|Publication number||US7012430 B2|
|Application number||US 10/714,509|
|Publication date||Mar 14, 2006|
|Filing date||Nov 14, 2003|
|Priority date||Nov 26, 1997|
|Also published as||US6040697, US6396273, US6714013, US20010005136, US20020167321, US20040155657, WO1999027380A1|
|Publication number||10714509, 714509, US 7012430 B2, US 7012430B2, US-B2-7012430, US7012430 B2, US7012430B2|
|Inventors||George J. Misic|
|Original Assignee||Medrad, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (31), Non-Patent Citations (73), Referenced by (47), Classifications (6), Legal Events (5)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application for patent is a continuation of U.S. application Ser. No. 10/151,491, filed May 20, 2002 now U.S. Pat. No. 6,714,013, which is a continuation of U.S. application Ser. No. 09/776,132, filed Feb. 2, 2001, now U.S. Pat. No. 6,396,273, which is a continuation of U.S. application Ser. No. 09/512,093, filed Feb. 24, 2000, now abandoned, which is a divisional of U.S. application Ser. No. 08/979,842, filed Nov. 26, 1997, now U.S. Pat. No. 6,040,697, the contents of which are incorporated herein by reference.
The present invention relates to the field of magnetic resonance imaging (MRI) systems and, more particularly, to coils for use in such systems.
It is well known in the field of MRI systems to provide radio frequency signals in the form of circularly polarized or rotating magnetic fields having an axis of rotation aligned with a main magnetic field. It is also well known to use receiving coils to intercept a radio frequency magnetic field generated by a human subject or an object in the presence of the main magnetic field in order to provide an image of the human subject or the object.
Receiving coils of this type were formed as volume coils in order to enclose a volume for receiving a body part such as a leg, arm or hand and intercept the radio magnetic field. See, for example, U.S. Pat. No. 4,411,270 issued to Damadian and U.S. Pat. No. 4,923,459 issued to Nambu. Additionally, surface receiving coils were developed for this purpose. The surface receiving coils were placed adjacent a region of interest. For a surface receiving coil, see U.S. Pat. No. 4,793,356 to Misic et al., for example.
Advances in the field of MRI systems have resulted in modifications to both volume receiving coils and surface receiving coils in order to improve their signal to noise ratios. This was achieved by modifying the receiving coils to receive perpendicular components of the radio frequency magnetic field. These improved coils are known as quadrature coils. Quadrature coils provided a significant signal to noise ratio improvement over non-quadrature coils. See, for example, U.S. Pat. No. 4,467,282 issued to Siebold and U.S. Pat. No. 4,707,664 issued to Fehn.
In U.S. Pat. No. 5,258,717, issued to Misic, a quadrature receiving coil system was provided, along with a data acquisition system. The data acquisition system taught by Misic included multiple image processing channels for processing a plurality of MRI signals and combining the processed signals to produce an image. The receiving coil system of Misic was formed of multiple quadrature receiving coils, the receiving coils being adapted to intercept both of the quadrature components of the magnetic resonance signals in a spatially dependent manner. Such quadrature coil systems provided coverage of a portion of a total target sensitive volume along an axis parallel to the main magnetic field. Consequently, each receiving coil of the system had a sensitive volume smaller than that which would otherwise be necessary. Thus, each receiving coil provided an improved signal to noise ratio for the region within its sensitive volume. Two leads were connected to each receiving coil and each lead was connected to a separate processing channel of the data acquisition system. The outputs of the processing channels were combined and a final data set from the entire target sensitive volume was calculated. The calculated data set had a better signal to noise ratio greater than that which could be achieved with a single receiving coil.
However, the various receiving coils of the prior art described had a number of artifact problems. For example, an image provided using the prior art receiving coils could have artifacts due to aliasing caused when the phase of a signal from a part of the anatomy within the field of the coil duplicates that of a location elsewhere. This occurs because a phase location of 370 degrees appears to the system as a phase location of 10 degrees. Thus, a signal from anatomy at a phase location of −350 or 370 degrees manifests itself in the image at a phase location of 10 degrees within the field of view. Elimination of phase wrap essentially halves the actual phase field of view, shifting from −90 to +90 degrees rather than from −180 to +180 degrees. However, this merely moves the alias location to more than +/−1.5 the field of view rather that eliminating it.
Another form of artifact, sometimes referred to as an annafact, can occur in either the frequency direction or the phase direction within prior art MRI systems. In this type of artifact, an area of anatomy that is at least partially within the excitation field of the body coil has a local Larmour frequency identical to a pixel within the imaging field of view. If there is any excitation and subsequent pickup of this material, it appears within the field of view superimposed upon the desired image, regardless of whether the artifact comes in from the frequency direction or the phase direction. The problems associated with this type of artifact are worsened by the use of higher speed gradients that are shorter in physical size and lower field uniformity.
It is therefore an objective of the invention to provide a coil system and/or method that eliminates soft tissue artifacts and aliasing artifacts typical of prior art systems and/or methods for imaging various regions of interest.
Another objective of the present invention is to provide improved signal to noise performance, for example, by permitting the use of smaller fields of view and thinner slices when performing imaging.
Another objective of the present invention is to provide greater image uniformity than provided in the prior art.
Another objective of the invention is to facilitate complete imaging of the regions of interest during a magnetic resonance imaging (MRI) procedure.
In a preferred embodiment, the invention provides a phased array coil system for use with a magnetic resonance imaging (MRI) system. The phased array coil system includes a first coil, a second coil, and an interface subsystem. The first coil defines a first region and the second coil defines a second region, with the first coil partially overlapping the second coil to define an overlap region formed by the intersection of the first and second regions. Overably connected with the first and second coils, the interface subsystem includes (i) a power splitter for splitting radio frequency (RF) power for delivery to the first and second coils and (ii) a phase compensator for adjusting the phase relationship of the RF power delivered to the first and second coils so that a magnetic field produced thereby in the overlap region is approximately equal to that produced near the center of each of the first and second regions.
In a related embodiment, the invention provides a phased array coil system for use with a magnetic resonance imaging (MRI) system. The phased array coil system includes a first coil, a second coil, and an interface subsystem. The first coil defines a first region and the second coil defines a second region, with the first coil partially overlapping the second coil to define an overlap region formed by the intersection of the first and second regions. Operably connected with the first and second coils, the interface subsystem includes (i) a power splitter for splitting radio frequency (RF) power for delivery to the first and second coils and (ii) a phase compensator for adjusting the phase relationship of the RF power delivered to the first and second coils to cause partial destructive/constructive interference thereof in the overlay region so that a magnetic field produced thereby in the overlay region is approximately equal to that produced near the center of each of the first and second regions.
In a further related embodiment, the invention provides a transmit/receive (T/R) phased array coil system for use with a magnetic resonance imaging (MRI) system. The T/R phased array coil system includes a first birdcage coil, a second birdcage coil, and an interface subsystem. The first birdcage coil encompasses a first region, the second birdcage coil encompasses a second region, with the first and second birdcage coils defining an overlap region in which one of the birdcage coils is partially overlapped by the other of the birdcage coils to form a phased array coil subsystem. Connected to the phased array coil subsystem, the interface subsystem includes a power splitter, an attenuator, a phase compensator, and a plurality of switches for enabling the interface subsystem to be switched between a transmit state and a receive state. In the transmit state, the power splitter allocates radio frequence (RF) power received from the MRI system between the first and second birdcage coils with the attenuator reducing the RF power directed to at least one of the first and second birdcage coils so that (A) a first magnetic field is applied through the first birdcage coil to the first region encompassed thereby and (B) a second magnetic field is applied through the second birdcage coil to the second region encompassed thereby with the phase compensator affecting a phase relationship between the first and second magnetic fields so that a resulting magnetic field produced thereby in the overlay region is approximately equal to the first and second magnetic fields produced near the center of the first and second regions, respectively. In the receive state, the interface subsystem receives from the phased array coil subsystem a response of an anatomical structure placed therein and conveys the response to the MRI system.
Referring now to
Quadrature receiving coils 12, 14 are of a type referred to as birdcage coils, as well known in the art. They are formed of circular conductive loops 20, 22 connected to each other and spaced apart from each other by conductive connection members 24. There may be eight electrically conductive connection members 24 or rods 24 joining circular conductive loops 20, 22. Each receiving coil 12, 14 of coil system 10 formed in this manner can function as a separate quadrature receiving coil within coil system 10.
Magnetic interaction between quadrature receiving coils 12, 14 is eliminated by positioning quadrature coils 12, 14 about drum support member 16 to provide radial symmetry about the axis parallel to the main magnetic field, which is the Z-axis shown in FIG. 1. Moreover, quadrature coil 12 is slightly larger in diameter than quadrature coil 14 so that coil 12 can overlap a portion of coil 14. The amount of overlap of coils 12, 14 is adjusted so that the net flux from one coil, as seen as the vector sum of the flux from the overlap region, exactly cancels the flux from the return through the balance of the coil. In this case the field vector of the overlap region can be substantially equal to the field vectors of the other two regions. This causes the net shared flux of zero and thus a net mutual inductance of zero between quadrature receiving coils 12, 14. Coils 12, 14 maintain their isolation regardless of the relative rotational position about their common axis.
Quadrature coils 12, 14 of receiving coil system 10 have symmetry about two planes parallel to the Z-axis. The two planes of symmetry are at right angles to each other. In addition, quadrature coils 12, 14 are arranged so that the rotating magnetic vector of each receiving coil 12, 14 is in the X-Y plane. However, the net rotating magnetic vectors of coils 12, 14 are spatially displaced from each other along the Z-axis. In this regard, each receiving coil 12, 14 intercepts the quadrature components of the magnetic resonance signal within its own sensitive volume.
Referring now to
Coaxial leads 30 a, b are connected to quadrature coil 14 at points that are at ninety degrees relative to each other and to ports 1, 2 of data acquisition system 34. Likewise, coaxial leads 32 a, b are connected to quadrature coil 12 at points that are disposed at ninety degrees relative to each other. Coaxial leads 32 a, b are also connected to ports 3, 4 of data acquisition system 34. An electrical network (not shown) can be interconnected between quadrature receiving coils 12, 14 and coaxial leads 30 a, b and 32 a, b to appropriately connect the cables to quadrature coils 12, 14. Such electrical networks are well known in the art. Furthermore, quadrature coils 12, 14 can be rotated (i.e., can accommodate different angular orientations) relative to one another without destroying the signal to noise improvements achieved in accordance with this prior art method. This is taught in U.S. Pat. No. 5,258,717 to Misic and incorporated by reference herein.
Referring now to
In the preferred embodiment of coil array system 60 (as discussed in more detail below with respect to FIG. 6), inner coil 64 can be formed with eight electrically conductive rods 66 fixed to electrically conductive end rings 70 a,b. Outer quadrature coil 68 can be formed of two sections: receive/transmit coil section 74 and auxiliary transmit coil section 72. Receive/transmit section 74 can be provided with eight electrically conductive rods 82 fixed to electrically conductive end rings 80 a,b which act cooperatively to define an array volume. Auxiliary transmit coil section 72 can be provided with eight electrically conductive rods 84 connecting electrically conductive end rings 80 b,c. Rods 66, 82 and 84 as well as end rings 70 a,b and 80 a,b,c can be any kind of electrical conductors such as, for example, conductive tubing, etched copper or copper tape or any other material suitable for inducing and detecting a magnetic field.
Furthermore, each conductive rod 84 of auxiliary transmit coil section 72 can be provided with a PIN diode 88. When PIN diodes 88 of auxiliary coil section 72 are forward biased, conductive rods 84 and ring 80 c are electrically coupled to receive/transmit coil section 74. Thus, PIN diodes 88 can be used to couple and decouple portions of rods 84 and thereby substantially couple and decouple transmit coil section 72 and transmit/receive coil section 74. When conductive rods 84 or rod extensions 84 are switched in by PIN diodes 88 in this manner, the effective length of receive/transmit coil section 74 can be extended to thereby define a further array volume. PIN diodes 88 are forward biased and the length of coil section 74 is thereby extended in this manner when electrical energy is applied to outer coil 68 for the purpose of creating a magnetic field to form a magnetic resonance image. Although PIN diodes 88 can be used in the preferred embodiment for extending the length of outer coil 68, any kind of coupling and decoupling circuit known to those skilled in the art can be used.
It will be understood that coil array system 60 can be used for left or right imaging of the musculoskeletal system of human subjects. For example, coil array system 60 can be used for imaging a knee, a foot, an ankle, a wrist or a hand. The anatomical structures that can be imaged and evaluated using coil array system 60 can include ligaments, tendons, cartilage, osseous structures, fluid filled bursa, adipose tissue, muscle and potential pathological lesions. Furthermore, coil array system 60 is adapted to permit easy placement of the anatomy of interest within the array volume defined by coils 64, 68 and adapted to be disposed on a base to permit positioning left and right of isocenter.
Referring now to
Energy from splitter 98 is applied to phase compensator 108 to obtain the correct phase relationship between the fields of coils 64, 68. The output of phase compensator 108 is applied to a ninety degree element 104. The outputs of the ninety degree element 104 are applied to isolated contact points 91, displaced ninety degrees from each other, by way of leads 92 and socket 96. Disposing contact points 91 at ninety degrees with respect to each other causes the orthogonal components of the rotating magnetic field signal to be completely received within coil system 64, 68.
Because the energy required by larger coil 68 may be more than the energy required by smaller coil 64, the energy supply path of smaller coil 64 is provided with attenuator 102 at the output of splitter 98. Additionally, a ninety degree element 104 is provided as previously described. The four outputs of the ninety degree elements 104 thus determine relative amplitudes and phases for driving the inputs of coil system 60 with the appropriate power levels and signal phases to provide the most uniform transmit field possible. For coil 64, energy from the outputs of the ninety degree element 104 is applied to coil 64 at contact points 93 by way of socket 96 and leads 94. Contact points 93 are disposed ninety degrees from each other as described with respect to contact points 91. In this manner, coil system 60 is provided with two quadrature pairs separated spatially along the Z-axis. Additionally, the voltage level and the phase applied to coils 64, 68 can be adjusted to provide a uniform field. Coils 64 and 68 can be crossed saddle quadrature coils or Helmholtz pairs.
It will be understood that alternative arrangements of attenuation and phase compensation can be used to obtain the required results. For example, both the attenuation and the phase compensation can be applied to one of the coils 64, 68 without any additional attenuation or phase compensation being applied to the other coil 64, 68. For example, the attenuation and phase compensation can be applied to the path of inner coil 64 only. Furthermore, if inner coil 64 serves as a receive only coil without serving as a transmit coil, then transmit power is applied only to outer coil 68. In this case, the transmit power can be applied to contact points 91 by way of a ninety degree element without necessarily using any additional attenuation or phase compensation. Further in this case, inner coil 64 does not require transmit decoupling.
Referring now to
For example, outer quadrature coil 154 is formed of coil sections 156, 160 wherein conductor rods 168 of coil section 156 are provided with PIN diodes 164. When PIN diodes 164 of coil section 156 are forward biased during transmission, the effective length of outer quadrature coil 154 is extended to be equal to the combined lengths of coil section 156 and coil section 160.
Each of the conductive rods 66, 82 and 84 of coil array system 60 can be provided with an adjustable tuning capacitor located at its mechanical center. The use of tuning capacitors in this manner is well known in the art and is not shown in order to simplify the drawings. The value of the tuning capacitors can be selected to allow each conductive rod 66, 82 and 84 to resonate at 63.87 MHz. A variable capacitor can be provided between the conductive rods containing the output contacts 91, 93. The additional variable capacitor can be used to optimize the isolation of the quadrature outputs.
A network for impedance matching the real part of the coil impedance to 50Ω through the two lattice baluns can be provided for each of the four conductive rods 66, 82 having contacts 91, 93. This can be accomplished using a series capacitive divider and an impedance transformation in the baluns. Additionally, each output port 122 can be followed by a balancing network including two series connected lattice baluns that are resonant at 63.87 MHz.
As shown in
Referring now to
As previously described with respect to coil system 60, splitters 104 can be used to provide four outputs of a selectively determined relative amplitude and phase to drive the four loops added to the current coil design with the appropriate power levels and signal phases to provide the most uniform transmit field possible. PIN diode networks 192 can be used to isolate the coil elements from the coil during transmission.
Thus, quadrature receiving coil system 60 and its alternate embodiments provide an improvement over previous receiving coils when multiple means for processing image signals are available. The sensitive volume of the coil system is expanded allowing for the interception of both quadrature components of MR signals in a spatially dependent manner, with each coil providing coverage of a portion of the desired sensitive volume along the axis parallel to the main magnetic field. Consequently, each coil had a sensitive volume smaller than that which would otherwise be necessary and each such coil provided improved signal to noise ratio from the region within its sensitive volume.
The above description is intended by way of example only and is not intended to limit the present invention in any way, except as set forth in the following claims. For example, it is to be understood that the present invention is not limited to two coil systems. Rather, the present invention may be embodied as an N-quadrature coil system, where N is an integer, and where N processing means are available for each coil system. Furthermore, the present invention can include any method and system for adding transmit capability to a quadrature phased array coil element by extending one part of the coil in transmit only, transmitting with both coils with proper amplitude and phase, and using external local transmit coil elements.
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|48||MRI Devices Corporation's Supplemental Response to Medrad's Interrogatory No. 11, Civil Action No. 02-2044 (Feb. 21, 2003).|
|49||MRI Devices' Memorandum Supporting Its Motion for Attorneys Fees and Expenses under 35 U.S.C. § 285 (Oct. 22, 2003).|
|50||MRI Devices' Memorandum Supporting Its Motion for Summary Judgment of Noninfringement of the '273 Patent ("MRIDC's Memo Supporting SJ Motion of Noninfringement").|
|51||MRI Devices' Memorandum Supporting Its Motion for Summary Judgment to Invalidate Claims 1,2,3,5,16 and 23 of U. S. Patent No. 6,396,273 (MRIDC's Memo Supporting Invalidity Motion).|
|52||MRI Devices' Memorandum Supporting Magistrate Judge Mitchell's Report and Recommendation (Jul. 11, 2003).|
|53||MRI Devices' Motion for Attorneys Fees and Expenses under 35 U.S.C. § 285 (Oct. 22, 2003).|
|54||MRI Devices' Motion for Summary Judgment of Noninfringement of the '273 Patent ("MRIDC's SJ Motion of Noninfringement").|
|55||MRI Devices' Motion for Summary Judgment to Invalidate Claims 1,2,3,5,16 and 23 of U.S. Patent No. 6,396,273 ("MRIDC's SJ Motion to Invalidate").|
|56||MRI Devices' Opposition to Medrad's Motion for Preliminary Injunction (Apr. 14, 2003).|
|57||MRI Devices' Reply Supporting Its Motion For Summary Judgment to Invalidate All Asserted Claims of U. S. Patent No. 6,396,273 (MRIDC's Reply).|
|58||MRI Devices' Response to Medrad's Motion to Vacate This Court's Entry of Summary Judgement (Sep. 24, 2003).|
|59||MRI Devices' Response to the Magistrate Judge's Report and Recommendation (Oct. 29, 2003).|
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|61||Plaintiff Medrad's Responses to Defendant's Fifth Set of Interrogatories, Civil Action No. 02-2044 (Feb. 21, 2003).|
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|U.S. Classification||324/318, 600/421|
|International Classification||G01V3/00, G01R33/3415|
|Apr 26, 2004||AS||Assignment|
Owner name: MEDRAD, INC., PENNSYLVANIA
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Effective date: 20040419
|Sep 14, 2009||FPAY||Fee payment|
Year of fee payment: 4
|Mar 14, 2013||FPAY||Fee payment|
Year of fee payment: 8
|Feb 11, 2014||AS||Assignment|
Owner name: BAYER MEDICAL CARE INC., PENNSYLVANIA
Free format text: CHANGE OF NAME;ASSIGNOR:MEDRAD, INC.;REEL/FRAME:032250/0165
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|Oct 27, 2015||AS||Assignment|
Owner name: BAYER HEALTHCARE LLC, NEW JERSEY
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