Abstract:
A system whereby a magnetic tip attached to a surgical tool is detected, displayed and influenced positionally so as to allow diagnostic and therapeutic procedures to be performed rapidly, accurately, simply, and intuitively is described. The tools that can be so equipped include catheters, guidewires, and secondary tools such as lasers and balloons, in addition biopsy needles, endoscopy probes, and similar devices. The magnetic tip allows the position and orientation of the tip to be determined without the use of x-rays by analyzing a magnetic field. The magnetic tip further allows the tool tip to be pulled, pushed, turned, and forcefully held in the desired position by applying an appropriate magnetic field external to the patient&#39;s body. A Virtual Tip serves as an operator control. Movement of the operator control produces corresponding movement of the magnetic tip inside the patient&#39;s body. Additionally, the control provides tactile feedback to the operator&#39;s hand in the appropriate axis or axes if the magnetic tip encounters an obstacle. The output of the control combined with the magnetic tip position and orientation feedback allows a servo system to control the external magnetic field by pulse width modulating the positioning electromagnet. Data concerning the dynamic position of a moving body part such as a beating heart offsets the servo systems response in such a way that the magnetic tip, and hence the secondary tool is caused to move in unison with the moving body part. The tip position and orientation information and the dynamic body part position information are also utilized to provide a display that allows three dimensional viewing of the magnetic tip position and orientation relative to the body part.

Description:
REFERENCE TO RELATED APPLICATIONS  
       [0001]     The present application is a divisional of U.S. application Ser. No. 10/621,196 titled APPARATUS AND METHOD FOR A CATHETER GUIDANCE CONTROL AND IMAGING, which was filed Jul. 15, 2003 which claims priority from U.S. Provisional Patent Application No. 60/396,302, filed Jul. 16, 2002, titled “CATHETER GUIDANCE CONTROL AND IMAGING APPARATUS AND METHOD,” the entire contents of which is hereby incorporated by reference. 
     
    
     BACKGROUND  
       [0002]     1. Field of the Invention  
         [0003]     The present invention relates to systems and techniques for guiding, steering, and advancing invasive medical devices such as catheters and catheter-type devices.  
         [0004]     2. Description of the Related Art  
         [0005]     In general, catheterization is performed by inserting an invasive device into an incision or a body orifice. Secondary tools such as guidewires and balloons are often advanced along the primary catheter to the area where the medical procedure is to be performed. These procedures rely on manually advancing the distal end of the invasive device by pushing, rotating, or otherwise manipulating the proximal end that remains outside of the body. Real-time x-ray imaging is a common method for determining the position of the distal end of the invasive device during the procedure. The manipulation continues until the distal end reaches the destination area where the diagnostic or therapeutic procedure is to be performed. This technique requires great skills on the part of the operator that can only be achieved after a protracted training period and extended practice. A high degree of manual dexterity is also required.  
         [0006]     For example, angioplasty involves advancing a balloon catheter over a previously placed guidewire into a narrowed arterial section. Once properly positioned in the narrowed arterial section, the balloon is inflated and dilates this section: The time consuming technical difficulties encountered during angioplasty procedure are similar to those associated with angiography. If the artery to be treated is torturous with sharp bends, it may be difficult to advance the guidewire to the stenosis. If the stenosis is severe or the artery is totally blocked, it may be difficult or even impossible to properly position the guidewire. Alternatively, if the guidewire is successfully positioned in tight, hard plaque, the balloon catheter, being of a necessarily larger diameter than the guidewire, may encounter sufficient resistance to cause the guiding catheter to disengage from the ostium. This eliminates the support required to facilitate balloon advancement. These technical difficulties can render the procedure unfeasible.  
         [0007]     Because of the difficulty involved in advancing a catheter into a desired location in the body, many diagnostic and therapeutic procedures employ a guidewire. The guidewire is first advanced into the heart or the artery and serves as a track and guide for a specific catheter. This technique is used to advance a catheter into the left ventricle and is especially important when studying aortic stenosis. Crossing the narrowed valve orifice is a challenge to the operator. Similarly, a guidewire is often manipulated into a blocked coronary artery and across the obstructive plaque. A therapeutic catheter, for example carrying a balloon, a laser, a stent, etc., is advanced over the guidewire, and placed at the site of the plaque. The narrowed site is then opened by inflating a balloon, operating a laser beam, or placing a stent. On occasions, the artery is torturous and severely narrowed and the plaque is irregular, calcified, or even totally occluding the artery. In these situations the placement of a guidewire beyond the narrowed site is very difficult and many times unsuccessful.  
         [0008]     In some procedures, a catheter is used to cut through the intra-atrial septum in order to create a shunt (in transposition of the great vessels), to treat the mitral valve (mitral valvuloplasty), or to monitor directly the pressure in the left atrium.  
         [0009]     The implantation of cardiac pacemakers is often essential for the survival of patients with heart rhythm or electrical conduction disturbances. This procedure is performed by the implantation of a small electrode in the heart cavity wall (ventricle or atrium). The other end of the electrode is attached to an electronic device which is implanted under the chest skin and that generates stimulation pulses to simulate the heart rhythm. Similar devices apply electrical shock when life-threatening heart electrical disturbances are detected by the electrodes (e.g., an Automatic Implantable Cardiac Defibrillator (AICD)). These electrodes are placed through a vein by pushing and manipulating under x-ray. Many times, the manipulation to place the electrodes in a proper position is difficult and the results are sub-optimal due to anatomical variations.  
         [0010]     During electrophysiological study, electrical signals occurring in the myocardium (heart muscle) are measured and recorded. This is accomplished by advancing an electrode-carrying catheter into the heart. The catheter is manipulated until the electrode touches the endocardial region of interest. This can be a cumbersome and time-consuming procedure because multiple measurements are often required to perform a complete study. In addition, accurately positioning the electrode using manual manipulation is a difficult process.  
         [0011]     Ablation of electrical pathways to eliminate heart rhythm disturbances eliminates potentially life threatening abnormal heart rhythms by ablating erroneous electrical pathways in the myocardium, that have been previously identified during an electrophysiological study. Ablation of these pathways using thermal or microwave energy delivered to a predetermined specific region by an energy-carrying catheter is the mainstay of the procedure. This catheter is placed in good contact with the selected endiocardial region, otherwise no ablation will occur. Additionally, the catheter must be precisely positioned in order to avoid damaging the normal electrical pathways. Given these exacting requirements, the imprecise nature of manual manipulation can cause this procedure to be especially difficult and time consuming.  
         [0012]     Mitral valvuloplasty is used to treate mitral valve stenosis by dilating the narrowed valve with a balloon. The current method involves advancing a catheter through the vena cava into the right atrium. An incision is made in the intra-atrial septum and the catheter is forced through the cut into the left atrium. A balloon is then advanced through the catheter into the mitral valve apparatus, and inflated to break the stenotic tissue. Notwithstanding a high success rate and a low risk of recurrent restenosis associated with this procedure, a known complication is an atrial septal defect induced by the puncture of the intra-atrial septum. Although much less aggressive than surgery, this procedure is lengthy, difficult, and requires special skills in addition to those normally requisite for catheterization.  
         [0013]     Mitral valvuloplasty (aorta to left atrium method) is considered by some to be a preferred alternative to the vena cava approach because the intra-artrial septum puncture is eliminated, thereby eliminating the potential complication of atrial septal defect. This procedure differs from the current method of mitral valvuloplasty in that the catheter is advanced through the aorta, the left atrium, and the aortic valve, for positioning into the left ventricle. A balloon is then advanced through the catheter into the mitral valve apparatus and inflated to break the stenotic tissue. Because a relatively rigid balloon is required to break the tissue narrowing the mitral valve, it is almost impossible to bring the balloon into proper alignment via the aorta and left ventricle due to the sharp acute angle between the aortic route and the required approach to the mitral valve.  
         [0014]     Myocardial revascularization is a therapeutic procedure that increases the blood supply to the heart muscle by inducing the formation of new small blood vessels in the myocardium. The surgery involves opening the chest wall and laser “drilling” multiple small channels from the heart external aspect (epicardium).  
         [0015]     Percutaneous myocardial revascularization is a catheter-based procedure for promoting angioneogensis. It involves advancing a laser catheter into the heart and performing the channelling from the heart inner aspect (endocardium). This approach is particularly applicable to patients who constitute a high surgical risk and who are beyond conventional catheter based therapy. Due to the accuracy required when positioning and fixating the laser catheter, this procedure does not appear to be implementable with currently available catheter technology.  
         [0016]     The foregoing procedures suffer from numerous disadvantages and limitations. A very high skill level is often required to properly manipulate the catheter into position. Extensive training is required to attain this skill level. Many of the procedures are tedious and time-consuming. This results in repeated and prolonged exposure of the patient and staff to the adverse effects of x-rays. The lengthy procedures also require the use of additional contrast material with associated risk to the patient. Procedures that require highly-accurate positioning of the catheter distal end (also referred to as the catheter tip) are difficult to perform and are not always feasible. The insertion, removal, and manipulation of secondary tools often causes the tip of the guiding catheter to be dislodged from the desired position. Time-consuming manipulation is required to correctly reposition the tip. The coronary arteries are sometimes torturous with sharp bends or blockages that make advancement of a guidewire or balloon difficult or even impossible. A principal source of catheter tip location information is the x-ray imaging system with its associated adverse side effects.  
         [0017]     Therefore, there is a great and still unsatisfied need for an apparatus and method for guiding, steering, and advancing invasive devices and for accurately controlling their position; for providing three dimensional imaging; and for minimizing the use of x-rays or other ionizing-type radiation  
       SUMMARY  
       [0018]     The present invention solves these and other problems by providing a magnetic catheter guidance and control apparatus that requires less training and less skill that prior art systems. The magnetic catheter guidance system can rapidly advance and position the catheter, thus minimizing x-ray and contrast material exposure. Moreover, the magnetic system used in the magnetic catheter guidance system can be used to locate the catheter tip to provide location feedback to the operator and the control system.  
         [0019]     One embodiment includes a catheter and a guidance and control apparatus that can accurately, and with relative ease, allow the surgeon/operator to position the catheter tip inside a patient&#39;s body. The catheter guidance and control apparatus can maintain the catheter tip in the correct position. One embodiment, includes a catheter with guidance and control apparatus that can steer a guidewire or balloon through arteries and forcefully advance it through plaque or other obstructions. One embodiment includes a catheter guidance and control apparatus that displays the catheter tip location with significantly reduced x-ray exposure to the patient and staff. One embodiment includes a catheter guidance and control apparatus that is more intuitive and simpler to use, that displays the catheter tip location in three dimensions, that applies force at the catheter tip to pull, push, turn, or hold the tip as desired, and that is capable of producing a vibratory or pulsating motion of the tip with adjustable frequency and amplitude to aid in advancing the tip through plaque or other obstructions. One embodiment provides tactile feedback at the operator control to indicate an obstruction encountered by the tip.  
         [0020]     In one embodiment, a catheter Guidance Control and Imaging (GCI) apparatus allows a surgeon to advance, accurately position and fixate a catheter, and to view the catheters&#39; position in three dimensions with the x-ray imagery overlaying the display. In one embodiment, the apparatus includes an operator control called a “Virtual Tip” which, in addition to being a model representation of the actual or physical catheter tip advancing within the patient&#39;s body, possesses a positional relationship to the catheter tip.  
         [0021]     The Virtual Tip includes a physical assembly, somewhat akin to a joystick, that can be manipulated by the surgeon and is also designed to deliver tactile feedback to the surgeon in the appropriate axis or axes if the actual tip encounters an obstacle. In other words, the Virtual Tip includes a joystick-type device that allows the surgeon to guide the actual catheter tip though the patient&#39;s body. Then the actual catheter tip encounters an obstacle, the Virtual Tip provides tactile force feedback to the surgeon to indicate the presence of the obstacle.  
         [0022]     In one embodiment, the physical catheter tip (the distal end of the catheter) includes a permanent magnet that responds to a magnetic field generated externally to the patient&#39;s body. The external magnetic field pulls, pushes, turns, and holds the tip in the desired position. One of ordinary skill in the art will recognize that the permanent magnet can be replaced or augmented by an electromagnet.  
         [0023]     The operator control provides the position and orientation command inputs to a servo system that controls the catheter tip position by regulating the magnetic force applied outside the patient&#39;s body. A measurement of the actual tip position and orientation is made via sensory apparatus that includes magnetic field sensors and temperature sensors. This measurement serves as a feedback to the servo system and the operator interface. In one embodiment, the servo system has a correction input that compensates for the dynamic position of a body part or organ, such as the heart, thereby offsetting the response such that the actual tip moves in unison with the beating heart.  
         [0024]     The operation of the catheter guidance system is as follows: i) the operator adjusts the physical position of the virtual catheter tip, ii) a change in the virtual tip position is encoded producing input data received at a control system, iii) the control system generates commands sent to servo system control apparatus, iv) the servo system control apparatus operates the servo mechanisms to adjust the electromagnetic field of external magnets, which v) causes the position of the actual magnetic catheter tip within the patient&#39;s body to change, vi) the new position of the actual catheter tip is then sensed by magnetic field sensors and temperature sensor arrays, which vii) provide feedback to the servo system control apparatus and the monitoring system of the operator interface thereby updating the displayed image of the actual catheter tip position in relation to the overlaid patient x-ray image.  
         [0025]     The operator can then make further adjustments to the virtual catheter tip position and the sequence of steps ii through vii are repeated in a way that is smooth and continuous to the user. In addition, throughout this procedure, feedback from the servo system control apparatus creates command logic when the actual catheter tip encounters an obstacle or resistance in its path. The command logic is used to control stepper motors physically coupled to the virtual catheter tip. The stepper motors are engaged to create resistance in the appropriate direction(s) that can be felt by the operator, and tactile feedback is thus provided to the surgeon. 
     
    
     BRIEF DESCRIPTION OF THE DRAWINGS  
       [0026]     The various features of the present invention and the manner of attaining them will be described in greater detail with reference to the following description, claims, and drawings, wherein reference numerals are reused, where appropriate, to indicate a correspondence between the referenced items.  
         [0027]      FIG. 1A  is a high-level system block diagram for a surgery system that includes an operator interface, a catheter guidance system, surgical equipment (e.g., a catheter to be guided), and a patient.  
         [0028]      FIG. 1B  is a block diagram of one embodiment of the catheter guidance system from  FIG. 1A .  
         [0029]      FIG. 1C  is a block diagram of the catheter guidance system of  FIG. 1B  showing additional details not shown in  FIG. 1B .  
         [0030]      FIG. 2  is a schematic diagram of a ground fault interrupter, an uninterruptable power supply, DC supplies, and a supervisory unit for use in the apparatus of  FIG. 1B .  
         [0031]      FIG. 3  is a schematic diagram of a system controller for use in the apparatus of  FIG. 1B .  
         [0032]      FIG. 4  is a schematic diagram of a virtual tip and calibration fixture controller for use in the apparatus of  FIG. 1B .  
         [0033]      FIG. 5  is an electrical block diagram of a virtual tip for use in the apparatus of  FIG. 1B .  
         [0034]      FIG. 6  is a perspective view of the Virtual Tip device in connection with the electrical block diagram of  FIG. 5 .  
         [0035]      FIG. 7  is a schematic diagram of an X axis controller and amplifier for use in the apparatus of  FIG. 1B .  
         [0036]      FIG. 8  is a schematic diagram of a Y axis controller and amplifier for use in the apparatus of  FIG. 1B .  
         [0037]      FIG. 9  is a schematic diagram of a Z axis controller and amplifier for use in the apparatus of  FIG. 1B .  
         [0038]      FIG. 10  is a schematic diagram of a communication controller for use in the apparatus of  FIG. 1B .  
         [0039]      FIG. 11  is a schematic diagram of a calibration fixture for use in the apparatus of  FIG. 1B .  
         [0040]      FIG. 12  is a perspective view of the calibration fixture (mechanical) of  FIG. 11 .  
         [0041]      FIG. 13  is an orthographic representation view illustrating a polar configuration of the electromagnets with their corresponding magnetic field sensors.  
         [0042]      FIG. 13A  is a possible polar configuration as a cluster of electromagnets forming the magnetic circuit with a C-Arm.  
         [0043]      FIG. 13B  is a representation of the geometrical layout of the coils, the arm and the table.  
         [0044]      FIG. 13C  is a block diagram representing the electronics scheme of clustered electromagnetic coils  
         [0045]      FIG. 13D  is a matrix representation of a vector  
         [0046]      FIG. 13E  is a representation of the characteristic matrix  
         [0047]      FIG. 13F  is a representation of the Inverse characteristic matrix  
         [0048]      FIG. 13G  is a representation of the product of the characteristic matrix with its Inverse matrix  
         [0049]      FIG. 13H  is a logical flow diagram of  FIG. 13G   
         [0050]      FIG. 14  illustrates various magnetic field sensors and temperature sensor pairs for use in the apparatus of  FIG. 1B .  
         [0051]      FIG. 15  and  15 A are fragmentary, perspective views of a catheter assembly and a guidewire assembly for use in the apparatus of  FIG. 1B .  
         [0052]      FIG. 15B  a representation of a catheter fitted with a magnetic tip and two piezoelectric rings.  
         [0053]      FIG. 16  illustrates a bi-plane X-ray ring incorporating the apparatus of  FIG. 1B .  
         [0054]      FIG. 16A  illustrates a top view of the apparatus of  FIG. 1B .  
         [0055]      FIG. 16B  illustrates an end view of the apparatus of  FIG. 1B .  
         [0056]      FIG. 16C  illustrates a side view of the apparatus of  FIG. 1B .  
         [0057]      FIG. 17  illustrates the use of the apparatus of  FIG. 1B  with cineangiographic equipment.  
         [0058]      FIG. 17A  illustrates the use of fiduciary markers synchronizing the fluoroscopy image.  
         [0059]      FIG. 17B  illustrates the use of fiduciary markers in performing a pacemaker electrode implementation.  
         [0060]      FIG. 18  is a vectorial representation of the magnitude and direction of the resultant force vector applied by the electromagnets of  FIG. 13 .  
         [0061]      FIG. 18A  illustrates the polarity of the magnetic tip of the catheter in relation to the virtual origin of the coordinate system.  
         [0062]      FIG. 18B  illustrates the resultant vector as detected by the magnetic field sensors of  FIGS. 20 and 20 A.  
         [0063]      FIG. 18C  illustrates the angle of the resultant vector of  FIG. 18B  in three dimensions.  
         [0064]      FIG. 19  illustrates the distance between two opposing electromagnets for use in the apparatus of  FIG. 1B .  
         [0065]      FIG. 19A  illustrates the distance between adjacent magnetic field sensors of  FIG. 19 .  
         [0066]      FIG. 20  is a representation of the process of deducing the location of the tip of  FIG. 18A  by the magnetic field sensors of  FIG. 19A .  
         [0067]      FIG. 20A  illustrates the result of further calculations of the signals from the magnetic field sensors of  FIG. 19A .  
         [0068]      FIG. 21  is a representation of the rotation of the magnetic tip of  FIG. 18A  in the Z axis (θ) direction.  
         [0069]      FIG. 22  is a representation of the translation of the magnetic tip of  FIG. 18A  in the Z axis (ΔZ) direction.  
         [0070]      FIG. 23  is a logical flow diagram of a controller forming part of the apparatus of  FIG. 1B , for determining the position of the actual tip of  FIG. 18A  in response to a new move command. 
     
    
     DETAILED DESCRIPTION  
       [0071]      FIGS. 1A, 1B  and  1 C show a system  700  that includes a guidance, control, and imaging (GCI) apparatus  501 . The system  700  further includes an operator interface equipment  500  and a surgical medical equipment  502 .  FIG. 1A  illustrates an embodiment of the GCI apparatus  501  that includes various functional units.  FIG. 1A  further illustrates the overall relationship between these functional units and the operator interface  500 , the auxiliary equipment  502  residing in the operating room, and the patient  390 .  FIG. 1B  provides further details of the inter-relationships of these functional units and some of their components.  
         [0072]      FIG. 1C  shows the inter-relation between the GCI apparatus  501 , surgical medical equipment  502 , operator interface equipment  500 , and a reference patient  390 . A more detailed description of the GCI apparatus  501  and other auxiliary equipment, such as the surgical medical equipment  502 , in the operating room will be described later in greater detail in connection with  FIGS. 16, 16A ,  16 B and  16 C. The system  700  is configured to guide a catheter or similar device having a distal end (also referred to herein as a tip) that enters the body.  
         [0073]      FIG. 2  is a block diagram that illustrates a first functional unit of GCI apparatus  501 , namely a power supply and control unit that includes a ground fault interrupter  1 , an uninterruptable power supply  300 , DC supplies  16 ,  17 ,  18 , and  19 , and a supervisory unit  301  for use in the system  700  of  FIG. 1B .  
         [0074]     Another functional unit of the GCI apparatus  501  is a system controller (SC)  302  which is illustrated in  FIG. 3 . Yet another functional unit of the GCI apparatus  501  is a virtual tip and calibration fixture controller (VT/CFC)  303  which is illustrated in  FIG. 4 . Still another functional unit of the GCI apparatus  501  is a virtual tip assembly (VT)  304  which is illustrated in  FIGS. 5 and 6 . Additional functional units of the GCI apparatus  501  include an X-Axis controller and amplifier (XCA)  305 , a Y-Axis controller and amplifier (YCA)  310 , and a Z-Axis controller and amplifier (ZCA)  315 . These functional units are each individually detailed by functional block diagrams in  FIGS. 7, 8 , and  9 , respectively. Still other functional units of the GCI apparatus  501  include a communication controller (CC)  320  which is depicted in detail in  FIG. 10 ; a calibration fixture (CF)  321  which is depicted in detail in  FIGS. 11 and 12 ; and magnetic field sensor (MFS) and temperature sensor (TS) pairs  374  that are illustrated in  FIG. 14 . The various magnetic field sensors and temperature sensor pairs  374  are used in the system  700  of  FIG. 1B . The magnetic field sensor or sensors can be Hall-effect sensors, superconducting sensors, or other sensors that sense a magnetic field such as, for example, the magnetic field produced by a magnet (or electromagnet) at the distal end of the catheter. In one embodiment, the magnetic field sensors are Hall-effect sensors. The temperature sensors can be thermistors or other temperature-sensing devices. The temperature sensors are described herein because many magnetic field sensing devices, such as, for example, Hall-effect sensors are temperature-dependent. However, the temperature sensors are optional and can be omitted when the additional accuracy afforded by the temperature sensors is not needed or when knowledge of the temperature of the magnetic sensors is not needed.  
         [0075]     Referring to  FIG. 1B , the power supply and control system  392  includes: a Ground Fault Interrupter (GFI)  1 ; an uninterruptable power supply (UPS)  300 ; a supervisory unit (SU)  301 ; individual DC power supplies XPS  16 , YPS  17 , and ZPS  18  that provide power to the X Axis Controller And Amplifier (XCA)  305 , the Y-axis Controller And Amplifier (YCA)  310 , and the Z-axis Controller And Amplifier (ZCA)  315 , respectively; and a DC system power supply (SPS)  19  that provides the DC power needed to operate other digital and analog circuitry of the GCI apparatus  501 . These components and their functional relationships are depicted in greater detail in  FIG. 2 .  
         [0076]     Referring now to  FIG. 2 , the Ground Fault Interrupter (GFI)  1  acts as a safety device by monitoring the AC input current in the line and the neutral. If an imbalance is detected, it is assumed that a stray path to ground is present (posing a shock hazard to the user or the patient). This detection will cause a trip that disconnects the load from the line.  100751  The uninterruptable power supply (UPS)  300  contains batteries  9 , a charging system  5 , an inverter  13 , and power switching circuitry. The UPS  300  automatically supplies the entire AC power requirements of the system  700  for the duration of a power failure, or until battery depletion occurs. A graceful system shutdown is initiated by a Supervisory Unit (SU)  301  and a system controller (SC)  302  if the power failure extends beyond battery capacity.  
         [0077]     Still referring to  FIG. 2 , an amplifier  3  and its current transformer monitor the AC line current. An isolation amplifier  4  monitors the AC voltage output of Ground Fault Interrupter (GFI)  1 . Charger  5  produces the desired DC power to charge battery  9  of the uninterruptable power supply  300 . An amplifier  8  monitors the voltage drop across shunt  7  to determine the charge current of the battery  9 . An amplifier  10  monitors the output voltage of the battery  9 . An amplifier  12  monitors the voltage drop across shunt  11  to determine load current of the battery  9 . An inverter  13  generates the AC power used by components of the GCI apparatus  501 . An isolation amplifier  14  monitors the AC output voltage of inverter  13 . An amplifier  15  and its current transformer monitor the current output of inverter  13 .  
         [0078]     A Supervisory Unit (SU)  301  monitors the signals from the following components: the AC line; and the outputs of the Ground Fault Interrupter (GFI)  1 , the uninterruptable power supply (UPS)  300 ; and the DC power supplies  16 ,  17 ,  18 , and  19 . The Supervisory Unit (SU)  301  informs the System Controller (SC)  302  of an AC power failure, a Ground Fault Interrupter (GFI) trip, an Uninterruptable Power Supply (UPS) failure or failure of the DC power supplies  16 ,  17 ,  18 , and  19 .  
         [0079]     As detailed in  FIG. 2 , the SU  301  includes an analog multiplexer  20  that connects a given signal to be monitored to a programmable gain amplifier  21 . A decode logic  26  in conjunction with an address latch  24  allow a microcontroller  30  to set the input channel of the analog multiplexer  20 . A microcontroller  30  executes a code resident in read only memory  28 . The decode logic  26  in conjunction with address latch  25  allow microcontroller  30  to set the gain of programmable gain amplifier  21 . Microcontroller  30  then strobes sample and hold circuit  22  via decode logic  26 . The output of sample and hold circuit  22  is thus a “snapshot” of the signal to be measured.  
         [0080]     Analog to digital converter  23  is issued a convert command by microcontroller  30  via decode logic  26 . When conversion is complete, analog to digital converter  23  interrupts microcontroller  30  via decode logic  26  and the digital representation of the measured signal is input by microcontroller  30 . A random access memory  29  is used to store sampled data during operation of the SU  301 . A non-volatile memory  27  stores data during power down. It is by this method that the various voltages and currents are monitored by supervisory unit  301 . Microcontroller  30  communicates with system controller  302  via buffer  31 . Control logic  32  allows system controller  302  to coordinate the power up-power down sequence in accordance with system conditions.  
         [0081]     With reference to  FIGS. 1B and 3 , System Controller (SC)  302  controls the power up-power down sequence in an orderly fashion and alerts the operator to the system status and any required corrective action via Communications Controller (CC)  320 , Computer  324 , and monitor  325 . In addition, System Controller (SC)  302  coordinates the operation of X Axis Controller and Amplifier (XCA)  305 , Y-Axis Controller and Amplifier (YCA)  310 , and Z Axis Controller and Amplifier (ZCA)  315 . Additionally, System Controller (SC)  302  communicates with Virtual Tip/Calibration Fixture Controller (VT/CFC)  321  and Communication Controller (CC)  320  via system bus  328 .  
         [0082]     As illustrated in  FIG. 1B , Servo Power Supply (XPS)  16  provides DC power to the X-Axis Controller and Amplifier (XCA)  305 . The XCA  305  energizes the electromagnets  132 X and  138 X that are located outside the patient&#39;s body. X Axis Controller and Amplifier (XCA)  305  monitors temperature sensor (TS) arrays  306 ,  309 , and magnetic field sensor arrays  307 ,  308 , and further drives Electromagnet (EM)  132 X and  138 X. Magnetic field sensor arrays  307  and  308  measure the magnetic flux in the X axis. Temperature sensor (TS) arrays  306  and  309  measure the temperature of magnetic field sensor arrays  307  and  308  so that X Axis Controller and Amplifier (XCA)  305  can apply temperature compensation factors to the magnetic field sensor outputs.  
         [0083]     The sensory outputs of these arrays  306 ,  307 ,  308 ,  309  provide feedback to XCA  305  concerning the position of the actual catheter tip  377  with reference to the X-axis. As it will become apparent from the present description, these electromagnets  132 X and  138 X affect the position of the actual catheter tip  377  inside the patient&#39;s body  390  in the X-axis.  
         [0084]     Servo Power Supply (YPS)  17  provides DC power to the Y-Axis Controller and Amplifier (YCA)  310  for energizing the electromagnets (EM)  132 Y and  138 Y that are located outside the patient&#39;s body. YCA  310  monitors the sensor arrays of the Y-axis that include temperature sensor (TS) arrays  311 ,  314 , and magnetic field sensor array  312 ,  313 . Magnetic field sensor arrays  312  and  313  measure the magnetic flux in the Y-axis. Temperature sensor (TS) arrays  311  and  314  measure the temperature of magnetic field sensor arrays  312  and  313  so that Y Axis Controller and Amplifier (YCA)  310  can apply temperature compensation factors to the magnetic field sensor outputs. The sensory outputs of these arrays  311 ,  312 ,  313 ,  314  provide feedback to the servo system controlled by YCA  310  concerning the position of the actual catheter tip  377  with reference to the Y-axis. As it will become apparent from the present description, these electromagnets  132 Y and  138 Y affect the position of the actual catheter tip  377  inside the patient&#39;s body  390  in the Y-axis.  
         [0085]     The Z-Axis Power Supply (ZPS)  18  provides DC power to the Z-Axis Controller and Amplifier (ZCA)  315  for energizing the electromagnets (EM)  132 Z and  138 Z that are located outside the patient&#39;s body. ZCA  315  monitors the sensor arrays of the Z-axis that include the following components: temperature sensor (TS) arrays  316 ,  318 , and magnetic field sensor arrays  317 ,  319 . Magnetic field sensor arrays  317  and  319  measure the magnetic flux in the Z axis. Temperature sensor (TS) arrays  316  and  318  measure the temperature of magnetic field sensor arrays  317  and  319 , so that Z Axis Controller and Amplifier (ZCA)  315  can apply temperature compensation factors to the magnetic field sensor outputs. The sensory outputs of these arrays  316 ,  317 ,  318 ,  319  provide feedback to the servo system controlled by ZCA  315  concerning the position of the actual catheter tip  377  with reference to the Z-axis. As it will become apparent from the present description, these electromagnets  132 Z and  138 Z affect the position of the actual catheter tip  377  inside the patient&#39;s body  390  in the Z-axis.  
         [0086]     Communication Controller (CC)  320  interfaces host system  323 , auxiliary equipment  322 , and the computer  324  to system bus  328 . The surgical and medical equipment  502  can include, for example, the host system  323  and auxiliary equipment  322 . The host system  323  contains data concerning the patient and the current procedure(s) and also archives data generated by the GCI apparatus  501 . Auxiliary equipment  322  can include the x-ray imaging system and other patient monitoring apparatus.  
         [0087]     The operator interface  500  includes, for example, Computer  324 , monitor  325 , keyboard  326 , and mouse  327 . The computer  324  allows the operator to adjust the system parameters and to perform calibration and diagnostic routines. Monitor  325  displays the actual catheter tip  377  position data with overlaid X-ray imagery and operator prompts. Keyboard  326  and mouse  327  are used for operator-entered data input.  
         [0088]     Virtual Tip/Calibration Fixture Controller (VT/CFC)  303  inputs encoder position, limit switch, and operator switch data from Virtual Tip assembly  304  to be used by XCA  305 , YCA  310 , and ZCA  315  in controlling the electromagnets  132 X,  138 X,  132 Y,  138 Y,  132 Z, and  138 Z. Also, Virtual Tip/Calibration Fixture Controller (VT/CFC)  303  outputs Tactile Feedback (TF) response and light emitting diode (LED) data to Virtual Tip (VT)  304  to be perceived by the operator as obstructions or resistance met by the actual catheter tip  377 .  
         [0089]      FIG. 3  illustrates the components of one embodiment of the system controller (SC)  302 . A detailed description of the functionality of these components will follow in the ensuing description of the drawings. SC  302  can be characterized as functioning in different modes: 1) a power-up/power-down mode, 2) a servo system controller mode, 3) a tactile feedback response mode, and 4) a calibration mode.  
         [0090]     In the power-up/power down mode, SC  302  coordinates power-up/power-down sequencing of the components of the GCI apparatus  501 , performs built-in system diagnostic functions, and reports any errors detected during diagnostic functions which are sent to the communications controller (CC)  320  and stored in memory  41 . These tasks are accomplished by microcontroller  33 . Error data is stored in Random Access Memory (RAM)  41  during system operation and in Non Volatile Memory (NVM)  39  during power down. Microcontroller  33  communicates with other system components via system bus  328  by setting the appropriate address and control bits to decode logic  38  that enables address buffer  34  and data buffer  35 . Data latch  36  and data buffer  37  similarly connect microcontroller  33  to Uninterruptable Power Supply (UPS)  300  and to supervisory unit (SU)  301  via control logic  32 .  
         [0091]     In the servo system controller mode, System Controller (SC)  302  calculates the actual tip (AT) position as further described in conjunction with  FIG. 23 . Then, using data from the virtual tip (VT)  405 , determines the appropriate position error, that is the difference between the actual tip position and the operator-desired tip position as indicated by the virtual tip position, to be sent to X Axis Controller and amplifier (XCA)  305 , Y-Axis Controller and amplifier (YCA)  310 , and Z-Axis Controller and amplifier (ZCA)  315  via the system bus  328 .  
         [0092]     In the tactile feedback response mode, System Controller SC  302  initiates tactile feedback response by providing feedback data to the virtual tip (VT)  304  via the system bus  328 , as described in detail in  FIG. 23 .  
         [0093]     During the calibration mode, System Controller (SC)  302  exercises Calibration Fixture (CF)  312  via Virtual Tip/Calibration Fixture controller (VT/CFC)  303  and correlates the position data from X-axis Controller and Amplifier (XCA)  305 , Y-axis Controller and Amplifier (YCA)  310 , and Z-axis Controller and Amplifier (ZCA)  305  with Calibration Fixture (CF)  321  encoders  64 C,  66 C,  68 C,  70 C, and  72 C.  
         [0094]      FIG. 4  illustrates the Virtual Tip And Calibration Fixture Controller (VT/CF)  303 . Data is stored in Random Access Memory (RAM)  50  during the system operation and in a Non Volatile Memory (NVM)  48  during power down. Microcontroller  42  communicates with System Controller (SC)  302  ( FIG. 3 ) via system bus  328  by setting the appropriate address and control bits to decode logic  47 , which enables address buffer  43  and data buffer  44 . Address latch  45  and data buffer  46  similarly connect microcontroller  42  with virtual tip (VT)  405  or calibration fixture (CF)  321 , as described below.  
         [0095]     Virtual Tip/Calibration Fixture (VT/CF) controller  303  inputs data from VT  304  or CF  321  concerning the encoder positions, limit “switch” closures, and operator input switch positions. Additionally, Virtual Tip/Calibration Fixture (VT/CF) controller  303  outputs data to Virtual Tip (VT)  304  to produce tactile feedback and to illuminate the LED indicators to alert the operator of various system conditions.  
         [0096]     Referring to  FIG. 5 , the electronic circuitry function of the VT assembly  304  is as follows. A decode logic  101  responds to address and control bits originating from Virtual Tip/Calibration Fixture controller (VT/CFC)  303  ( FIG. 3 ), enabling data buffer  51  and setting its direction for transferring data. Step latches  52  and  53  store incoming data sent from the VT/CFC  303  to be presented to stepper drivers  54 ,  56 ,  58 ,  60  and  62  when strobed by decode logic  101 . Stepper motors  55 ,  57 ,  59 ,  61 , and  63  respond to the stepper driver outputs to provide tactile feedback to the operator. The stepper motors  55 ,  57 ,  59 ,  61 , and  63  create tactile feedback by producing resistance in the appropriate axial or angular coordinates as follows: stepper motor  55  in the X-axis  400 ; stepper motor  57  in the Y-axis  401 , stepper motor  59  in the Z-axis  402 ; stepper motor  61  in the angular direction of θ; and stepper motor  63  in the angular direction of EL.  
         [0097]     Still referring to  FIG. 5 , the absolute encoders  64 ,  66 ,  68 ,  70 , and  72  are mechanically coupled to the corresponding stepper motors  55 ,  57 ,  59 ,  61 , and  63 , and provide position feedback to the VT/CFC  303  during Tactile Feedback (TF) as well as inform the VT/CFC  303  of the Virtual Tip (VT) position during manual adjustments of the VT  405  by the operator. Encoder outputs are buffered by  65 ,  67 ,  69 ,  71 , and  73 , to temporarily store and transfer axial and angular position information to VT/CFC  303 . Limit “switches”  74 ,  75 ,  76 ,  77 ,  78 , and  79  flag the ends of the three linear axes, in order to limit the mechanical motion of the virtual tip  405 , and to allow synchronization of the mechanics of the virtual tip assembly  304  and the electronics of  FIG. 5 . “Switches”  80  and  81  indicate when angular  0  and EL are at zero position, for synchronizing of the mechanics of the virtual tip assembly  304  and the electronics shown in  FIG. 5 . Latch  82  strobes decode logic  101  in order to store these data defining positional limits. Operator switches  83 ,  84 ,  85 ,  86 ,  87 ,  88 ,  89 , and  90  are read and latched by latch  91 , in order to store their command, since these switches are momentary (i.e., momentary contact as opposed to a stable switch position). LEDs  92 ,  93 ,  94 ,  95 ,  96 ,  97 ,  98 , and  99  are driven by LED latch  100 .  
         [0098]      FIG. 7  illustrates the X axis controller and amplifier (XCA)  305 . XCA  305  receives and amplifies signals in the form of sensory data from the x-axis magnetic field sensors sensor arrays  307  and  308  and temperature sensor arrays  306  and  309 . Using this sensory data, a code is executed in microcontroller  102 X to create positional feedback to the VT/CFC  303  and other system components via system bus  328 . Microcontroller  102 X also receives data from VT/CFC  303  and other system components via system bus  328  to use in generating commands that will control the excitation of the external electromagnets  132 X and  138 X to affect the position of the actual catheter tip in the X-axis. XCA  305  also generates error and correcting signals to be used during the calibration and normal system operation. These functions will now be described.  
         [0099]     First, the method by which XCA  305  monitors the sensory data from the MFS arrays  307  and  308  and temperature sensor arrays  306  and  309  will be explained. Magnetic field sensors sensor array  307  includes magnetic field sensors  113   x,    114   x,    115   x  and  116   x.  Magnetic field sensors sensor array  308  includes magnetic field sensors  117   x,    118   x,    119   x,  and  120   x.  Temperature sensor array  306  includes temperature sensors  122   x,    123   x,    124   x,  and  125   x.  Temperature sensor array  309  includes temperature sensors  126   x,    127   x,    128   x,  and  129   x.  The physical positions of these sensors and relations to one another are described in conjunction with  FIG. 13 . Microcontroller  102   x  executes a mathematical procedure that is described in conjunction with  FIGS. 18, 18A ,  18 B and  18 C, that calculates positional data based on input from the sensor arrays  307  and  308 . Input and output data is stored in Random Access Memory (RAM)  103   x  during system operation. Non Volatile Memory (NVM)  105   x  stores data such as temperature compensation parameters which are used in combination with measured temperature sensor array  306  and  309  data to make necessary corrections to data from the magnetic field sensors  113 X,  114 X,  115 X,  116 X.  117 X,  118 X,  119 X, and  120 X.  
         [0100]     The collecting of sensory data is initiated by decode logic  106   x  in conjunction with address latch  111   x  that allows microcontroller  102   x  to set the input channel of analog multiplexer  112   x.  Similarly, decode logic  106   x  in conjunction with address latch  109   x  allows microcontroller  102   x  to set the gain of programmable gain amplifier  110   x  in order to compensate for variations in signal strength from the sensor arrays  307 ,  308 ,  306 , and  309 . Microcontroller  102   x  strobes sample and hold circuit  108   x  via decode logic  106   x,  so that microcontroller  102   x  is able to perform other functions while periodically sampling the data temporarily stored in sample and hold circuit  108 X. The output of sample and hold circuit  108   x  is thus a “snapshot” of the signal to be measured.  
         [0101]     Analog-to-Digital Converter (ADC)  107   x  is issued a “convert” command by microcontroller  102   x  via decode logic  106   x  to convert the data from the position sensors  307  and  308  from analog to digital, so that the digital system can interpret the data. When the conversion is complete, analog to digital converter  107   x  interrupts microcontroller  102   x  via decode logic  106   x  and the digital representation of the measured signal is input by microcontroller  102   x.  It is by this method that the magnetic field sensors  113   x,    114   x,    115   x,    116   x,    117   x,    118   x,    119   x,  and  120   x  as well as the temperature sensors  122   x,    123   x,    124   x,    125   x,    126   x,    127   x,    128   x,  and  129   x  are monitored. Similarly, the voltage drop across the shunts  131 X and  137 X is measured to determine the current flow through the electromagnets  132 X and  138 X.  
         [0102]     Still referring to  FIG. 7 , current source  121   x  provides the control current to bias the magnetic field sensors  113 X,  114 X,  115 X,  116 X,  117 X,  118 X,  119 X, and  120 X since they operate best in a constant current mode and require stability for reliable sensing. Temperature sensor bias supply  130   x  supplies the voltage for the temperature sensors  122 X,  123 X,  124 X,  125 X,  126 X,  127 X,  128 X,  129 X.  
         [0103]     The method by which XCA  305  generates commands to control the movement of the actual catheter tip  377  in the X-axis will now be explained. Microcontroller  102 X receives data from VT/CFC  303  and other system components via system bus  328  to use in generating commands that will control the movement. Microcontroller  102   x  in conjunction with decode logic  106   x  controls modulators  144   x  and  146   x  to provide the correct move signal and command. Preamplifiers  143   x,  and  145   x  amplify the modulators outputs and drive final amplifiers  135   x,    136   x,    141   x,  and  142   x.  Diodes  133   x,    134   x,    139   x,  and  140   x  protect the final amplifiers from a surge of back electromotive force due to the inductive nature of the electromagnet coils  132 X and  138 X.  
         [0104]     Electromagnet coils  132   x  and  138   x  produce a magnetic field that affects the position of the actual catheter tip in the X-Axis.  
         [0105]     Microcontroller  102 X communicates with VT/CFC  303  and other system components via system bus  328  by setting the appropriate address and control bits to decode logic  106   x,  which enables address buffer  148   x  and data buffer  147   x.    
         [0106]     Non Volatile Memory (NVM)  105   x  also stores calibration data to be used during calibration operations in conjunction with the calibration fixture  321  and VT/CFC  303 . These operations and the source of the calibration data will be described later in conjunction with  FIG. 23 . Further, Non Volatile Memory (NVM)  105   x  stores error codes to be used during power down operations controlled by the System Controls (SC)  302 .  
         [0107]      FIG. 8  illustrates The Y-axis controller and amplifier (YCA)  310  which operates in a similar manner to the XCA  305  of  FIG. 7 . YCA  310  receives and amplifies the signals from the Y-axis magnetic field sensor arrays  312  and  313  and temperature sensor arrays  311  and  314 . Using this incoming sensory data, a code is executed in microcontroller  102 Y to create positional feedback to the VT/CFC  303  and other system components via system bus  328 . Microcontroller  102 Y also receives data from VT/CFC  303  and other system components via system bus  328  to use in generating commands that will control excitation of the external electromagnets  132 Y and  138 Y to affect the position of the actual catheter tip  377  in the Y-axis. YCA  310  also generates error and correcting signals to be used during the calibration and normal system operation. These functions will now be described.  
         [0108]     First, the method by which YCA  310  monitors the sensory data from MFS arrays  312  and  313  and temperature sensor arrays  311  and  314  will first be explained. Magnetic field sensor array  312  includes magnetic field sensors  113   y,    114   y,    115   y  and  116   y.  Magnetic field sensor array  313  includes magnetic field sensors  117   y,    118   y,    119   y,  and  120   y.  Temperature sensor array  311  includes temperature sensors  122   y,    123   y,    124   y,  and  125   y.  Temperature sensor array  314  includes temperature sensors  126   y,    127   y,    128   y,  and  129 y. The physical positions of these sensors and relations to one another are described in conjunction with  FIG. 13 .  
         [0109]     Microcontroller  102   y  executes a mathematical procedure, that described in conjunction with  FIGS. 18, 18A ,  18 B and  18 C, that calculates positional data based on input from the sensor arrays  312  and  313 . Input and output data is stored in Random Access Memory (RAM)  103   y  during system operation. Non Volatile Memory (NVM)  105   y  stores data such as temperature compensation parameters which are used in combination with measured temperature sensor array  311  and  314  data to make necessary corrections to data from the magnetic field sensors  113 Y,  114 Y,  115 Y,  116 Y,  117 Y,  118 Y,  1   19 Y, and  120 Y.  
         [0110]     The collecting of sensory data is initiated by decode logic  106   y  in conjunction with address latch  111   y,  which allows microcontroller  102   y  to set the input channel of analog multiplexer  112   y.  Similarly, decode logic  106   y  in conjunction with address latch  109   y  allows microcontroller  102   y  to set the gain of programmable gain amplifier  110   y,  in order to compensate for variations in signal strength from the sensor arrays  311 ,  312 ,  313 , and  314 . Microcontroller  102   y  strobes sample and hold circuit  108   y  via decode logic  106   y,  to allow microcontroller  102   y  to perform other functions while periodically sampling the data temporarily stored in sample and hold circuit  108 Y. The output of sample and hold circuit  108   y  is thus a “snapshot” of the signal to be measured.  
         [0111]     Analog to Digital Converter (ADC)  107   y  is issued a convert command by microcontroller  102   y  via decode logic  106   y  to convert the data from the position sensors  312  and  313  from analog to digital, so that the digital system can interpret the data. When the conversion is complete, analog to digital converter  107   y  interrupts microcontroller  102   y  via decode logic  106   y  and the digital representation of the measured signal is input by microcontroller  102 y. It is by this method that the magnetic field sensors  113   y,    114   y,    115   y,    116   y,    117   y,    118   y,    119   y,  and  120   y  as well as the temperature sensors  122   y,    123   y,    124   y,    125   y,    126   y,    127   y,    128   y,  and  129   y  are monitored. Similarly, the voltage drop across the shunts  131  Y and  137 Y is measured to determine the current flow through the electromagnets  132 Y and  138 Y.  
         [0112]     Still referring to  FIG. 8 , current source  121   y  provides the control current to bias the magnetic field sensors  113 Y,  114 Y  115 Y,  116 Y,  117 Y,  118 Y,  119 Y, and  120 Y, since they operate best in a constant current mode and require stability for reliable sensing. Temperature sensor bias supply  130   y  supplies the voltage for the temperature sensors  122 Y,  123 Y,  124 Y,  125 Y,  126 Y.  127 Y,  128 Y, and  129 Y.  
         [0113]     The method by which YCA  310  generates commands that will control the movement of the actual catheter tip in the Y-Axis will now be explained. Microcontroller  102 Y receives data from VT/CFC  303  and other system components via system bus  328  to use in generating commands that will control the movement of the actual catheter tip in the Y-axis will now be explained. Microcontroller  102   y  in conjunction with decode logic  106   y  controls modulators  144   y  and  146   y  to provide the correct move signal and command. Preamplifiers  143   y,  and  145   y  amplify the modulators outputs and drive final amplifiers  135   y,    136   y,    141   y,  and  142 y. Diodes  133   y,    134   y,    139   y,  and  140   y  protect the final amplifiers from a surge of back electromotive force due to the inductive nature of the electromagnet coils  132 Y and  138 Y. Electromagnet coils  132   y  and  138   y  produce the magnetic field which will affect the position of the actual catheter tip  377  in the Y-Axis.  
         [0114]     Microcontroller  102 Y communicates with VT/CFC  303  and other system components via system bus  328  by setting the appropriate address and control bits to decode logic  106   y,  which enables address buffer  148   y  and data buffer  147   y.    
         [0115]     Non Volatile Memory (NVM)  105   y  also stores calibration data to be used during calibration operations in conjunction with the calibration fixture  321  and VT/CFC  303 . These operations and the source of the calibration data will be described later in conjunction with  FIG. 23 . Further, Non Volatile Memory (NVM)  105   y  stores error codes to be used during power down operations controlled by the System Controls (SC)  302 .  
         [0116]      FIG. 9  illustrates the Z-axis controller and amplifier (ZCA)  315  which operates in a similar manner to that of  FIGS. 7 and 8 . ZCA  315  receives and amplifies the signals from the z-axis magnetic field sensor arrays  312  and  313  and temperature sensor arrays  311  and  314 . Using the incoming sensory data, a code is executed in microcontroller  102 Z to create positional feedback to the VT/CFC  303  and other system components via system bus  328 . Microcontroller  102 Z also receives data from VT/CFC  303  and other system components via system bus  328 , to use in generating commands that will control the excitation of the external electromagnets  132 Z and  138 Z to affect the position of the actual catheter tip  337  in the Z-axis. ZCA  315  also generates error and correcting signals to be used during the calibration and normal system operation. These functions will now be described.  
         [0117]     First, the method by which ZCA  315  monitors the sensory data from MFS arrays  317  and  318  and temperature sensor arrays  316  and  319  will first be explained. Magnetic field sensor array  317  includes magnetic field sensors  113   z,    114   z,    115   z  and  116   z.  Magnetic field sensor array  318  includes magnetic field sensors  117   z,    118   z,    11   9   z,  and  120   z.  Temperature sensor array  316  includes temperature sensors  122   z,    123   z,    124   z,  and  125   z.  Temperature sensor array  319  includes temperature sensors  126   z,    127   z,    128   z,  and  129   z.  The physical positions of these sensors and relation to one another are described in conjunction with  FIG. 13 .  
         [0118]     Microcontroller  102   z  executes a mathematical procedure that is described in conjunction with  FIGS. 18, 18A ,  18 B and  18 C, and that calculates positional data based on input from the sensor arrays  317  and  318 . Input and output data is stored in Random Access Memory (RAM)  103   z  during system operation. Non Volatile Memory (NVM)  105   z  stores data such as temperature compensation parameters that are used in combination with measured data from the temperature sensor arrays  316  and  319 , to make necessary corrections to the data from the magnetic field sensors  11   3 Z,  114 Z,  11   5 Z,  116 Z,  117 Z,  11   8 Z,  1   19 Z, and  120 Z.  
         [0119]     The collecting of sensory data is initiated by decode logic  106   z  in conjunction with address latch  111   z  that allows microcontroller  102   z  to set the input channel of analog multiplexer  112 z. Similarly, decode logic  106   z  in conjunction with address latch  109   z  allows microcontroller  102   z  to set the gain of programmable gain amplifier  110   z,  in order to compensate for variations in signal strength from the sensor arrays  316 ,  317 ,  318 , and  319 .  
         [0120]     Microcontroller  102   z  strobes sample and hold circuit  108   z  via decode logic  106   z,  to allow microcontroller  102   z  to perform other functions while periodically sampling the data temporarily stored in sample and hold circuit  108 Z. The output of sample and hold circuit  108   z  is thus a “snapshot” of the signal to be measured. Analog to Digital Converter (ADC)  107   z  is issued a convert command by microcontroller  102   z  via decode logic  106   z,  to convert the data from the position sensors  317  and  318  from analog to digital, so that the digital system can interpret the data. When the conversion is complete, analog to digital converter  107   z  interrupts microcontroller  102   z  via decode logic  106   z  and the digital representation of the measured signal is input by microcontroller  102 z. It is by this method that the magnetic field sensors  113   z,    114   z,    115   z,    116   z,    117   z,    118   z,    119   z,  and  120   z  as we the temperature sensors  122   z,    123   z,    124   z,    125   z,    126   z,    127   z,    128   z,  and  129   z  are monitored. Similarly, the voltage drop across the shunts  131 Z and  137 Z is measured to determine the current flow through the electromagnets  132 Z and  138 Z.  
         [0121]     Still referring to  FIG. 9 , current source  121   z  provides the control current to bias the magnetic field sensors  113 Z,  114 Z,  115 Z,  116 Z,  117 Z,  118 Z,  119 Z, and  120 Z since they operate best in a constant current mode, and require stability for reliable sensing. Temperature sensor bias supply  130   z  supplies the voltage for the temperature sensors  112 Z,  123 Z,  124 Z  125 Z,  126 Z,  127 Z,  128 Z, and  129 Z.  
         [0122]     The method by which ZCA  315  generates commands that will control the movement of the actual catheter tip in the Z-axis will now be explained. Microcontroller  102 Z receives data from VT/CFC  303  and other system components via system bus  328 , to use in generating commands that will control the movement of the actual catheter tip in the Z-axis will now be explained. Microcontroller  102   z  in conjunction with decode logic  106   z  controls modulators  144   z  and  146   z  to provide the correct move signal and command. Preamplifiers  143   z,  and  145   z  amplify the modulators outputs and drive final amplifiers  135   z,    136   z,    141   z,  and  142 z. Diodes  133   z,    134   z,    139   z,  and  140   z  protect the final amplifiers from a surge of back electromotive force due to the inductive nature of the electromagnet coils  132 Z and  138 Z. Electromagnet coils  132   z  and  138   z  produce the magnetic field which will affect the position of the actual catheter tip in the Z-axis.  
         [0123]     Microcontroller  102 Z communicates with VT/CFC  303  and other system components via system bus  328  by setting the appropriate address and control bits to decode logic  106   z,  which enables address buffer  148   z  and data buffer  147   z.    
         [0124]     Non Volatile Memory (NVM)  105   z  also stores calibration data to be used during calibration operations in conjunction with the calibration fixture  321  and VT/CFC  303 . These operations and the source of the calibration data will be described later in conjunction with  FIG. 23 . Further, Non Volatile Memory (NVM)  105   z  stores error codes to be used during power down operations controlled by the System Controls (SC)  302 .  
         [0125]      FIG. 10  illustrates the communication controller (CC)  320  whose main function is to communicate with other system components via system bus  328 . The position data received from the XCA  305 , YCA  310 , and ZCA  315  is stored in Random Access Memory (RAM)  156  during system operation and in Non Volatile Memory (NVM)  154  during power down, in order to retain the position of the actual tip inside the patient&#39;s body. Microcontroller  149  communicates with other system components via system bus  328 , by setting the appropriate address and control bits to decode logic  153 , which enables address buffer  150  and data buffer  151 . Similarly, microcontroller  149  communicates with PC  324 , auxiliary equipment  322 , and host system  323  via communication I/O port  152 , by setting address and control bits to decode logic  153  or responding to an interrupt from port  152 . This is done for a number of reasons, such as the need to display the actual process and procedure of the operation on a CRT display.  
         [0126]      FIG. 11  illustrates the electrical circuitry of the calibration fixture (CF)  321  and  FIG. 12  illustrates the mechanical implementation of the calibration fixture (CF)  321 . The purpose of the CF,  321 , is to define the steps and limits of motion in each possible direction of the virtual tip  405 . This information is communicated to the VT/CFC  303  and used to synchronize the electronic circuitry and physical operations during normal operation of the GCI apparatus  501 .  
         [0127]     The calibration magnet  411  is manipulated in relation to the five possible axes defined by the X-axis  406 , the Y-axis  407 , the Z-axis  408 , the θ axis  409 , and the EL axis  410 . These axes correspond exactly to the five directions of movement possible for the virtual tip  405 , which is the maximum number of degrees of freedom possible for the actual tip  377 . The manipulation of calibration magnet  411  is accomplished by the electronic circuitry of the calibration fixture  321  as implemented in  FIG. 11 .  
         [0128]     The circuitry of  FIG. 11  operates as follows: A decode logic  101   c  responds to address and control bits originating from VT/CFC  303  and enables data buffer  51   c  and sets its direction. Step latches  52   c  and  53   c  store data to be presented to stepper drivers  54   c,    56   c,    58   c,    60   c,  and  62   c  when strobed by decode logic  101   c.  Stepper motors  55   c,    57   c,    59   c,    61   c,  and  63   c  respond to the stepper drive outputs to manipulate the magnetic calibration tip in the  5  axes. Absolute encoders  64   c,    66   c,    68   c,    70   c,  and  72   c  are mechanically coupled to the corresponding stepper motors and provide position feedback to the VT/CFC  303 . The outputs of the encoders  64 C,  66 C,  68 C,  70 C and  72 C are buffered by data buffers  65   c,    67   c,    69   c,    71   c  and  73   c  to temporarily store and transfer the data. Limit “switches”  74   c,    75   c,    76   c,    77   c,    78   c,  and  79   c  flag the ends of the three linear axes X, Y and Z. “Switches”  80   c  and  81   c  indicate when θ and EL are at zero position. Limit latch  82   c  stores this data when strobed by decode logic  101   c.    
         [0129]      FIG. 13  Illustrates the polar configuration  374  of the electromagnets  132 X,  132 Y,  132 Z,  138 Z,  138 Y, and  138 Z, the magnetic field sensors and temperature sensor pairs  350 ,  351 ,  352 ,  353 ,  354 , 355 ,  356 ,  357 ,  358 ,  359 ,  360 ,  361 ,  362 ,  363 ,  364 ,  365 ,  366 ,  367 ,  368 ,  369 ,  370 ,  371 ,  372 , and  373 . The electromagnets  132   x,    132   y,    132   z  are arranged in three orthogonal axes X, Y, Z, or as shown in  FIGS. 13A and 13B .  
         [0130]      FIG. 13A  and  FIG. 13B  illustrate a polar clustered configuration poles where the operating table  389  and electromagnets  901 ,  902 , and  903  are configured relative to  904 ,  905 , and  906 , as approximately shown and mounted by the use of support assembly  391  configured as a C-Arm to compliment and close the magnetic field circuit. The polar configuration  374  is further expressed as a non-symmetrical distribution of the polar arrangement where electromagnet  901  and its counterpart  903  are rotated to provide a lobed electromagnetic field. This arrangement further optimizes the magnetic circuit and provides for free access for the physician and the patient while the Z axis electromagnets  905  and  906  do not obstruct the available access space as approximately shown by  FIG. 13  and  FIG. 16 . Furthermore  FIG. 13  and  FIG. 13A  and  FIG. 13B  compliment each other and are an alternative to the bi-plane ring shown in  FIG. 16 ,  FIG. 16A ,  FIG. 16B  and  FIG. 16C . Both arrangements represent a possible approach provided in accommodating the imaging technology modalities such as x-ray, Cat-Scan, Pet-Scan and Ultrasound, while  FIG. 16  provides for the GCI apparatus  501  as a natural access for a fluoroscopic imaging on a bi-plane arrangement.  FIGS. 13, 13A  and  13 B enable geometry with a bore of approximately 25 inches which is capable of incorporating a computer tomography apparatus and/or the modality noted above. Further embodiment of using the geometrical arrangement noted in  FIGS. 13A and 13B  is expressed in the ensuing descriptions of  FIGS. 13C, 13D ,  13 E,  13 F,  13 G and  13 H. The two competing architectures shown in  FIGS. 16, 16A ,  16 B  16 C and  FIG. 13A, 13B , provide for advantages and disadvantages in mounting the operating interface equipment  500 , surgical medical equipment  502 , and the GCI apparatus  501 . Further  FIGS. 13A and 13B  illustrate an alternative arrangement of the coils attached to the C-arm,  391 , and table  389 . In this arrangement coils  901  through  906  are shown in a cluster configuration. This geometry diverts from the intuitive orthogonal structure of coils commonly used when generating vectors or vector gradients with the aide of electromagnetic coils.  FIG. 13B  further illustrates the six coils,  901  through  906 , configured in a flower-like structure, or a cluster. Three of the coils are mounted at the top of the C-arm  391 , and three at the bottom. The three coils forming the upper cluster are further shifted by 120 degrees relative to each other, as are the bottom three coils. In addition, the coils of the cluster at the top of the C-arm are also tilted downward somewhat, at an angle of 15 to 20 degrees, as are the coils of the cluster at the bottom of the C-arm tilted upward, as shown in  FIG. 13B . The entire cluster at the top of the C-arm is rotated with respect to the bottom cluster by an angle of 60 degrees.  
         [0131]     In  FIG. 13B , the coils at the top of the C-arm  391  are marked as  901 ,  902 , and  903 , counting clockwise, and the bottom coils are marked  904 ,  905  and  906 , counting in a counter clockwise direction. Coils  901  and  903  work as a pair and are designated as the X-axis pair of coils, coils  902  and  904  work as another pair and are designated as the Y-axis pair of coils, and coils  905  and  906  are the third pair and are designated as the Z- axis pair of coils.  
         [0132]      FIGS. 13C, 13D ,  13 E,  13 F,  13 G and  13 H, show an alternative architecture of the GCI apparatus  501  whereby the polar configuration noted in  FIGS. 16, 16A ,  16 B, and  16 C, is altered to accommodate the cluster configuration of the electro-magnet circuit as shown in  FIGS. 13A and 13B .  FIG. 13B  is a simplified block diagram of the electrical scheme of the various components of the system. The system comprises a power supply,  910 , a joystick,  900 , feeding three channels, X, Y, and Z, where the three signals taken together form a matrix V,  923 , shown in  FIG. 13D , comprising elements Vj x , Vj y  and Vj z . This arrangement is further explained in  FIGS. 13D, 13E ,  13 F,  13 G and  13 H.  FIG. 13C , the X-axis channel, comprises an Op-Amp  911 , a current amplifier  910 , and coil pair  901 ,  903 . The Y-axis channel comprises an Op-Amp  913 , a current amplifier  912 , and coil pair  902 ,  904 . The Z-axis channel comprises an Op-Amp  915 , a current amplifier  914 , and coil pair  905 ,  906 . As shown, each pair of coils is connected in series and further connected to the output of power amplifiers,  910 ,  912 , and  914 , for the X, Y and Z axes, respectively. The alternative architecture to  FIG. 1  shown in  FIG. 13C  receives its input signal command from the joystick,  900 . Upon command from the operator using the joystick  900  to move in one or more axes, the joystick  900  sends its signal to an array of operational amplifiers,  911 ,  913 , and  915 , corresponding to the X, Y, and the Z axes respectively. Op-Amps  911 ,  913 , and  915  translate the signal received from joystick  900  and perform an Inverse operation on the matrix of the three signals for the three axes. The Op-Amp array  932  multiplies the signal from joystick  900  represented as vector V,  923 , by another matrix M-inverse, shown in  FIG. 13F and 13G  as  927 , such that the output of the Op-Amp array  932  is M-inverse times V, where M is the characteristic matrix  925  of the cluster arrangement comprising the six coils  901  through  906 . The output from the Op-Amp array  932 , comprising Op-Amps  911 ,  913 , and  915 , is obtained, and is fed to power amplifiers  910 ,  912 , and  914 , driving the six coils  901  through  906  to obtain the result of generating a motion in the desired direction, hence providing the apparatus  501  with the ability to translate the desired motion of the operator or the clinician as to move the catheter tip  377  in a body lumen of a patient,  390 . This scheme as shown in  FIGS. 13D, 13E ,  13 F, and  13 G, is reduced further in  FIG. 13H  where the input signal V,  931 , from Joystick  900 , is fed to an Mchar-Inverse Op-Amp array,  932 . The resultant output from the array  932  is the matrix product Mchar-Inverse by the vector V. This signal is fed to current amplifiers  928 , their signal output represented by the vector B,  933 , is then fed as the respective current to the coils  901  through  906 , thereby producing the result of translating the hand-movement of the clinician into the appropriate signal, thus moving the catheter tip to the desired location.  
         [0133]     In summary, the alternative arrangement shown above provides GCI  501  a method in which a competing architecture to  FIG. 1  is employed where a non-symmetrical arrangement of the coils is linearized through the use of the scheme shown in  FIG. 13H , thereby producing the desired results. This is shown in  FIG. 13E .  
         [0134]      FIG. 14  shows an arrangement of the magnetic field sensors and temperature sensor pairs into sensor arrays  306 ,  307 ,  308 ,  309 ,  311 ,  312 ,  313 ,  314 ,  316 ,  317 ,  318 , and  319 . Each orthogonal axis is divided into two poles by positioning a second electromagnet coaxially with the first. For example, electromagnet  132   x  is coaxial with electromagnet  138   x,  electromagnet  132   y  is coaxial with electromagnet  138   y,  and electromagnet  132   z  is coaxial with electromagnet  138   z.  Since the rotational movements of the virtual tip  405  defined by θ  403  and EL  404 , as shown in  FIG. 6  occur within the X-Y plane and the X-Z plane respectively, electromagnet poles along the X-, Y- and Z-axes are sufficient to affect movement of the actual catheter tip  377  in exactly the same five axes as defined for the virtual tip  405  as previously described in connection with  FIG. 6 .  
         [0135]     In one embodiment, each magnetic field sensor contained in the MFS arrays  307 ,  308 ,  312 ,  313 ,  317 , and  319 , is paired with a temperature sensor (TS) contained in temperature sensor arrays  306 ,  309 ,  311 ,  314 ,  316 , and  318 . These paired combinations are detailed in  FIG. 14  and in the table below. The magnetic field sensors-temperature sensor (MFS/T) pairs are arranged in quadrants on the pole face of the electromagnets  132   x,    132   y,    132   z,    138   x,    138   y,  and  138   z.    
         [0136]     As shown in  FIG. 13 , the MFS/TS pairs  350 ,  351 ,  352 , and  353  are arranged in quadrants on electromagnet  132   x  pole face. Magnetic field sensor and temperature sensor (TS) pairs  354 ,  355 ,  356 , and  357  are arranged in quadrants on electromagnet  138   x  pole face. Magnetic field sensor and temperature sensor (TS) pairs  358 ,  359 ,  360 , and  361  are arranged in quadrants on electromagnet  132   y  pole face. Magnetic field sensor and temperature sensor (TS) pairs  362 ,  363 ,  364 , and  365  are arranged in quadrants on electromagnet  138   y  pole face. Magnetic field sensor and temperature sensor (TS) pairs  366 ,  367 ,  368 , and  369  are arranged in quadrants on electromagnet  132   z  pole face. Magnetic field sensor and temperature sensor (TS) pairs  370 ,  371 ,  372 , and  373  are arranged in quadrants on electromagnet  138   z  pole face.  
         [0137]      FIG. 14  illustrates the pairing of the magnetic field sensors and temperature sensors as mounted in  FIG. 13 . The magnetic field sensors and temperature sensors are mounted as isothermal pairs, and each pair functions in conjunction with each other. The magnetic field sensors measure the position of the actual tip  377  during the measurement phase, as controlled by microcontrollers  102   x,    102   y  and  102   z  of XCA  305 , YCA  310  and ZCA  315 , respectively, during which time the electromagnets  132 X,  132 Y,  132 Z,  138 X,  138 Y, and  138 Z are de-energized. This is done in order to be able to take accurate and sensitive measurements with the magnetic field sensor arrays  307 ,  308 ,  312 ,  313 ,  317 , and  318 , as they would otherwise be saturated with the flux from the electromagnets. The temperature sensor arrays  306 ,  309 ,  311 ,  314 ,  316 , and  319  monitor the ambient temperature to detect an increase that may be uncomfortable for the patient or potentially damaging to surrounding tissues, and provide correctional data for calculating position based on the magnetic field sensors. The isothermal pairs are as follows: 
        magnetic field sensor  113 X and temperature sensor (TS)  122   x  form pair  350 . Magnetic field sensor  114   x  and temperature sensor (TS)  123   x  form pair  351 . Magnetic field sensor  115   x  and temperature sensor (TS)  124   x  form pair  352 . Magnetic field sensor  116   x  and temperature sensor (TS)  125   x  form pair  353 .Magnetic field sensor  117   x  and temperature sensor (TS)  126 X form pair  354 . Magnetic field sensor  118   x  and temperature sensor (TS)  127   x  form pair  355 . Magnetic field sensor  119   x  and temperature sensor (TS)  128   x  form pair  356 . Magnetic field sensor  120   x  and temperature sensor (TS)  129   x  form pair  357 . Magnetic field sensor  113   y  and temperature sensor (TS)  122   y  form pair  358 . Magnetic field sensor  114   y  and temperature sensor (TS)  123   y  form pair  359 . Magnetic field sensor  115   y  and temperature sensor (TS)  124   y  form pair  360 . Magnetic field sensor  116   y  and temperature sensor (TS)  125   y  form pair  361 . Magnetic field sensor  117   y  and temperature sensor (TS)  126   y  form pair  362 . Magnetic field sensor  118   y  and temperature sensor (TS)  127   y  form pair  363 . Magnetic field sensor  1   19   y  and temperature sensor (TS)  128   y  form pair  364 . Magnetic field sensor  120   y  and temperature sensor (TS)  129   y  form pair  365 . Magnetic field sensor  113   z  and temperature sensor (TS)  122   z  form pair  366 . Magnetic field sensor  114   z  and temperature sensor (TS)  123   z  form pair  367 . Magnetic field sensor  115   z  and temperature sensor (TS)  124   z  form pair  368 . Magnetic field sensor  116   z  and temperature sensor (TS)  125   z  form pair  369 . Magnetic field sensor  117   z  and temperature sensor (TS)  126   z  form pair  370 . Magnetic field sensor  118   z  and temperature sensor (TS)  127   z  form pair  371 . Magnetic field sensor  119   z  and temperature sensor (TS)  128   z  form pair  372 . Magnetic field sensor  120   z  and temperature sensor (TS)  128   z  form pair  373 .          
         [0139]      FIGS. 15 and 15 A show an improved catheter assembly  375  and guidewire assembly  379  to be used with the GCI apparatus  501 . The catheter assembly  375  is a tubular tool that includes a catheter body  376  which extends into a flexible section  378  that possesses increased flexibility for allowing a more rigid responsive tip  377  to be accurately steered through a torturous path.  
         [0140]     The magnetic catheter assembly  375  in combination with the GCI apparatus  501  reduces or eliminates the need for the plethora of shapes normally needed to perform diagnostic and therapeutic procedures. This is due to the fact that during a conventional catheterization procedure, the surgeon often encounters difficulty in guiding the conventional catheter to the desired position, since the process is manual and relies on manual dexterity to maneuver the catheter through a tortuous path of, for example, the cardiovascular system. Thus, a plethora of catheters in varying sizes and shapes are be made available to the surgeon in order to assist him/her in the task, since such tasks require different bends in different situations due to natural anatomical variations within and between patients.  
         [0141]     By using the GCI apparatus  501 , only a single catheter would be needed for most, if not all patients, because the catheterization procedure is now achieved with the help of an electromechanical system that guides the magnetic catheter and guidewire assembly  375  and  379  to the desired position within the patient&#39;s body  390  as dictated by the surgeon&#39;s manipulation of the virtual tip  405 , without relying on the surgeon pushing the catheter, quasi-blindly, into the patient&#39;s body. The magnetic catheter and guidewire assembly  375 ,  379  (i.e., the magnetic tip can be attracted or repelled by the electromagnets  132 X,  132 Y,  132 Z) provides the flexibility needed to overcome tortuous paths, since the GCI apparatus  501  overcomes most, if not all of the physical limitations faced by the surgeon while attempting to manually advance the catheter tip  377  through the patient&#39;s body.  
         [0142]     The guidewire assembly  379  is a tool with a guidewire body  380  and a flexible section  382 , which possesses increased flexibility for allowing a more rigid responsive tip  381  to be accurately steered around sharp bends so as to navigate a torturous path. The responsive tips  377  and  381  of both the catheter assembly  375  and the guidewire assembly  379 , respectively, include magnetic elements such as permanent magnets. The tips  377  and  381  include permanent magnets that respond to the external flux generated by the electromagnets  132 X,  132 Y,  132 Z and  138 X,  138 Y,  138 Z.  
         [0143]     The responsive tip  377  of the catheter assembly  375  is tubular, and the responsive tip  381  of the guidewire assembly  379  is a solid cylinder. The responsive tip  377  of catheter assembly  375  is a dipole with longitudinal polar orientation created by the two ends of the magnetic element positioned longitudinally within it. The responsive tip  381  of guidewire assembly  379  is a dipole with longitudinal polar orientation created by the two ends of the magnetic element  377  positioned longitudinally within it. These longitudinal dipoles allow the manipulation of both responsive tips  377  and  381  with the GCI apparatus  501 , as the electromagnets  132 X,  132 Y,  132 Z,  138 X,  138 Y, and  138 Z will act on the tips  377  and  381  and “drag” them in unison to a desired position as dictated by the operator.  
         [0144]      FIG. 15B  illustrates a further improvement of catheter assembly  375  and guide-wire assembly  379  to be used with the GCI apparatus  501 , where the catheter assembly  950  is fitted with an additional two piezoelectric rings,  951  and  952 , located as shown. An ultrasonic detector in combination with apparatus  501  provides an additional detection modality of the catheter tip whereby an ultrasonic signal is emitted as to excite the two piezoelectric rings and provide a measure of rotation of the catheter tip relative to the north pole axis of the magnet  377 . With the aide of the computer  324 , the GCI apparatus  501  is capable of defining the angle of rotation of the tip  377  and in a more elaborate scheme known to those familiar with the art the piezoelectric rings  951 ,  952 , can provide additional position information to define the position, orientation, and rotation of the catheter tip  377  relative to the stereotactic framing as described further in  FIGS. 17 and 17 A.  
         [0145]      FIG. 16  illustrates a bi-plane x-ray ring incorporating the apparatus of  FIG. 1B .  FIGS. 16A, 16B  and  16 C are further elaboration of  FIG. 16 , and show in further detail, elements that could not be depicted by the isometric view of  FIG. 16 , or were omitted from  FIG. 16  for clarity. Additionally,  FIGS. 16A, 16B , and  16 C are top, end, and side views respectively of the electromagnet and imaging assembly  391  and support assembly  385 .  
         [0146]      FIG. 16  further illustrates the overall relationship between the operating table  389 , the patient  390 , a T-axis encoder  394 , a trunnion  388 , a support assembly  385 , a polar support  391 , a G-axis encoder  393 , the x-ray source  383 , an image intensifier  384 , the electromagnets  132 X,  132 Y,  132 Z, an overall arrangement referred to as polar configuration  374 , electromagnets  138 X  138 Y,  138 Z, the power supply and control system  392 , the auxiliary equipment  322 , the host system  323 , the PC  324 , the virtual tip assembly  304 , the calibration fixture  321 , the mouse  327 , the keyboard  326 , the monitor  325 , as they are approximately oriented for visual aid. The function of the components that has not yet been described will be explained in the ensuing paragraphs, with reference to  FIG. 16, 16A ,  16 B, and  16 C.  
         [0147]     The T-axis encoder  394  and the G-axis encoder  393  provide the system with gantry position information for use in calculating the desired coordinate rotation prior to energizing the electromagnet. The trunnion  388  acts as a truss for the support assembly  385 . Polar support  391  pivots on the G-axis of support assembly  385 . The polar assembly  391  supports the x-ray source  383  and x-ray image intensifier  384  that produce x-ray images to be overlaid with the actual catheter position image on the monitor  325  of the operator interface  500 . Polar support  391  provides a mounting surface for electromagnets  132 X,  132 Y,  132 Z,  138 X,  138 Y, and  138 Z in their appropriate coaxial arrangements as was already described in  FIG. 13 .  
         [0148]      101441  The trunnion  388  is centered on an axis, namely the T-axis  387  depicted in  FIG. 16A . The T-axis encoder  394  is mechanically coupled to the trunnion  388  to encode positional data of the support assembly  385  in the T-axis. A gimbal-axis (G-axis)  386 , depicted in  FIG. 16A , intersects with the T-axis  378  at the center point of the polar support  391 . This center point coincides exactly with the center point of the X-ray field of view. A G-axis encoder  393  is mechanically coupled to the support assembly  385  along the G-axis  386 . A detailed description of the functionality of the above components will follow in the ensuing description.  
         [0149]      FIG. 16  Illustrates the x-ray support assembly  385  and  391  as configured on an anteroposterior projection with 20 degrees of caudal angulation (AP caudal).  FIG. 17  illustrates a general connection of the GCI apparatus  501  to cineangiographic equipment  502 . The cineoangiographic equipment  502  is interfaced with the GCI apparatus  501  through operator interface equipment  500 . The cineoangiography image of an arterial tree is shown on video monitor  325 , with the x-ray image of catheter tip  377  position superimposed. The display of these images is synchronized by the GCI apparatus  501  via the communications controller  320 , and is realized on the monitor  325  of the operator interface  500 .  
         [0150]      FIG. 17A  illustrates forming a stereotactic frame in support of position definition of the catheter tip relative to the frame. This method utilizes fiduciary markers formed as an approximate cube.  
         [0151]     The solution presented herein is a method of capturing the Fluoroscopic Image generated by the x-ray Apparatus and/or ultrasonic imaging technique to create Referential Markers for synchronizing the image of the catheter tip or guide wire, which is generated by the GCI apparatus and superimpose that image onto the fiduciary markers which are represented digitally and are linked dynamically as to create one image which moves in unison with the area of interest. For example, the beating heart and its cardio-output, the pulmonary expansion and contraction, or a spasm of the patient, can be dynamically captured and linked together as to achieve unison motion between the catheter&#39;s tip and the body&#39;s organ in question.  
         [0152]      FIG. 17A  further illustrates the image capture technique of superimposing the fiduciary markers  700 A 1 ,  700 A 2 ,  700 A 3 ,  700 A 4 ,  700 B 1 ,  700 B 2 ,  700 B 3 , and  700 B 4  onto the fluoroscopic/ultrasonic image, generated as shown in image  17 . The scheme provided identifies the dynamic location of the catheter tip  377  with reference to the fluoroscopic/ultrasonic image. The referential frame formed by the fiduciary markers  700 Ax defines the catheter&#39;s tip position relative to the stereotactic frame. Furthermore, by employing a technique of geometric projection this method provides for a synchronized image-capture relative to catheter tip,  377  thereby affording the superimposition of the fluoroscopic/ultrasonic image relative to both the fiduciary markers and the catheter tip on a dynamic basis, hence, providing position definition with a frame of reference.  
         [0153]      FIG. 17B  illustrates the implantation of cardiac pacemaker  801  with electrodes as shown, placed in area relative to the S.A. Node  802 , A.V. Node  803 , and a bundle of His  804 . Further illustrated are the right and left bundle branches  805 . Pacemaker implantation is essential for the survival of patients with heart rhythm or electrical conduction disturbances. This procedure is performed by the implantation of a small electrode in the heart cavity wall (ventricle or atrium). The other end of the electrode is attached to an electronic device  801  which is implanted under the chest skin and which generates stimulation pulses to simulate the heart rhythm. Similar devices apply electrical shock when life threatening heart electrical disturbances are detected by the electrodes (Automatic Implantable Cardiac Defibrillator (AICD). These electrodes are placed through a vein by pushing and manipulating under fluoroscopy. Through the use of the apparatus proposed GCI  501  and guidewire  379  fitted with magnetic tip  381  is used to carry and place the electrodes of pacemaker  801  in its proper position by using the method and apparatus described in this patent. By employing the fiduciary markers  700 A 1 ,  700 A 2 ,  700 A 3 ,  700 A 4 ,  700 B 1 ,  700 B 2 ,  700 B 3 , and  700 B 4  the physician navigates the guidewire  379  through the heart lumen while having a continuous dynamic referential frame identifying the guidewire tip  381  and as shown in  17  and further illustrated by  FIG. 17A . Many times, the manipulation to place the electrodes in a proper position is difficult and the results are sub-optimal due to anatomical variations. The use of the proposed apparatus  501  provides simplicity in performing such a complex operation while the physician is capable of moving, pushing, and placing the electrodes of pacemaker  801  in its precise anatomical position without compromise due to the inability of navigating, guiding, controlling, and imaging the movement of the guidewire and the pacemaker electrodes accurately.  
         [0154]     Having described the constituent components of the GCI apparatus  501 , its general and mathematical operations for controlling the position of the actual catheter tip  377  in relation to adjustments made to the virtual tip  405  and calculations to determine the new location of the actual catheter tip  377  will now be explained with reference to  FIGS. 18 through 23 .  
         [0155]     Upon application of power, the built-in test routines residing in Supervisory Unit (SU)  301 , System Controller (SC)  302 , X-axis controller and amplifier (XCA)  305 , Y-axis controller and amplifier (YCA)  310 , Z-axis controller and amplifier (ZCA)  315 , Communication Controller (CC)  320 , Computer  324 , and Virtual Tip/Calibration Fixture Controller (VT/CFC)  303 , perform a series of self diagnostic tests. In addition, certain tests are performed on a continuous basis in the background. Exemplary background tests include DC power supply voltage and current monitoring, AC voltage and current monitoring and communication tests. These background tests are interleaved between normal functions in a manner that is transparent to the user.  
         [0156]     The results of the test routines are reported to System Controller (SC)  302 . System Controller (SC)  302  compares these results to expected values stored in Non Volatile Memory (NVM)  39  ( FIG. 3 ). Following a test failure or the detection of any anomalous behavior, System Controller (SC)  302  determines the severity of the situation. If an uncorrectable condition exists, System Controller (SC)  302  initiates a graceful power down. If, on the other hand, corrective action can be taken to alleviate or eliminate the problem, System Controller (SC)  302  instructs Computer  324  to sound an alarm, and instructs the monitor  325  to display an error prompt. Any detected failures are also stored as error codes in Non Volatile Memory (NVM)  39  for later review and troubleshooting.  
         [0157]     In one embodiment, the Virtual Tip  405  and the Calibration Fixture (CF)  321  ( FIGS. 5, 6 ,  11 , and  12 ) have  8  inches of travel in the X, Y, and Z axes. This corresponds to the 8″×8″×8″ control area of the polar configuration  374  ( FIG. 13 ). The Virtual Tip  405  and the Calibration Fixture  321  also have 360° of rotation in the θ and elevation axes.  
         [0158]     Stepper motors  55 C,  57 C  59 C,  61 C, and  63 C with the coupled encoders  64 C,  66 C,  68 C,  70 C and  72 C revolve once during an  8 -inch excursion in the X, Y, or Z axes. Stepper motors  55 C,  57 C  59 C,  61 C, and  63 C have, for example, a resolution of  400  half steps per revolution, which equates to a positioning resolution of 0.022″. Additionally, the encoders may have a resolution of 512 bits per revolution, which equates to a measurement resolution of 0.015625″. In the θ and EL axes, the stepper motor resolution may be 0.9° and the encoder resolution may be 0.703125°.  
         [0159]     During calibration, Calibration Fixture (CF)  321  is placed within the polar configuration  374  and connected to Virtual Tip/Calibration Fixture Controller (VT/CFC)  303 . Virtual Tip/Calibration Fixture Controller (VT/CFC)  303  then moves Calibration Fixture (CF)  321  by sending codes to drive stepper motors  55   c,    57   c,    59   c,    61   c,  and  63   c.  Encoders  64   c,    66   c,    68   c,    70   c,  and  72   c  are then read by Calibration Fixture (CF)  321  to determine the present position and orientation of magnet  411 . The position data from the encoders is compared to the position data derived from magnetic field sensor arrays  307 ,  308 ,  312 ,  313 ,  317 , and  318  ( FIGS. 1, 7 ,  8 , and  9 ). The magnetic field sensor arrays  307 ,  308 ,  312 ,  313 ,  317  and  318  responses are thus characterized for the full range of the magnet  411  positions and orientations, and hence for the magnetic catheter tip  377  as well.  
         [0160]     During normal operation, Virtual Tip  405  is connected to Virtual Tip/Calibration Fixture Controller (VT/CFC)  303 . As tip  405  is manipulated, Virtual Tip/Calibration Fixture Controller (VT/CFC)  303  reads encoders  64 ,  66 ,  68 ,  70 , and  72 . The position data obtained from the Virtual Tip  405  is used by the System Controller  302  to determine the desired position (DP) of the actual tip (AT) and to control its motion as defined in the description of  FIG. 23 .  
         [0161]     The electromagnetic field generated by electromagnets  132   x,    132   y,    132   z,    138   x,    138   y,  and  138   z  of  FIG. 13  will produce a resultant force on the actual catheter assembly tip  377  and guidewire assembly tip  381  ( FIGS. 15 and 15 A). This resultant force can be represented by force vector B  600  with a given magnitude and direction. This resultant force vector B together with its constituent vectors are illustrated in  FIG. 18 . Vector B is the resultant vector of the force vectors emanating from the six electromagnets  132   x,    132   y,    132   z,    138   x,    138   y,  and  138   z  together, upon a move command from the XCA  305 , YCA  310  and ZCA  315 . Vector Bx  601  is the projection of Vector B  600  on the X-axis, Vector By  602  is the projection of Vector B  600  on the Y-axis, and Vector Bz  603  is the projection of vector B  600  on the Z-axis. The angles α  604 , β  605 , and δ  606  are the corresponding angles between the vectors B  600  and Bx  601 , vectors B  600  and By  602 , and vectors B  600  and Bz  603 , respectively.  
         [0162]     As stated earlier, and still referring to  FIG. 18 , the magnitude of the force vector B  600  resulting from the electromagnetic field is 
 
 B=√{square root over (Bx     2     +By     2     +Bz     2     )} 
 
 and its direction is given by the three angles below: 
 
α=cos −1    Bx , β=cos −1    By , δa =cos −1   Bz  
 
         [0163]     The force vector B is produced through commands sent from system controller  102  based on: 1) inputs from sensor arrays  307 ,  308 ,  312 ,  313 ,  317 , and  318  processed by XCA  301 , YCA  310  and ZCA  315  on the location of the actual catheter tip  377  within the patient&#39;s body  390 , and 2) inputs from VT/CFC  303  on the desired position of the actual catheter tip  377  as indicated by virtual tip  405  position. A code stored in ROM  40  of system controller  302  ( FIG. 3 ) is processed by microcontroller  33  to generate the constituent vector components Bx  601 , By  602 , and Bz  603  of B  600 . The magnitude of each of these constituent vectors will be translated to the appropriate XCA  305 , YCA  310 , and ZCA  315  to cause changes in modulator outputs, which, in turn, change the electromagnetic field produced by electromagnets  132   x  and  138   x,    132   y  and  138   y  , and  132   z  and  138   z.  The constituent vectors Bx, By and Bz will then be physically realized as electromagnetic fluxes along the X-, Y- and Z-axes and thereby produce a resultant force B  600  on the actual catheter tip  377  to effectively drag it to the desired position.  
         [0164]     The new position of the actual catheter tip  377  is then determined in order to verify that is indeed in the desired position or if further adjustments are necessary or if an obstacle has been encountered. The methods by which system controller  302  determines the new actual catheter tip  377  position will be explained mathematically with reference to  FIGS. 18A through 22 .  
         [0165]     The following notations were assigned to the variables associated with  FIGS. 18A, 19 , and  19 A and will be used in the ensuing discussion: 
        a N : The most distal end of the magnetic element of the actual catheter tip assembly as indicated by its North dipole (see e.g.,  FIG. 18A ).     a S : The proximal end of the magnetic element of the actual catheter tip assembly  377  as indicated by its south dipole (see e.g.,  FIG. 18A ).     a D : Length of the actual catheter tip magnet  377  equal to the distance between the points a N  and a S  (refer to  FIG. 18A ).     X D : Distance between opposite coaxial poles along the x-axis, that is the distance between the polar faces of electromagnets  132   x  and  138   x  (refer to numeral reference  616  in  FIG. 19 ).     −x 1 , −x 2 , −x 3 , −x 4 : MFS and TS pairs  354 ,  355 ,  356 ,  357 , respectively. (see  FIGS. 13 and 19 A).     d: The Distance between each consecutive MFS/TS pair, that is the distance between MFS/TS pair  354  and MFS/TS  355 , MFS/TS  355  and MFS/TS pair  356 , and so forth (refer to  FIG. 19A ).     x 1 , x 2 , x 3 , x 4 : MFS and TS Pairs  350 ,  351 ,  352 ,  353 , respectively (refer to  FIGS. 13 and 19 A).     ROT: The angle of rotation θ in the X-Y plane (refer to numeral reference  625  in  FIG. 21 ).     ELEV: The angle of EL in the X-Z plane (refer to numeral reference  626  in  FIG. 22 ).        
 
         [0175]     The electromagnetic field induced by electromagnets  132   x,    132   y,    132   z,    138   x,    138   y,  and  138   z  of  FIG. 13  produces a resultant force on the actual catheter assembly tip  377  and guidewire assembly tip  381  ( FIGS. 15 and 15 A). This resultant force can be characterized as a force vector with a given magnitude and direction, and is illustrated in  FIG. 18  along with its constituent vectors. Vector B  600  is the resultant vector of the force vectors emanating from the six electromagnets  132   x,    132   y,    132   z,    138   x,    138   y,  and  138   z  together, upon a move command from the XCA  305 , YCA  310  and ZCA  315 . Vector Bx  601  is the projection of Vector B on the X-axis, Vector By  602  is the projection of Vector B on the Y-axis, and Vector Bz  603  is the projection of vector B on the Z-axis. The angles α  604 , β  605 , and δ  606 , are the corresponding angles between the vectors B and Bx, vectors B and By, and vectors B and Bz, respectively.  
         [0176]      FIG. 18A  illustrates one embodiment of a magnetic catheter tip  607 . This magnetic tip  607  corresponds to the combination of the responsive tip  377  of the catheter assembly  375  and the responsive tip  381  of the guidewire assembly  379  ( FIGS. 15 and 15 A). The magnetic tip  607  is represented by its two poles a N ,  607 A and as  607 B in connection with a Virtual Origin  608 . The Virtual Origin  608  is defined by the center of travel of the Virtual Tip (VT)  405  in the X-, Y-, and Z-axes  400 ,  401  and  402  ( FIG. 6 ). The Virtual Origin  608  also coincides with the center of the travel of the calibration magnet  411  in the X-, Y-, and Z-axes  406 ,  407  and  408 , during calibration ( FIG. 12 ). The assumption is that the Virtual Origin  608  is in the center of the x-ray field of view, as well as the center of the sagnetic field sensors (MFS) sensing volume and the center of the electromagnet (EM) control volume. The Virtual Origin  608  also coincides with the center of travel of the Calibration Fixture (CF) in the X, Y, and Z axes, during calibration.  
         [0177]      FIG. 18B  illustrates the resultant position vector An  609  that defines the position of the catheter tip  607  as detected by the magnetic field sensor arrays  307 ,  308 ,  312 ,  313 ,  317 , and  318  and computed by microcontrollers  102   x,    102   y  and  102   z  of XCA  305 , YCA  310  and ZCA  315 . The constituent vectors Xn, Yn, and Zn are the projections of the position vector An on the X-axis, Y-axis and Z-axis, respectively. The angles α  609 A, β  609 B, and γ  609 C, are the projected angles of the vector A N  on the X, Y, and Z axes, respectively. This orthogonal representation corresponds to the polar configuration  374  of  FIG. 16 .  
         [0178]      FIG. 18C  illustrates the angular representation of the resultant position vector of catheter tip  607  in 3 dimensions. The position vector An  609  shown in  FIG. 18B  define the location of a N    607 A which is one of the two poles of the magnetic tip  607 , is projected on the X-Y plane. This projected vector θ XY    615  can be defined by an angle θ X    613  with relation to the X-axis, and an angle θ Y    614  with relation to the Y-axis. The projection on the X-Z plane and Y-Z planes are not shown thus the angular relationship of location a N  with the Z-axis  612  is not shown for purposes of simplicity. These angular relationships of the position vector An defining the location a N , as exemplified by θ X    613  and θ Y    614  are used in the calculations defining the positions of the actual catheter tip  377  as sensed by the magnetic field sensors sensor arrays  307 ,  308 ,  312 ,  313 ,  317 , and  318 . An explanation of these calculations will be provided later.  
         [0179]      FIG. 19  illustrates the distance XD  616  between two opposite faces or poles of the electromagnets. The distance XD is used in calculations made during the operation of the system which will be explained in the following discussion.  
         [0180]      FIG. 19A  illustrates a distance d  617  between two adjacent X-axis magnetic field sensors. Magnetic field sensors −X 1  and −X 2   618  and  619  respectively. Also shown in  FIG. 19A  are two additional magnetic field sensors, −X 3  and −X 4 . The magnetic field sensors −X 1 , −X 2 , −X 3 , −X 4  are the MFS and the temperature sensor (TS) pairs, corresponding to  354 ,  355 ,  356 , and  357 , respectively, and X 1 , X 2 , X 3 , and X 4  are the MFS and TS pairs corresponding to  350 ,  351 ,  352 , and  353 , respectively.  
         [0181]      FIG. 20  illustrates the geometrical process by which the system deduces the true location of the magnetic tip  607  from the data it receives from the magnetic field sensors X 1 , X 2 , X 3 , and X 4 . The resultant vector A  620  is further manipulated by the system to generate position co-ordinates  621  and  622  of the tip  607 , thereby identifying the location of the actual tip  377 . This geometrical process will become apparent in the following discussion.  
         [0182]      FIG. 20A  further illustrates components of the position vectors  622  and  621  obtained by additional mathematical manipulation and calculations done on the signals that are received from the magnetic field sensors X 1 , X 2 , X 3 , and X 4 . The location of the actual tip  377  is defined by the position co-ordinates shown as  621  and  622 . Position  623  is the measured position of the actual catheter tip  377  as determined by the magnetic field sensors X 1 , X 2 , X 3 , and X 4 , and position  624  is its calculated position as determined by the system control  302 . Under ideal conditions, the positions  623  and  624  are equal to each other.  
         [0183]      FIG. 21  illustrates the rotation  625  of the tip  607  around the Z-axis (θ). The rotation is actually an arc motion occurring or oscillating in the X-Y plane.  FIG. 22  illustrates the translation  626  of the tip  607  in the Z-axis.  
         [0184]     The system controller (SC)  302  deduces the location of the actual catheter tip  377  from the signals generated by the magnetic field sensor arrays  307 ,  308 ,  312 ,  313 ,  317 , and  318 . This is done as described in the following paragraphs.  
         [0185]     The following notations are assigned to the variables associated with  FIGS. 18A, 19 , and  19 A: 
        a N : North direction.     a S : South direction.     a D : Length of Tip Magnet.     X D : Distance between opposite Poles  132   x  to  138   x.       −x 1 , −x 2 , −x 3 , −x 4 : MFS and TS pairs  354 ,  355 ,  356 ,  357 , respectively.     d: The Distance between magnetic field sensors and temperature sensor pairs  354  and  355 , etc.     x 1 , x 2 , x 3 , x 4 : MFS and TS Pairs  350 ,  351 ,  352 ,  353 , respectively.     ROT: θ AXIS     ELEV: EL AXIS        
 
         [0195]     With reference to  FIGS. 18   a,    18   b,  and  18   c,  the positions of the actual tips  377  are defined by the orthogonal vectors a N , A N  and as, A S . These orthogonal vectors are the resultant vectors of their constituent x, y and z components: 
 
 A   N =( Xn, Yn, Zn ), 
 
         [0196]     where Xn, Yn, and Zn are the projections of orthogonal vector A N  on the X, Y, and Z axes (refer to  FIG. 18B ), and, 
 
 A   S =( Xs, Ys, Zs ) 
 
 where Xs, Ys and Zs are the projections of orthogonal vector A S  on the X-, Y-, and Z-axes, respectively. 
 
         [0197]     The directions of orthogonal vectors A N  and A S  from the origin are defined by the following angles (refer to  FIG. 18B ): 
        α is the angle to the X axis;     β is the angle to the Y axis; and     γ is the angle to the Z axis.        
 
         [0201]     Similarly, the directions of the vector B are shown in  FIG. 18  and defined by the three angles: α, β, and γ.  
         [0202]     The distance of the vector A N  from the virtual origin to the point a N    607 A ( FIG. 18C ) is calculated by the following equation: 
 
 a   N   =√{square root over (Xn     2     +Yn     2     +Zn     2     )},  
 
         [0203]     and the angles defining the direction of vector AN are calculated by the following equations:  
       α   =         cos     -   1       ⁡     [     Xn   An     ]       =       cos     -   1       ⁡     [     Xn         Xn   2     +     Yn   2     +     Zn   2           ]             
       β   =         cos     -   1       ⁡     [     Yn   An     ]       =       cos     -   1       ⁡     [     Yn         Xn   2     +     Yn   2     +     Zn   2           ]             
       Υ   =         cos     -   1       ⁡     [     Zn   An     ]       =       cos     -   1       ⁡     [     Zn         Xn   2     +     Yn   2     +     Zn   2           ]             
 
         [0204]     With three orthogonal planes shown in  FIG. 18C  on which the positional vector A N  is projected, producing the constituent vectors in each plane and their respective angles. The vectors in these three planes, X-Y, X-Z, and Y-Z are as follows:  
         [0205]     In the X-Y plane the angles of the projected vector θxy with respect to the X-axis and the Y-axis (refer to  FIG. 18C ) are expressed as follows:  
           θ   ⁢           ⁢   x     =     arctan   ⁡     (     Xn   Yn     )         ,   and       
           θ   ⁢           ⁢   y     =     arctan   ⁡     (     Yn   Xn     )         ,       
 
 where the magnitude of the projected vector Oxy in the X-Y plane is: 
 
 Axy=√{square root over (Xn     2     +Yn     2     )}.  
 
         [0206]     Similarly, the angles of the projected vector θxy with respect to the X-axis and the Z-axis are expressed as follows:  
           θ   ⁢           ⁢   x     =     arctan   ⁡     (     Xn   Zn     )         ,   and       
           θ   ⁢           ⁢   z     =     arctan   ⁡     (     Zn   Xn     )         ,       
 
         [0207]     and the magnitude of the projected vector θxz in the X-Z plane is: 
 
 Axz=√{square root over (Xn     2     +Zn     2     )}.  
 
         [0208]     Similarly, the angles of the projected vector Oxy with respect to the Y-axis and the Z-axis are expressed as follows:  
           θ   ⁢           ⁢   y     =     arctan   ⁡     (     Yn   Zn     )         ,   and       
         θz   =     arctan   ⁡     (     Zn   Yn     )         ,       
 
 and the magnitude of the projected vector θyz in the Y-Z plane is: 
 
 Ayz=√{square root over (Yn     2     +Zn     2     )}.  
 
         [0209]     It should be noted that the mathematical solution of the vector A S =(X S ,Y S ,Z S ) follows the mathematical solution of the vector A N =(X N ,Y N ,Z N ).  
         [0210]     As shown in  FIG. 18A , if the distance D  607  between a N  and a S  is known, then: 
 
 D =√{square root over (( Xn−Xs ) 2 +( Yn−Ys ) 2 +( Yn−Ys ) 2 )}
 
         [0211]     To illustrate how system controller  302  determines the position of the actual catheter tip, the calculations used by microprocessor  102   x  of XCA  305  with respect to the X-axis and the virtual origin  608  will now be described, with the understanding that microprocessors  102   y  of YCA  310  and  102   z  of ZCA  315  will perform similar calculations, with each generating positional data concerning the Y- and Z-axes, respectively.  
         [0212]     The transfer functions of the co-planar magnetic field sensors (x 1 , x 2 , x 3 , x 4 ) are known from the calibration routine (fx 1 , fx 2 , fx 3 , fx 4 ) as shown in  FIG. 20 , and they are as follows: 
 
 −X   1 =−( V   −x     1   ( f   −x     1   ))+ X   1 =( V   −x     1   ( f   −x     1   )) 
 
 −X   2 =−( V   −x     2   ( f   −x     2   ))+ X   2 =( V   −x     2   ( f   −x     2   )) 
 
 −X   3 =−( V   −x     3   ( f   −x     3   ))+ X   3 =( V   −x     3   ( f   −x     3   )) 
 
 −X   4 =−( V   −x     4   ( f   −x     4   ))+ X   4 =( V   −x     4   ( f   −x     4   )) 
 
         [0213]     Each MFS/TS pair  354 ,  355 ,  356 ,  357  mounted on the polar face of electromagnet  138   x  will provide location data to microprocessor  102   x  of XCA  305 . The measured distance to a N    607 A, for example, from MFS/TS pair  354  will be referred to as (−x 1 ); the distance measured by MFS/TS pair  355  will be referred to as (−x 2 ); the distance measured by MFS/TS pair  356  will be referred to as (−x 3 ); the distance measured by MFS/TS pair  357  will be referred to as (−x 4 ).  
         [0214]     Likewise, each MFS/TS pair  350 ,  351 ,  352 ,  353  mounted on the polar face of electromagnet  132   x  will provide location data to microprocessor  102   x  of XCA  305 . The measured distance of a N    607 A from MFS/TS pair  350  will be referred to as (+x 1 ); the distance measured by MFS/TS pair  351  will be referred to as (+x 2 ); the distance measured by MFS/TS pair  352  will be referred to as (+x 3 ); the distance measured by MFS/TS pair  353  will be referred to as (+x 4 ).  
         [0215]     Since the MFS/TS pairs are arranged in a quadrant around the central X-axis, the individually measured distances of each MFS/TS temperature sensor are combined mathematically to determine the distance along the x-axis itself. This is done by determining a positional vectors Ax 1 x 2 , Ax 2 x 3 , Ax 3 x 4 , and Ax 1 x 4 . With reference to  FIG. 20 , the magnitude of positional vector Ax 2 x 3 , for example, is given by the following equation:  
           Ax   2     ⁢     x   3       =           x   2     ⁢     x   3     ⁢     Sin   ⁡     (     θ   ⁢           ⁢     x   2     ⁢     x   3       )         d     .         
 
         [0216]     The magnitude of the positional vectors Ax 1 x 2 , Ax 3 x 4 , and Ax 1 x 4  are calculated in a similar way.  
         [0217]     In addition, as shown in  FIG. 20A , the angle θx 1 x 2 , which, for example, is the sum of the angles between Ax 1 x 2  and x 1  and Ax 1 x 2  and x 2, gives the direction of Ax   1 x 2  as follows:  
         θ   ⁢           ⁢     x   1     ⁢     x   2       =       cos     -   1       ⁡     (         d   2     -     x   1   2     -     x   2   2         2   ⁢     x   1     ⁢     x   2         )           
 
         [0218]     The numerical solution, is graphically shown in  FIG. 20A  is achieved by using the canonical formalism described below. It should be noted that this numerical solution is performed in for example in a background mode by microprocessor  102   x  of XCA  305  and similarly for y axis and z axis.  
           hx   1     ⁢     x   2       =         x   1     ⁢     x   2     ⁢     sin   ⁡     (     θ   ⁢           ⁢     x   1     ⁢     x   2       )         d         
           Bx   1     ⁢     x   2       =         x   1   2     -       hx   1     ⁢     x   2   2               
         θ   ⁢           ⁢     x   2     ⁢     x   3       =       cos     -   1       ⁡     (         d   2     -     x   2   2     -     x   3   2         2   ⁢     x   2     ⁢     x   3         )           
           Ax   2     ⁢     x   3       =         x   2     ⁢     x   3     ⁢     Sin   ⁡     (     θ   ⁢           ⁢     x   2     ⁢     x   3       )         d         
           Bx   2     ⁢     x   3       =         x   2   2     -       hx   2     ⁢     x   3               
           P   B     ⁢     x   1       =           x   1           B         ⁢     x   2   2       +       x   2           B         ⁢     x   3   2               
           Ax   1     ⁢     x   2       =         x   1   2     -       P   B     ⁢     x   1   2               
 
 The angles of θx 2 x 3, θx   3 x 4 , and θx 1 x 4  are calculated in a similar way. 
 
         [0219]     Based on the distances Ax 1 x 2 , Ax 2 x 3 , Ax 3 x 4 , and Ax 1 x 4  from the polar face  138   x  to the point a N , an average distance (−x n ) is determined as follows:  
         -   x     =       (         (       -     x   1       -       x   2     ⁢   A       )     +     (       -     x   2       -       x   3     ⁢   A       )     +     (       -     x   3       -       x   4     ⁢   A       )     +     (       -     x   4       -       x   1     ⁢   A       )       4     )     .         
 
         [0220]     Likewise, the distance from the polar face  132   x  to the point a N  is determined as follows:  
         +   x     =       (           x   1     ⁢     x   2     ⁢   A     +       x   2     ⁢     x   3     ⁢   A     +       x   3     ⁢     x   4     ⁢   A     +       x   4     ⁢     x   1     ⁢   A       4     )     .         
 
         [0221]     In one embodiment, when weighting the averages by using more accurate sensors yields better results (as determined during calibration), then a weighted average is used.  
         [0222]     The distance of a N  from the virtual origin  608  is determined since the virtual origin is the common point of reference between the VT assembly  304  and the calibration fixture (CF)  321 . These distances are given for the three axes by the following sets of equations, where X D    616  is the distance between two coaxial electromagnets  132   x  and  138   x  (refer to  FIG. 19 ), Y D  is the distance between two coaxial electromagnets  132   y  and  138   y,  and Z D  is the distance between two coaxial electromagnets  132   z  and  138   z:   
           X   D     2     +     (     -   X     )         
           X   D     2     +     (     +   X     )         
       where   ⁢     :         
           (         X   D     2     +     (     -   X     )       )     +     (         X   D     2     +     (     -   X     )       )       =     X   D         
 
         [0223]     The same calculations apply to the y and z axes positions and with the three axes positions known will yield an absolute position. Therefore, relative to the virtual origin:  
       Xn   =     {                   X   D     2     -     (     -   Xn     )                   (     +   Xn     )     -       X   D     2             ⁢           ⁢   Xs     =     {                   X   D     2     -     (     -   Xs     )                   (     +   Xs     )     -       X   D     2             ⁢     
     ⁢   Yn     =     {                   Y   D     2     -     (     -   Yn     )                   (     +   Yn     )     -       Y   D     2             ⁢           ⁢   Ys     =     {                   Y   D     2     -     (     -   Ys     )                   (     +   Ys     )     -       Y   D     2             ⁢     
     ⁢   Zn     =     {                   Z   D     2     -     (     -   Zn     )                   (     +   Zn     )     -       Z   D     2             ⁢           ⁢   Xs     =     {               Z   D     2     -     (     -   Zs     )                   (     +   Zs     )     -       Z   D     2                                       
 
         [0224]     The system controller  302  deduces the following from the calculations to determine the center point of the magnetic element of the actual catheter tip:  
       Xc   =       Xn   -   Xs     2         
       Yc   =       Yn   -   Ys     2         
       Zc   =       Zn   -   Zs     2         
 
         [0225]     Thus the GCI apparatus  501  derives the rotation in the X-Y plane as follows:  
       RotC   =       tan     -   1       ⁡     (       Yn   -   Ys       Xn   -   Xs       )           
 
 and the elevation in the X-Z plane as follows:  
       elevC   =       tan     -   1       ⁡     (       Zn   -   Zs       Xn   -   Xs       )           
 
         [0226]     Using these results, system controller  302  can compare the actual catheter tip  377  location to the desired tip location.  FIG. 23  illustrates a logical computational flow taken by the system controller (SC)  302  in determining the position of the actual tip  377 , using the following mathematical relations: 
        1. System Controller (SC)  302  inhibits X-axis controller and amplifier (XCA)  305 , Y-axis controller and amplifier (YCA)  310 , and Z-axis controller and amplifier (ZCA)  315  modulator outputs.     2. X-axis controller and amplifier (XCA)  305 , Y-axis controller and amplifier (YCA)  310 , and Z-axis controller and amplifier (ZCA)  315  read the magnetic field sensor array  307 ,  308 ,  312 ,  313 ,  317 , and  318  outputs.     3. X-axis controller and amplifier (XCA)  305 , Y-axis controller and amplifier (YCA)  310 , and Z-axis controller and amplifier (ZCA)  315  read temperature sensor (TS) array  306 ,  309 ,  311 ,  314 ,  316 , and  319  outputs.     4. X-axis controller and amplifier (XCA)  305 , Y-axis controller and amplifier (YCA)  310 , and Z-axis controller and amplifier (ZCA)  315  apply digital temperature compensation to the outputs of the magnetic field sensor arrays  307 ,  308 ,  312 ,  313 ,  317 , and  318  by referring to correction data (typically stored in Non Volatile Memory  105   x,    105   y,  and  105   z ).     5. System Controller (SC)  302  inputs the corrected magnetic field sensor data from X-axis controller and amplifier (XCA)  305 , Y-axis controller and amplifier (YCA)  310 , and Z-axis controller and amplifier (ZCA)  315 , and interpolates a 5-axis data set from the three orthogonal components (Bx, By, Bz) of the magnetic field produced by the actual tip. The tip position is calculated using the following two relations: 
            a) The magnitude of the force vector B  600  is given by the equation: 
 
 B=√{square root over (Bx     2     +By     2     +Bz     2     )}; and  
    b) the direction of the force vector B is given by the three resultant angles, as:  
         α   =         cos     -   1       ⁢   Bx     B       ,     β   =         cos     -   1       ⁢   By     B       ,     δ   =         cos     -   1       ⁢   Bz     B           
   
            6. System Controller (SC)  302  inputs the cardio position (CP) from the auxiliary equipment (x-ray, ultrasound, etc)  322  via Communication Controller (CC)  320 . The cardio position (CP) data set is dynamic due to the beating of the heart.     7. System Controller (SC)  302  calculates the actual position (AP) by combining the cardio position (CP) and the HP data sets.     8. System Controller (SC)  302  inputs Virtual Tip  405  position data from Virtual Tip/Calibration Fixture Controller (VT/CFC)  303 .     9. System Controller (SC)  302  calculates the DP by combining the cardio position (CP) data set with that of the Virtual Tip (VT).     10. System Controller (SC)  302  then determines the position error (PE) by comparing the DP with the AP.     11. If the position error PE is less than an error threshold value, then the System Controller (SC)  302  enables X-axis controller and amplifier (XCA)  305 , Y-axis controller and amplifier (YCA)  310  and Z-axis controller and amplifier (ZCA)  315  with the continues to use the same modulation and polarity.     12. If the position error PE is greater than the error threshold value, then the System Controller SC  302  alters the duty cycle and/or polarity of the modulation inputs to XCA  305 , YCA  310 , and ZCA  315  accordingly.        
 
         [0241]     The System Controller (SC)  302  controls the stepper motors  55 ,  57 ,  59 ,  61 , and  63  via the Virtual Tip/Calibration Fixture Controller (VT/CFC)  303  to produce tactile feedback if the position error (PE) exceeds a predetermined amount in a predetermined time in any axis or axes, thereby notifying the operator of an obstruction encountered by the catheter tip. That is, it is assumed that if the PE is not eliminated by the normal operation of the GCI apparatus  501  within an expected amount of time or cycles of steps 1 through 12 above, then an obstacle is likely to have been encountered by the actual catheter tip. This is perceived by the operator through tactile feedback generated by resistance produced the stepper motors  55 ,  57 ,  59 ,  61 , and  63  acting on the virtual tip  405 .  
         [0242]     The operation of the virtual tip  405  is relatively simple and intuitive to the user or surgeon. The surgeon simply pushes, pulls, or rotates the virtual tip  405  in the desired direction to cause a similar movement of the catheter tip  377  within the patient&#39;s body. If an obstruction is encountered by the catheter tip  377 , the virtual tip  405  responds with tactile feedback in the form of resistance to movement in the appropriate axis or axes. Thus, the surgeon can “feel” the actual tip as it is advanced. When tip  405  is released, the catheter tip  377  is forcefully held in its current position. System Controller (SC)  302  correlates the AT position with CP data obtained from auxiliary equipment  322  and via CC  320  it communicates with PC  324  in order to present monitor  325  with the combined tip and x-ray/ultrasonic imagery. The display of the three-dimensional AT position is continuously updated on a real-time basis with HP data. Relatively fewer frames of x-ray imagery are used to overlay the display with CP data. This correlation of AT and CP data is possible because the x-ray and the MFS arrays have a common reference point (i.e., both are stationary relative to the beating heart).The present technique significantly reduces x-ray exposure to the patient and staff while providing a superior method of observing the heart and catheter tip  377 .  
         [0243]     Accordingly, it can be seen that the new catheter guidance and control apparatus and method provide an arrangement which is: relatively easy to use effectively; requires minimal training to master; rapidly advances and accurately positions the catheter tip; requires fewer types of catheters; forcefully fixates the catheter tip in the desired position; steers a guidewire through a torturous path; forcefully advances a guidewire or balloon through plaque; displays the catheter tip position in three dimensions; significantly reduces the amount of contrast material the patient is exposed to; significantly reduces the amount of X-radiation the patient and medical staff are exposed to; is intuitive to use; and produces tactile feedback to indicate when the catheter tip encounters an obstruction.  
         [0244]     Although the preceding description contains much specificity, this should not be construed as limiting the scope of the invention, but as merely providing illustrations of embodiments thereof. Many other variations are possible within the scope of the present invention. For example, the modulation of the electromagnets can be controlled in such a way as to cause a vibratory or pulsating motion of the tip to aid in crossing plaque; the responsive tip(s) can be electromagnetic rather than permanent magnets; the magnetic field external to the body can be generated by a permanent magnet or magnets; the control of the external magnetic field can be accomplished by manually administering the field generating devices; AC induction with its associated magnetic effects can be utilized by causing a coil or coils wound around the tip to respond to an impressed time variant field; materials with Curie temperatures within a few degrees of body temperature can be used as magnetic flux switches for selective tip control by irrigating them with fluids having appropriate temperatures; electrostatic phenomena can enhance magnetic effects; artificial intelligence can replace the operator control for producing command inputs; an expert system can replace or augment operator inputs; the apparatus can be used to incubate various body cavities and organs other than the heart; the apparatus can be used for human and animal procedures such as egg harvesting and embryo implantation; the responsive tip can be attached to a coherent fiber optic bundle to provide viewing of internal structures with unprecedented maneuverability; internal radioisotope therapy can be precisely performed by delivering a palletized source directly to a tumor using a guided catheter; internal tissue samples can be obtained without major surgery; a fiber optic light guide equipped with a responsive tip can be accurately positioned to deliver laser light to a specific internal location without major surgery; previously difficult liposuction and other subcutaneous surgical procedures can be performed accurately, and so forth. Thus, the scope of the invention is limited only by the claims.