing for obtaining discrete coils' winding positions (step S7). The thus-obtained winding positions are used to wind coil wires around each bobbin (step S9).
- In the present embodiment, the processing from steps S1 silk to S7 is partly or entirely provided as an application program for designing the elliptic cylindrical ASGC. The program is given with a not-shown recording medium or transmission recording medium.
- As stated above, to practically design the elliptic cylindrical ASGC, it is preferable that magnetic gradients be set to their desired intensities, the linearity in the magnetic field which is able to cover an imaging region be secured, and the inductance values be as small as possible. The winding positions of the coil wires are determined on the above qualitative analysis, so that the elliptic cylindrical ASGC can be designed for actual applications. Therefore, characteristics inherently given to the elliptic cylindrical ASGC, that is, higher energy efficiency and the whole-body examination for adults can be attained.
- (Second Embodiment)
- Referring to FIG. 10, a second embodiment of the present invention will now be described.
- FIG. 10 shows a Z-
coil 12Z′ of an elliptic cylindrical ASGC according to the second embodiment, and corresponds to the coil structure shown in FIG. 2. The Z-coil 12Z′ has amain coil 21′ whose section perpendicular to its axial direction is almost elliptic and ashield coil 22′ arranged outside the main coil and whose section perpendicular to its axial direction is approximately circular. Namely, while themain coil 21′ is still kept in shape to an elliptic cylinder, theshield coil 22′ is shaped into a cylinder. This is able to reduce the number of windings to the same magnetic gradient intensities and linearity in the magnetic field as those in the ASGC according to the first embodiment, thereby the inductance values being lowered - In the second embodiment, the ASGC coil is designed such that a current density function is given to the main coil, and a current density function of the shield coil corresponding to, that of the main coil is calculated based on known techniques such as a finite element method. The obtained current density function of the shield coil is then expressed by superposition of analytic formulas. Weight coefficients of those analytic formulas are specified as values dependent on the major axis, minor axis, and axis length, and a coil radius of the shield coil. The weight coefficients are given as known values, then inductance values and a magnetic field to the ASGC are calculated using equations that express inductance values and a magnetic field to a cylindrical coil. This provides an elliptic cylindrical ASGC of which main coil is shaped into an elliptic cylinder alone, with the ASGC having desired magnetic gradient intensities and a desired linearity in the magnetic field.
- The present invention is not necessarily limited to the configurations described in the above embodiments, but the ASGC according to the present invention is able to employ other various configurations within the scopes derived from the descriptions in the appended claims.
Claims (10)
Applications Claiming Priority (3)
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JP151956/2000 | 2000-05-23 | ||
JP2000151956A JP4421079B2 (en) | 2000-05-23 | 2000-05-23 | MRI gradient coil |
JP2000-151956 | 2000-05-23 |
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US6479998B1 US6479998B1 (en) | 2002-11-12 |
US20020171425A1 true US20020171425A1 (en) | 2002-11-21 |
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US09/863,007 Expired - Lifetime US6479998B1 (en) | 2000-05-23 | 2001-05-23 | Active shield type of elliptic cylinder-shaped gradient coil for magnetic resonance imaging |
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Cited By (5)
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US20030095022A1 (en) * | 2001-11-13 | 2003-05-22 | Kci Licensing, Inc. | Static magnetic field, method of creation, and resting surface therein |
NL1026189C2 (en) * | 2003-05-15 | 2005-07-12 | Ge Med Sys Global Tech Co Llc | Systems and method for gradient compensation in magnetic resonance imaging. |
CN104391262A (en) * | 2014-11-27 | 2015-03-04 | 南京磁晨医疗技术有限公司 | MRI (magnetic resonance imaging) gradient coil assembly method |
US9541617B2 (en) | 2011-01-14 | 2017-01-10 | Hitachi, Ltd. | Gradient coil device and magnetic resonance imaging device |
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JP4789254B2 (en) * | 2006-05-01 | 2011-10-12 | 株式会社日立メディコ | Magnetic resonance imaging apparatus having a horizontal static magnetic field type elliptic cylindrical gantry and an active shield type gradient magnetic field coil apparatus adapted thereto |
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US5177441A (en) | 1989-06-16 | 1993-01-05 | Picker International, Inc. | Elliptical cross section gradient oil |
US5266913A (en) * | 1991-08-27 | 1993-11-30 | British Technology Group Usa Inc. | Screened electromagnetic coil of restricted length having optimized field and method |
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JP4191840B2 (en) | 1999-02-15 | 2008-12-03 | 株式会社東芝 | Gradient coil device |
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2000
- 2000-05-23 JP JP2000151956A patent/JP4421079B2/en not_active Expired - Lifetime
-
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- 2001-05-23 US US09/863,007 patent/US6479998B1/en not_active Expired - Lifetime
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US20030095022A1 (en) * | 2001-11-13 | 2003-05-22 | Kci Licensing, Inc. | Static magnetic field, method of creation, and resting surface therein |
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Also Published As
Publication number | Publication date |
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JP4421079B2 (en) | 2010-02-24 |
JP2001327478A (en) | 2001-11-27 |
US6479998B1 (en) | 2002-11-12 |
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