US20010047133A1 - Imaging device with magnetically permeable compensator - Google Patents

Abstract

A system and method for tracking the position and orientation of a probe such as a catheter whose transverse inner dimension may be at most about two millimeters. Three planar antennas that at least partly overlap are used to transmit electromagnetic radiation simultaneously, with the radiation transmitted by each antenna having its own spectrum. In the case of single-frequency spectra, the antennas are provided with mechanisms for decoupling them from each other. A receiver inside the probe includes sensors of the three components of the transmitted field, with sensors for at least two of the three components being pairs of sensors, such as coils, disposed symmetrically with respect to a common reference point. In one variant of the receiver, the coils are collinear and are wound about cores that are mounted in pairs of diametrically opposed apertures in the housing of the probe. In another variant of the receiver-catheter combination, the catheter is configured with an inner and outer sleeve connected at their ends by one or more flexible elements on which the coils are mounted. Each member of a pair of coils that sense the same component of the transmitted field is connected to a different input of a differential amplifier. The position and orientation of the receiver relative to the antennas are determined noniteratively, by setting up an overdetermined set of linear equations that relates the received signals to transmitter-receiver amplitudes, solving for the amplitudes and inferring the position coordinates and the orientation angles of the receiver relative to the transmitter from these amplitudes. For the purpose of navigating the probe within the body of a patient, the antennas are rigidly attached to an imaging device such as a fluoroscope, to provide a common frame of reference for both the acquired images of the patient and the measured position and orientation of the receiver. Alternatively, a second receiver is rigidly attached to the imaging device to provide the common frame of reference. In a third alternative, a third receiver is rigidly attached to the patient during imaging, and the mutual positions and orientations of the patient and the imaging device thus measured are used in subsequent navigation of the probe within the body of the patient. An imaging device that includes an electrically conductive surface is provided with a magnetically permeable compensator for minimizing distortion of the transmitted field. A scheme is provided for retrofitting an apparatus such as the receiver to a prior art catheter.

Description

• This is a Divisional of U.S. Ser. No. 09/463,177, pending.[0001]
FIELD AND BACKGROUND OF THE INVENTION
• The present invention relates to electromagnetic tracking devices and, more particularly, to a system and method for tracking a medical probe such as a catheter as the probe is moved through the body of a patient.[0002]
• It is known to track the position and orientation of a moving object with respect to a fixed frame of reference, by equipping the moving object with a transmitter that transmits electromagnetic radiation, placing a receiver in a known and fixed position in the fixed frame of reference, and inferring the continuously changing position and orientation of the object from signals transmitted by the transmitter and received by the receiver. Equivalently, by the principle of reciprocity, the moving object is equipped with a receiver, and a transmitter is placed in a known and fixed position in the fixed frame of reference. Typically, the transmitter includes three orthogonal magnetic dipole transmitting antennas; the receiver includes three orthogonal magnetic dipole receiving sensors; and the object is close enough to the stationary apparatus (transmitter or receiver), and the frequencies of the signals are sufficiently low, that the signals are near field signals. Also typically, the system used is a closed loop system: the receiver is hardwired to, and explicitly synchronized with, the transmitter. Representative prior art patents in this field include US 4,287,809 and U.S. Pat. No. 4,394,831, to Egli et al.; U.S. Pat. No. 4,737,794, to Jones; U.S. Pat. No. 4,742,356, to Kuipers; U.S. Pat. No. 4,849,692, to Blood; and U.S. Pat. No. 5,347,289, to Elhardt. Several of the prior art patents, notably Jones, present non-iterative algorithms for computing the position and orientation of magnetic dipole transmitters with respect to magnetic dipole receivers.[0003]
• An important variant of such systems is described in U.S. Pat. No. 5,600,330, to Blood. In Blood's system, the transmitter is fixed in the fixed reference frame, and the receiver is attached to the moving object. Blood's transmitting antennas are spatially extended, and so cannot be treated as point sources. Blood also presents an algorithm which allows the orientation, but not the position, of the receiver relative to the transmitter to be calculated non-iteratively.[0004]
• Systems similar to Blood's are useful for tracking a probe, such as a catheter or an endoscope, as that probe is moved through the body of a medical patient. It is particularly important in this application that the receiver be inside the probe and that the transmitter be external to the patient, because transmitting antennas of sufficient power would not fit inside the confined volume of the probe. A representative prior art system of this type is described in PCT[0005]Publication WO 96/05768, entitled “Medical Diagnosis, Treatment and Imaging Systems”, which is incorporated by reference for all purposes as if fully set forth herein. Medical applications of such systems include cismyocardial revascularization, balloon catheterization, stent emplacement, electrical mapping of the heart and the insertion of nerve stimulation electrodes into the brain.
• Perhaps the most important application of this tracking is to intrabody navigation, as described by Acker in U.S. Pat. No. 5,729,129, with reference to PCT Publication No. WO 95/09562. A three-dimensional image, such as a CT or MRI image, of the patient is acquired. This image includes fiducial markers at predetermined fiducial points on the surface of the patient. Auxiliary receivers similar to the receiver of the probe are placed at the fiducial points. The signals received by the auxiliary receivers are used to register the image with respect to the transmitter frame of reference, so that an icon that represents the probe can be displayed, superposed on a slice of the image, with the correct position and orientation with respect to the image. In this way, a physician can see the position and orientation of the probe with respect to the patient's organs.[0006]
• WO 96/05768 illustrates another constraint imposed on such systems by the small interior dimensions of the probe. In most prior art systems, for example, the system of Egli et al., the receiver sensors are three concentric orthogonal coils wound on a ferrite core. The coils are “concentric” in the sense that their centers coincide. Such a receiver of sufficient sensitivity would not fit inside a medical probe. Therefore, the sensor coils of[0007]WO 96/05768 are collinear: the three orthogonal coils are positioned one behind the other, with their centers on the axis of the probe, as illustrated in FIG. 3 ofWO 96/05768. This reduces the accuracy of the position and orientation measurements, because instead of sensing three independent magnetic field components at the same point in space, this receiver senses three independent magnetic field components at three different, albeit closely spaced, points in space.
• A further, consequent concession of the system of[0008]WO 96/05768 to the small interior dimensions of a catheter is the use of coils wound on air cores, rather than the conventional ferrite cores. The high mutual coupling of collinear coils wound on ferrite cores and measuring three independent field components at three different points in space would distort those measurements sufficiently to make those measurements fatally nonrepresentative of measurements at a single point.
• Another drawback of the system of[0009]WO 96/05768 relates to the geometry of the transmitter antennas. These are three nonoverlapping flat coplanar coils, preferably arranged in a triangle. Because the strength of the field transmitted by one of these coils falls as the reciprocal cube of the distance from the coil, the receiver usually senses fields of very disparate strength, which further degrades the accuracy of the position and orientation measurements. Acker addresses this problem by automatically boosting the power supplied to transmitting coils far from the receiver. In U.S. Pat. No. 5,752,513, Acker et al. address this problem by overlapping the coplanar transmitting coils.
• Acker et al. transmit time-multiplexed DC signals. This time multiplexing slows down the measurement. Frequency multiplexing, as taught in[0010]WO 96/05768, overcomes this problem, but introduces a new problem insofar as the transmitting coils are coupled by mutual inductance at non-zero transmission frequency, so that the transmitted field geometry is not the simple geometry associated with a single coil, but the more complex geometry associated with several coupled coils. This complicates and slows down the calculation of the position and orientation of the receiver relative to the transmitter coils. PCT Publication WO 97/36143, entitled “Mutual Induction Correction”, addresses this problem by generating, at each transmitter coil, counter-fields that cancel the fields generated by the other transmitter coils.
• A further source of slowness in calculating the position and orientation of the receiver is the iterative nature of the calculation required for a spatially extended transmitter. As noted above, Blood calculates the position of the receiver iteratively. Even in the DC case, Acker et al. calculate both the position and the orientation of the receiver iteratively.[0011]
• There is thus a widely recognized need for, and it would be highly advantageous to have, a faster and more accurate method for tracking a medical probe inside the body of a patient.[0012]
SUMMARY OF THE INVENTION
• According to the present invention there is provided a system for tracking a position and an orientation of a probe, including a plurality of first sensors, each of the first sensors for detecting a different component of a vector force field, each of the first sensors including two sensor elements disposed symmetrically about a common reference point in the probe, the first sensors being mounted inside the probe.[0013]
• According to the present invention there is provided a method for determining a position and an orientation of an object with respect to a reference frame, including the steps of: (a) providing the object with three independent sensors of electromagnetic radiation; (b) providing three independent transmitting antennas of the electromagnetic radiation, each of the transmitting antennas having a fixed position in the reference frame, at least one of the transmitting antennas being spatially extended; (c) transmitting the electromagnetic radiation, using the transmitting antennas, a first of the transmitting antennas transmitting the electromagnetic radiation of a first spectrum, a second of the transmitting antennas transmitting the electromagnetic radiation of a second spectrum independent of the first spectrum, and a third of the transmitting antennas transmitting the electromagnetic radiation of a third spectrum independent of the first spectrum; (d) receiving signals corresponding to the electromagnetic radiation, at all three of the sensors, at a plurality of times, in synchrony with the transmitting of the electromagnetic radiation; and (e) inferring the position and the orientation of the object noniteratively from the signals.[0014]
• According to the present invention there is provided a system for determining a position and an orientation of an object, including: (a) a plurality of at least partly overlapping transmitter antennas; (b) a mechanism for exciting the transmitter antennas to transmit electromagnetic radiation simultaneously, the electromagnetic radiation transmitted by each of the transmitter antennas having a different spectrum; (c) at least one electromagnetic field sensor, associated with the object, operative to produce signals corresponding to the electromagnetic radiation; and (d) a mechanism for inferring the position and the orientation of the object from the signals.[0015]
• According to the present invention there is provided a system for determining a position and an orientation of an object, including: (a) a plurality of at least partly overlapping transmitter antennas; (b) a mechanism for exciting each of the transmitter antennas to transmit electromagnetic radiation of a certain single independent frequency and phase, the mechanism including, for each of the transmitter antennas, a mechanism for decoupling the each transmitter antenna from the electromagnetic radiation transmitted by every other transmitter antenna; (c) at least one electromagnetic field sensor, associated with the object, operative to produce signals corresponding to the electromagnetic radiation; and (d) a mechanism for inferring the position and the orientation of the object from the signals.[0016]
• According to the present invention there is provided a catheter, including: (a) a housing having a transverse inner dimension of at most about two millimeters; and (b) at least one coil, wound about a solid core, mounted inside the housing.[0017]
• According to the present invention there is provided a system for navigating a probe inside a body, including: (a) a receiver of electromagnetic radiation, inside the probe; (b) a device for acquiring an image of the body; and (c) a transmitter, of the electromagnetic radiation, including at least one antenna rigidly attached to the device so as to define a frame of reference that is fixed with respect to the device.[0018]
• According to the present invention there is provided a system for navigating a probe inside a body, including: (a) a first receiver of electromagnetic radiation, inside the probe; (b) a device for acquiring an image of the body; and (c) a second receiver, of the electromagnetic radiation, rigidly attached to the device so as to define a frame of reference that is fixed with respect to the device.[0019]
• According to the present invention there is provided a method of navigating a probe inside a body, including the steps of: (a) providing a device for acquiring an image of the body; (b) simultaneously: (i) acquiring the image of the body, and (ii) determining a position and orientation of the probe with respect to the image; and (c) displaying the image of the body with a representation of the probe superposed thereon according to the position and the orientation.[0020]
• According to the present invention there is provided a device for sensing an electromagnetic field at a point, including at least four sensing elements, at least two of the sensing elements being disposed eccentrically with respect to the point.[0021]
• According to the present invention there is provided a method for determining a position and an orientation of an object with respect to a reference frame, including the steps of: (a) providing the object with three independent sensors of electromagnetic radiation; (b) providing three independent transmitting antennas of the electromagnetic radiation, each of the transmitting antennas having a fixed position in the reference frame, at least one of the transmitting antennas being spatially extended; (c) transmitting the electromagnetic radiation, using the transmitting antennas, a first of the transmitting antennas transmitting the electromagnetic radiation of a first spectrum, a second of the transmitting antennas transmitting the electromagnetic radiation of a second spectrum independent of the first spectrum, and a third of the transmitting antennas transmitting the electromagnetic radiation of a third spectrum independent of the first spectrum; (d) receiving signals corresponding to the electromagnetic radiation, at all three of the sensors, at a plurality of times, in synchrony with the transmitting of the electromagnetic radiation; (e) setting up an overdetermined set of linear equations relating the signals to a set of amplitudes, there being, for each of the sensors: for each transmitting antenna: one of the amplitudes; and (f) solving the set of linear equations for the amplitudes.[0022]
• According to the present invention there is provided a method of navigating a probe inside a body, including the steps of: (a) providing a device for acquiring an image of the body; (b) simultaneously: (i) acquiring the image of the body, and (ii) determining a position and an orientation of the body with respect to the image; (c) determining a position and an orientation of the probe with respect to the body; and (d) displaying the image of the body with a representation of the probe superposed thereon according to both of the positions and both of the orientations.[0023]
• According to the present invention there is provided a device for sensing an electromagnetic field at a point, including: (a) two sensing elements, each of the sensing elements including a first lead and a second lead, the first leads being electrically connected to each other and to ground; and (b) a differential amplifier, each of the second leads being electrically connected to a different input of the differential amplifier.[0024]
• According to the present invention there is provided a catheter including: (a) an outer sleeve having an end; (b) an inner sleeve having an end and slidably mounted within the outer sleeve; (c) a first flexible member connecting the end of the outer sleeve to the end of the inner sleeve; and (d) a first coil mounted on the first flexible member.[0025]
• According to the present invention there is provided a system for determining a position and an orientation of an object, including:(a) at least one transmitter antenna for transmitting an electromagnetic field; (b) a first electromagnetic field sensor, associated with the object and including two sensing elements responsive to a first component of the transmitted electromagnetic field, each of the sensing elements including a first lead and a second lead, the first leads being electrically connected to each other and to ground; and (c) a first differential amplifier, each of the second leads being electrically connected to a different input of the first differential amplifier.[0026]
• According to the present invention there is provided an imaging device, including: (a) an electrically conducting surface; (b) a magnetically permeable compensator; and (c) a mechanism for securing the compensator relative to the surface so as to substantially suppress a distortion of an external electromagnetic field caused by the surface.[0027]
• According to the present invention there is provided a device for sensing an electromagnetic field, including: (a) a housing, including a first pair of diametrically opposed apertures, (b) a first core mounted in the first pair of apertures; and (c) a first coil of electrically conductive wire wound about the core.[0028]
• According to the present invention there is provided a probe for interacting with a body cavity, including: (a) a substantially cylindrical catheter; (b) a satellite; and (c) a mechanism for reversibly securing the satellite at a fixed position and orientation relative to the catheter after the catheter and the satellite have been inserted into the body cavity.[0029]
• Each receiver sensor of the present invention includes two sensor elements placed symmetrically with respect to a reference point inside the probe. All the sensor element pairs share the same reference point, so that the measured magnetic field components are representative of the field component values at the single reference point, instead of at three different points, as in the prior art system, despite the confined transverse interior dimensions of the probe. Because of the symmetric disposition of the sensor elements with respect to the reference point, the measured magnetic field components are representative of the field components at the reference point, despite the individual sensing elements not being centered on the reference point. This property of not being centered on the reference point is termed herein an eccentric disposition with respect to the reference point.[0030]
• In one preferred embodiment of the receiver of the present invention, the sensor elements are helical coils. Within each sensor, the coils are mutually parallel and connected in series. As in the case of the prior art receivers, the coils are arranged with their centers on the axis of the probe. To ensure that coils of different sensors are mutually perpendicular, the probe housing includes mutually perpendicular pairs of diametrically opposed apertures formed therein, the coils whose axes are perpendicular to the axis of the probe are wound about cores whose ends extend past the ends of the respective coils, and the ends of the cores are mounted in their respective apertures.[0031]
• In another preferred embodiment of the receiver of the present invention, with three sensors, the sensor elements are flat rectangular coils bent to conform to the shape of the cylindrical interior surface of the probe. The sensor elements of the three sensors are interleaved around the cylindrical surface. The advantage of this preferred embodiment over the first preferred embodiment is that this preferred embodiment leaves room within the probe for the insertion of other medical apparati.[0032]
• As noted above, within any one sensor, the coils are connected in series. This connection is grounded. The other end of each coil is connected, by one wire of a twisted pair of wires, to a different input of a differential amplifier.[0033]
• In a preferred embodiment of a cardiac catheter that incorporates a receiver of the present invention, the catheter includes an inner sleeve mounted slidably within an outer sleeve. One of the sensors includes two coils mounted within the inner sleeve, towards the distal end of the catheter. The distal end of the inner sleeve is connected to the distal end of the outer sleeve by flexible strips. Each of the other sensors includes two coils mounted on opposed lateral edges of a pair of flexible strips that flank the inner sleeve, with the inner sleeve running between the two members of the pair. When the inner sleeve is in the extended position thereof relative to the outer sleeve, the flexible strips lie flat against the inner sleeve, and the catheter can be maneuvered towards a patient's heart via the patient's blood vessels. When the end of the catheter has been introduced to the targeted chamber of the heart, the inner sleeve is withdrawn to the retracted position thereof relative to the outer sleeve, and the pairs of flexible strips form circles that are concentric with the reference point. Also mounted on the outward-facing surfaces of the flexible strips and, optionally, on the distal end of the inner sleeve, are electrodes for electrophysiologic mapping of the heart. Alternatively, the electrode on the distal end of the inner sleeve may be used for ablation of cardiac tissue, for example in the treatment of ventricular tachycardia.[0034]
• An alternative preferred embodiment of the cardiac catheter of the present invention has an inflatable balloon connecting the distal ends of the inner and outer sleeves. The coils of the external sensors are mounted on the external surface of the balloon. When the inner sleeve is in the extended position thereof relative to the outer sleeve, the balloon lies flat against the inner sleeve, and the catheter can be maneuvered towards the patient's heart via the patient's blood vessels. When the end of the catheter has been introduced to the targeted chamber of the heart, the inner sleeve is withdrawn to the retracted position thereof relative to the outer sleeve, and the balloon is inflated to a sphere that is concentric with the reference point.[0035]
• Although the primary application of the receiver of the present invention is to tracking a probe by receiving externally generated electromagnetic radiation, the scope of the present invention includes receivers for similar tracking based on the reception of any externally generated vector force field, for example, a time varying isotropic elastic field.[0036]
• The algorithm of the present invention for inferring the position and orientation of the receiver with respect to the transmitter is similar to the algorithm described in co-pending Israel Patent Application 122578. The signals received by the receiver are transformed to a 3×3 matrix M. The columns of M correspond to linear combinations of the amplitudes of the transmitted fields. The rows of M correspond to the receiver sensors. A rotationally invariant 3×3 position matrix W and a 3×3 rotation matrix T are inferred noniteratively from the matrix M. The Euler angles that represent the orientation of the receiver relative to the transmitter antennas are calculated noniteratively from the elements of T, and the Cartesian coordinates of the receiver relative to the transmitter antennas are calculated from the elements of W A preliminary calibration of the system, either by explicitly measuring the signals received by the receiver sensors at a succession of positions and orientations of the receiver, or by theoretically predicting these signals at the successive positions and orientations of the receiver, is used to determine polynomial coefficients that are used in the noniterative calculation of the Euler angles and the Cartesian coordinates. In essence, the extra time associated with an iterative calculation is exchanged for the extra time associated with an initial calibration. One simplification of the algorithm of the present invention, as compared to the algorithm of IL 122578, derives from the fact that the system of the present invention is a closed loop system.[0037]
• The preferred arrangement of the transmitter antennas of the present invention is as a set of flat, substantially coplanar coils that at least partially overlap. Unlike the preferred arrangement of Acker et al., it is not necessary that every coil overlap every other coil, as long as each coil overlaps at least one other coil. The most preferred arrangement of the transmitter antennas of the present invention consists of three antennas. Two of the antennas are adjacent and define a perimeter. The third antenna partly follows the perimeter and partly overlaps the first two antennas. The elements of the first column of M are sums of field amplitudes imputed to the first two antennas. The elements of the second column of M are differences of field amplitudes imputed to the first two antennas. The elements of the third column of M are linear combinations of the field amplitudes imputed to all three antennas that correspond to differences between the field amplitudes imputed to the third antenna and the field amplitudes that would be imputed to a fourth antenna that overlaps the portion of the first two antennas not overlapped by the third antenna.[0038]
• The signals transmitted by the various antennas of the present invention have different, independent spectra. The term “spectrum”, as used herein, encompasses both the amplitude and the phase of the transmitted signal, as a function of frequency. So, for example, if one antenna transmits a signal proportional to coscot and another antenna transmits a signal proportional to sincot, the two signals are said to have independent frequency spectra because their phases differ, even though their amplitude spectra both are proportional to δ(ω). The term “independent spectra”, as used herein, means that one spectrum is not proportional to another spectrum. So, for example, if one antenna transmits a signal equal to cos ωt and another antenna transmits a signal equal to 2 cos ωt, the spectra of the two signals are not independent. Although the scope of the present invention includes independent transmitted signals that differ only in phase, and not in frequency, the examples given below are restricted to independent transmitted signals that differ in their frequency content.[0039]
• The method employed by the present invention to decouple the transmitting antennas, thereby allowing each antennas to transmit at only a single frequency different from the frequencies at which the other antennas transmit, or, alternatively, allowing two antennas to transmit at a single frequency but with a predetermined phase relationship between the two signals, is to drive the antennas with circuitry that makes each antenna appear to the fields transmitted by the other antennas as an open circuit. To accomplish this, the driving circuitry of the present invention includes active circuit elements such as differential amplifiers, unlike the driving circuitry of the prior art, which includes only passive elements such as capacitors and resistors. By “driving circuitry” is meant the circuitry that imposes a current of a desired transmission spectrum on an antenna, and not, for example, circuitry such as that described in WO 97/36143 whose function is to detect transmissions by other antennas with other spectra and generate compensatory currents.[0040]
• With respect to intrabody navigation, the scope of the present invention includes the simultaneous acquisition and display of an image of the patient and superposition on that display of a representation of a probe inside the patient, with the representation positioned and oriented with respect to the image in the same way as the probe is positioned and oriented with respect to the patient. This is accomplished by positioning and orienting the imaging device with respect to the frame of reference of the transmitter, in one of two ways. Either the transmitter antennas are attached rigidly to the imaging device, or a second receiver is attached rigidly to the imaging device and the position and orientation of the imaging device with respect to the transmitter are determined in the same way as the position and orientation of the probe with respect to the transmitter are determined. This eliminates the need for fiducial points and fiducial markers. The scope of the present invention includes both 2D and 3D images, and includes imaging modalities such as CT, MRI, ultrasound and fluoroscopy. Medical applications to which the present invention is particularly suited include transesophageal echocardiography, intravascular ultrasound and intracardial ultrasound. In the context of intrabody navigation, the term “image” as used herein refers to an image of the interior of the patient's body, and not to an image of the patient's exterior.[0041]
• Under certain circumstances, the present invention facilitates intrabody navigation even if the image is acquired before the probe is navigated through the patient's body with reference to the image. A third receiver is attached rigidly to the limb of the patient to which the medical procedure is to be applied. During image acquisition, the position and orientation of the third receiver with respect to the imaging device is determined as described above. This determines the position and orientation of the limb with respect to the image. Subsequently, while the probe is being moved through the limb, the position and orientation of the probe with respect to the limb is determined using the second method described above to position and orient the probe with respect to the imaging device during simultaneous imaging and navigation. Given the position and orientation of the probe with respect to the limb and the orientation and position of the limb with respect to the image, it is trivial to infer the position and orientation of the probe with respect to the image.[0042]
• Many imaging devices used in conjunction with the present invention include electrically conducting surfaces. One important example of such an imaging device is a fluoroscope, whose image intensifier has an electrically conducting front face. According to the present invention, the imaging device is provided with a magnetically permeable compensator to suppress distortion of the electromagnetic field near the electrically conducting surface as a consequence of eddy currents induced in the electrically conducting surface by the electromagnetic waves transmitted by the transmitting antennas of the present invention.[0043]
• The scope of the present invention includes a scheme for retrofitting an apparatus such as the receiver of the present invention to a catheter to produce an upgraded probe for investigating or treating a body cavity of a patient. A tether provides a loose mechanical connection between the apparatus and the catheter while the apparatus and the catheter are inserted into the patient. When the apparatus and the catheter reach targeted body cavity, the tether is withdrawn to pull the apparatus into a pocket on the catheter. The pocket holds the apparatus in a fixed position and orientation relative to the catheter.[0044]
BRIEF DESCRIPTION OF THE DRAWINGS
• The invention is herein described, by way of example only, with reference to the accompanying drawings, wherein:[0045]
• FIG. 1 is a schematic diagram of a system of the present invention;[0046]
• FIG. 2A is a partly cut away perspective view of a probe and a receiver;[0047]
• FIG. 2B is a circuit diagram of the receiver of FIG. 2A;[0048]
• FIG. 2C illustrates features of the receiver of FIG. 2A that suppress unwanted electromagnetic coupling;[0049]
• FIG. 3 is an axial sectional view of a probe and a receiver;[0050]
• FIG. 4A shows two coils of opposite helicities;[0051]
• FIG. 4 shows two coils of identical helicities;[0052]
• FIG. 5 shows a second preferred embodiment of a receiver;[0053]
• FIG. 6 is a plan view of three loop antennas and two phantom loop antennas;[0054]
• FIGS. 7A, 7B and[0055]7C show alternative configurations of paired adjacent loop antennas;
• FIG. 8 is a schematic block diagram of driving circuitry[0056]
• FIG. 9 shows a C-mount fluoroscope modified for real-time intrabody navigation[0057]
• FIG. 10 shows a coil of the receiver of FIG. 5;[0058]
• FIG. 11 shows a CT scanner modified for imaging in support of subsequent intracranial navigation;[0059]
• FIG. 12A is a partly cut-away perspective view of a cardiac catheter of the present invention in the retracted position thereof;[0060]
• FIG. 12B is a perspective view of the catheter of FIG. 12A in the extended position thereof;[0061]
• FIG. 12C is an end-on view of the catheter of FIG. 12[0062]ain the retracted position thereof;
• FIG. 13A is a partly cut-away side view of a second embodiment of the cardiac catheter of the present invention in the retracted and inflated position thereof;[0063]
• FIG. 13B is an end-on view of the catheter of FIG. 13A in the retracted and inflated position thereof;[0064]
• FIG. 14 is a partial perspective view of the C-mount fluoroscope of FIG. 9, including a magnetically permeable compensator;[0065]
• FIG. 15 is a partial exploded perspective view of a preferred embodiment of the probe and receiver of FIG. 2A;[0066]
• FIG. 16 illustrates a scheme for retrofitting an apparatus such as the receiver of FIG. 2A to a catheter.[0067]
DESCRIPTION OF THE PREFERRED EMBODIMENTS
• The present invention is of a system and method for tracking the position and orientation of an object relative to a fixed frame of reference. Specifically, the present invention can be used to track the motion of a medical probe such as a catheter or an endoscope within the body of a patient.[0068]
• The principles and operation of remote tracking according to the present invention may be better understood with reference to the drawings and the accompanying description.[0069]
• Referring now to the drawings, FIG. 1 illustrates, in general terms, a system of the present invention. Within a[0070]probe10 is rigidly mounted areceiver14.Receiver14 includes threefield component sensors16,18, and20, each for sensing a different component of an electromagnetic field.Sensor16 includes twosensor elements16aand16b. Sensor18 includes twosensor elements18aand18b.Sensor20 includes twosensor elements20aand20b. Typically, the sensor elements are coils, and the sensed components are independent magnetic field components.Sensor elements16aand16bare on opposite sides of, and equidistant from, acommon reference point22. Similarly,sensor elements18aand18bare on opposite sides of, and equidistant from,point22, andsensor elements20aand20balso are on opposite sides of, and equidistant from,point22. In the illustrated example,sensors16,18 and20 are disposed collinearly along alongitudinal axis12 ofprobe10, but other configurations are possible, as discussed below.
• The system of FIG. 1 also includes a[0071]transmitter24 of electromagnetic radiation.Transmitter24 includes three substantially coplanarrectangular loop antennas26,28 and30 connected to drivingcircuitry32.Loop antennas26 and28 are adjacent and are partly overlapped byloop antenna30. Drivingcircuitry32 includes appropriate signal generators and amplifiers for driving each ofloop antennas26,28 and30 at a different frequency. The electromagnetic waves generated bytransmitter24 are received byreceiver14. The signals fromreceiver14 that correspond to these electromagnetic waves are sent toreception circuitry34 that includes appropriate amplifiers and A/D converters.Reception circuitry34 and drivingcircuitry32 are controlled by a controller/processor36 that typically is an appropriately programmed personal computer. Controller/processor36 directs the generation of transmitted signals by drivingcircuitry32 and the reception of received signals byreception circuitry34. Controller/processor36 also implements the algorithm described below to infer the position and orientation ofprobe10. Note that the system of FIG. 1 is a closed-loop system: the reception of signals fromreceiver14 is synchronized with the transmission of electromagnetic waves bytransmitter24.
• FIG. 2 shows a particular, slightly modified embodiment of[0072]receiver14. FIG. 2A is a perspective, partly cut away view ofprobe10 withreceiver14 mounted in thehousing11 thereof. FIG. 2B is a circuit diagram ofreceiver14. In this embodiment,sensor elements16a,16b,18aand18bare coils of conducting wire wound onferrite cores70.Coils16aand16bare mutually parallel.Coils18aand18bare mutually parallel and are perpendicular to coils16aand16b.Coils16a,16b,18aand18ball are perpendicular toaxis12. Instead ofsensor20 with twosensor elements20aand20b, the embodiment of FIG. 2 has asingle coil20′ of conducting wire wound on aferrite core70.Coil20′ is parallel toaxis12 and therefore is perpendicular to coils16a,16b,18aand18b.Coil20′ is centered onreference point22.Sensors16,18 and20′ are connected toreception circuitry34 by twisted wire pairs38. As shown in the circuit diagram of FIG. 2B, coils16aand16bare connected in series, and coils18aand18bare connected in series.
• Because[0073]sensors16,18 and20′ of FIG. 2 all measure field components at thesame reference point22, coils16a,16b,18a,18band20′ can be wound onferrite cores70 instead of the air cores of WO 96/05768 without causing undue distortion of the received signals, despite the small transverseinterior diameter72, typically less than two millimeters, ofprobe10 whenprobe10 is a catheter.
• Wire pairs[0074]38 are twisted in order to suppress electromagnetic coupling between wire pairs38 and the environment, and in particular to suppress electromagnetic coupling between wire pairs38 andtransmitter24. FIG. 2C is a circuit diagram that shows further features of the present invention that suppress this electromagnetic coupling. FIG. 2C is drawn with particular reference tosensor16, but the same features apply, mutatis mutandis, to sensor18.
• [0075]Coils16aand16bare connected in series by inner leads116aand116bthereof. Outer lead216aofcoil16ais connected, bywire38aoftwisted wire pair38, to a positive input126aof a differential amplifier128 ofreception circuitry34.Outer lead216bofcoil16bis connected, by wire38boftwisted wire pair38, to a negative input126bof differential amplifier128. Inner leads116aand116balso are connected to ground124 by awire122. For illustrational clarity,wire38ais drawn as a solid line, wire38bis drawn as a dotted line andwire122 is drawn as a dashed line.
• FIG. 15 is a partial exploded perspective view of a preferred embodiment of[0076]probe10 andreceiver14.Housing11 is substantially cylindrical, with tworecesses511 and513 incised therein. The boundary of eachrecess511 or513 includes a pair of diametrically opposed apertures:apertures510 and512 in the boundary ofrecess511 andapertures514 and516 in the boundary ofrecess513.Arrows530 and532 show two of the three components of a cylindrical coordinate system for describing position within and alonghousing11.Arrow530 points in the longitudinal direction.Arrow532 points in the azimuthal direction.Aperture pair510,512 is displaced both longitudinally and azimuthally fromaperture pair514,516.
• [0077]Coil16ais a coil of electrically conducting wire that is wound about a core70a.Core70ais mounted inapertures514 and516: end518 ofcore70a, that extends beyondcoil16a, is mounted inaperture514 and is secured rigidly in place by a suitable glue, and end520 ofcore70a, that extends beyondcoil16ain the opposite direction, is mounted inaperture516 and is secured rigidly in place by a suitable glue. Similarly,coil18ais a coil of electrically conducting wire that is wound about a core70b.Core70bis mounted inapertures510 and512: end522 ofcore70b, that extends beyondcoil18a, is mounted inaperture510 and is secured rigidly in place by a suitable glue, and end524 ofcore70b, that extends beyondcoil18ain the opposite direction, is mounted inaperture512 and is secured rigidly in place by a suitable glue.
• FIG. 15 also shows the preferred azimuthal separation of[0078]aperture pair514,516 fromaperture pair510,512.Aperture pair514,516 is perpendicular toaperture pair510,512, in the sense thataperture pair514,516 is displaced 90°, in the direction ofarrow532, fromaperture pair510,512. This makes core70aperpendicular tocore70b, and hence makescoils16aand18amutually perpendicular.
• In the case of[0079]probe10 being a catheter for invasively probing or treating a body cavity such as a chamber of the heart, it is preferable thathousing11 be made of a nonmagnetic metal such as nitinol, titanium, iconel, phynox or stainless steel.Housing11 thus is sufficiently flexible to bend under the lateral forces of the walls of blood vessels through whichprobe10 is inserted towards the body cavity, and sufficiently resilient to return to its unstressed shape, withcoils16aand18amutually perpendicular, when the portion ofprobe10 that includesreceiver14 reaches the interior of the body cavity. Surprisingly, it has been found that the use of a conductive metal as the material ofhousing11 does not distort the electromagnetic field sensed byreceiver14 despite the current eddies induced inhousing11 by the electromagnetic waves generated bytransmitter24.Apertures510,512,514 and516 are most conveniently formed by laser cutting. The accuracy of the mutual perpendicularity ofcoils16aand18aobtained in this manner has been found to be superior to the accuracy obtained by forminghousing11 as a solid cylindrical block and drilling mutually perpendicular recesses in the block to receivecoils16aand18a.
• [0080]Coils16band18bare mounted similarly in similar pairs of diametrically opposed, azimuthally and longitudinally displaced apertures. This ensures that coils16aand16bare mutually parallel, that coils18aand18bare mutually parallel, and that coils16band18bare mutually perpendicular.
• In an alternative structure (not shown) of[0081]housing11,housing11 is formed as an open, spring-like frame that includesapertures510,512,514 and516 in the form of small rings that are sized to accept theends518,520,522 and524 ofcores70aand70b. The spring-like nature of this embodiment ofhousing11 allowscoils16aand18ato be mounted therein simply by forcingends518,520,522 and524 into their respective apertures, and also allowshousing11 to flex during insertion towards a body cavity of a patient and to return to its unstressed shape upon arrival inside the body cavity.
• FIG. 3 is an axial sectional view of[0082]receiver14 mounted in a variant ofprobe10 that has twosections10aand10bconnected by aflexible connector40. As in FIG. 2,sensors16 and18 includesensor elements16a,16b,18aand18bthat are coils of conducting wire wound on air cores and that are perpendicular toaxis12.Sensor elements16aand16bare mutually parallel,sensor elements18aand18bare mutually parallel, andsensor elements16aand16bare perpendicular tosensor elements18aand18b.Sensor20 includes two sensor elements: coils20aand20bof conducting wire wound on air cores.Coils20aand20bare equidistant fromreference point22 and are parallel toaxis12. Likecoils16aand16band likecoils18aand18b, coils20aand20bare connected in series.Flexible connector40 allows this variant ofprobe10 to bend as this variant ofprobe10 is moved within a medical patient. Sensor element pairs16,18 and20 are disposed symmetrically with respect toreference point22 in the sense that whenprobe10 of FIG. 3 is straight, as drawn,sensor elements16aand16bare on opposite sides of, and equidistant from,reference point22; and likewisesensor elements18aand18bare on opposite sides of, and are equidistant from,reference point22; andsensor elements20aand20bare on opposite sides of, and are equidistant from,reference point22. Note that whenprobe10 of FIG. 3 is straight,sensor elements16a,16b,18a,18b,20aand20ball are collinear, alongaxis12 that intersectspoint22, and so are disposed symmetrically with respect topoint22.
• For coil pairs such as[0083]pairs16aand16bto produce signals representative of a magnetic field component atpoint22 when the coil pairs are connected as shown in FIG. 2A, the two coils must have opposite helicity, as illustrated in FIG. 4A, so that, in a spatially uniform time varying magnetic field, the signals induced in the two coil pairs16aand16breinforce each other instead of canceling each other. Coil pairs16aand16bthat have identical helicities, as illustrated in FIG. 4B, may be used to measure a magnetic field component gradient atpoint22. Alternatively, coil pairs of identical helicities may be used to measure magnetic field components if the top of one coil is connected to the bottom of the other coil.
• FIG. 5 illustrates a second class of preferred embodiments of[0084]receiver14. In FIG. 5, a conceptual cylindrical surface is denoted by dashedlines42 and dashed circles44. The embodiment ofreceiver14 illustrated in FIG. 5 includes threesensors16,18 and20, each with twosensor elements16cand16d,18cand18d, and20cand20d, respectively. Each sensor element is a flat rectangular coil, of many turns of conducting wire, that is bent into an arcuate shape to conform to the shape of the cylindrical surface.Sensor elements16c,18cand20care interleaved aroundcircle44a.Sensor elements16d,18dand20dare interleaved aroundcircle44b.Sensor elements16cand16dare disposed symmetrically with respect toreference point22, meaning thatsensor elements16cand16dare on opposite sides ofreference point22, are equidistant fromreference point22, and are oriented so that an appropriate 180° rotation aboutpoint22maps sensor16cintosensor16d. Similarly,sensor elements18cand18dare disposed symmetrically with respect toreference point22, andsensor elements20eand20dare disposed symmetrically with respect toreference point22.Sensor elements16cand16dare connected in series, in a manner similar tosensor elements16aand16b, to respond to one component of the magnetic field.Sensor elements18cand18dare connected similarly in series to respond to a second component of the magnetic field that is independent of the first component, andsensor elements20cand20dare connected similarly in series to respond to a third component of the magnetic field that is independent of the first two components. Most preferably,sensor elements16c,16d,18c,18d,20cand20dare sized and separated so that these three magnetic field components are orthogonal. In practice, the cylindrical surface whereaboutsensor elements16c,16d,18c,18d,20cand20dare disposed could be the inner surface ofprobe10 or the outer surface of a cylindrical sleeve adapted to fit insideprobe10. In the case of this embodiment ofreceiver14 formed on the outer surface of a cylindrical sleeve,sensor elements16c,16d,18c,18d,20cand20dmay be fabricated by any one of several standard methods, including photolithography and laser trimming. FIG. 10 illustrates the preferred geometry ofsensor elements16c,16d,18c,18d,20cand20d: a flatrectangular spiral17 of anelectrical conductor19. Only four turns are shown inspiral17, for illustrational simplicity. Preferably, however, there are several hundred turns inspiral17. For example, aspiral17, intended for a cylindrical surface of a diameter of 1.6 millimeters, in whichconductor19 has a width of 0.25 microns, and in which the windings are separated by gaps of 0.25 microns, has167 turns.
• FIGS. 12A, 12B and[0085]12C illustrate the distal end of acardiac catheter300 of the present invention. FIG. 12A is a partly cut-away perspective view ofcatheter300 in the retracted position thereof. FIG. 12B is a perspective view ofcatheter300 in the extended position thereof. FIG. 12C is an end-on view ofcatheter300 in the retracted position thereof.Catheter300 includes a flexible cylindricalinner sleeve302 slidably mounted in a flexible cylindricalouter sleeve304. Connectingdistal end306 ofinner sleeve302 todistal end308 ofouter sleeve304 are four flexible rectangular strips310. Wheninner sleeve302 is in the extended position thereof relative toouter sleeve304, strips310 are flush againstinner sleeve302, as shown in FIG. 12B. Wheninner sleeve302 is in the retracted position thereof relative toouter sleeve304, strips310 bow outward in circular arcs, as shown in FIG. 12A.
• [0086]Catheter300 includes a set of three orthogonal electromagnetic field component sensors316,318 and320, in the manner ofreceiver14 of FIG. 1. First sensor316 includescoils316aand316bmounted on oppositelateral edges312aand314aofstrip310aand on oppositelateral edges312cand314cofstrip310c.Coil316ais mounted onlateral edges312aand312c.Coil316bis mounted onlateral edges314aand314b. Second sensor318 includescoils318aand318bmounted on oppositelateral edges312band314bofstrip310band on oppositelateral edges312dand314dofstrip310d.Coil318ais mounted onlateral edges312band312d.Coil318bis mounted onlateral edges314band314d. Third sensor320 includescoils320aand320b.Inner sleeve302 is cut away in FIG. 12A to showcoils320aand320b. For illustrational clarity, the wires ofcoils316aand318aare shown in FIGS. 12A and 12B as dashed lines, and only two turns are shown for each coil, although in practice at least nine turns of 45-micron-diameter copper wire are used. Note that the wires ofcoil316arun throughinner sleeve302, fromlateral edge312atolateral edge312c, and do not terminate at the intersection oflateral edges312aand312cwithinner sleeve302. Similarly, the wires ofcoil318ado not terminate at the intersection oflateral edges312band312dwithinner sleeve302, but instead run fromlateral edge312btolateral edge312d. Also for illustrational clarity, lateral edges312 are shown much wider than they really are in preferred embodiments ofcatheter300.Coils320aand320bare wound around a permeable core (not shown).
• In a typical embodiment of[0087]catheter300, the length ofinner sleeve302 exceeds the length ofouter sleeve304 by 15.7 mm in the extended position. Also in a typical embodiment ofcatheter300, each ofcoils320aand320bis about 1.1 mm long and about 1.1 mm in diameter and includes about400 turns of 10 micron diameter copper wire.
• [0088]Coils320aand320bare parallel and equidistant from acentral point322. Whencatheter300 is opened to the retracted position thereof, as shown in FIGS. 12A and 12C, the circular arcs formed by strips310 are concentric withpoint322. This makes coils316a,316b,318aand318bcircular and concentric withpoint322, withcoils316aand316bbeing mutually parallel, and withcoils318aand318bbeing mutually parallel, so thatpoint322 then becomes the reference point for electromagnetic field measurements.
• In the extended position thereof,[0089]catheter300 is thin enough, preferably less than about 2 mm in diameter, to be inserted via the blood vessels of a patient into the patient's heart. Once the distal end ofcatheter300 is inside the desired chamber of the patient's heart,inner sleeve302 is withdrawn relative toouter sleeve304 to putcatheter300 in the retracted position thereof. Sensors316,318 and320 are used in conjunction withtransmitter24 in the manner described below to determine the location and orientation of the distal end ofcatheter300 within the patient's heart.
• Mounted on outward faces[0090]324 of strips310 are fourelectrodes326. Mounted ondistal end306 ofinner sleeve302 is anelectrode328.Electrodes326 and328 may be used for electrophysiologic mapping of the patient's heart. Alternatively, high RF power levels may be applied to selected heart tissue viaelectrode328 to ablate that tissue in the treatment of conditions such as ventricular tachycardia.
• FIGS. 13A and 13B illustrate the distal end of an[0091]alternative embodiment400 of the cardiac catheter of the present invention. FIG. 13A is a partly cut-away side view ofcatheter400 in the retracted position thereof. FIG. 13B is an end-on view ofcatheter400 in the retracted position thereof. Likecatheter300,catheter400 includes a flexible cylindricalinner sleeve402 slidably mounted in a flexible cylindricalouter sleeve404. Connectingdistal end406 ofinner sleeve402 todistal end408 ofouter sleeve404 is a single flexible member: aninflatable latex balloon410. Wheninner sleeve402 is in the extended position thereof relative toouter sleeve404,balloon410 is flush againstinner sleeve402. After the illustrated distal end ofcatheter400 has been introduced to the targeted chamber of a patient's heart,inner sleeve402 is withdrawn to the retracted position thereof, andballoon410 is inflated to assume a spherical shape.
• Like[0092]catheter300,catheter400 includes a set of three orthogonal electromagnetic field component sensors416,418 and420, in the manner ofreceiver14 of FIG. 1. First sensor416 includesparallel coils416aand416bmounted as shown onouter surface412 ofballoon410. Second sensor418 includesparallel coils418aand418bmounted orthogonally tocoils416aand416bonouter surface412, as shown. Third sensor420 includes coils420aand420b.Balloon410 andinner sleeve402 are cut away in FIG. 13A to show coils420aand420b. Coils420aand420bare parallel and equidistant from acentral point422. Whencatheter400 is opened to the retracted position thereof andballoon410 is inflated to a spherical shape,outer surface412 is a sphere concentric withpoint422. This makes coils416a,416b,418aand418bcircular and concentric withpoint422, so thatpoint422 then becomes the reference point for electromagnetic field measurements.
• Also as in the case of[0093]catheter300,catheter400 includes fourelectrodes426, similar toelectrodes326, mounted onouter surface412, and anelectrode428, similar toelectrode328, mounted ondistal end406 ofinner sleeve402.
• FIG. 6 is a plan view of[0094]loop antennas26,28 and30.Loop antenna26 is a rectangle withlegs26a,26b,26cand26d.Loop antenna28 is a rectangle of the same shape and size asloop antenna26, and withlegs28a,28b,28cand28d.Legs26band28dare adjacent.Loop antenna30 also is rectangular, withlegs30a,30b,30cand30d.Leg30aoverlies legs26aand28a;leg30boverlies the upper half ofleg28b; andleg30doverlies the upper half ofleg26d, so thatloop antenna30 overlaps half ofloop antenna26 and half ofloop antenna28. Also shown in phantom in FIG. 6 is a fourthrectangular loop antenna46 and a fifthrectangular loop antenna48 that are not part oftransmitter24 but are referred to in the explanation below.Loop antenna46 is of the same shape and size asloop antenna30, and overlaps the halves ofloop antennas26 and28 that are not overlapped byloop antenna30.Loop antenna48 matches the outer perimeter defined byloop antennas26 and28.
• To understand the preferred mode of the operation of the system of the present invention, it is helpful to consider first a less preferred mode, based on time domain multiplexing, of operating a similar system that includes all five loop antennas of FIG. 6. In this less preferred mode,[0095]loop antenna48 is energized using a sinusoidal current of angular frequency ω₁. Then,loop antennas26 and28 are energized by oppositely directed sinusoidal currents of angular frequency ω₁. Finally,loop antennas30 and46 are energized by oppositely directed sinusoidal currents of angular frequency ω₁. The idea of this energization sequence is to produce, first, a field above the transmitter that is spatially symmetric in both the horizontal and the vertical direction as seen in FIG. 6, then a field above the transmitter that is antisymmetric in the horizontal direction and symmetric in the vertical direction, and finally a field that is symmetric in the horizontal direction and antisymmetric in the vertical direction. These three fields are linearly independent, and all three fields have significant amplitude all the way across the transmitter. The signals output by the three sensors ofreceiver14 in response to the electromagnetic waves so generated are sampled at times t_mbyreception circuitry34. The sampled signals are:
• s[0096]⁰_im=c⁰_i,1cos ω₁t_m+c⁰_i,2sin ω₁t_mfromloop antenna48
• s[0097]^h_im=c^h_i,1cos ω₁t_m+c^h_i,2sin ω₁t_mfromloop antennas26 and28
• s[0098]^v_im=c^v_i,1cos ω₁t_m+c^v_i,2sin ω₁t_mfromloop antennas30 and46
• where i indexes the sensor that receives the corresponding signal. Coefficients c[0099]⁰_i,1, c^h_i,1and c^v_i,1are the in-phase amplitudes of the received signals. Coefficients c⁰_i,2, c^h_i,2and c^v_i,2are the quadrature amplitudes of the received signals. Because ω₁is sufficiently low thatreceiver14 is in the near fields generated by the loop antennas, in principle the quadrature amplitudes should be identically zero. Because of inevitable phase distortions, for example inreception circuitry34, the quadrature amplitudes generally are not zero.
• Note that amplitudes c[0100]⁰_i,j, c^h_i,jand c^v_i,1(j=1,2)could be obtained by usingonly loop antennas26,28 and30. The sampled signals obtained by energizingloop antennas26,28 and30 separately with identical sinusoidal currents of angular frequency ω₁are:
• s[0101]¹_im=c¹_icos ω₁t_m+c²_isin ω₁t_mfromloop antenna26
• s[0102]²_im=c³_icos ω₁t_m+c⁴_isin ω₁t_mfromloop antenna28
• s[0103]³_im=c⁵_icos ω₁t_m+c⁶_isin ω₁t_mfromloop antenna30
• the coefficients c[0104]¹_i, c³_iand c⁵_ibeing in-phase amplitudes and the coefficients c²_i, c⁴_iand c⁶_ibeing quadrature amplitudes. Because the field radiated byloop antennas26 and28 when identical currents J flow therein is the same as the field generated byloop antenna48 when current J flows therein,
• c⁰_i,1=c¹_i+c³_i  (1)
• c⁰_i,2=c²_i+c⁴_i  (2)
• By definition,[0105]
• c^h_i,1=c¹_i−c³_i  (3)
• c^h_i,2=c²_i−c⁴_i  (4)
• Finally, the fact that the field radiated by[0106]loop antenna48 could also be emulated by identical currents flowing throughloops30 and46 gives
• c^v_i,1=2c⁵_i−c¹_i−c³_i  (5)
• c^v_i,1=2c⁶_i−c²_i−c⁴_i  (6)
• In the preferred mode of the operation of the system of the present invention,[0107]loop antennas26,28 and30 are energized simultaneously with sinusoidal currents of angular frequencies ω₁, ω₂and ω₃, respectively. The sampled signals now are
• s_im=c_i1cos ω₁t_m+c_i2sin ω₁t_m+c_i3cos ω₂t_m+c_i4sin ω₂t_m+c_i5cos ω₃t_m+c_i6sin ω₃t_m  (7)
• Note that now, amplitudes c[0108]_i1and c_i2refer to frequency ω₁, amplitudes ω_i3and c_i4refer to frequency ω₂, and amplitudes c_i5and c_i6refer to frequency ω₃. The sampled signals are organized in a matrix s of three rows, one row for each sensor ofreceiver14, and as many columns as there are times t_m, one column per time. Amplitudes c_ijare organized in a matrix c of three rows and six columns. The matrices s and c are related by a matrix A of six rows and as many columns as there are in matrix s:
• s=cA  (8)
• Almost always, there are many more than six columns in matrix s, making equation (8) highly overdetermined. Because the transmission frequencies and the reception times are known, matrix A is known. Equation (8) is solved by right-multiplying both sides by a right inverse of matrix A: a matrix, denoted as A[0109]⁻¹, such that AA⁻¹=I, where I is the 6×6 identity matrix. Right inverse matrix A⁻¹is not unique. A particular right inverse matrix A⁻¹may be selected by criteria that are well known in the art. For example, A⁻¹may be the right inverse of A of smallest L²norm. Alternatively, matrix c is determined as the generalized inverse of equation (8):
• c=sA^T(AA^T)⁻¹  (9)
• where the superscript “T” means “transpose”. The generalized inverse has the advantage of being an implicit least squares solution of equation (8).[0110]
• In the special case of evenly sampled times t[0111]_m, solving equation (8) is mathematically equivalent to the cross-correlation of WO 96/05768. Equation (8) allows the sampling of the signals fromreceiver14 at irregular times. Furthermore, there is no particular advantage to using frequencies ω₁, ω₂and ω₃that are integral multiples of a base frequency. Using closely spaced frequencies has the advantage of allowing the use of narrow-band filters inreception circuitry34, at the expense of the duration of the measurement having to be at least about 2π/Δω, where Δω is the smallest frequency spacing, except in the special case of two signals of the same frequency and different phases.
• Because[0112]receiver14 is in the near field oftransmitter24, coefficients c_ijof equation (7) are the same as coefficients c^j_i. It follows that equations (1)-(6) still hold, and either of two 3×3 matrices M can be formed from the elements of matrix c for further processing according to the description in co-pending Israel Patent Application 122578, an in-phase matrix$\begin{array}{cc}M=\left[\begin{array}{ccc}{c}_{1,1}^0& c_{1,1}^h& c_{1,1}^v\\ c_{2,1}^0& c_{2,1}^h& c_{2,1}^v\\ c_{3,1}^0& c_{3,1}^h& c_{3,1}^v\end{array}\right]& \left(10\right)\end{array}$

  
• or a quadrature matrix[0113]$\begin{array}{cc}M=\left[\begin{array}{ccc}{c}_{1,2}^0& c_{1,2}^h& c_{1,2}^v\\ c_{2,2}^0& c_{2,2}^h& c_{2,2}^v\\ c_{3,2}^0& c_{3,2}^h& c_{3,2}^v\end{array}\right]& \left(11\right)\end{array}$

  
• Note that because the system of the present invention is a closed-loop system, there is no sign ambiguity in M, unlike the corresponding matrix of co-pending Israel Patent Application 122578.[0114]
• Let T be the orthonormal matrix that defines the rotation of[0115]probe10 relative to the reference frame oftransmitter24. Write M in the following form:
• M=ET₀T  (12)
• where T[0116]₀is an orthogonal matrix and E is in general a nonorthogonal matrix. In general, T₀and E are functions of the position ofprobe10 relative to the reference frame oftransmitter24. Let
• W²=MM^T=ET₀TT^T₀E^T=EET  (13)
• W[0117]²is real and symmetric, and so can be written as W²=Pd²P^T=(PdP^T)², where d²is a diagonal matrix whose diagonal elements are the (real and positive) eigenvalues of W²and where P is a matrix whose columns are the corresponding eigenvectors of W². Then W=PdP^T=E also is symmetric. Substituting in equation (12) gives:
• M=PdP^TT₀T  (14)
• so that[0118]
• T=T₀^TPd⁻¹P^TM  (15)
• If T[0119]₀is known, then T, and hence the orientation ofprobe10 with respect to the reference frame oftransmitter24, can be computed using equation (15).
• For any particular configuration of the antennas of[0120]transmitter24, T₀may be determined by either of two different calibration procedures.
• In the experimental calibration procedure,[0121]probe10 is oriented so that T is a unit matrix,probe10 is moved to a succession of positions relative totransmitter24, and M is measured at each position. The equation
• T₀=Pd⁻¹P^TM  (16)
• gives T[0122]₀at each of those calibration positions.
• There are two variants of the theoretical calibration procedure, both of which exploit reciprocity to treat[0123]receiver14 as a transmitter andtransmitter24 as a receiver. The first variant exploits the principle of reciprocity. The sensor elements are modeled as point sources, including as many terms in their multipole expansions as are necessary for accuracy, and their transmitted magnetic fields in the plane oftransmitter24 are calculated at a succession of positions relative thereto, also withprobe10 oriented so that T is a unit matrix. The EMF induced in the antennas oftransmitter24 by these time-varying magnetic fields is calculated using Faraday's law. The transfer function ofreception circuitry34 then is used to compute M at each calibration position, and equation (16) gives T₀at each calibration position. In the second variant, the magnetic field generated by each antenna oftransmitter24 at the three frequencies ω₁, ω₂and ω₃is modeled using the Biot-Savart law. Note that each frequency corresponds to adifferent sensor16,18 or20. The signal received at each sensor is proportional to the projection of the magnetic field on the sensitivity direction of the sensor whenobject10 is oriented so that T is a unit matrix. This gives the corresponding column of M up to a multiplicative constant and up to a correction based on the transfer function ofreception circuitry34.
• To interpolate T[0124]₀at other positions, a functional expression for T₀is fitted to the measured values of T₀. Preferably, this functional expression is a polynomial. It has been found most preferable to express the Euler angles α, β and γ that define T₀as the following 36-term polynomials. The arguments of these polynomials are not direct functions of Cartesian coordinates x, y and z, but are combinations of certain elements of matrix Wthat resemble x, y and z, specifically, a=W₁₃/(W₁₁+W₃₃), which resembles x; b=W₂₃/(W₂₂+W₃₃), which resembles y, and c=log(1/W₃₃), which resembles z. Using a direct product notation, the 36-term polynomials can be expressed as:
• α=(a, a³, a⁵)(b, b³, b⁵)(1,c, c², c³)AZcoe  (17)
• β=(a, a³, a⁵)(1,b², b⁴, b⁶)(1,c, c²)ELcoe  (18)
• γ=(1,a², a⁴, a⁶)(b, b³, b⁵)(1,c, c²)RLcoe  (19)
• where AZcoe, ELcoe and RLcoe are 36-component vectors of the azimuth coefficients, elevation coefficients and roll coefficients that are fitted to the measured or calculated values of the Euler angles. Note that to fit these 36-component vectors, the calibration procedure must be carried out at at least 36 calibration positions. At each calibration position, W is computed from M using equation (13), and the position-like variables a, b and c are computed from W as above.[0125]
• Similarly, the Cartesian coordinates x, y and z of[0126]probe10 relative to the reference frame oftransmitter24 may be expressed as polynomials. It has been found most preferable to express x, y and z as the following 36-term polynomials:
• x=(a, a³, a⁵)(1,b, b⁴)(1,c, c², c³)Xcoe  (20)
• y=(1, a², a⁴)(b, b³, b⁵)(1,c², c³)Ycoe  (21)
• z=(1,a², a⁴)(1,b², b⁴)(1,d, d², d³)Zcoe  (22)
• where Xcoe, Ycoe and Zcoe are 36-component vectors of the x-coefficients, the y-coefficients, and the z-coefficients, respectively; and d=log(c). As in the case of the Euler angles, these position coordinate coefficients are determined by either measuring or computing M at at least 36 calibration positions and fitting the resulting values of a, b and c to the known calibration values of x, y and z. Equations (17) through (22) may be used subsequently to infer the Cartesian coordinates and Euler angles of moving and[0127]rotating probe10 noniteratively from measured values of M.
• Although the antenna configuration illustrated in FIGS. 1 and 6 is the most preferred configuration, other configurations fall within the scope of the present invention. FIGS. 7A, 7B and[0128]7C show three alternative configurations of pairedadjacent loop antennas26′ and28′. The arrows indicate the direction of current flow that emulates a single loop antenna coincident with the outer perimeter ofantennas26′ and28′. Other useful coplanar overlapping antenna configurations are described in PCT Publication No. WO 96/03188, entitled “Computerized game Board”, which is incorporated by reference for all purposes as if fully set forth herein.
• FIG. 8 is a schematic block diagram of driving[0129]circuitry32 for driving ageneric antenna25 that represents any one ofloop antennas26,28 or30. Adigital signal generator50 generates samples of a sinusoid that are converted to an analog signal by a D/A converter52. This analog signal is amplified by anamplifier54 and sent to thepositive input60 of adifferential amplifier58.Loop antenna25 is connected both to theoutput64 ofdifferential amplifier58 and to thenegative input62 ofdifferential amplifier58.Negative input62 also is grounded via aresistor66. The feedback loop thus set updrives antenna25 at the frequency of the sinusoid generated bysignal generator50, and makesantenna25 appear to be an open circuit at all other frequencies.
• Unlike the circuitry of WO 97/36143, which acts to offset the influence of one loop antenna on another, the circuitry of FIG. 8 decouples[0130]loop antenna25 from the other loop antennas. The superiority of the present invention over WO 97/36143 is evident. Consider, for example, how WO 97/36143 and the present invention correct for the mutual inductances ofloop antenna26, radiating at a frequency ω₁, andloop antenna30, radiating at a frequency ω₂. The goal is to set up the field of frequency ω₁that would be present ifonly loop antenna26, and notloop antenna30, were present, and to set up the field of frequency ω₂that would be present ifonly loop antenna30, and notloop antenna26, were present. By Faraday's and Ohm's laws, the time rate of change of the magnetic flux throughloop antenna26 is proportional to the current throughloop antenna26, and the time rate of change of the magnetic flux throughloop antenna30 is proportional to the current throughloop antenna30. In the absence ofloop antenna30,loop antenna26 sets up a certain time-varying magnetic flux of frequency ω₁across the area that would be bounded byloop antenna30 ifloop antenna30 were present. The method of WO 97/36143 forces the time rate of change of this magnetic flux throughloop antenna30 to be zero. Because the magnetic flux has no DC component, the magnetic flux itself throughloop antenna30 therefore also vanishes, which is contrary to the situation in the absence ofloop antenna30. By contrast, the present invention makesloop antenna30 appear to be an open circuit at frequency ω₁and so does not change the magnetic flux from what it would be in the absence ofloop antenna30.
• FIG. 9 shows, schematically, a C-[0131]mount fluoroscope80 modified according to the present invention for simultaneous real-time image acquisition and intrabody navigation.Fluoroscope80 includes the conventional components of a C-mount fluoroscope: anx-ray source82 and animage acquisition module84 mounted on opposite ends of a C-mount78, and a table86 whereon the patient lies.Image acquisition module84 converting x-rays that transit the patient on table86 into electronic signals representative of a 2D image of the patient. C-mount78 is pivotable about anaxis76 to allow the imaging of the patient from several angles, thereby allowing the reconstruction of a 3D image of the patient from successive 2D images. In addition, either areceiver114, similar toreceiver14, ortransmitter24, is rigidly mounted on C-mount78.Receiver114 ortransmitter24 serves to define a frame of reference that is fixed relative to C-mount78. The other components shown in FIG. 1, i.e., drivingcircuitry32,reception circuitry34, and control/processing unit36, are connected totransmitter24 and toreceiver14 inprobe10 as described above in connection with FIG. 1. In addition, signals fromreceiver114 that correspond to the electromagnetic waves generated bytransmitter24′ are sent toreception circuitry134 that is identical toreception circuitry34, and controller/processor36 directs the reception of received signals byreception circuitry134 and the acquisition of an image of the patient byimage acquisition module84 offluoroscope80.
• By determining the position and orientation of[0132]probe10 relative to the frame of reference defined bytransmitter24, controller/processor36 determines the position and orientation ofprobe10 relative to each acquired 2D image. Alternatively, the electromagnetic signals are transmitted by atransmitter24′ that is not attached to C-mount78, and controller/processor36 determines the position and orientation ofprobe10 relative to the 2D images by determining the positions and orientations ofreceivers14 and114 relative totransmitter24′. Controller/processor36 synthesizes a combined image that includes both the 3D image of the patient acquired byfluoroscope80 and anicon representing probe10 positioned and oriented with respect to the 3D image of the patient in the same way asprobe10 is positioned and oriented with respect to the interior of the patient. Controller/processor36 then displays this combined image on amonitor92.
• C-[0133]mount fluoroscope80 is illustrative rather than limitative. The scope of the present invention includes all suitable devices for acquiring 2D or 3D images of the interior of a patient, in modalities including CT, MRI and ultrasound in addition to fluoroscopy.
• Under certain circumstances, the image acquisition and the intrabody navigation may be done sequentially, rather than simultaneously. This is advantageous if the medical imaging facilities and the medical treatment facilities can not be kept in the same location. For example, the human skull is sufficiently rigid that if a receiver of the present invention is rigidly mounted on the head of a patient using an appropriate headband, then the position and orientation of the receiver is a sufficient accurate representation of the position and orientation of the patient's head to allow intracranial navigation. FIG. 11 shows a[0134]head94 of a patient inside a (cut-away)CT scanner98. As in the case offluoroscope80 of FIG. 9,receiver114 andtransmitter24 are rigidly attached toCT scanner98,transmitter24 being so attached via anarm100.CT scanner98 acquires 2D x-ray images of successive horizontal slices ofhead94. Areceiver214 is rigidly mounted onhead94 using aheadband96. As the 2D images are acquired, the position and orientation ofreceiver214 with respect to each image is determined by the methods described above for determining the position and orientation ofprobe10 with respect to the 2D images acquired byfluoroscope80. These positions and orientations are stored, along with the 2D images, in control/processing unit36. Subsequently, during medical treatment ofhead94 that requires navigation ofprobe10 throughhead94, the position and orientation ofprobe10 inhead94 is determined using signals fromreceivers14 and214 in the manner described above for positioning and orientingprobe10 with respect to C-mount78 offluoroscope80 usingreceivers14 and114. Given, now, for each 2D CT image, the position and orientation ofprobe10 with respect toreceiver214 and the position and orientation ofreceiver214 with respect to that 2D image, it is trivial to determine the position and orientation ofprobe10 with respect to that 2D image. As in the case of the simultaneous imaging and navigation depicted in FIG. 9, controller/processor36 now synthesizes a combined image that includes both the 3D image ofhead94 acquired byCT scanner98 and anicon representing probe10 positioned and oriented with respect to the 3D image ofhead94 in the same way asprobe10 is positioned and oriented with respect tohead94. Controller/processor36 then displays this combined image onmonitor92.
• As in the case of[0135]fluoroscope80,CT scanner98 is illustrative rather than limitative. The scope of the present invention includes all suitable devices for acquiring 2D or 3D images of a limb of a patient, in modalities including MRI, ultrasound and fluoroscopy in addition to CT. Note that this method of image acquisition followed by intrabody navigation allows the a centrally located imaging device to serve several medical treatment facilities.
• FIG. 14 is a partially exploded, partial perspective view of a C-[0136]mount fluoroscope80′ modified according to one aspect of the present invention. Like C-mount fluoroscope80, C-mount fluoroscope80′ includes anx-ray source84 and animage acquisition module82 at opposite ends of a C-mount78.Image acquisition module82 includes animage intensifier83, afront face85 whereof facesx-ray source84, and aCCD camera87, mounted on the end ofimage intensifier83 that is oppositefront face85, for acquiring images that are intensified byimage intensifier83.Image intensifier83 is housed in acylindrical housing91. In addition,fluoroscope80′ includes anannular compensator500 made of a magnetically permeable material such as mu-metal.
• The need for[0137]compensator500 derives from the fact thatfront face85 is electrically conductive. The electromagnetic waves generated bytransmitter24 or24′ induce eddy currents infront face85 that distort the electromagnetic field sensed byreceiver14. Placing a mass of a magnetically permeable substance such as mu-metal in the proper spatial relationship withfront face85 suppresses this distortion. This is taught, for example, in U.S. Pat. No. 5,760,335, to Gilboa, which patent is incorporated by reference for all purposes as if fully set forth herein, in the context of shielding a CRT from external radiation without perturbing the electromagnetic field external to the CRT.
• Preferably,[0138]compensator500 is a ring, 5 cm in axial length, of mu metal foil 0.5 mm thick.Compensator500 is slidably mounted on theexternal surface89 ofcylindrical housing91, as indicated by double-headedarrows504, and is held in place by friction. It is straightforward for one ordinarily skilled in the art to select a position ofcompensator500 onhousing91 that provides the optimal suppression of distortions of the electromagnetic field outsideimage intensifier83 due to eddy currents infront face85.
• It often is desirable to retrofit a new apparatus such as[0139]receiver14 to an existing catheter rather than to design anew probe10 that includes both the new apparatus and the functionality of an already existing probe. This retrofit capability is particularly important ifprobe10 would have been used for medical applications, and both the apparatus and the existing probe had already been approved for medical applications by the relevant regulatory bodies. Such a retrofit capability then would preclude the need to obtain regulatory approval for the new probe, a process that often is both expensive and time-consuming.
• FIG. 16 illustrates just such a retrofit capability, for adapting a[0140]satellite550 to a substantiallycylindrical catheter552 for invasively probing or treating a body cavity such as a chamber of the heart.Satellite550 is an instrumentation capsule that may containreceiver14 or any other medically useful apparatus. For example,satellite550 may contain an apparatus for ablating cardiac tissue. A catheter such ascatheter552 is introduced to the body cavity of a patient via the patient's blood vessels, via an introducer sheath. It is important that the external diameter of the introducer sheath be minimized, to reduce the risk of bleeding by the patient. Consequently, the external diameter ofcatheter552 also must be minimized, and any scheme for retrofittingsatellite550 tocatheter552 must allowsatellite550 to be introduced into the introducer sheath along withcatheter552. It is the latter requirement that generally precludes simply attachingsatellite550 tocatheter552. In addition, ifsatellite550 includesreceiver14, with the intention of usingreceiver14 to track the position and orientation ofcatheter550, then, whensatellite550 andcatheter552 are deployed within the body cavity,satellite550 must have a fixed position and orientation relative tocatheter552.
• The retrofitting scheme of FIG. 16 achieves these ends by providing[0141]satellite550 andcatheter552 with a mechanism for providing only a loose mechanical connection betweensatellite550 andcatheter552 assatellite550 andcatheter552 are introduced to the body cavity, and only then securingsatellite550 tocatheter552 at a fixed position and orientation relative tocatheter552. FIG. 16A shows a thinflexible tether554 attached toproximal end556 ofsatellite550. Tether554 provides a mechanical link to the outside of the patient. Depending on the instrumentation installed intether554,tether554 may also provide a communications link to the outside of the patient. For example, ifsatellite550 includesreceiver14, then extensions of wire pairs38 are included intether554. Rigidly attached to tether554 is a hollowcylindrical sleeve558 whose inner diameter is the same as the outer diameter ofcatheter552.
• The remainder of the mechanism for reversibly securing[0142]satellite550 tocatheter552 is shown in FIG. 16B.Catheter552 is provided, neardistal end564 thereof, with apocket560 made of a flexible, resilient, elastic material.Pocket560 is attached rigidly to the outer surface ofcatheter552.Pocket560 includes anaperture562, which isadjacent catheter552 at the proximal end ofcatheter552, and which accommodatestether554.Pocket560 is sized to accommodatesatellite550 snugly therein via an opening indistal end566 ofpocket560.
• [0143]Satellite550,catheter552 and the associated securing mechanism are assembled as shown in FIG. 16C, withtether554 running throughaperture562,sleeve558 encirclingcatheter552 proximal ofpocket560, andsatellite550 distal ofpocket560.Catheter552 andtether554 are shown emerging from the distal end of aprotective jacket568. Preferably,sleeve558 is made of a low-friction material such as Teflon™, to allowsleeve558 to slide freely alongcatheter552. The assembly shown in FIG. 16C is introduced to the introducer sheath withsatellite550 in front ofcatheter552. During this introduction,pocket560 is compressed against the outer surface ofcatheter552 by the introducer sheath. Tether554 is sufficiently flexible to bend along withcatheter552 andjacket568 as the assembly shown in FIG. 16C passes through the patient's blood vessels, but is sufficiently rigid to pushsatellite550 ahead ofdistal end564 ofcatheter552 ascatheter552 is inserted into the patient. As a result,satellite550 anddistal end564 ofcatheter552 reach interior of the targeted body cavity in the configuration illustrated in FIG. 16C. At this point,pocket560 opens, andtether554 is pulled to withdrawsatellite550 intopocket560 via the opening indistal end566 ofpocket560.Satellite550 andtether554 now are held bypocket560,sleeve558 andjacket568 in a fixed position and orientation relative tocatheter552, as illustrated in FIG. 16D.
• Subsequent to treatment,[0144]tether554 is pushed to restore the configuration shown in FIG. 16C, to allowcatheter552 andsatellite550 to be withdrawn from the patient.
• While the invention has been described with respect to a limited number of embodiments, it will be appreciated that many variations, modifications and other applications of the invention may be made.[0145]

Claims (4)

What is claimed is:

1. An imaging device, comprising:

(a) an electrically conducting surface;

(b) a magnetically permeable compensator; and

(c) a mechanism for securing said compensator relative to said surface so as to substantially suppress a distortion of an external electromagnetic field caused by said surface.

2. The imaging device of

claim 1

, wherein said compensator includes mu-metal.

3. The imaging device of

claim 1

, wherein said mechanism is integral with said compensator.

4. The imaging device of

claim 3

, further comprising:

(d) a substantially cylindrical housing having an outer surface, said electrically conducting surface being positioned at one end of said housing;

and wherein said compensator is annular, slidably mounted on said outer surface and frictionally secured to said housing.

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