Abstract:
With a view toward implementing an RF coil easy to uniformize the strength of a magnetic filed, the RF coil is provided with a first current path group of  182 - 186  including a plurality of linear current passes placed in parallel with one another, a second current pass group of  182 ′- 186 ′ placed so as to have the relations in mirror image with respect to the first current pass group, and a third current pass group of  192 - 196 ′ in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the first and second current pass groups while bypassing the first and second current pass groups.

Description:
BACKGROUND OF THE INVENTION  
         [0001]    The present invention relates to an RF coil (radio frequency coil) and a magnetic resonance imaging system, and particularly to a flat type RF coil and a magnetic resonance imaging system having such an RF coil.  
           [0002]    In a magnetic resonance imaging (MRI) system, a target to be shot or imaged is carried in an internal bore of a magnet system, i.e., a bore or space in which a static magnetic field is formed. A gradient magnetic field and a high-frequency magnetic field are applied to produce a magnetic resonance signal within the target. A tomogram is produced (reconstructed) based on its received signal.  
           [0003]    In a magnet system using permanent magnets for the purpose of generating a static magnetic field, a flat type RF coil is provided close to the pair of permanent magnets opposite to each other to thereby apply a high-frequency magnetic field.  
           [0004]    As the flat type RF coil, one is used which has patterns for current passes such as shown in FIG. 1 by way example. As shown in the same drawing, the RF coil has a pair of main passes  26  and return passes  27  which connect these main passes in series so that the directions of currents flowing therethrough become identical.  
           [0005]    In order to uniformize the distribution of an intensity distribution of a high-frequency magnetic field in an imaging space or volume, main passes respectively comprise two current passes  26   a  and  26   b  and  26   a ′ and  26   b ′ connected in parallel as shown in FIG. 2 by way of example. The two current passes  26   a  and  26   b  and  26   a ′ and  26   b ′ are placed in parallel with a predetermined interval held therebetween.  
           [0006]    Uniformly or appropriately proportionally-distributed currents are passed through these two current passes  26   a  and  26   b  ( 26   a ′ and  26   b ′) to thereby achieve the uniformization of the intensity distribution of the high-frequency magnetic field. The proportion of the currents is adjusted by selecting values of circuit parts such as capacitors inserted into the passes.  
           [0007]    As another technique, as shown in FIG. 3 by way of example, each of main passes  26  is formed of a wide conductor and a high-frequency magnetic field is formed by a distributed current flowing therethrough.  
           [0008]    Since each of circuit parts normally has an error allowed for its nominal value from the viewpoint of standards, the ratio in current between the two current passes must accurately be adjusted while the error is being corrected in the RF coil having the configuration shown in FIG. 2, and hence a great deal of working man-hours are required. Further, since an eddy current based on a gradient magnetic field flows in the broad conductor in the RF coil having the configuration shown in FIG. 3, a gradient magnetic field characteristic is degraded.  
         SUMMARY OF THE INVENTION  
         [0009]    Therefore, an object of the present invention is to implement an RF coil easy to uniformize the strength of a magnetic field and a magnetic resonance imaging system having such an RF coil. Further, the implementation of an RF coil free of an eddy current developed due to a gradient magnetic field and a magnetic resonance imaging system having such an RF coil is an object. 
           [0010]    (1) The invention according to one aspect, for solving the above problems is an RF coil which comprises a first current pass group including a plurality of linear current passes placed on a plane surface in parallel with one another, a second current pass group which includes a plurality of linear current passes parallel to one another and is placed on the plane surface in such a relationship as to have a mirror image parallel to the first current pass group, and a third current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the first and second current pass groups while bypassing the first and second current pass groups along the plane surface.  
           [0011]    In the invention according to the present aspect, all the linear electrical passes are connected in series so that they are identical in current direction through the first and second current pass groups. Therefore, currents for all the linear electrical passes or main passes are rendered identical to one another without any adjustments. Therefore, the uniformity of a high-frequency magnetic field is uniquely determined according to the spatial arrangement of the linear electrical passes.  
           [0012]    (2) The invention according to another aspect, for solving the above problems is an RF coil which comprises a first current pass group including a plurality of linear current passes placed on a first plane surface in parallel with one another, a second current pass group which includes a plurality of linear current passes parallel with one another and is placed on the first plane surface in such a relationship as to have a mirror image parallel to the first current pass group, a third current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the first and second current pass groups while bypassing the first and second current pass groups along the first plane surface, a fourth current pass group including a plurality of linear current passes which are placed on a second plane surface opposed in parallel with the first plane surface with a space interposed therebetween, so as to extend parallel to the direction of the current passes of the first current pass group, a fifth current pass group which includes a plurality of linear current passes parallel with one another and is placed on the second plane surface in such a relationship as to have a mirror image parallel to the fourth current pass group, and a sixth current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the fourth and fifth current pass groups while bypassing the fourth and fifth current pass groups along the second plane surface.  
           [0013]    In the invention according to the present aspect, two RF coils each having the same configuration as the RF coil described in (1) are laid out in an opposing relationship with a space defined therebetween. Therefore, a composite high-frequency magnetic field can be, formed between the two.  
           [0014]    (3) The invention according to a further aspect, for solving the above problems is an RF coil which comprises a first current pass group including a plurality of linear current passes placed on a first plane surface in parallel with one another, a second current pass group which includes a plurality of linear current passes parallel with one another and is placed on the first plane surface in such a relationship as to have a mirror image parallel to the first current pass group, a third current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the first and second current pass groups while bypassing the first and second current pass groups along the first plane surface, a seventh current pass group including a plurality of linear current passes which are placed on a third plane surface adjacent to the first plane surface and opposed in parallel therewith, so as to extend parallel to one another along the direction orthogonal to the direction of the current passes of the first current pass group, an eighth current pass group which includes a plurality of linear current passes parallel to one another and is placed on the third plane surface in such a relationship as to have a mirror image parallel to the seventh current pass group, and a ninth current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the seventh and eighth current pass groups while bypassing the seventh and eighth current pass groups along the third plane surface.  
           [0015]    In the invention according to the present aspect, two RF coils each having the same configuration as the RF coil described in (1) are combined together so that main passes are made vertical to each other. It is therefore possible to form a high-frequency magnetic field according to a quadrature system.  
           [0016]    (4) The invention according to a still further aspect, for solving the above problems is an RF coil which comprises a first current pass group including a plurality of linear current passes placed on a first plane surface in parallel with one another, a second current pass group which includes a plurality of linear current passes parallel with one another and is placed on the first plane surface in such a relationship as to have a mirror image parallel to the first current pass group, a third current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the first and second current pass groups while bypassing the first and second current pass groups along the first plane surface, a seventh current pass group including a plurality of linear current passes which are placed on a third plane surface adjacent to the first plane surface and opposed in parallel therewith, so as to extend parallel to one another along the direction orthogonal to the direction of the current passes of the first current pass group, an eighth current pass group which includes a plurality of linear current passes parallel to one another and is placed on the third plane surface in such a relationship as to have a mirror image parallel to the seventh current pass group, a ninth current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the seventh and eighth current pass groups while bypassing the seventh and eighth current pass groups along the third plane surface, a fourth current pass group including a plurality of linear current passes which are placed on a second plane surface opposed in parallel with the first plane surface with a space interposed therebetween, so as to extend parallel to the direction of the current passes of the first current pass group, a fifth current pass group which includes a plurality of linear current passes parallel with one another and is placed on the second plane surface in such a relationship as to have a mirror image parallel to the fourth current pass group, a sixth current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the fourth and fifth current pass groups while bypassing the fourth and fifth current pass groups along the second plane surface, a tenth current pass group including a plurality of linear current passes which are placed on a fourth plane surface adjacent to the second plane surface and opposed in parallel therewith, so as to extend parallel to one another along the direction orthogonal to the direction of the current passes of the fourth current pass group, an eleventh current pass group which includes a plurality of linear current passes parallel to one another and is placed on the fourth plane surface in such a relationship as to have a mirror image parallel to the tenth current pass group, and a twelfth current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the tenth and eleventh current pass groups while bypassing the tenth and eleventh current pass groups along the fourth plane surface.  
           [0017]    In the invention according to the present aspect, two quadrature type RF coils each having the same configuration as the RF coil described in (3) are placed in an opposing relationship with a space defined therebetween. It is therefore possible to form a composite high-frequency magnetic field in the space defined therebetween.  
           [0018]    (5) The invention according to a still further aspect, for achieving the above problems is a magnetic resonance imaging system for forming an image, based on magnetic resonance signals acquired using a static magnetic filed, a gradient magnetic field and a high-frequency magnetic field, which comprises an RF coil for generating the high-frequency magnetic field, including a first current pass group including a plurality of linear current passes placed on a plane surface in parallel with one another, a second current pass group which includes a plurality of linear current passes parallel to one another and is placed on the plane surface in such a relationship as to have a mirror image parallel to the first current pass group, and a third current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the first and second current pass groups while bypassing the first and second current pass groups along the plane surface.  
           [0019]    In the invention according to the present aspect, as an RF coil for the generation of a high-frequency magnetic field, one is used wherein all the linear electrical passes are series-connected so as to become identical in current direction through the first and second current pass groups, and currents flowing through all the linear electrical passes, i.e., main passes are rendered identical without any adjustments. Therefore, the uniformity of a high-frequency magnetic field is uniquely determined according to the spatial arrangement of the linear electrical passes.  
           [0020]    (6) The invention according to a still further aspect, for solving the above problems is a magnetic resonance imaging system for forming an image, based on magnetic resonance signals acquired using a static magnetic filed, a gradient magnetic field and a high-frequency magnetic field, which comprises an RF coil for generating the high-frequency magnetic field, including a first current pass group including a plurality of linear current passes placed on a first plane surface in parallel with one another, a second current pass group which includes a plurality of linear current passes parallel to one another and is placed on the first plane surface in such a relationship as to have a mirror image parallel to the first current pass group, a third current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the first and second current pass groups while bypassing the first and second current pass groups along the first plane surface, a fourth current pass group including a plurality of linear current passes which are placed on a second plane surface opposed in parallel with the first plane surface with a space interposed therebetween, so as to extend parallel to the direction of the current passes of the first current pass group, a fifth current pass group which includes a plurality of linear current passes parallel with one another and is placed on the second plane surface in such a relationship as to have a mirror image parallel to the fourth current pass group; and a sixth current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the fourth and fifth current pass groups while bypassing the fourth and fifth current pass groups along the second plane surface.  
           [0021]    In the invention according to the present aspect, as RF coils for the generation of high-frequency magnetic fields, ones are used wherein two RF coils each having the same configuration as the RF coil described in (1) are placed in an opposing relationship with a space defined therebetween. It is therefore possible to form a composite high-frequency magnetic field in the space defined therebetween.  
           [0022]    (7) The invention according to a still further aspect, for solving the above problems is a magnetic resonance imaging system for forming an image, based on magnetic resonance signals acquired using a static magnetic filed, a gradient magnetic field and a high-frequency magnetic field, which comprises an RF coil for generating the high-frequency magnetic field, including a first current pass group including a plurality of linear current passes placed on a first plane surface in parallel with one another, a second current pass group which includes a plurality of linear current passes parallel with one another and is placed on the first plane surface in such a relationship as to have a mirror image parallel to the first current pass group, a third current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the first and second current pass groups while bypassing the first and second current pass groups along the first plane surface, a seventh current pass group including a plurality of linear current passes which are placed on a third plane surface adjacent to the first plane surface and opposed in parallel therewith, so as to extend parallel to one another along the direction orthogonal to the direction of the current passes of the first current pass group, an eighth current pass group which includes a plurality of linear current passes parallel to one another and is placed on the third plane surface in such a relationship as to have a mirror image parallel to the seventh current pass group, and a ninth current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the seventh and eighth current pass groups while bypassing seventh and eighth current pass groups along the third plane surface.  
           [0023]    In the invention according to the present aspect, as an RF coil for the generation of a high-frequency magnetic field, one, is used wherein two RF coils each having the same configuration as the RF coil described in (1) are combined together so that main passes are made vertical to each other. It is therefore possible to form a high-frequency magnetic field according to a quadrature system.  
           [0024]    (8) The invention according to a still further aspect, for solving the above problems is a magnetic resonance imaging system for forming an image, based on magnetic resonance signals acquired using a static magnetic filed, a gradient magnetic field and a high-frequency magnetic field, which comprises an RF coil for generating the high-frequency magnetic field, including a first current pass group including a plurality of linear current passes placed on a first plane surface in parallel with one another, a second current pass group which includes a plurality of linear current passes parallel with one another and is placed on the first plane surface in such a relationship as to have a mirror image parallel to the first current pass group, a third current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the first and second current pass groups while bypassing the first and second current pass groups along the first plane surface, a seventh current pass group including a plurality of linear current passes which are placed on a third plane surface adjacent to the first plane surface and opposed in parallel therewith, so as to extend parallel to one another along the direction orthogonal to the direction of the current passes of the first current pass group, an eighth current pass group which includes a plurality of linear current passes parallel to one another and is placed on the third plane surface in such a relationship as to have a mirror image parallel to the seventh current pass group, a ninth current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the seventh and eighth current pass groups while bypassing the seventh and eighth current pass groups along the third plane surface, a fourth current pass group including a plurality of linear current passes which are placed on a second plane surface opposed in parallel with the first plane surface with a space interposed therebetween, so as to extend parallel to the direction of the current passes of the first current pass group, a fifth current pass group which includes a plurality of linear current passes parallel with one another and is placed on the second plane surface in such a relationship as to have a mirror image parallel to the fourth current pass group, a sixth current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the fourth and fifth current pass groups while bypassing the fourth and fifth current pass groups along the second plane surface, a tenth current pass group including a plurality of linear current passes which are placed on a fourth plane surface adjacent to the second plane surface and opposed in parallel therewith, so as to extend parallel to one another along the direction orthogonal to the direction of the current passes of the fourth current pass group, an eleventh current pass group which includes a plurality of linear current passes parallel to one another and is placed on the fourth plane surface in such a relationship as to have a mirror image parallel to the tenth current pass group, and a twelfth current pass group in which all the linear electrical passes are series-connected so as to be identical in current direction through both groups of the tenth and eleventh current pass groups while bypassing the tenth and eleventh current pass groups along the fourth plane surface.  
           [0025]    In the invention according to the present aspect, as RF coils for the generation of high-frequency magnetic fields, ones are used wherein two quadrature type RF coils each having the same configuration as the RF coil described in (3) are placed in an opposing relationship with a space defined therebetween. It is therefore possible to form a composite high-frequency magnetic field in the space defined therebetween.  
           [0026]    According to the present invention, an RF coil easy to uniformize the strength of a magnetic field and a magnetic resonance imaging system having such an RF coil can be implemented. Further, an RF coil which does not cause eddy currents due to a gradient magnetic field, and a magnetic resonance imaging system having such an RF coil can be implemented. 
       
    
    
       [0027]    Further objects and advantages of the present invention will be apparent from the following description of the preferred embodiments of the invention as illustrated in the accompanying drawings.  
       BRIEF DESCRIPTION OF THE DRAWINGS  
       [0028]    [0028]FIG. 1 is a schematic illustration depicting patterns of current passes for a conventional example illustrative of a transmission coil.  
         [0029]    [0029]FIG. 2 is a schematic illustration showing patterns of current passes for a conventional example illustrative of a transmission coil.  
         [0030]    [0030]FIG. 3 is a schematic illustration depicting patterns of current passes for a conventional example illustrative of a transmission coil.  
         [0031]    [0031]FIG. 4 is a block diagram of a system showing one example of an embodiment according to the present invention.  
         [0032]    [0032]FIG. 5 is a diagram showing one example of a pulse sequence executed by the system shown in FIG. 4.  
         [0033]    [0033]FIG. 6 is a diagram illustrating one example of a pulse sequence executed by the system shown in FIG. 4.  
         [0034]    [0034]FIG. 7 is a typical diagram depicting the structure of a magnet system employed in the system shown in FIG. 4 in the neighborhood of each transmission coil unit thereof.  
         [0035]    [0035]FIG. 8 is a schematic illustration showing patterns of current passes for the transmission coil unit shown in FIG. 7.  
         [0036]    [0036]FIG. 9 is a schematic illustration depicting patterns of current passes for the transmission coil units shown in FIG. 7.  
         [0037]    [0037]FIG. 10 is a schematic illustration showing patterns of current passes for the transmission coil units shown in FIG. 7.  
         [0038]    [0038]FIG. 11 is a schematic illustration depicting patterns of current passes for the transmission coil unit shown in FIG. 7.  
         [0039]    [0039]FIG. 12 is a schematic illustration showing patterns of current passes for the transmission coil units shown in FIG. 7. 
     
    
     DETAILED DESCRIPTION OF THE INVENTION  
       [0040]    Preferred embodiments of the present invention will hereinafter be described in detail with reference to the accompanying drawings. A block diagram of a magnetic resonance imaging system is shown in FIG. 4. The present system is one example of an embodiment of the present invention. One example of an embodiment related to a system of the present invention is shown according to the configuration of the present system.  
         [0041]    As shown in FIG. 4, the present system has a magnetic system  100 . The magnetic system  100  has main magnetic field magnet units  102 , gradient coil units  106  and transmission coil units  108 . Any of these main magnetic field magnet unit  102  and respective coil units comprises, paired ones opposed to one another with a space, interposed therebetween. Further, any of them has a substantially disc shape and is placed with its central axis held in common. A target  300  is placed on a cradle  500  in an internal bore of the magnetic system  100  and carried in and out by unillustrated conveying means. A receiving coil unit  110  is mounted to a shot or imaged portion of the target  300 .  
         [0042]    The main magnetic field magnet unit  102  forms a static magnetic field in the internal bore of the magnetic system  100 . The direction of the static magnetic field is approximately orthogonal to the direction of the body axis of the target  300 . Namely, the main magnetic field magnet unit  102  forms a so-called vertical magnetic field. The main magnetic field magnet unit  102  is configured using a permanent magnet or the like, for example. Incidentally, the main magnetic field magnet unit  102  is not limited to the permanent magnet and may of course be configured using a superconductive electromagnet or a normal conductive electromagnet or the like.  
         [0043]    The gradient coil unit  106  produces gradient magnetic fields used for causing the intensity of the static magnetic field to have a gradient or slope. The produced gradient magnetic fields include three types of gradient magnetic fields of a slice gradient magnetic field, a read out gradient magnetic field and a phase encode gradient magnetic field. The gradient coil unit  106  has unillustrated 3-systematic gradient coils in association with these three types of gradient magnetic fields.  
         [0044]    The three-systematic gradient coils respectively produce three gradient magnetic fields for applying gradients to static magnetic fields respectively as viewed in three directions orthagonal to one another. One of the three directions corresponds to the direction (vertical direction) of the static magnetic field and is normally defined as a z direction. Another one thereof corresponds to a horizontal direction and is normally defined as a y direction. The remaining one corresponds to the direction orthogonal to the z and y directions and is normally defined as an x direction. The x direction is orthogonal to the z direction within the vertical plane and perpendicular to the y direction within the horizontal plane. x, y and z are also called gradient axes below.  
         [0045]    Any of x, y and z can be set as an axis for a slice gradient. When any of them is set as the slice gradient axis, one of the remaining two is set as an axis for a phase encode gradient and the other thereof is set as an axis for a read out gradient. The 3-systematic gradient coils will further be explained later.  
         [0046]    The transmission coil unit  108  transmits an RF excitation signal for exciting a spin in a body of the target  300  to a static magnetic field space. The transmission coil unit  108  is one example of an embodiment of an RF coil employed in the present invention. One example of the embodiment related to the RF coil employed in the present invention is shown based on the configuration of the transmission coil unit  108 . The transmission coil unit  108  will further be described later.  
         [0047]    A gradient driver  130  is connected to the gradient coil unit  106 . The gradient driver  130  supplies a drive signal to the gradient coil unit  106  to generate a gradient magnetic field. The gradient driver  130  has unillustrated 3-systematic drive circuits in association with the 3-systematic gradient coils in the gradient coil unit  106 .  
         [0048]    An RF driver  140  is connected to the RF coil unit  108 . The RF driver supplies a drive signal to the transmission coil unit  108  to transmit an RF excitation signal, thereby exciting the spin in the body of the target  300 .  
         [0049]    The receiving coil unit  110  receives therein a magnetic resonance signal by which the excited spin is produced. A data collector  150  is connected to the receiving coil unit  110 . The data collector  150  takes in or captures a signal received by the receiving coil unit  110  and collects it as view data.  
         [0050]    A controller  160  is connected to the gradient driver  130 , the RF driver  140  and the data collector  150 . The controller  160  controls the gradient driver  130  to data collector  150  respectively to execute shooting or imaging.  
         [0051]    The output side of the data collector  150  is connected to a data processor  170 . The data processor  170  is configured using a computer or the like, for example. The data processor  170  has an unillustrated memory. The memory stores a program and various data for the data processor  170  therein. The function of the present system is implemented by allowing the data processor  170  to execute the program stored in the memory.  
         [0052]    The data processor  170  causes the memory to store the data captured from the data collector  150 . A data space is defined in the memory. The data space forms a two-dimensional Fourier space. The data processor  170  transforms these data in the two-dimensional Fourier space into two-dimensional inverse Fourier form to thereby produce (reconstruct) an image for the target  300 . The two-dimensional Fourier space is also called a “k space”.  
         [0053]    The data processor  170  is connected to the controller  160 . The data processor  170  is above the controller  160  in rank and generally controls it. Further, a display unit  180  and an operation or control unit  190  are connected to the data processor  170 . The display unit  180  is made up of a graphic display or the like. The operation unit  190  comprises a keyboard or the like provided with a pointing device.  
         [0054]    The display unit  180  displays a reconstructed image and various information outputted from the data processor  170 . The operation unit  190  is operated by an operator and inputs various commands and information or the like to the data processor  170 . The operator controls the present system on an interactive basis through the display unit  180  and the operation unit  190 .  
         [0055]    [0055]FIG. 5 shows one example of a pulse sequence used when imaging or shooting is done by the present system. The present pulse sequence corresponds to a pulse sequence of a gradient echo (GRE) method.  
         [0056]    Namely, (1) shows a sequence of a α° pulse for RF excitation employed in the GRE method. Numerals (2) , (3), (4) and (5) similarly respectively show sequences of a slice gradient Gs, a read out gradient Gr, a phase encode gradient Gp and a gradient echo MR. Incidentally, the α° pulse is typified by a central signal. The pulse sequence proceeds from left to right along a time axis t.  
         [0057]    As shown in the same drawing, α° excitation for the spin is carried out based on the α° pulse. A flip angle α° is less than or equal to 90°. At this time, the slice gradient Gs is applied to effect selective excitation on a predetermined slice.  
         [0058]    After the α° excitation, the spin is phase-encoded based on the phase encode gradient Gp. Next, the spin is firstly dephased based on the read out gradient Gr. Next, the spin is rephased to generate a gradient echo MR. The signal strength of the gradient echo MR reaches a maximum after an echo time TE has elapsed since the excitation. The gradient echo MR is collected as view data by the data collector  150 .  
         [0059]    Such a pulse sequence is repeated 64 to 512 times in a cycle TR (repetition time). Each time it is repeated, the phase encode gradient Gp is changed and different phase encodes are carried out every time. Thus, view data for 64 to 512 views for filing in a k space can be obtained.  
         [0060]    Another example of a pulse sequence for magnetic resonance imaging is shown in FIG. 6. The pulse sequence corresponds to a pulse sequence of a spin echo (SE) method.  
         [0061]    Namely, (1) shows a sequence of a 90° pulse and a 180° pulse for RF excitation employed in the SE method. Numerals (2), (3), (4) and (5) similarly respectively show sequences of a slice gradient Gs, a read out gradient Gr, a phase encode gradient Gp and a spin echo MR. Incidentally, the 90° pulse and 180° pulse are respectively typified by central signals. The pulse sequence proceeds from left to right along a time axis t.  
         [0062]    As shown in the same drawing, 90° excitation for the spin is carried out based on the 90° pulse. At this time, the slice gradient Gs is applied to effect selective excitation on a predetermined slice. After a predetermined has elapsed since the 90° excitation, 180° excitation based on the 180° pulse, i.e., spin inversion is carried out. Even at this time, the slice gradient Gs is applied to effect selective inversion on the same slice.  
         [0063]    The read out gradient Gr and the phase encode gradient Gp are applied during a period in which the 90° excitation and the spin reversal are carried out. The spin is dephased based on the read out gradient Gr. Further, the spin is phase-encoded based on the phase encode gradient Gp.  
         [0064]    After the spin reversal, the spin is rephased based on the read out gradient Gr to produce a spin echo MR. The signal strength of the spin echo MR reaches a maximum after TE has elapsed since the 90° excitation. The spin echo MR is collected as view data by the data collector  150 . Such a pulse, sequence is repeated 64 to 512 times in a cycle TR. Each time it is repeated, the phase encode gradient Gp is changed and different phase encodes are carried out every time. Thus, view data for 64 to 512 views for filling in a k space can be obtained.  
         [0065]    Incidentally, the pulse sequence used for imaging is not limited to the GRE method or SE method. The pulse sequence may be other suitable techniques such as an FSE (Fast Spin Echo) method, a fast recovery FSE (Fast Recovery Fast Spin Echo) method, echo planar imaging (EPI), etc.  
         [0066]    The data processor  170  transforms the view data in the k space into two-dimensional inverse Fourier form to thereby reconstruct a tomogram for the target  300 . The reconstructed image is stored in its corresponding memory and displayed on the display unit  180 .  
         [0067]    [0067]FIG. 7 typically shows the structure of the magnet system  100  located in the neighborhood of the transmission coil unit  108  in the form of a cross-sectional view. In the same drawing, O indicates the center of a static magnetic field, i.e., a magnet center, and x, y and z indicate the aforementioned three directions respectively.  
         [0068]    A spheric volume SV of a radius R with the magnet center  0  as the center is a shooting or imaging area. The magnet system  100  is configured so that the static magnetic field and gradient magnetic field have a predetermined accuracy in the SV.  
         [0069]    A pair of main magnetic field magnet units  102  has a pair of pole pieces  202  opposed to each other. The pole piece  202  is composed of a magnetic material having high permeability such as a soft iron or the like and serves so as to uniformize a magnetic flux distribution in a static magnetic field space.  
         [0070]    The pole pieces  202  are respectively shaped substantially in the form of discs but protrude in the direction (z direction) in which their peripheral edge portions are orthogonal to their plate surfaces, i.e., in the direction in which the pole pieces  202  are opposed to each other. Thus, the pole pieces  202  have bottom plate portions and protruded peripheral edge portions. The protruded peripheral edge portions serve so as to make up for reductions in magnetic flux density at the peripheral edges of the pole pieces  202 .  
         [0071]    The gradient coil units  106  and transmission coil units  108  are respectively provided in their corresponding concave portions of the pole pieces  202 , which are defined inside the protruded peripheral edge portions. Any of the respective coil units is shaped in the form of a substantially disc. The coil units are mounted to their corresponding polar surfaces of the pole pieces  202  so as to successively form layers by unillustrated appropriate mounting means.  
         [0072]    Patterns for current passes of the transmission coil unit  108  are shown in FIG. 8 by a diagrammatic illustration. As shown in the same drawing, the transmission coil unit  108  has linear plural main current passes (main passes)  182 ,  184 ,  186 ,  182 ′,  184 ′ and  186 ′ parallel to a y direction at a portion near the center O of a circle. The main pass  182  is closest to the center O. The main passes  184  and  186  are successively kept away from the center O. The main passes  182 ′,  184 ′ and  186 ′ are similar to the above.  
         [0073]    The main passes  182 ,  184  and  186  show one example illustrative of an embodiment of a first current pass group employed in the present invention. The main passes  182 ′,  184 ′ and  186 ′ show one example illustrative of an embodiment of a second current pass group employed in the present invention.  
         [0074]    The main passes  182 ,  184  and  186  and the main passes  182 ′,  184 ′ and  186 ′ have the relations in mirror images with respect to a y axis which passes through the center O of the circle within an xy plane. While an example illustrative of a total of six main passes provided by three is shown herein, the number of main passes may be an appropriate even number corresponding to four or more.  
         [0075]    Return passes  192 ,  194 ,  196 ,  192 ′,  194 ′ and  196 ′ for the main passes are formed along the circumference of the circle. The return passes  192 ,  194 ,  196 ,  192 ′,  194 ′ and  196 ′ show one example illustrative of an embodiment of a third current pass group employed in the present invention.  
         [0076]    The return pass  192  connects the main passes  182  and  184  to each other in series so that they are identical in current direction. The return pass  194  connects the main passes  184  and  186  to each other in series so that they are identical in current direction. The return pass  196  connects the main passes  186  and  182 ′ to each other in series so that they are identical in current direction.  
         [0077]    The return pass  192 ′ connects the main passes  182 ′ and  184 ′ to each other in series in such a manner that they are identical in current direction. The return pass  194 ′ connects the main passes  184 ′ and  186  to each other in series in such a way that they are identical in current direction. The return pass  196 ′ connects the main passes  186 ′ and  182  to each other in series in such a manner that they are identical in current direction.  
         [0078]    A capacitor  402  is connected in series with the return pass  192 ′ and constitutes an LC circuit together with the main passes  182  through  186 ′ and return passes  192  through  196 ′. The resonance frequency of the LC circuit is tuned to a magnetic resonance frequency. An RF drive signal is supplied from the RF driver  140  to both ends of the capacitor  402 .  
         [0079]    Incidentally, a tuning capacitor may be series-connected to an appropriate one point or plural points of the main passes  182  through  186 ′ and return passes  192  through  196 ′ in addition to the capacitor  402 .  
         [0080]    The main passes  182 ,  184 ,  186 ,  182 ′,  184 ′ and  186 ′ are all connected in series through the return passes  192 ,  194 ,  196 ,  192 ′,  194 ′ and  196 ′ in such a manner that they are identical in current direction. Thus, the values of currents, which flow through the main passes  182 ,  184 ,  186 ,  182 ′,  184 ′ and  186 ′, are all identical to one another without the need for any adjustment.  
         [0081]    An intensity or strength distribution of a high-frequency magnetic field in an imaging or shooting space is determined according to the placement or layout of the main passes  182  through  186 ′ on an xy plane. The layout of the main passes  182  through  186 ′ for uniformizing the intensity distribution of the high-frequency magnetic field or bringing the high-frequency magnetic field to a desired distributed state can be determined by calculation.  
         [0082]    One example of the layout of the main passes  182  through  186 ′ takes such a form that the two main passes  184  and  186  ( 184 ′ and  186 ′) relatively far away from the center O, of the three main passes are disposed so as to approach each other as shown in the drawing.  
         [0083]    Thereby, the main passes  184  and  186  ( 184 ′ and  186 ′) exerts operation similar to the flowing of double currents through the single main pass on a shooting or imaging space. This would substantially lead to the fact that currents are proportionally distributed to the two main passes  26   a  and  26   b  at a ratio of 1:2 in the conventional RF coil shown in FIG. 2. Namely, the substantial current distribution can accurately be carried out without depending on values of circuit parts or the like in the present coil. Since it is unnecessary to use a wide conductor for each main pass, eddy currents developed due to a gradient magnetic field present no problem.  
         [0084]    By connecting all the passes in series, the length of a conductor constituting each pass increases and the inductance of the coil becomes large. Therefore, one small in capacitance can be used for the tuning capacitor  402 . Further, when a magnetic resonance signal is received by the receiving coil unit  110 , a blocking impedance for bringing the transmission coil unit  108  to a disable state can be increased.  
         [0085]    Further, since the currents flow through all the main passes in series, a magnetomotive force increases in proportional to the number of the main passes. Therefore, the field intensity per power to be supplied increases as compared with the conventional RF coil shown in FIG. 2 or  3 . On the contrary, required power for carrying out the achievement of the same magnetic field strength can be reduced.  
         [0086]    As shown in FIG. 9, a pair of transmission coil units  108  having such coil patterns is opposed to each other with a shooting or spheric space or volume SV interposed therebetween. The pair of transmission coil units  108  is supplied with drive signals opposite in phase to each other. Thus, the sum of high-frequency magnetic fields developed in the pair of transmission coil units  108  is applied to the shooting volume SV.  
         [0087]    Main passes  182 ,  184  and  186  for one of the pair of transmission coil units  108  show one example illustrative of an embodiment of a first current pass group employed in the present invention, main passes  182 ′,  184 ′ and  186 ′ for one thereof show one example illustrative of an embodiment of a second current pass group employed in the present invention, and return passes  192 ,  194 ,  196 ,  192 ′,  194 ′ and  196 ′ for one thereof show one example illustrative of an embodiment of a third current pass group employed in the present invention.  
         [0088]    Main passes  182 ,  184  and  186  for the other of the pair of transmission coil units  108  show one example illustrative of an embodiment of a fourth current pass group employed in the present invention, main passes  182 ′,  184 ′ and  186 ′ for the other thereof show one example illustrative of an embodiment of a fifth current pass group employed in the present invention, and return passes  192 ,  194 ,  196 ,  192 ′,  194 ′ and  196 ′ for the other thereof show one example illustrative of an embodiment of a sixth current pass group employed in the present invention.  
         [0089]    As shown in FIG. 10 by way of example, a transmission coil unit  118  having coil patterns rendered different in main-pass direction by 90° within an xy plane may be superimposed on the transmission coil unit  108 . It is needless to say that the two should be isolated from each other.  
         [0090]    A coil pattern of the transmission coil unit  118  is shown in FIG. 11. As shown in the same drawing, the transmission coil unit  118  is equivalent to one obtained by turning the coil pattern shown in FIG. 8 by 90°.  
         [0091]    If described ex integro, then the transmission coil unit  118  has linear plural main passes  282 ,  284 ,  286 ,  282 ′,  284 ′ and  286 ′ parallel in an x direction at a portion near the center O of a circle. The main pass  282  is closest to the center O. The main passes  284  and  286  are successively kept away from the center O. The main passes  282 ′,  284 ′ and  286 ′ are similar to the above.  
         [0092]    The main passes  282 ,  284  and  286  show one example illustrative of an embodiment of a seventh current pass group employed in the present invention. The main passes  282 ′,  284 ′ and  286 ′ show one example illustrative of an embodiment of an eighth current pass group employed in the present invention.  
         [0093]    Return passes  292 ,  294 ,  296 ,  292 ′,  294 ′ and  296 ′ are formed along the circumference of the circle. The return passes  292 ,  294 ,  296 ,  292 ′,  294 ′ and  296 ′ show one example illustrative of an embodiment of a ninth current pass group employed in the present invention.  
         [0094]    The return pass  292  connects the main passes  282  and  284  to each other in series so that they are identical in current direction. The return pass  294  connects the main passes  284  and  286  to each other in series so that they are identical in current direction. The return pass  296  connects the main passes  286  and  282 ′ to each other in series so that they are identical in current direction.  
         [0095]    The return pass  292 ′ connects the main passes  282 ′ and  284 ′ to each other in series in such a manner that they are identical in current direction. The return pass  294 ′ connects the main passes  284 ′ and  286  to each other in series in such a way that they are identical in current direction. The return pass  296 ′ connects the main passes  286 ′ and  282  to each other in series in such a manner that they are identical in current direction.  
         [0096]    A capacitor  502  is connected in series with the return pass  292 ′ and constitutes an LC circuit together with the main passes  282  through  286 ′ and return passes  292  through  296 ′. The resonance frequency of the LC circuit is tuned to a magnetic resonance frequency. An RF drive signal is supplied from the RF driver  140  to both ends of the capacitor  502 .  
         [0097]    As shown in FIG. 12 by way of example, a pair of transmission coil units  108  having such coil patterns are opposed to each other with an imaging or spheric volume SV interposed therebetween together with one transmission coil unit  108 . The pair of transmission coil units  118  is supplied with drive signals opposite in phase to each other. Thus, the sum of high-frequency magnetic fields developed in the pair of transmission coil units  118  is applied to the shooting or spheric volume SV.  
         [0098]    Main passes  282 ,  284  and  286  for one of the pair of transmission coil units  118  show one example illustrative of an embodiment of a seventh current pass group employed in the present invention, main passes  282 ′,  284 ′ and  286 ′ for one thereof show one example illustrative of an embodiment of an eighth current pass group employed in the present invention, and return passes  192 ,  194 ,  196 ,  192 ′,  194 ′ and  196 ′ for one thereof show one example illustrative of an embodiment of a ninth current pass group employed in the present invention.  
         [0099]    Main passes  282 ,  284  and  286  for the other of the pair of transmission coil units  118  show one example illustrative of an embodiment of a tenth current pass group employed in the present invention, main passes  282 ′,  284 ′ and  286 ′ for the other thereof show one example illustrative of an embodiment of an eleventh current pass group employed in the present invention, and return passes  192 ,  194 ,  196 ,  192 ′,  194 ′ and  196 ′ for the other thereof show one example illustrative of an embodiment of a twelfth current pass group employed in the present invention.  
         [0100]    A drive signal for the transmission coil unit  108  and a drive signal for the transmission coil unit  118  are different 90° in phase from each other. Thus, the transmission coils  108  and the transmission coil units  118  perform so-called quadrature operations to produce high-frequency magnetic fields turned within an xy plane in the imaging or spheric volume SV.  
         [0101]    While the example of the RF coil dedicated for transmission has been described above, an RF coil perfectly identical in configuration to this coil can also be used for reception of a magnetic resonance signal. In that case, receive signals are captured from both ends of capacitors  402  and  302 . Incidentally, the uniformization of the strength of a magnetic field developed in a transmission coil is equivalent to the uniformization of the distribution of sensitivity in a receiving coil.  
         [0102]    Many widely different embodiments of the invention may be configured without departing from the spirit and the scope of the present invention. It should be understood that the present invention is not limited to the specific embodiments described in the specification, except as defined in the appended claims.