Abstract:
A TEM resonator RF coil with excellent operating characteristics comprising a plurality of ring segments on the orifice capable of being segmented by slits on the orifice are installed with a first conducting pattern connecting to the line element, a second conducting pattern disposed symmetrically on the left and right of the first conducting pattern, a capacitor connecting these conducting patterns, and a connection means spanning the adjacent ring segments and connecting the second conducting patterns.

Description:
BACKGROUND OF THE INVENTION 
     The present invention relates to an RF (radio frequency) coil, shield and a magnetic resonance imaging apparatus, and particularly relates to a TEM (transverse electromagnetic mode) resonator RF coil, a shield used to adjust TEM RF coils, and a magnetic resonance imaging apparatus using the TEM resonator RF coil. 
     In magnetic resonance imaging apparatus using for example a high magnetic field of approximately 3 T (tesla) as the static magnetic field, TEM resonator RF coils are utilized on account of a high RF (radio frequency) signal transmit/receive efficiency to receive magnetic resonance signals occurring from spin excitation and RF excitation of the spin of the imaging target. 
     The TEM resonator RF coil has a cylindrical tube  700  as shown in FIG.  1 . Both ends of the tube  700  have orifices  702 ,  702 ′. The orifices  702 ,  702 ′ have openings  704 ,  704 ′ concentrically formed with a smaller inner diameter than the inner diameter of the tube  700 . 
     The tube  700  and the orifices  702 ,  702 ′ are formed with consecutive conductive elements. Tube bodies having a tube  700  and orifice  702 ,  702 ′ of this kinds are called shields or cavities. 
     A plurality of line elements  802  are disposed on the inner side of the shield in parallel with the shield axis. The line elements  802  form an LC series circuit. Both ends of the plural line elements  802  are respectively coupled mechanically and electrically to the orifices  702 ,  702 ′, and arranged concentrically along the periphery of the openings  704 ,  704 ′. The line elements  802  are separated from the inner side of the tube  700 . 
     A rotating RF magnetic field is generated within the surface axially perpendicular to the columnar space enclosed by the line elements  802 , by supplying an RF signal to specified locations of an RF coil of this structure. The RF signal (magnetic resonance signal) generated by the rotating spin on the same plane is extracted from specified positions of this RF coil. 
     In actual magnetic resonance imaging, the shield is separated into a plurality of slits  706  in the axial and radial directions as shown for example in FIG.  2 . Each of the shield segments separated by the slits  706  are electrically isolated, preventing excess current from flowing along the outer periphery of the shield during application of a magnetic field gradient, and preventing disturbances in the static magnetic field during excess current flow. 
     In the RF coil having the shield separated by slits, the shield effect is decreased because both ends of the orifices  702 ,  702 ′ are separated into individual segments by the slits  706 . When this kind of RF coil is used as the head coil for capturing images of the cranium, the neck section of the target image is added as an external load to the other orifice so that the electrical characteristics are asymmetrical along the coil axis and the RF coil operation tends to be unstable. 
     To achieve stable operation, capacitors  122  are disposed to connect the adjoining shield segments on both ends of the orifices  702 ,  702 ′ of the shield as shown in FIG.  3 . 
     Capacitors used as the capacitor  122  have for example, sufficient high impedance in a frequency region of 1 kilohertz to 10 kilohertz and for example, sufficiently low impedance in the frequency range of approximately 128 megahertz. 
     The orifices  702 ,  702 ′ connected by such capacitors are equivalent to an electrical short in the RF region across the slit  706 . A plurality of the line elements  802  therefore have a value equivalent to conductive elements each jointly connected on both ends, so the shield effect in the RF region is improved, and operation is stabilized regardless of whether a load is present or absent in the vicinity of the orifices  702 ,  702 ′. 
     In the 1 kilohertz to 10 kilohertz frequency region on the other hand, the capacitor  122  has a sufficiently high impedance so that excess current does not flow to the outer periphery during application of a magnetic field gradient forming the signal in the same frequency range. Therefore the effect of excess current on the static magnetic field can be prevented. 
     The RF coil imaging object can be easily input and output so that a two-segment structure along the axis can be formed as shown for example in FIG. 4, and both segments joined by a connector. In such a case, the width of the slit  706  in the connector joint must be wider than the other sections so that the static electrical coupling in that section is weak and the shield effect deteriorates. 
     In the joint of the connector  124 , the slits  706 ,  706 ′ are respectively rotated into both shield segment sides as shown for example in FIG. 5, conductive foil lands  126 ,  126 ′ are respectively formed, and electrically connected to the connector  124 , and the slits  706 ,  706 ′ respectively bridged to the capacitors  122 ,  122 ′. In this way a sufficient static electrical connection can be maintained in the segments. 
     In the above segmented TEM resonator RF coil, the conductive pattern for electrical connection to the connectors is different from the conductive pattern of other RF coils so that the circuits in the segments have poor uniformity, and the operating characteristics as an RF coil deteriorate. 
     SUMMARY OF THE INVENTION 
     It is an object of the present invention to provide a TEM resonator RF coil with excellent operating characteristics, a shield for adjusting this type of RF coil, and a magnetic resonance imaging apparatus using this TEM resonator RF coil. 
     (1) To solve the above problems, in a first aspect of the invention, a TEM resonator RF coil is comprised of a cylindrical shield having a ring-shaped orifice at both ends, a plurality of line elements connected at both ends to the orifice and arranged at equal intervals along an opening of the orifice, a plurality of slits segmenting the shield into two equally portioned positions at line element intervals in parallel along the axis and forming a plurality of ring segments on the orifice, and the plural ring segments are comprised of a first conducting pattern connected to the line elements, a second conducting pattern disposed symmetrically for the line elements in two directions from the line elements towards the slit, capacitors connecting the first conducting pattern with the second conducting pattern, and a connection means to electrically connect the second conducting patterns spanning the adjacent ring segments. 
     In this aspect of the invention, the circuits between the segments are uniform (equivalent) because the plural ring sections made from an orifice segmented by slits, have a first conducting pattern connected to the line elements, a second conducting pattern disposed symmetrically to the first conducting pattern for the line elements, in two directions from the line elements towards the slit. 
     (2) In another aspect of the invention to solve the above problems, the RF coil according to (1) is characterized in that the shield can be divided into two portions at the slit locations. 
     In this aspect of the invention, the shield can be segmented into two portions at the slit locations so that the uniformity of the circuits is continually maintained between segments, and the imaging object can be easily inserted and removed. 
     (3) In another aspect of the invention to solve the above problems, the RF coil according to (1) is characterized in that the shield can be disassembled into a plurality of cylinder segments per the slit locations. 
     In this aspect of the invention, the shield can be disassembled into a plurality of cylinder segments at the slit locations so that the uniformity of the circuits is continually maintained between segments, and frequency alignment to the same frequency can be performed in each segment. 
     (4) In another aspect of the invention to solve the above problems, the TM resonator RF coil comprises a cylindrical shield having a ring-shaped orifice at both ends, a plurality of line elements connected at both ends to the orifice and arranged at equal intervals along the opening of the orifice, a plurality of slits segmenting the shield into two equally portioned positions at line element intervals in parallel along the axis and characterized in that the shield can be disassembled into a plurality of cylinder segments at the slit locations. 
     In this aspect of the invention, the shield can be disassembled into a plurality of cylinder segments at the slit locations so that frequency alignment to the same frequency can be performed in each segment. 
     (5) In another aspect of the invention to solve the above problems, the RF coil according to (2) or (4) is characterized in comprising a support means to support the plural cylinder segments so as to constitute a whole cylinder. 
     In this aspect of the invention, the plural cylinder segments are supported as a whole cylinder by the support means. 
     (6) In another aspect of the invention to solve the above problems, an RF coil according to (5) is characterized in that the support means can be divided into at least two portions in parallel along the axis. 
     In this aspect of the invention, the support means can be divided into two portions so the imaging object can be easily inserted and removed. 
     (7) In another aspect of the invention to solve the above problems, a shield includes a fit portion capable of receiving one cylinder segment for an RF coil according to (3) or (4). 
     In this aspect of the invention, during frequency alignment of the segments to the same frequency, the shield acquires a jig for fitting the segment into the fit portion. 
     (8) In another aspect of the invention to solve the above problems, the shield according to (7) coil is characterized in having slits corresponding to the slits in the RF coil according to (3) or (4). 
     In this aspect of the invention, the shield has slits corresponding to the slits in the RF coil and so is equivalent to the RF coil shield. 
     (9) In another aspect of the invention to solve the above problems, in a magnetic resonance imaging apparatus for forming images based on magnetic resonance signals acquired by applying a high frequency magnetic field to an object for imaging under a static magnetic field and a gradient magnetic field, an RF coil for at least either applying the high frequency magnetic field or acquiring the magnetic resonance signal is a TEM resonator coil comprised of a cylindrical shield having a ring-shaped orifice at both ends, a plurality of line elements connected at both ends to the orifice and arranged at equal intervals along the opening of the orifice, a plurality of slits segmenting the shield into two equally portioned positions at line element intervals in parallel along the axis and forming a plurality of ring segments on the orifice, and the magnetic resonance imaging apparatus is characterized in that the plural ring segments are respectively comprised of a first conducting pattern connected to the line elements, a second conducting pattern disposed symmetrically for the line elements in two directions from the line elements towards the slits, capacitors connecting the first conducting pattern with the second conducting pattern, and a connection means to electrically connect the second conducting patterns spanning the adjacent ring segments. 
     In this aspect of the invention, a plurality of ring segments on the orifice capable of being divided by the slits, respectively have a first conducting pattern connecting the line elements, and a second conducting pattern disposed symmetrically for the line elements in two directions from the line elements towards the slit, so that the uniformity of the circuits is continually maintained between segments. By utilizing an RF coil of this type, high quality imaging can be performed. 
     (10) In another aspect of the invention to solve the above problems, a magnetic resonance imaging apparatus according to (9) is characterized in that the shield can be segmented into two portions at the slit locations. 
     In this aspect of the invention, the shield can be segmented into two portions at the slit locations so that the uniformity of the circuits is continually maintained between segments, and the imaging object can be easily inserted and removed. 
     (11) In another aspect of the invention to solve the above problems, a magnetic resonance imaging apparatus according to (9) is characterized in that the shield can be disassembled into a plurality of cylinder segments at the slit locations. 
     In this aspect of the invention, the shield can be disassembled into a plurality of cylinder segments at the slit locations so that the uniformity of the circuits is continually maintained between segments, and frequency alignment to the same frequency can be performed in each segment. By utilizing an RF coil of this type, high quality imaging can be performed. 
     (12) In another aspect of the invention to solve the above problems, in a magnetic resonance imaging apparatus for forming images based on magnetic resonance signals acquired by applying a high frequency magnetic field to an object for imaging under a static magnetic field and a gradient magnetic field; an RF coil for at least applying the high frequency magnetic field or acquiring the magnetic resonance signal is a TEM resonator coil comprised of a cylindrical shield having a ring-shaped orifice at both ends, a plurality of line elements connected at both ends to the orifice and arranged at equal intervals along the opening of the orifice, a plurality of slits segmenting the shield into two equally portioned positions at line element intervals in parallel along the axis, and the magnetic resonance imaging apparatus is characterized in using an RF coil with a shield capable of being disassembled into a plurality of cylinder segments at the slit locations. 
     In this aspect of the invention, the shield can be disassembled into a plurality of cylinder segments at the slit locations so that frequency alignment to the same frequency can be performed in each segment. By utilizing an RF coil of this type, high quality imaging can be performed. 
     (13) In another aspect of the invention to solve the above problems, a magnetic resonance imaging apparatus according to (11) or (12) is characterized in comprising a support means to support the plural cylinder segments so as to constitute a whole cylinder. 
     In this aspect of the invention, a plurality of cylinder segments can therefore be supported together as a whole cylinder by the support means. 
     (14) In another aspect of the invention to solve the above problems, a magnetic resonance imaging apparatus according to (13) is characterized in that the support means can be divided along the axis into at least two portions. 
     In this aspect of the invention, the support means is divided into two portions so that the imaging object can be easily inserted and removed. 
     Therefore, the present invention provides a TEM resonator RF coil with excellent operating characteristics, a shield used to adjust the TEM RF coil, and a magnetic resonance imaging apparatus using the TEM resonator RF coil of the invention. 
     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 
     FIG. 1 is a pattern drawing of a TEM resonator RF coil. 
     FIG. 2 is a pattern drawing of the TEM resonator RF coil. 
     FIG. 3 is a pattern drawing of the TEM resonator RF coil. 
     FIG. 4 is a pattern drawing of the TEM resonator RF coil. 
     FIG. 5 is a pattern drawing of a portion of the RF coil shown in FIG.  4 . 
     FIG. 6 is a block diagram of one embodiment of the apparatus of the invention. 
     FIG. 7 is a pattern drawing of an RF coil for the apparatus shown in FIG.  6 . 
     FIG. 8 is a pattern drawing of a portion of the RF coil shown in FIG.  7 . 
     FIG. 9 is a pattern drawing of a portion of the RF coil shown in FIG.  7 . 
     FIG. 10 is a pattern drawing of the RF coil shown in FIG.  6 . 
     FIG. 11 is a pattern drawing of RF coil segments shown in FIG.  7 . 
     FIG. 12 is a vertical cross sectional view of the RF coil segments shown in FIG.  11 . 
     FIG. 13 is a pattern drawing of a portion of the RF coil shown in FIG.  7 . 
     FIG. 14 is a pattern drawing of an alignment jig for the segment shown in FIG.  11 . 
     FIG. 15 is a pattern drawing of a support frame for installing the segments shown in FIG.  11 . 
     FIG. 16 is a drawing showing a typical pulse sequence implemented by the apparatus shown in FIG.  6 . 
     FIG. 17 is a drawing showing a typical pulse sequence implemented by the apparatus shown in FIG.  6 . 
    
    
     DETAILED DESCRIPTION OF THE INVENTION 
     The embodiments of the present invention are hereafter described in detail while referring to the accompanying drawings. A block diagram of the magnetic resonance imaging apparatus is shown in FIG.  6 . This apparatus is an example of the embodiment of the invention. The embodiment relating to the apparatus of the invention is shown by means of the structure of this apparatus. 
     This apparatus has a magnet system  100  as shown in FIG.  6 . The magnet system  100  has a main magnetic field coil unit  102 , a gradient coil unit  106  and a RF (radio frequency) coil  108 . These coils have a generally cylindrical shape and are mutually arrayed on the same axis. An imaging object  300  is loaded on a cradle  500  in the largely columnar bore (inner space) of the magnet system  100 , and carried in and carried out on a carry means not shown in the drawing. 
     The main magnetic field coil unit  102  forms a static magnetic field in the bore (inner space) of the magnet system  100 . The direction of the static field is largely parallel to the body axis of the imaging object  300  or in other words is a horizontal magnetic field. The main magnetic field coil unit  102  is formed using for example, a super-conductive coil. Of course, the present invention is not limited to a super-conductive coil and may use an ordinary conductive coil. 
     The gradient coil unit  106  generates a gradient magnetic field for making the static magnetic field intensity have a gradient. The generated gradient magnetic field is of three types: a slice gradient field, a readout gradient field and a phase encode gradient magnetic field. The gradient coil unit  106  has a three-system gradient coil (not shown in the drawing) for generating these three types of gradient magnetic fields. 
     The RF coil unit  108  forms a high frequency magnetic field for excitation for a spin within the body of the imaging object  300  in the static magnetic field space. The forming of a high frequency magnetic field hereafter also refers to transmission of the RF excitation signal. The RF coil unit  108  receives the magnetic waves generated by the spin excitation or in other words receives the magnetic resonance signal. The RF coil unit  108  is one embodiment of the RF coil of the invention. The embodiment of the RF coil of the invention is shown by means of the structure of the RF coil unit  108 . The RF coil unit  108  is explained again later in detail. 
     A gradient drive unit  130  is connected to the gradient coil unit  106 . The gradient coil unit  106  applies a drive signal to the gradient coil unit  106  and generates a gradient magnetic field. The gradient drive unit  130  has three system drive circuits not shown in the drawing, corresponding to the three types of gradient coils in the gradient coil unit  106 . 
     The RF drive unit  140  is connected to the RF coil unit  108 . The RF drive unit  140  applies a drive signal to the RF coil unit  108  and transmits an RF excitation signal, and causes spin excitation within the body of the imaging object  300 . 
     A data acquisition unit  150  is also connected to the RF coil unit  108 . The data acquisition unit  150  is input with the receive signal received by the RF coil unit  108 , and collects these signals as view data. 
     A control unit  160  is connected to the gradient drive unit  130 , the RF drive unit  140  and the data acquisition unit  150 . The control unit  160  controls the respective gradient drive unit  130  through data acquisition unit  150  and performs imaging. 
     A data processing unit  170  is connected to the output side of the data acquisition unit  150 . The data processing unit  170  is for instance comprised by such as a computer. The data processing unit  170  has a memory not shown in the drawing. The memory stored all types of data and programs for the data processing unit  170 . The functions of this apparatus are achieved by running the programs stored in the memory of the data processing unit  170 . 
     The data processing unit  170  stores data input from the data acquisition unit  150  into the memory. The memory is internally has data spaces. The data spaces are comprised of two-dimensional Fourier spaces. The data processing unit  170  performs two-dimensional inverse Fourier conversion of these two-dimensional Fourier spatial data and generates (reconstructs) an image of the imaging object  300 . The two-dimensional Fourier space is called a k-space. 
     The data processing unit  170  is connected to the control unit  160 . The data processing unit  170  coordinates the processing in the control unit  160 . A display unit  180  and an operating unit  190  are also connected to the data processing unit  170 . The display unit  180  is comprised of such as a graphic display. The operating unit  190  is comprised of a keyboard including a pointing device. 
     The display unit  180  displays the reconstructed image output from the data processing unit  170  and information of various types. The operating unit  190  inputs commands and information of various types to the data processing unit  170  by user operation. The user operates the apparatus interactively by way of the display unit  180  and the operating unit  190 . 
     The structure of the RF coil unit  108  is shown in FIG.  7 . The RF coil unit  108  as shown in the figure, is a TEM resonator RF coil having a structure in common with that shown in FIG.  7 . 
     The RF coil unit  108  described once again, has a cylindrical tube  110 . The tube  110  has the orifices  112 ,  112 ′ on both ends. The orifices  112 ,  112 ′ have openings  114 ,  114 ′ concentrically formed with a smaller diameter than the diameter of the tube  110 . 
     The tube  110  and the orifices  112 ,  112 ′ are comprised of insulator elements such as plastics covered with conductive foil in a plurality of equivalent portions by means of the axial and radial slits  116 . The coding of the slit is shown in one location. The tube bodies holding such a tube  110  and the orifices  112 ,  112 ′ comprise a shield or a cavity. This shield is an example of the embodiment of the shield of the invention. The slit  116  is one example of the embodiment of the slit of this invention. 
     A plurality of line elements  118  are formed in parallel with the axis on the inner side of the shield. The coding onto the line element is shown in one location. The line element  118  is one example of the embodiment of the line element of the invention. 
     The line element  118  is formed of a bar shaped conductor having capacitors (not shown in drawing) in the center in series, and along with the shield forms a closed loop LC circuit. The supply and receiving of the RF signal is performed at both ends of the capacitors of a specified line element  118 . 
     The plural line elements  118  are respectively electrically and mechanically connected at both ends to the orifices  112 ,  112 ′, and arranged at equal intervals concentrically along the periphery of the openings  114 ,  114 ′. The coupling position of the line elements  118  on the orifices  112 ,  112 ′ is in the center of the ring segments formed on the orifices  112 ,  112 ′ divided by the slits  116 . The line elements  118  are maintained a specified distance from the inner surface of the tube  110 . 
     The RF coil unit  108  is for example divided into eight equal parts by the slits  116 . One of these equally divided units is hereafter referred to as a segment. The cylinder segments are comprised of eight of these equivalent segments. 
     The structures described above are all common to the RF coil shown in FIG.  2 . In the RF coil  108 , the eight ring segments formed at the orifices  112 ,  112  on both sides of the shield share a common conductor pattern and circuit components disposed on that pattern. 
     A front view of one ring segment and a portion of the adjoining ring segments are shown in FIG.  8 . The conductor pattern for the ring segment, as shown in FIG. 8 has a main land  302  connected to the edges of the line element  118 , and two sub lands  304  formed symmetrically on the both left and right sides of the main land  302 . The main land  302  and the sub land  304  are separated by the slits  402 . 
     The main land  302  is an example of an embodiment the first conductor pattern of the invention. The sub lands  304  are an example of an embodiment of the second conductor pattern of the invention. 
     The mainland  302  and the sub lands  304  are connected by a capacitor  502 . The capacitor  502  is an example of the embodiment of the capacitor of the invention. A mica condenser having a sufficiently high impedance for example, in the 1 kilohertz to 10 kilohertz frequency range, and for example a sufficiently low impedance for example in the 128 megahertz frequency range, and having a capacitance for instance, of 1000 picofarads may be used as the capacitor  502 . 
     The sub lands  304  separated from the sub land of the adjoining ring segments by the slit  116  are connected by a conductor  602  with the sub lands of the adjoining ring segments. Copper foil or a copper mesh sheet for example, may be used as the conductor  602 . 
     The main land  302  and the sub lands  304  connected by the capacitor  502  are effectively an electrical short across the slit  402  in the high frequency range. The shorting of the slit  116  between the adjacent lands by the conductor  602 , applies an equivalent value in the RF range to the plural line elements  118  connected at both ends to the orifices  112 ,  112 ′. The shield effect is therefore improved in the RF range, and operation is stabilized regardless of whether a load is present or not in the vicinity of the orifice  112 ,  112 ′. 
     The capacitor  502  on the other hand, has a sufficiently high impedance in the 1 kilohertz to 10 kilohertz range so that there is no flow of excess current on the outer periphery of the shield during application of the gradient magnetic field constituting the signal in that same frequency range. The effect that excess current exerts on a magnetic field can therefore be prevented. 
     The conductive pattern and the components may be arranged in the ring segments as shown for example in FIG.  9 . The main land  302  is divided into two segments by the slit  404  as shown in FIG. 9, forming the land  302 ′ connecting to the edge of the line element  118 , and the land  302 ″ connecting to tube  110  of the shield, and the lands  302 ′,  302 ″ are connected by the capacitor  504 . The capacitor  504  constitutes a portion of the LC circuit of the RF coil unit  108 . 
     The bisymmetrical conductive pattern of the ring segments as shown in FIG.  8  and FIG. 9 are identical in all the ring segments. All of the segments therefore have identical circuit conditions, and circuit uniformity can therefore be maintained in all segments involving the center axis of the RF coil  108 . The operating characteristics of the RF coil are therefore improved. 
     In the head coil type RF coil  108 , has a structure separable into two portions along the axis and so is easily inserted on the head section of the imaging object  300  as shown in FIG.  10  and uniformity of the segment circuits can also be maintained even when both segments are joined by connectors. 
     The RF coil unit  108  has a structure which can be disassembled in segment  119  units as shown in FIG.  11  and is preferable in the point that alignment to the same frequency can be easily performed in the manufacturing stage. A vertical cross sectional view of the segment  119  is shown in FIG.  12 . The conductor pattern  112  of the orifices  112  on the segment  119  is not limited to the example shown in FIG. 8 or FIG.  9  and may overall comprise the single pattern as shown in FIG.  13 . 
     When aligning such kind of segments  119  to the same frequency, a frequency alignment jig shown in FIG. 14 is utilized. The frequency alignment jig  103  shown in this figure forms a cylindrical shape. 
     The frequency alignment jig  103  is equivalent to an RF coil unit  108  as shown in FIG. 7 with one segment removed and also a shield with all line elements in other segments removed. However, the point with the segment removed is non-metallic and a non-magnetic concentric tube. 
     The frequency alignment jig  103  therefore has an orifice  132  comprised of ring segments with one cutout segment portion, and also has a slit  136 . The cutout portion of the orifice  132  forms a fit portion  105  attached to the segment  119  during frequency alignment. The fit portion  105  has a shape and dimensions allowing fitting of the tube  110 . The frequency alignment jig  103  is an example of an embodiment of the shield of the invention. The example of the embodiment relating to the shield of the invention is shown by means of the frequency alignment jig  103  structure. 
     For alignment to the same frequency, the segment  119  is fitted into the fit portion  105  of this frequency alignment jig  103  with a non-metallic and non-magnetic clamp, connected to the specified measuring equipment and the LC value of the circuit aligned. This alignment is mainly performed by adjusting the capacitance of the capacitor in serial with the line element  118 . 
     The frequency alignment jig  103  can also be used in other applications to test if individual segments are defective or not to check for operating defects in the RF coil  108 . The defect points can in this way easily be found. The defective segment can therefore then be repaired or replaced. 
     The RF coil unit  108  is assembled using all the segments  119  after alignment to the same frequency is complete. A cylindrical support frame  113  as shown in FIG. 10 is used in the assembly. The support frame  113  is an example of the embodiment of the support means of the invention. 
     Each segment is installed by means of the appropriate clamping jig on the inner side of the support frame  113  comprising the cylinder. The support frame  113  and the clamping jig are for example comprised of a non-metallic and non-magnetic material such as plastics. The fact that the support frame  113  can be divided into two portions along the axis is preferable for making the inserting and removing of the imaging object  300  on the completed RF coil easy to perform. 
     The imaging operation of this apparatus is now described. An example of the pulse sequence when imaging with this apparatus is shown in FIG.  16 . This pulse sequence is the gradient echo method (GRE). 
     In other words, in the figure, (1) is the RF excitation α° pulse sequence in the GRE method. Also, (2), (3) and (4) are respectively, the slice gradient Gs, the readout gradient Gr, the phase encode gradient Gp and the gradient echo MR sequences. The α° pulse represents the center signal. The pulse sequence proceeds from left to right along the time axis t. 
     The spin α° excitation by the α° pulse is therefore performed as shown in FIG.  16 . The flip angle α°°is not more than 90 degrees. The excitation selected for the specified slice applied with the slice gradient Gs is performed at this time. 
     After α° excitation, spin phase decoding is performed by the phase encode gradient Gp. Next, the spin is first dephased by the readout gradient Gr, the spin then rephased, and a gradient echo MR generated. The gradient echo MR signal intensity is a maximum at the time point after echo time TE from the α° excitation. The gradient echo MR is collected as view data by the data acquisition unit  150 . 
     A pulse sequence of this kind is repeated 64 to 512 times at the period TR (repetition time). The phase encode gradient GP is changed each time the pulse sequence is repeated, and different phase encoding performed each time. View data for views 64 to 512 filling the k space are obtained in this way. 
     An example of another pulse sequence for magnetic resonance imaging is shown in FIG.  17 . This pulse sequence is an SE pulse sequence produced by the spin echo method. 
     In other words, (1) is an RF excitation 90 degree pulse and 180 degree pulse sequence by the SE method. In the same way, (2), (3), and (4) are respectively the slice gradient Gs, the readout gradient Gr, the phase encode gradient Gp and the spin echo MR sequences. The 90 degree pulse and 180 degree pulse respectively represent the center signals. The pulse sequence proceeds from left to right along the time axis t. 
     The 90 degree spin excitation is performed by the 90 degree pulse as shown in the same figure. The excitation selected for the specified slice applied with the slice gradient Gs is performed at this time. After 90 degree excitation at the specified time, 180 degree excitation by the 180 degree pulse or in other words, an inverted spin is performed. The slice gradient Gs is also applied at this time, and selective inversion of the same slice is performed. 
     The readout gradient Gr and the phase encode gradient Gp are applied in the period of 90 degree excitation and spin inversion. Spin dephasing is performed by the readout gradient Gr. Spin phase encoding is performed by the phase encode gradient Gp. 
     After spin inversion, the spin is rephased by the readout gradient Gr, and the spin echo MR generated. The spin echo MR signal intensity is a maximum at the time point after time TE from the 90 degree excitation. The spin echo MR is collected as view data by the data acquisition unit  150 . 
     A pulse sequence of this kind is repeated 64 to 512 times at the period TR (repetition time). The phase encode gradient GP is changed each time the pulse sequence is repeated, and different phase encoding performed each time. View data for views 64 to 512 filling the k space are obtained in this way. 
     The pulse sequence utilizing in the imaging is not limited to the GRE method or the SE method and other methods such as FSE (Fast Spin Echo), fast recovery FSE (Fast Recovery Fast Spin Echo), and EPI (Echo Planar Imaging) may also be utilized as needed. 
     The data processing unit  170  performs two-dimensional inverse Fourier transforming of the view data of the k space and reconstructs a stepped image of the imaging object  300 . The reconstructed image is stored in the memory or displayed on the display unit  180 . The operating characteristics of the RF coil  108  are excellent so an image of high quality can be obtained. 
     In the above examples, the RF coil  108  was used for both sending and receiving, needless to say however, the RF signal of the RF coil  108  may also be exclusively for sending or exclusively for receiving. 
     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 claim.